Patent Publication Number: US-2021178389-A1

Title: Fluid transfer devices with integrated flow-based assay and methods of using the same

Description:
CROSS-REFERENCE TO RELATED APPLICATIONS 
     This application claims priority to and the benefit of U.S. Provisional Patent Application Ser. No. 62/946,680, filed Dec. 11, 2019, entitled “Fluid Transfer Devices with Integrated Flow-Based Assay and Methods of Using the Same,” the disclosure of which is incorporated herein by reference in its entirety. 
    
    
     BACKGROUND 
     Embodiments described herein relate generally to the procurement of bodily fluid samples and point of care diagnostic testing, and more particularly to bodily fluid transfer devices with an integrated flow-based assay system such as, for example, a lateral flow assay allowing for initial point of care diagnostic testing. 
     Health care practitioners routinely perform various types of microbial as well as other broad diagnostic tests on patients using parenterally obtained bodily fluids. In some instances, effective treatment of some serious patient conditions can be time dependent with delays in treatment potentially resulting in increased risk of morbidity and/or mortality. For example, sepsis is a serious patient condition that generally results from a bacterial infection (or less commonly a fungal or viral infection). Sepsis is an unusual systemic reaction to what otherwise can be ordinary infection, and likely represents a pattern of response by the immune system to injury. A hyper-inflammatory response is generally followed by an immunosuppressive phase during which multiple organ dysfunction is present and the patient is susceptible to nosocomial infection. Septic patients usually present with malaise, fever, chills, and leukocytosis, which may prompt doctors to evaluate such patients for the presence of bacteria in the bloodstream—typically via bacterial culture testing. 
     As bacterial culture testing and/or other advanced diagnostic technologies evolve and improve, the speed, accuracy (both sensitivity and specificity), and value of information that can be provided to clinicians continues to improve. Examples of such diagnostic technologies can include, for example, microbial detection, molecular diagnostics, genetic sequencing (e.g., deoxyribonucleic acid (DNA), ribonucleic acid (RNA), next-generation sequencing (NGS), etc.), biomarker identification, and/or the like. Some known culturing methods and/or other diagnostic technologies can be prone to contamination, which can produce results that are inaccurate, distorted, adulterated, falsely positive, falsely negative, and/or otherwise not representative of the actual condition (or in vivo condition) of the patient. In turn, these results can lead to faulty, inaccurate, confused, unsure, low confidence, and/or otherwise undesired clinical decision-making. In some instances, contamination can result from the presence of biological matter—including cells external to the intended sample source and/or other external contaminants—that inadvertently are included in the bodily fluid sample being analyzed. Some known devices and/or systems can be used to reduce the likelihood of contamination and/or adulteration of bodily fluid samples used for testing, which can reduce a likelihood of inaccurate or false diagnostic test results and lead to better patient outcomes. For example, some known devices can be designed to divert and sequester an initial volume of bodily fluid, which is more likely to contain contaminants. 
     While such diagnostic technologies are capable of providing highly sensitive and/or specific information from tests of clean or unadulterated bodily fluid, the tests often can take between 6 hours to about 5 days or more to yield results. Moreover, known diagnostic technologies are often performed using systems that require highly trained personnel and/or often employ specifically tailored culture protocols for identification of various bacterial species. Such culture methods and/or diagnostic technologies are therefore not suitable for rapid diagnosis and/or efficient screening that may be necessary to treat certain rapidly advancing illnesses. For example, sepsis can rapidly progress to multiple organ dysfunction and/or death, which may prompt doctors to prescribe treatments (e.g., antibiotics) before receiving the results of the diagnostic testing. 
     Accordingly, a need exists for rapid testing of bodily fluids such as, for example, point of care diagnostic testing using lateral flow assays or other rapid diagnostic technologies. In addition, a need exists for integrating rapid testing (e.g., lateral flow assays) into devices, which can be used to procure additional bodily fluid samples from the patient such as, for example, devices configured to procure bodily fluid samples with reduced contamination. 
     SUMMARY 
     Embodiments and methods described herein relate to bodily fluid transfer devices with an integrated flow-based assay (e.g., a lateral flow assay) allowing for initial point of care diagnostic testing. In some embodiments, a system includes a flow-based assay device and a fluid transfer device. The fluid transfer device has an inlet configured to be placed in fluid communication with a bodily fluid source and an outlet configured to be placed in fluid communication with a sample reservoir. The fluid transfer device includes a sequestration chamber and a port in selective communication with the sequestration chamber. The sequestration chamber is configured to be placed in fluid communication with the inlet to receive a first volume of bodily fluid when the fluid transfer device is in a first state. The outlet is configured to be placed in fluid communication with the inlet to receive a second volume of bodily fluid when the fluid transfer device is in a second state. The flow-based assay device is configured to be coupled to the port to receive a portion of the first volume of bodily fluid when the fluid transfer device is in a third state. The flow-based assay device is configured to provide an indication associated with the presence of a target analyte in the portion of the first volume of bodily fluid. 
    
    
     
       BRIEF DESCRIPTION OF THE DRAWINGS 
         FIG. 1  is a schematic illustration of a fluid transfer and assay system according to an embodiment. 
         FIG. 2  is a schematic illustration of a lateral flow assay device according to an embodiment. 
         FIG. 3  is a schematic illustration of a fluid transfer and assay system according to an embodiment. 
         FIG. 4  is a schematic illustration of a fluid transfer and assay system according to an embodiment. 
         FIGS. 5A and 5B  are schematic illustrations of a fluid transfer and assay system in a first state and a second state, respectively, according to an embodiment. 
         FIGS. 6A-6D  are schematic illustrations of at least a portion of a fluid transfer and assay system in a first, a second, a third, and a fourth state, respectively, according to an embodiment. 
         FIGS. 7A-7D  are schematic illustrations of at least a portion of a fluid transfer and assay system in a first, a second, a third, and a fourth state, respectively, according to an embodiment. 
         FIG. 8  is a perspective view of a fluid transfer and assay device (or system) according to an embodiment. 
         FIGS. 9A-9D  are cross-sectional views of the fluid transfer and assay device (or system) of  FIG. 12 , shown in a first, a second, a third, and a fourth state, respectively. 
         FIG. 10  is a perspective view of a fluid transfer and assay device (or system) according to an embodiment. 
         FIG. 11  is a side view of the fluid transfer and assay device (or system) of  FIG. 10 , with a housing of the device being partially transparent to illustrate internal features of the device. 
         FIGS. 12A and 12B  are side views of the fluid transfer and assay device (or system) of  FIG. 11  in a first state. 
         FIG. 12C  is a side view of the fluid transfer and assay device (or system) of  FIG. 11  in a second state. 
         FIG. 12D  is side perspective view of the fluid transfer and assay device (or system) of  FIG. 11  in a third state. 
         FIGS. 13-16  are various views of a fluid transfer and assay device (or system) according to an embodiment. 
         FIGS. 17-20  are various views of a fluid transfer and assay device (or system), each according to a different embodiment. 
     
    
    
     DETAILED DESCRIPTION 
     Any of the fluid transfer devices described herein can be configured to receive, procure, and/or transfer a flow, bolus, volume, etc., of bodily fluid. In addition, any of the fluid transfer devices described herein can include an integrated device for performing one or more rapid diagnostic tests on at least a portion of the bodily fluid procured by the fluid transfer device. In some embodiments, the fluid transfer device can be a syringe, a transfer adapter, and/or any other device configured to receive a flow of bodily fluid. In some embodiments, the fluid transfer device can be a fluid diversion and/or sequestration device configured to receive and sequester an initial volume of bodily fluid from subsequent sample volumes used, for example, in culture testing and/or the like. In such embodiments, the integrated device for rapid diagnostic testing can be configured to receive at least a portion of the initial volume of bodily fluid or at least a portion of the subsequent sample volumes. The integrated device for rapid diagnostic testing can be, for example, a lateral flow assay and/or any other suitable diagnostic testing device. The integrated device for rapid diagnostic testing can be used to test the volume of bodily fluid and to provide at least qualitative results, which in turn, can be output on or by the device for visual inspection. In other instances, the testing device can communicate data associated with the results to an electronic device (e.g., via a wired or wireless network), which can then perform any suitable analysis on the data and can, for example, graphically represent at least some of the data on a display of the device (e.g., the qualitative or quantitative test results). 
     In some implementations, a rapid diagnostic testing device can be included or integrated into a fluid transfer device (e.g., a sample collection device) and used to provide initial test results of a procured bodily fluid. The initial test results can be supplemented with additional tests of the procured bodily fluid such as culture testing. For example, the integrated rapid diagnostic testing device (also referred to herein as “rapid testing device” or “initial testing device”) can provide a way for performing relatively fast testing of bodily fluid for the presence of microbes (e.g., Gram-Positive bacteria, Gram-Negative bacteria, fungi, or viruses) or other types of biological matter (e.g., specific types of cells, biomarkers, proteins, antigens, enzymes, blood components, etc.), which can inform clinician decision making regarding treatment strategies. In some implementations, the initial testing device can test for bacteria and/or other infections that can lead to and/or otherwise result in sepsis, thereby allowing the clinician to provide rapid treatment such as broad spectrum antibiotics. Moreover, the fluid transfer devices described herein can procure additional sample volumes that can be used for more sensitive testing such as culture testing or other technologies such as molecular polymerase chain reaction (PCR), magnetic resonance and other magnetic analytical platforms, automated microscopy, spatial clone isolation, flow cytometry, whole blood (“culture free”) specimen analysis (e.g., NGS) and associated technologies, morphokinetic cellular analysis, and/or other common, advanced, or evolving technologies used to characterize patient specimens and/or to detect, identify, type, categorize, and/or characterize specific organisms, antibiotic susceptibilities, and/or the like. 
     In some embodiments, a system includes a flow-based assay device and a fluid transfer device. The fluid transfer device has an inlet configured to be placed in fluid communication with a bodily fluid source and an outlet configured to be placed in fluid communication with a sample reservoir. The fluid transfer device includes a sequestration chamber and a port in selective communication with the sequestration chamber. The sequestration chamber is configured to be placed in fluid communication with the inlet to receive a first volume of bodily fluid when the fluid transfer device is in a first state. The outlet is configured to be placed in fluid communication with the inlet to receive a second volume of bodily fluid when the fluid transfer device is in a second state. The flow-based assay device is configured to be coupled to the port to receive a portion of the first volume of bodily fluid when the fluid transfer device is in a third state. The flow-based assay device is configured to provide an indication associated with the presence of a target analyte in the portion of the first volume of bodily fluid. 
     In some embodiments, a system includes a fluid transfer device that has an inlet configured to receive a flow of bodily fluid from a bodily fluid source, an outlet configured to be placed in fluid communication with a sample reservoir, a sequestration chamber configured to receive a first volume of bodily fluid, and a port at least temporarily in fluid communication with the sequestration chamber. The fluid transfer device is configured to transition between a first state in which the sequestration chamber is in fluid communication with the inlet to receive a first volume of bodily fluid, and a second configuration in which the outlet is in fluid communication with the inlet to receive a second volume of bodily fluid. The port of the sequestration chamber allows a flow gas to flow through the sequestration chamber as the sequestration chamber receives the first volume of bodily fluid. A flow-based assay device is configured to be coupled to the fluid transfer device in the second state. A portion of the flow-based assay device engages the port when coupled to the fluid transfer device to allow a portion of the first volume of bodily fluid to be transferred from the sequestration chamber to the flow-based assay device. The flow-based assay device is configured to provide an indication associated with the presence of a target analyte in the portion of the initial volume of the bodily fluid. 
     In some embodiments, a method includes placing an inlet of a fluid transfer device in fluid communication with a bodily fluid source, receiving a first volume of bodily fluid from the inlet and into a sequestration chamber of the fluid transfer device, with a flow controller of the fluid transfer device allowing a flow of gas, but not a flow of bodily fluid, through the flow controller to vent the sequestration chamber during the receiving. Transitioning the fluid transfer device from the first state to a second state after the first volume of bodily fluid is received in the sequestration chamber. In response to the fluid transfer device being in the second state: establishing fluid communication between the inlet and an outlet of the fluid transfer device to allow a second volume of bodily fluid to flow to a sample reservoir in fluid communication with the outlet. Conveying a portion of the first volume of bodily fluid from the sequestration chamber to a sample element of a flow-based assay device fluidically coupled, at least temporarily, to the sequestration chamber; and conveying a buffer solution to the sample element of the flow-based assay device. 
     In some embodiments, a system includes a fluid transfer device and a lateral flow assay device. The fluid transfer device includes an inlet configured to be placed in fluid communication with a bodily fluid source, an outlet configured to be placed in fluid communication with a sample reservoir, and a sequestration chamber configured to receive an initial volume of bodily fluid. The fluid transfer device configured to be transitioned between (1) a first state in which the sequestration chamber is in fluid communication with the inlet to receive the initial volume of bodily fluid, (2) a second state in which the outlet is in fluid communication with the inlet to receive a subsequent flow of bodily fluid, and (3) a third state in which the lateral flow assay device is coupled to a port in fluid communication with the sequestration chamber. The lateral flow assay device is configured to receive a portion of the initial volume of bodily fluid and to determine the presence of a target analyte in the initial volume of bodily fluid. 
     As used in this specification and/or any claims included herein, the singular forms “a,” “an,” and “the” include plural referents unless the context clearly dictates otherwise. Thus, for example, the term “a member” is intended to mean a single member or a combination of members, “a material” is intended to mean one or more materials, and/or the like. 
     As used herein, “bodily fluid” can include any fluid obtained directly or indirectly from a body of a patient. For example, “bodily fluid” includes, but is not limited to, blood, cerebrospinal fluid, urine, bile, lymph, saliva, synovial fluid, serous fluid, pleural fluid, amniotic fluid, mucus, sputum, vitreous, air, and/or the like, or any combination thereof. 
     As used herein, the words “proximal” and “distal” refer to the direction closer to and away from, respectively, a user who would place a device into contact with a patient. Thus, for example, the end of a device first touching the body of a patient would be a distal end of the device, while the opposite end of the device (e.g., the end of the device being manipulated by the user) would be a proximal end of the device. 
     As used herein, the terms “about,” “approximately,” and/or “substantially” when used in connection with stated value(s) and/or geometric structure(s) or relationship(s) is intended to convey that the value or characteristic so defined is nominally the value stated or characteristic described. In some instances, the terms “about,” “approximately,” and/or “substantially” can generally mean and/or can generally contemplate a value or characteristic stated within a desirable tolerance (e.g., plus or minus 10% of the value or characteristic stated). For example, a value of about 0.01 can include 0.009 and 0.011, a value of about 0.5 can include 0.45 and 0.55, a value of about 10 can include 9 to 11, and a value of about 100 can include 90 to 110. Similarly, a first surface may be described as being substantially parallel to a second surface when the surfaces are nominally parallel. While a value, structure, and/or relationship stated may be desirable, it should be understood that some variance may occur as a result of, for example, manufacturing tolerances or other practical considerations (such as, for example, the pressure or force applied through a portion of a device, conduit, lumen, etc.). Accordingly, the terms “about,” “approximately,” and/or “substantially” can be used herein to account for such tolerances and/or considerations. 
     As used herein, the terms “first,” “initial,” and/or “pre-sample” when used to describe a volume of bodily fluid can be used interchangeably to describe an amount, portion, or volume of bodily fluid that is collected, diverted, sequestered, tested, etc. prior to procuring a “sample” volume. A “first,” “initial,” and/or “pre-sample” volume can be a predetermined, defined, desired, and/or given amount of bodily fluid. For example, a predetermined and/or desired pre-sample volume of bodily fluid such as blood can be a drop of blood, a few drops of blood, a volume of about 0.1 milliliter (mL), about 0.2 mL, about 0.3 mL, about 0.4 mL, about 0.5 mL, about 0.6 mL, about 0.7 mL, about 0.8 mL, about 0.9 mL, about 1.0 mL, about 2.0 mL, about 3.0 mL, about 4.0 mL, about 5.0 mL, about 6.0 mL, about 7.0 mL, about 8.0 mL, about 9.0 mL, about 10.0 mL, about 20.0 mL, about 50.0 mL, and/or any volume or fraction of a volume therebetween. In other instances, a pre-sample volume can be greater than 50 mL or less than 0.1 mL. As a specific example, a predetermined and/or desired pre-sample volume can be between about 0.1 mL and about 5.0 mL. As another example, a pre-sample volume can be, for example, a volume or combined volume of any number of lumen (e.g., the lumen of a needle and/or the combined lumen that form at least a portion of a flow path from the bodily fluid source to an initial collection chamber, portion, reservoir, etc.). As yet another example, a pre-sample volume can be, for example, a volume of bodily fluid sufficient to perform initial or pre-sample testing such as, for example, rapid diagnostic testing using lateral flow assay and/or any other rapid testing device. 
     As used herein, the terms “second,” “subsequent,” and/or “sample” when used to describe a volume of bodily fluid can be used interchangeably to describe an amount, portion, or volume of bodily fluid that is collected after collecting a first, initial, and/or pre-sample volume of bodily fluid. A “second,” “subsequent,” and/or “sample” volume can be either a random volume or a predetermined or desired volume of bodily fluid collected after collecting, diverting, sequestering, and/or testing a pre-sample volume of bodily fluid. In some instances, a desired sample volume of bodily fluid can be about 10 mL to about 60 mL. In other instances, a desired sample volume of bodily fluid can be less than 10 mL or greater than 60 mL. In still other instances, a desired sample volume can be at least partially based on one or more tests, assays, analyses, and/or processes to be performed on the sample volume. 
     In some implementations, a second, subsequent, and/or sample volume of bodily fluid can be used in one or more sample or diagnostic tests such as, for example, culture testing and/or the like. In some instances, collecting a “sample” volume of bodily fluid subsequent to the collection, sequestration, isolation, and/or testing of a “pre-sample” volume of bodily fluid can result in a lower likelihood of the sample volume containing contaminants such as dermally residing microbes and/or the like. Accordingly, the sample volume of bodily fluid can be suitable for sensitive testing that may otherwise be prone to inaccurate results due to contamination. 
     The embodiments described herein and/or portions thereof can be formed or constructed of one or more biocompatible materials. In some embodiments, the biocompatible materials can be selected based on one or more properties of the constituent material such as, for example, stiffness, toughness, durometer, bioreactivity, etc. Examples of suitable biocompatible materials include metals, glasses, ceramics, or polymers. Examples of suitable metals include pharmaceutical grade stainless steel, gold, titanium, nickel, iron, platinum, tin, chromium, copper, and/or alloys thereof. A polymer material may be biodegradable or non-biodegradable. Examples of suitable biodegradable polymers include polylactides, polyglycolides, polylactide-co-glycolides (PLGA), polyanhydrides, polyorthoesters, polyetheresters, polycaprolactones, polyesteramides, poly(butyric acid), poly(valeric acid), polyurethanes, and/or blends and copolymers thereof. Examples of non-biodegradable polymers include nylons, polyesters, polycarbonates, polyacrylates, polysiloxanes (silicones), polymers of ethylene-vinyl acetates and other acyl substituted cellulose acetates, non-degradable polyurethanes, polystyrenes, polyvinyl chloride, polyvinyl fluoride, poly(vinyl imidazole), chlorosulphonate polyolefins, polyethylene oxide, and/or blends and copolymers thereof. 
     Referring now to the drawings,  FIG. 1  is a schematic illustration of a fluid transfer and assay system  100 , according to an embodiment. While various components, elements, features, and/or functions may be described below, it should be understood that they have been presented by way of example only and not limitation. Those skilled in the art will appreciate that changes may be made to the form and/or features of the fluid transfer and assay system  100  without altering the ability of the fluid transfer and assay system  100  to perform the function of procuring bodily fluid samples and providing rapid diagnostic testing methods, as described herein. 
     The fluid transfer and assay system  100  (also referred to herein as “system”) can include at least a fluid transfer device  105  and a rapid diagnostic testing device  170 . In some implementations, the system  100  can optionally include at least one electronic device  190  and/or at least one fluid collection device  195 . 
     The fluid transfer device  105  (also referred to herein as “transfer device”) can be any suitable shape, size, and/or configuration, as described herein with reference to specific embodiments. In some implementations, the transfer device  105  can be configured to withdraw bodily fluid (e.g., blood) from a patient and into the transfer device  105 . In addition, the transfer device  105  can be configured to transfer at least some of the withdrawn bodily fluid to one or more other devices, reservoirs, containers, vials, machines, tests, assays, etc., such as the rapid diagnostic testing device  170  and/or one or more of the optional fluid collection devices  195 . 
     In some embodiments, the transfer device  105  can be configured to transfer, direct, and/or divert certain amounts or volumes of the bodily fluid into (or through) one or more portions of the transfer device  105 , and subsequently transfer such amounts or volumes into one or more devices coupled to or integrated with the transfer device  105 , into one or more sample reservoirs, containers, bottles, etc., and/or the like. For example, the transfer device  105  can be configured to transfer a first portion, amount, or volume of bodily fluid into or through a first or sequestration portion of the transfer device  105  and subsequently transfer a second portion, amount, or volume (e.g., a subsequent amount) of bodily fluid into a second or sampling portion of the transfer device  105 . In some embodiments, the transfer device  105  and/or the sequestration portion of the transfer device  105  can be configured to sequester the first amount of bodily fluid (e.g., within the sequestration portion of the transfer device  105 ) from the subsequent amount of bodily fluid, as described in further detail herein with reference to specific embodiments. In some implementations, the transfer device  105  can be configured to transfer at least some of the first amount of bodily fluid (e.g., contained in the sequestration portion of the transfer device  105 ) to the rapid diagnostic testing device  170  and at least some of the second amount of bodily fluid to one or more of the optional fluid collection devices  195 . 
     The rapid diagnostic testing device  170  (also referred to herein as “rapid testing device” or simply “testing device”) can be any suitable shape, size, and/or configuration, as described herein with reference to specific embodiments. In some embodiments, the rapid testing device  170  can be removably coupled to the transfer device  105  or any suitable portion thereof (e.g., an inlet portion, an outlet portion, a sequestration portion, a sampling portion, and/or any other suitable portion). In other embodiments, the rapid testing device  170  can be integrated into the transfer device  105 . For example, the transfer device  105  and the rapid testing device  170  can be unitarily or monolithically formed and/or otherwise integrated. In still other embodiments, the transfer device  105  can include and/or can form a port, adapter, and/or receiving portion to which the rapid testing device  170  can be coupled or into which the rapid testing device  170  can be inserted to establish fluid communication therebetween. In some such embodiments, coupling the rapid testing device  170  to the transfer device  105  can be operable to transition one or more flow controllers, valves, septa, ports, seals, etc. from a closed or sealed state to an open state to allow fluid communication between the transfer device  105  and the testing device  170 . 
     In some implementations, the rapid testing device  170  can be configured to receive the first amount of bodily fluid from the transfer device  105  and to use the first amount of bodily fluid to perform one or more tests, assays, and/or diagnostic procedures. For example, the rapid testing device  170  can be a chromatographic lateral flow immunoassay that can test for any suitable analytes, biomarkers, proteins, molecules, particles, and/or the like. Chromatographic lateral flow immunoassays (referred to herein as “lateral flow assays” or “LFAs”) are typically nitrocellulose-based devices configured to detect the presence of a target analyte in a sample (e.g., a biologic sample and/or bodily fluid sample such as blood, urine, etc.). In general, an LFA includes a series of capillary beds, such as pieces of porous paper, microstructured or sintered polymer(s), and/or the like that can be disposed in desired positions and/or arrangements on a substrate to direct a flow of a sample (e.g., at least some of the first amount of bodily fluid) along a portion of the LFA. 
     LFAs can be used for a broad range of applications where it is desirable to have a relatively fast, easy to use, and low-cost way for rapid antigen detection. LFAs are typically performed with little or no sample or reagent preparation, which can allow for usable test results in as little as a few minutes (or longer if more sensitive test results are desirable). Moreover, in some implementations, an LFA can be configured to test for analytes, and/or biomarkers that are produced by the human body in response to in vivo conditions (e.g., infections such as sepsis), which in turn, can mean that such an LFA has a relatively low sensitivity to contaminants (e.g., dermally residing microbes or the like) that may be included in the first amount of bodily fluid withdrawn from a patient via the transfer device  105 . 
     Typically, two types of LFAs are used depending on a size and/or a number of binding sites on the target analyte. Specifically, competitive LFAs are generally used when testing for smaller analytes while sandwich LFAs are generally used when testing for larger analytes. For context, a home pregnancy test is a well-known sandwich lateral flow assay. In some instances, it may be desirable to use a sandwich LFA to test for antigens, analytes, and/or biomarkers associated with, for example, sepsis and/or other infectious conditions within a sample of bodily fluid such as blood. While the embodiments described herein include and/or implement a sandwich LFA, it should be understood that the embodiments are not limited thereto. For example, any of the embodiments described herein can use and/or implement a competitive LFA and/or any other suitable rapid diagnostic testing device. 
     A schematic example of a sandwich LFA  170 A is shown in  FIG. 2  for context. The sandwich LFA  170 A (referred to herein as “LFA”) includes a substrate  171  on which a sample element  172 , a conjugate element  173 , a capture element  174 , a control element  175 , and a wick  176 . The substrate  171  can be any suitable shape, size, and/or configuration. For example, the substrate  171  can be a rectangular backing card or strip of constant width and a predetermined length capable of providing sufficient surface area for accommodating the various components of the LFA  170 A. The substrate  171  can be made of a semi-rigid polymer designed to deliver uniformity and lay-flat properties. The substrate  171  can include one or more pressure sensitive adhesives configured to facilitate attaching the various components of the LFA  170 A, as further described herein. 
     As shown, the sample element  172  is generally disposed at one end of the substrate and is configured to receive a sample volume. The sample element  172  can be a pad that provides a surface to receive a sample of blood and/or other biofluids for analysis and facilitates transport of the sample to other components of the lateral flow test strip in a smooth, continuous and homogeneous manner. The sample element  172  can be any suitable shape, size, and/or configuration. The conjugate element  173  is disposed adjacent to the sample element  172  in a downstream direction. The conjugate element  173  contains a dried matrix (e.g., a salt-sugar matrix) configured to include desired bio-active particles. The bio-active particles contained in the matrix include specific antibodies and/or affinity reagents (e.g., DNA aptamers, protein binders, etc.) that have been immobilized on or in the conjugate element  173 . The antibodies and/or affinity reagents can be selected based on the target molecule (e.g., an antigen or analyte), that the LFA  170 A is configured to detect. In addition, the antibodies and/or affinity reagents are directly or indirectly conjugated to a molecule configured to allow detection. For example, the antibodies can be labeled with a colored particle (e.g., latex having a blue color, colloidal gold having a red color, and/or any other suitable particle), a fluorescent particle, a magnetic particle, an enzyme for subsequent signal generation, and/or the like. Thus, the labeled antibodies can bind to the desired antigens or analytes, thereby producing a labeled or target analyte  177  that can be detected in other portions or by other elements of the LFA  170 A. 
     The capture element  174  is disposed adjacent to and/or downstream of the conjugate element  173  and contains particles or molecules that have been immobilized in or on the capture element  174 . The particles or molecules can be configured to bind to the labeled analyte  177 , thereby capturing or immobilizing the labeled analyte  177  in or on the capture element  174 . As a concentration of the captured and/or immobilized labeled analyte  177  increases (e.g., a number of molecules within the capture element  174  increases), the optical density of the detection molecule (e.g., colored label) also increases. In this manner, the LFA  170 A is configured to present a discrete colorimetric signal line, region, or strip to indicate a presence of the target analyte in the sample volume (e.g., a positive test result). 
     The control element  175  is disposed adjacent to and/or downstream of the capture element  174 . The control element  175  contains particles or molecules that have been immobilized in or on the control element  175 . In contrast to the capture element  174 , the particles or molecules contained in the control element  175  can configured to bind to multiple different particles such as, for example, the labeled analyte  177 , the labeled bio-active particles that are not bound to an antigen, and/or the like. Accordingly, the control element  175  can be configured to bind to and/or otherwise immobilize labeled particles not otherwise immobilized in or on the capture element  174 . Thus, the control element  175  can present a colored portion or strip, which can be used to show that a reaction occurred and/or that the test was performed. For example, if a target analyte is not present in a sample volume, it may be desirable to confirm that the assay was performed properly and that the negative result (no colored strip presented on or by the capture element  174 ) is indicative of the condition of the sample volume and not a malfunction of the LFA  170 A. The wick  176  is disposed adjacent to and/or downstream of the control element  175  and is configured to absorb or wick portions of the sample that have not been immobilized in or on the capture element  174  and/or the control element  175 . 
     Assay 
     The LFA  170 A can be used to test for the presence of any suitable target analyte, biomarker, molecule, particle, etc. in a sample volume (e.g., a blood sample or any other suitable sample of bodily fluid). For example, any of the embodiments described herein can include and/or implement an LFA (e.g., the LFA  170 A) and/or any other suitable flow-based rapid diagnostic system configured to test for the presence of specific analytes or biomarkers that can provide information used to diagnose a patient condition such as, for example, sepsis. 
     For example, blood lactate can be a biomarker used in the clinical diagnosis and management of sepsis. In some instances, a host of other biomarkers can be used as an alternative to or in addition to lactate to guide clinical decision making. A non-exhaustive list of suitable biomarkers can include pro-inflammatory cytokines and/or chemokines, which are associated with the hyper-inflammatory phase of sepsis; C-reactive protein and/or procalcitonin (PCT), which are synthesized in response to infection and inflammation; biomarkers associated with the activation of neutrophil and/or monocytes; anti-inflammatory cytokines, which are associated with the immunosuppressive phase of sepsis; and/or alterations of the cell surface markers of monocytes and/or lymphocytes. In some instances, combinations of pro- and anti-inflammatory biomarkers in a multiplexed LFA can be used, for example, to identify patients who are developing severe sepsis before substantial organ dysfunction. In some instances, one or more aptamers can be synthesized to target specific pro-inflammatory biomarkers, anti-inflammatory biomarkers, and/or any other suitable biomarker such as any of those described herein. 
     Lactate 
     In some implementations, any of the embodiments described herein can be used to detect lactate biomarkers, PCT biomarkers, and/or any other suitable biomarker described herein associated with and/or otherwise used to identify sepsis. For example, in some implementations, the rapid testing device  170  can be configured to test blood lactate levels in a sample of bodily fluid (e.g., blood) using, for example, a portable blood gas analyzer. In other implementations, the rapid testing device  170  can be an LFA (e.g., the LFA  170 A) configured to test for blood (e.g., whole blood, serum, etc.) lactate biomarkers (e.g., antigens). For example, the effectiveness of using serum lactate levels in the diagnosis of sepsis is shown below in Table 1, which presents the results of a study of acute hospital mortality according to serum lactate levels in septic patients requiring vasopressors (e.g., an agent that results in blood vessel constriction). 
     
       
         
           
               
               
               
             
               
                   
                 TABLE 1 
               
             
            
               
                   
                   
               
               
                   
                 Initial Serum Lactate Level (mmol/L) 
                   
               
            
           
           
               
               
               
               
               
            
               
                 Hospital Mortality 
                 &lt;4 
                 4-8 
                 &gt;8 
                 P value 
               
               
                   
               
               
                 24-hour mortality, n (%) 
                 1 (10.0) 
                 14 (35.0) 
                 19 (52.8) 
                 0.011 
               
               
                 48-hour mortality, n (%) 
                 3 (30.0) 
                 26 (65.0) 
                 26 (72.2) 
                 0.033 
               
               
                   
               
            
           
         
       
     
     Lactic acid is the end product of anaerobic breakdown of glucose in tissues, which can dissociate into lactate, the hydroxy monocarboxylic acid anion that is the conjugate base of lactic acid arising from the deprotonation of the carboxy group. Evolution of lactate in the body takes place when the energy demand by tissues is not met by adequate aerobic respiration. Lactate can be transported in the blood to the liver, where it is converted back to glucose via the Cori cycle. However, without adequate clearance of lactate by the liver and kidney the accumulated concentration of lactate can result in lactic acidosis. Clinically, causes of acidosis can be classified as type A disorders, in which there is a decreased tissue oxygenation such as with sepsis, and type B disorders causes by certain drugs and/or toxins along with systemic disease, among others. Medical evidence suggests patients with persistently elevated levels of lactate have increased morbidity and mortality. Excess lactate in the body can also cause hemorrhage, respiratory failure, trauma, seizures, ischemia, renal issues, hepatic disease, tissue hypoxia, shock, blood loss, anemia, among others. Therefore, lactate monitoring is of prime importance to diagnose and evaluate health concerns which occur in oxygen deficit situations (i.e., situations where lactate levels in the body increase beyond the accepted values). Concentrations of lactate in the blood for healthy, unstressed individuals have been reported to be in the range of 0.1-1.0 millimolar (mM). In contrast, critically ill individuals, such as those presenting with severe sepsis or septic shock, can exhibit concentrations higher than 4 mM. 
     Lactate can exist as one of two optical isomers, L-lactate and its mirror image, D-lactate. Analytical methods used to detect and quantify lactate include High Performance Liquid Chromatography (HPLC), fluorimetry, colorimetric test, chemiluminescence, and magnetic resonance spectroscopy. Although these methods can provide accurate results, they suffer from drawbacks such as time-consuming sample preparation, use of expensive instrumentation, and the need of trained personnel. Consequently, the use of these analytical methods to detect and quantify lactate in biofluids is better suited to centralized laboratories, and their implementation as point of care diagnostic tool can be limited. 
     Detection of lactate levels in biofluids including blood and/or plasma can alternatively be achieved with the use of enzymes. These enzymes can be immobilized on a solid surface or support (e.g., biosensor) to provide reactive sites which catalyze lactate chemical reactions by stabilizing transition reaction states or decreasing the activation energy of the particular lactate chemical reactions, producing one or more species that can be monitored to correlate its evolution with the concentration of lactate. For example, L-lactate can be detected using enzymes such as L-lactate oxidase (LOD) and L-lactate dehydrogenase (LDH). LOD is a globular flavoprotein that can be obtained from a variety of bacterial sources such as  Pediococcus, Aerococcus, viridans , and  Mycobacterium . The source of LOD can have an impact on the range of pH that the enzyme can show sufficient catalytic activity, exhibiting typical ranges between 4 and 9. LOD, being a member of the flavin mononucleotide (FMN) family, employs FMN as a cofactor to catalyze the oxidation of hydroxyl acids in its reactions involving glycolate oxidase, L-lactate, monooxygenase, flavocytochrome b2, long chain α-hydroxyl acid oxidase, and L-mandelate dehydrogenase. LOD can be immobilized on a solid support and be exposed to biofluids such as blood and plasma for detecting the presence of L-lactate. LOD can catalyze the oxidation of L-lactate to pyruvate (PA) in the presence of dissolved oxygen, producing reduced LOD and hydrogen peroxide (H 2 O 2 ) as a byproduct. The hydrogen peroxide produced from lactate oxidation can be accurately quantified by a secondary chemical and/or electrochemical reaction. For example, hydrogen peroxide produced by during the oxidation of lactate in the presence of LOD enzymes can be electrochemically reduced or oxidized to generate an electrical signal that can be monitored by an electrode. The reduced LOD enzyme can be then re-oxidized in a second reaction step on the electrode, as shown in reaction scheme below: 
     
       
         
         
             
             
         
       
     
     Similar to LOD, LDH enzymes can be used to detect and quantify the presence of L-lactate in various biofluids. LDH is a quaternary protein that can be found in animals, plants, and prokaryotes. LDH is present thought tissues and is released during tissue damage. LDH enzymes include five different isozymic forms, distinguished by slight structural differences. Depending on the source, LHD enzymes are known to be stable over a relatively narrow pH range of 5-8, and more particularly, a pH range of around 7.2-7.4. LDH can also catalyze the reaction of L-lactate to pyruvate (PA) through its cofactor, Nicotinamide adenine dinucleotide (NAD), which can exist in an oxidized (NAD + ) and reduced (NADH) form. During the reaction, LHD converts L-lactate into Pyruvate (PA) and NAD +  to NADH. Detection of lactate with LDH enzyme can be then achieved by a secondary reaction, as described above with reference to the detection of L-lactate with LOD enzymes. For example, NADH can be electrochemically oxidized under the influence of an applied electrical potential generated with an electrode, with the current generated being proportional to the L-lactate concentration, as shown in reaction scheme below: 
     
       
         
         
             
             
         
       
     
     The use of enzymes to detect lactate in biofluids via lactate enzymatic oxidation relies on the conversion of lactate to one or more byproducts such as NADH and hydrogen peroxide (H 2 O 2 ) that can be accurately quantified by means of a secondary reaction, as described above. The secondary reaction frequently involves an electrochemical transformation that generates a transient electric current proportional to the amount of lactate present in the sample, carried out at the surface of an electrode (e.g., electrochemical techniques for lactate sensing). Alternatively, the byproducts of the enzymatic reactions of lactate can be quantified by photo transfer processes (e.g., electro-chemiluminescence and fluorescence techniques for lactate sensing), as further described herein. 
     Biosensors that rely on electrochemical techniques for detection of lactate (i.e., electrochemical biosensors) use enzymes immobilized onto a supporting substrate located close to or in the vicinity of an electrode surface. The performance characteristics of electrochemical biosensor can vary greatly depending on the source of the enzyme, environmental conditions including pH and temperature, the methods used to immobilize the enzyme to the biosensor, the chemical nature of the matrix or support used to immobilize the enzyme and/or the electron transfer mechanism. The enzymes can be immobilized according to different methods, and their reactivity depends on their interactions with the support, the nature of the enzymes, and the presence of adsorbed species, mediators and additives. Common enzyme immobilization techniques include physical adsorption, entrapment behind a dialysis membrane or polymeric film, covalent coupling through a cross linking agent, and incorporation within the bulk of a carbon composite matrix. 
     Challenges associated with the immobilization of enzymes include reproducibility, stability, and deactivation due to evolution and/or accumulation of inhibitors and or fouling species. For example, LOD enzymes immobilized via physical adsorption on biosensors comprising Au electrodes can exhibit stability losses of 50% after just 1 month of storage, whereas LOD enzymes immobilized in mesoporous silica using a polymer matrix of polyvinyl alcohol (PVA) can exhibit 98% of their initial activity after 9 months. As a result, the development of sensors that use LOD enzymes to detect lactate requires identifying appropriate immobilization techniques, suitable matrix support, and used and/or storage environmental conditions, such that the activity of the enzyme or shell life can be retained for long periods of time. 
     Electrochemical biosensors of lactate detection typically include an apparatus comprising two or three electrode sensing platforms. Accurate measurement of lactate often includes use of a reference electrode (commonly made of Ag/AgCl 2 ), that is kept at a close proximity of the working electrode in order to maintain a stable and known potential. The working electrode serves as a transducer, while the counter electrode establishes a path to pass the current due to the potential changes at the working electrode. Common approaches to measure the electrical signals produced during detection of lactate include cyclic voltammetry, amperometry, and potentiometry. Electrochemical biosensors can offer high sensitivity, wide linear range and rapid response. However, their use presents limitations due to complex experimental set up, passivation of the system due to fouling agents, and signal reduction and interference due to competing reactions. For example, the electrochemical quantification of hydrogen peroxide (H 2 O 2 ) produced during the enzymatic oxidation of L-lactate over LOD enzymes require high oxidation potentials, which leads to interferences caused by other electro-oxidizable species. 
     Lateral flow assays (LFA) configured to test for blood (e.g., whole blood, serum, etc.) lactate biomarkers (e.g., antigens) provide an alternate tool to facilitate and/or aid in the diagnosis of sepsis. As described above with reference to  FIG. 2 , an LFA can be performed over a strip comprising one or more components assembled over a plastic backing laminate or substrate  171 . The components of an LFA configured for quantifying lactate in blood and/or other biofluids can include at least a sample element  172  and a conjugate element  173 . 
     The sample element  172  can be a pad that provides a surface to receive a sample of blood and/or other biofluids for analysis and facilitates transport of the sample to other components of the lateral flow test strip in a smooth, continuous and homogeneous manner, as described above. The sample element  172  can be any suitable shape and/or size. In some embodiments the shape of the sample element  172  can be a rectangular strip configured to adsorb and receive a volume of a sample of blood and/or other biofluids. In other embodiments, the shape of the sample element  172  can be a rectangular strip in which one of its ends includes a region having larger dimensions than the width of the strip to facilitate pipetting a volume of the sample of blood and/or other biofluids. For example, the sample element  172  can be a rectangular strip that includes circular shaped region attached to one of the strip&#39;s end. The circular shaped region of the sample element  172  can provide a larger surface area for receiving the sample of blood and/or other biofluids via a micropipette. Alternatively, in some embodiments, the sample element  172  can include a large diameter circular shaped region with various rectangular strips stemming from the center of the circular shaped region in the radial direction. Each rectangular strip can facilitate transport of a portion of the sample of blood and/or other biofluids to other components of the lateral flow test strip for simultaneous detection of multiple biomarkers (i.e., multiplexing), and/or for replicating assays for validation purposes. 
     The sample element  172  can be disposed onto the surface of a plastic backing laminate to provide mechanical support to the LFA. In some embodiments, the sample element  172  can include an adhesive coated on one surface of the sample pad to facilitate attachment to a plastic backing laminate. The shape and dimensions of the sample element  172  can be predetermined such that the sample element can be disposed onto a plastic backing laminate. The thickness of the sample element  172  can be selected to facilitate adhesion of the sample element  172  to the plastic backing laminate while maintaining the mechanical structure of the pad. Additionally, the thickness of the sample element  172  can be selected to accommodate large volumes of blood and/or other biofluids, preventing oversaturation of the sample on the pad, and channeling to the plastic backing laminate. For example, in some embodiments, the thickness of the sample element  172  can between 0.18 mm and 0.34 mm. 
     The sample element  172  can be made of cellulose, nitrocellulose, glass fiber, and/or any other suitable material. In some embodiments, the sample element  172  can be made of a cellulose membrane and/or a chromatographic paper configured to facilitate linear flow rates of about 3 to 5 mm/min. The sample element  172  can also include one or more chemical reagents configured to pre-treat the sample prior to its transportation to other downstream components. In some embodiments, the surface of the sample element  172  can be impregnated with an aqueous buffer solution that provide an environment with controlled pH. In some embodiments, the surface of the sample element  172  can be impregnated with a buffer solution including, but not limited to phosphate-buffered saline (PBS), 2-ethanesulfonic acid (MES), tris(hydroxymethyl)aminomethane (TRIS), piperazine-N, N′-bis (PIPES), 3-morpholinopropane-1-sulfonic acid (MOPS), 2-[4-(2-hydroxyethyl)piperazin-1-yl] ethanesulfonic acid (HEPES), [tris(hydroxymethyl)methylamino] propanesulfonic acid (TAPS), N-Cyclohexyl-2-aminoethanesulfonic acid (CHES), and/or N-cyclohexyl-3-aminopropanesulfonic acid (CAPS). 
     In some embodiments, the sample element  172  can include one or more components configured to capture and separate species present in the blood and/or other biofluid that can cause interference with the LFA assay. For example, in some embodiments, the sample element  172  can include one or more regions configured to separate red blood cells present in a blood and/or other biofluid sample. In some instances, the region(s) configured to separate blood cells can be one or more separate pads that can be disposed over the sample element  172 . In other embodiments, the blood separation region can be a pad located adjacent to the sample element  172 . In some instances, the blood separation pad can include one or more layers such as a polyester matrix and a composite matrix, designed to have asymmetric morphologies with different porosities and pore size distributions that facilitate capture of the cellular components of blood (i.e., red cells, white cells, and platelets) in the larger pores, while allowing flow of plasma downstream trough smaller size pores. 
     The conjugate element  173  of an LFA for detection and quantification of lactate from blood and/or other biofluid samples can be a pad located adjacent downstream to the sample element  172 . The conjugate element  173  can contain a dried matrix (e.g., a salt-sugar matrix) that includes bio-active species that can react with lactate and produces species that can be detected by colorimetric methods, as further described herein. The conjugate element  173  can be configured to accommodate one or more bio-active species that can be released upon contact with the moving liquid sample deposited on the upstream sample element  172 . As described above with reference to the sample element  172 , the conjugate element  173  can be a pad of any suitable shape and/or size. In some embodiments the shape of the conjugate element  173  can be a strip having a size and/or shape substantially similar to those of the sample element  172 . In some embodiments, the conjugate element  173  and the sample element  172  can be made of a single pad and can be disposed at opposite ends thereof, and optionally attached to the surface of a plastic backing laminate to provide mechanical support to the LFA. In yet another embodiment, the conjugate element  173  and the sample element  171  can be made of a single pad that includes a rectangular strip in which a first end of the strip comprises a region having a larger dimension than the width of the strip to provide an area to accommodate the bio-active species for lactate oxidation and colorimetric detection, and a second end of the strip, opposite to the first end, having a larger dimension than the width of the strip to provide an area to accommodate a volume of a sample of blood and/or other biofluids. Alternatively, in some embodiments, the conjugate element  173  can be include multiple rectangular strips that are coupled to a large diameter circular shaped region in the radial direction, with the large diameter circular shaped region being configured to accommodate the sample element  171 . In this configuration, each conjugate element  173  can facilitate detection of multiple biomarkers (i.e., multiplexing) present in a portion of the sample of blood and/or other biofluid, and/or for replicating assays for validation purposes. 
     The conjugate element  173  can include a dried matrix configured to include desired bio-active species for detection and quantification of lactate in a sample of blood and/or other biofluid. For example, in this embodiment, the matrix of the conjugate element  173  can include both a detection enzyme and a quantification enzyme. The detection enzyme can be configured to exhibit high activity and selectivity for the catalytic oxidation of lactate, producing one or more byproducts which can be monitored by means of a secondary chemical reaction to quantify the concentration of lactate present in the sample. For example, in some embodiments, the matrix of the conjugate element  173  can include a detection enzyme such as L-lactate oxidase (LOD). In other embodiments, the matrix of the conjugate element  173  can include other suitable detection enzymes such as such as L-lactate dehydrogenase (LDH). The one or more detection enzymes can be loosely deposited on the surface of the conjugate element  173  pad such that they can be dissolved in a volume of a sample of blood and/or other biofluids flown from the sample element  172 . 
     The quantification enzyme can be configured to exhibit high activity and selectivity for the stoichiometric conversion of one or more species produced during the enzymatic oxidation of lactate, generating a signal that can be quantified. In some embodiments, the dried matrix can include one or more haem-containing enzymes such as catalases and/or peroxidases that can catalyze redox reactions with hydroperoxides such as hydrogen peroxide (H 2 O 2 ) produced during lactate oxidation. The haem-containing enzyme can be, for example, a horseradish peroxidase which can catalyze the redox reaction of hydrogen peroxide (H 2 O 2 ) and 3,3′-diaminobenzidine (DAB), producing a dark brown insoluble product that can be detected and quantified by colorimetry. 
     While the LFA  170 A is described above as also including the capture element  174 , a control element  175 , and a wick  176 , in this embodiment, detection of lactate can be performed, for example, on or at the conjugate element  173 . Thus, the LFA need not include a separate capture element, control element, and/or wick. 
     In some embodiments, for example, the LFA can be coupled to an optical device such as an CMOS or a CCD camera configured to collect images of the 3,3′-diaminobenzidine (DAB) dark brown precipitate resulted from oxidation with hydrogen peroxide, to determine the concentration of lactate originally present in the sample. For example, in some embodiments, the conjugate element  173  of the LFA can imaged by the camera of a peripheral device such as a smartphone or a dedicated optical detector, and the intensity of the images can be analyzed by image software in order to estimate the concentration of DAB precipitate, the concentration of hydrogen peroxide, and thus the concentration of lactate originally present in the sample. In some embodiments, the concentration of lactate present in the sample can be determined by (1) recording images of the DAB brown precipitate, (2) calculating the grayscale mode value with the aid of image processing software, and (3) correlating the grayscale mode value with concentration of lactate present in samples of know lactate content. The range of grayscale mode value that an image can assume is zero to 255, with values closer to zero corresponding to darker images, and values closer to 255 corresponding to lighter images. 
     Later Flow Assays (LFA) configured to detect lactate in blood and/or other biofluids can overcome certain shortcomings observed with lactate detection approaches that rely on electrochemical reactions to quantify the amount of hydrogen peroxide (H 2 O 2 ) produced upon lactate oxidation. As described above, the enzymatic reaction of hydrogen peroxide (H 2 O 2 ) with 3,3′-diaminobenzidine (DAB) produces a brown-colored precipitate that is insoluble in the sample of blood and/or biofluid and that can be quantify by optical methods such as colorimetry. Furthermore, the reaction of hydrogen peroxide and DAB proceeds under pH and temperature conditions similar to those required for the oxidation of lactate. Thus, the use of additives in the dried matrix of the LFA can protect the both the detection enzyme and the quantification enzyme from decomposition, facilitating storage for periods of time as long as 9 months, as further described herein. In contrast, electrochemical methods to detect and quantify lactate typically require use of high oxidation potentials to convert hydrogen peroxide to an electrical signal Those potentials can frequently trigger interfering reactions of other electro-oxidizable species present in the sample of blood and/or biofluid, which leads to inaccurate results. Additionally, the immobilization of enzyme to a solid surface can present several challenges including (1) the need for complex and/or time-consuming fabrication and characterization methods, and reduced stability of the enzyme during storage. 
     In some embodiments, the detection enzyme and the quantification enzyme can be contained in the dried matrix in the presence of one or more chemical reagents and/or stabilizing additives configured to preserve the activity and stability of the enzymes during storage as well as during oxidation of lactate in the blood and/or other biofluid samples. For example, the dried matrix can include a weak acid or base (e.g., a buffer agent) that can be dissolved in the blood and/or other biofluid sample, and can dissociate in the sample to establish an equilibrium between their acid species and their conjugates, maintaining the pH of the sample within a range of values in which the enzymes exhibit high catalytic activity. In some embodiments, the dried matrix can include one or more buffer agents such as phosphate-buffered saline (PBS), 2-ethanesulfonic acid (MES), tris(hydroxymethyl)aminomethane (TRIS), piperazine-N, N′-bis (PIPES), 3-morpholinopropane-1-sulfonic acid (MOPS), 2-[4-(2-hydroxyethyl)piperazin-1-yl] ethanesulfonic acid (HEPES), [tris(hydroxymethyl)methylamino] propanesulfonic acid (TAPS), N-Cyclohexyl-2-aminoethanesulfonic acid (CHES), and/or N-cyclohexyl-3-aminopropanesulfonic acid (CAPS) 
     In some embodiments, the dried matrix can include a polysaccharide such as chitosan, a non-toxic biocompatible biopolymer which can provide antimicrobial activity, and antioxidant activity to preserve the chemical integrity of the enzymes for extensive periods of time. In some embodiments, the chitosan stabilizer can be accompanied by one or more reagents configured to increase the solubility of chitosan in the sample of blood and/or other biofluid. For example, in some embodiments, the dried matrix can include chitosan and a weak organic acid such as formic acid, acetic acid, and/or propionic acid, suitable to increase the solubility of chitosan in a volume of blood and/or a biofluid. In some embodiments, the dried matrix can include a combination of additives including chitosan, acetic acid, and/or buffer agents, adsorbed on the surface of the conjugate  173  and configured to be dissolved in a volume of blood and/or biofluid transported from the sample element  170 . 
     The Lateral flow assays (LFA) configured to test for lactate in blood and/or other biofluids as described above can detect lactate present in various samples including buffer solutions, serum, plasma and/or whole blood. More specifically, in some embodiments, the LFA can exhibit a dynamic range of detectable lactate of 2-6 (mM), and a sensitivity equal to or higher than 0.5 mM lactate in buffer and/or serum samples. In some embodiments, the LFA can exhibit a cutoff lactate concentration of 2 mM and 4 mM in buffer/serum. The total time required to obtain lactate results using the LFA configured for lactate detection can be about 10 min. The LFA configured for lactate detection can remain relatively stable over time with a degradation occurring primarily in the first week of test, when subjected to accelerated degradations studies at 37 C. More specifically, the LFA configured for lactate detection can remain stable for up to 4 weeks at 37 C, showing small changes in the signal response, supporting the idea that the LFA assay will remain viable for an extended period of time. 
     Procalcitonin 
     In some implementations, the rapid testing device  170  can be an LFA (e.g., the LFA  170 A) configured to test for the PCT biomarker. For example, the effectiveness of using the serum PCT biomarker concentrations in blood in the diagnosis of sepsis is shown below in Table 2, which presents the results of a study of the diagnosis of sepsis, severe sepsis, and septic shock according to serum PCT measurements. 
     
       
         
           
               
               
             
               
                   
                 TABLE 2 
               
             
            
               
                   
                   
               
               
                   
                 Serum PCT range (ng/ml) 
               
            
           
           
               
               
               
               
               
               
            
               
                 Diagnosis 
                 &lt;0.5 
                 &gt;0.5 &amp; &lt;2.0 
                 &gt;2.0 &amp; &lt;10 
                 &gt;10 
                 Total 
               
               
                   
               
            
           
           
               
               
               
               
               
               
               
               
            
               
                 Sepsis 
                 4 (7.7%) 
                 15 
                 (28.8%) 
                 19 
                 (36.5%) 
                 14 (26.9%) 
                 52 (100%) 
               
               
                 Severe Sepsis 
                 1 (4.0%) 
                 5 
                 (20.0%) 
                 9 
                 (36.0%) 
                 10 (40.0%) 
                 25 (100%) 
               
               
                 Septic Shock 
                 1 (4.3%) 
                 5 
                 (17.4%) 
                 7 
                 (30.4%) 
                 11 (47.8%) 
                 23 (100%) 
               
               
                   
               
            
           
         
       
     
     Procalcitonin (PCT) is a 116 amino acid peptide that has an approximate molecular weight MW of 14.5 kDa and belong to the calcitonin family of peptides. The PCT molecule consist of three sections, the amino terminus (57 amino acids), immature calcitonin (33 amino acids) and calcitonin carboxyl-terminus peptides 1 (CCP-1) known as katacalcin (21 amino acids). PCT is a precursor hormone of calcitonin, which is not detectable in healthy individuals since the peptide is not released into the blood in the absence of systematic inflammation. In case of a sepsis caused by bacterial infections, however, PCT synthesis is induced in tissues and therefore becomes detectable in blood. Production of PCT can be triggered by bacterial toxins such as endotoxins and cytokines (e.g., interleukin (IL)-1beta, interleukin-6 and tumor necrosis factor (TNF)-alpha). PCT levels can increase rapidly between 2 hr and 6 hr, and peaks within 6 hr to 24 hr of bacterial infection. In addition to bacterial infections, some fungal and parasitic infections have been associated with the release of PCT in the blood stream. Additional conditions that trigger high levels of PCT in the body include recent major surgeries, severe trauma, severe burns, prolonged cardiogenic shock and chronic kidney diseases. 
     The lack of ability in some extra-thyroidal tissues to cleave PCT to its mature form, calcitonin, allows the accumulation of PCT in the blood. Consequently, PCT can be used as a biomarker with relatively high differentiation between bacterial and viral inflammations that can be used in patients suffering of sepsis. Moreover, PCT levels can be related to and/or indicative of the severity of a bacterial infection. In sepsis cases, a prompt diagnosis of bacterial infection reduces the risk of unnecessary or inappropriate use of antibiotics that could increase the resistance to antibiotics or the toxic side effects in patient. 
     Conventional approaches to diagnose sepsis caused by bloodstream infections include culturing blood, urine, cerebrospinal fluid, of bronchial fluid specimens. These test approaches can typically take between 24 hours to 48 hours to produce result, and often times can facilitate identification of pathogens, providing information about the type of microorganism and its susceptibility towards antibiotics. Clinical symptoms, however, can manifest in the absence of a positive culture, leading to medical treatment based on false negative results. The half-life of PCT (25 hrs to 30 hrs) coupled with its specificity for bacterial infection and its substantial absence in healthy individuals, make PCT a suitable biomarker of bacterial infection. 
     PCT can be quantified by immunoassays based on the sandwich ELISA principle. In those immunoassays, antibody-procalcitonin-antibody complexes are formed and quantified by one or more instrumentation techniques including chemiluminescence, enzymatic, fluorescent, and turbidimetric immunoassays. For example, the chemiluminescence assay for PCT uses a two-step sandwich approach. In this method, anti-PCT monoclonal antibodies conjugated with alkaline phosphatase are added to a patient sample in the presence of a reagent buffer. After incubation, paramagnetic particles coated with monoclonal anti-PCT antibody are added to the test. PCT binds with the paramagnetic particles while the anti-PCT antibodies in solution react with different antigenic sites of the PCT molecule. The particles are separated by magnets from the non-conjugated material. A chemiluminescent substrate is added to the test and the light generated by the reaction is measured using a luminometer, where photon generation is proportional to the concentration of PCT in the sample. 
     Alternatively, PCT can be measured using a quantitative homogeneous assay (BRAHMS, Hennigsdorf, Germany) based on Time Resolved Amplified Cryptate Emission technology (TRACE). The test involves directing a nitrogen laser 337 nm beam at a sample containing PCT and 2 fluorescently labeled antibodies recognizing different epitopes of the PCT peptide. Exposure to the laser excitation triggers transfer of non-radiative energy between donor and acceptor molecules; the donor molecule emitting a long-lived fluorescent signal at 620 nm, and the acceptor molecule emitting a short-lived signal at 665 nm. When both donor and acceptor molecules are brought into proximity by binding to PCT, the resultant signal is amplified at 665 nm and lasts for a few microseconds, long enough to be detected after decay of background fluorescence common in biological samples. 
     Lateral flow assays (LFA) configured to test for blood (e.g., whole blood, serum, etc.) PCT biomarkers (e.g., antigens) provide an alternative tool for the diagnosis of sepsis. As described above with reference to  FIG. 2 , an LFA can be performed over a strip comprising one or more components assembled over a substrate  171 . The components of an LFA configured for detecting and quantifying PCT in blood and/or other biofluids can include a sample element  172 , a conjugate element  173 , a capture element  174 , a control element  175 , and a wick  176 . 
     The substrate  171  can be a backing laminate or a backing card configured to provide mechanical support to components of the LFA, as described above. The substrate  171  can be any suitable shape, size, and/or configuration, as described above. For example, the substrate  171  can be a rectangular backing card or strip of constant width and a predetermined length capable of providing sufficient surface area for accommodating the various components of the LFA. The substrate  171  can be made of a semi-rigid polymer designed to deliver uniformity and lay-flat properties. The substrate  171  can include one or more pressure sensitive adhesives configured to facilitate attaching the various components of the LFA, as further described herein. 
     The sample element  172  can be a pad that provides a surface to receive a sample of blood and/or other biofluids for analysis and facilitates transport of the sample to other components of the lateral flow test strip in a smooth, continuous and homogeneous manner. The sample element  172  can be any suitable shape and/or size. In some embodiments the shape of the sample element  172  can be a rectangular strip configured to adsorb and receive a volume of a sample of blood and/or other biofluids. The sample element  172  can be disposed onto the surface of the substrate  171  to provide mechanical support to the LFA. In some embodiments, the sample element  172  can include an adhesive coated on one surface of the sample pad to facilitate attachment to a plastic backing laminate. The shape and dimensions of the sample element  172  can be predetermined such that the sample element can be disposed onto a plastic backing laminate. The thickness of the sample element  172  can be selected to facilitate adhesion of the sample element  172  to the plastic backing laminate while maintaining the mechanical structure of the pad. Additionally, the thickness of the sample element  172  can be selected to accommodate large volumes of blood and/or other biofluids, preventing oversaturation of the sample on the pad, and channeling to the plastic backing laminate. The sample element  172  can be made of cellulose, nitrocellulose, glass fiber, and/or any other suitable material. 
     The conjugate element  173  of an LFA for detection and quantification of PCT from blood and/or other biofluid samples can be a pad located adjacent downstream to the sample element  172 , as shown in  FIG. 2 . The conjugate element  173  can be any suitable shape and/or size. In some embodiments, the shape of the sample element  172  can be a rectangular strip of similar width as that of the sample member  171 , disposed onto the surface of the substrate  171  to provide mechanical support to the LFA. The conjugate element  173  can contain a dried matrix (e.g., a salt-sugar matrix) that includes bio-active particles and additives. The bio-active particles contained in the matrix include specific antibodies and/or affinity reagents (e.g., DNA aptamers, protein binders, etc.) that have been immobilized on or in the conjugate element  173 . For example, in some embodiments the surface of the sample element  172  can be impregnated with an aqueous buffer solution that provide an environment with controlled pH. In some embodiments, the surface of the sample element  172  can be impregnated with a buffer solution including, but not limited to borate buffer solution, phosphate-buffered saline (PBS), 2-ethanesulfonic acid (MES), tris(hydroxymethyl)aminomethane (TRIS), piperazine-N, N′-bis (PIPES), 3-morpholinopropane-1-sulfonic acid (MOPS), 2-[4-(2-hydroxyethyl)piperazin-1-yl] ethanesulfonic acid (HEPES), [tris(hydroxymethyl)methylamino] propanesulfonic acid (TAPS), N-Cyclohexyl-2-aminoethanesulfonic acid (CHES), and/or N-cyclohexyl-3-aminopropanesulfonic acid (CAPS). 
     The dried matrix of the sample element  172  can include one or more surfactants used as a wetting agent for solubilizing polar species present in the sample. For example, in some embodiments, the dried matrix of the conjugate element  173  can include nonionic surfactants such as glycidol, tergitol, ethoxylated and alkoxylated fatty acids, ethoxylated amines, alkyl and nonyl-phenol ethoxylates, ethoxylated sorbitan esters, castor oil ethoxylate and the like. The dried matrix can include one or more biocide reagents configured to facilitate extending the shelf life of the LFA by inhibiting a broad spectrum of microbes. The biocide reagents can be formulated in the dried matrix of the conjugate element  173  at low concentrations in order to minimize and/or avoid potential health hazards, toxicology problems, and disposal issues. For example, in some embodiments, dried matrix can include 5-Chloro-2-methyl-4-isothiazolin-3-one (CMIT), 2-Methyl-4-isothiazolin-3-one (MIT), proprietary glycol, modified alkyl carboxylate, and/or other commercially available preservative formulations such as proclin 300™. In some embodiments, the dried matrix can include one or more detergents or any amphiphilic molecule that can be used for protein solubilization such as tween 20, Triton X, octylthio glucoside and others. 
     The dried matrix of the conjugate element  173  can include one or more antibodies and/or affinity reagents conjugated to a molecule configured to allow detection. In some embodiments, the dried matrix can include one or more detector antibodies that can bind to PCT and exhibit high stability. For example, in some embodiments the detector antibodies can include procalcitonin human antibodies including monoclonal anti-PCT antibody 14A2cc, monoclonal anti-CT antibody 796, PP3, and the like. 
     The detector antibodies can be immobilized to one or more colored particle (e.g., latex having a blue color, colloidal gold having a red color, and/or any other suitable particle), a fluorescent particle, a magnetic particle or any other suitable particle that can be used for the capture and quantification of PCT in a sample of blood and/or other biofluid. In some embodiments, the detector antibodies can be immobilized to a gold nanoparticle. Gold nanoparticles and/or gold nano-shells can be functionalized with antibodies that are exhibit specific binding activity towards certain regions of the PCT molecule (e.g., bioconjugation). During bioconjugation, the surface of gold nanoparticles can be functionalized with detector antibodies using physical methods that rely on physical interactions between the detector antibody and the surface of the gold nanoparticle, such as ionic interactions, hydrophobic interactions, and/or dative binding. Physical interactions occur by spontaneous absorption of antibodies onto the surface of the gold nanoparticles. In the case of ionic interactions, positively charged groups in the detector antibodies are attracted to the negatively charged surface of the gold nanoparticles. Hydrophobic interactions occur between hydrophobic parts of the detector antibodies and the metal surface. 
     Advantages of functionalization of gold nanoparticles with detector antibodies via physical methods include ease of fabrication, simplicity, low cost, rapid fabrication, and use of minimal additives and/or chemicals that can cause harmful toxicological effects. However, certain disadvantages of physical methods can include the use of large amounts of detector antibodies in the preparation of the functionalized gold nanoparticles, the random orientation of the detector antibodies and the relative ease of replacement of the detector antibody by other molecules with similar characteristics. These disadvantages can often result in high assay variability and low PCT capture capacity, due to the low specificity of the binding modality on the gold nanoparticle. For example, the conjugation of antibodies to the surface of the gold nanoparticle can proceed by nonspecific bindings sites that may occlude the regions of the antibody suitable for PCT capture. For example, in some instances, the antibodies can be physically adsorbed on the surface of the gold nanoparticle by interactions between the constant domains present in the heavy chain and the surface of the nanoparticle. In this configuration, the antigen binding sites of the antibody may be partially available for interacting with PCT. In other instances, the antibodies can be physically adsorbed on the surface of the gold nanoparticle by interactions between the PCT antigen binding cite, which precludes interactions of the antigen binding sites and PCT. 
     Alternatively, in some embodiments, the antibodies can be conjugated to the gold nanoparticles by chemical methods involving covalent bonds, such as chemisorption via thiol derivatives, bifunctional linkers, and/or adapter molecules. Direct functionalization of gold nanoparticles with thiol derivative groups can be achieved by the chemical reaction between gold and sulfur atoms creating a strong bond on the surface of the particle. For example, Thiol-functionalized antibodies can be directly attached to the gold nanoparticles. However, this approach presents challenges such as the use of reaction conditions that may harm the stability of the nanoparticles and may require harsh conditions. 
     The embodiments, implementations, and/or methods described herein can overcome these limitations, for example, by including the use of other groups that can be attached to the gold nanoparticles surface using bifunctional linkers providing specific functionalization in the surface of the gold nanoparticle. For example, carboxilated polyethylene glycol (PEG) molecules functionalized with thiol groups (PEG-SH) can be used to functionalize the surface of the gold nanoparticles. The PEG molecules functionalized to the gold nanoparticles can also include carboxyl terminated groups. These carboxyl terminated groups can be modified with a coupling chemistry including water-soluble carbodiimide (EDC) and N-hydroxy-succinimide (NHS) compounds to create a reactive functional group that binds to the primary amine groups in an antibody molecule. The water-soluble carbodiimide reacts with carboxylic moieties in the PEG containing gold nanoparticles to create an intermediate active group that will react with N-hydroxy-succinimide compound to form a reactive ester groups. When in direct contact with the antibodies, the primary amine groups in the antibody react with the ester group formed in the surface of the gold nanoparticle. This reaction is designed to create amide bonds to attach antibodies to the gold nanoparticles without adding a spacer molecule between them. 
     The capture element  174  of an LFA for detection and quantification of PCT from blood and/or other biofluid samples can be a pad disposed adjacent to and/or downstream of the conjugate element  173 , containing particles or molecules that have been immobilized in or on the capture element  174 . As described above with reference to  FIG. 2 , the particles or molecules can be configured to bind to the detector antibodies conjugated to the colored particles described above with reference to the conjugate element  173 , as the flow downstream in a volume of the blood and/or other biofluid sample. In some embodiments, the capture element  174  can include capture antibodies immobilized and/or chemically bound to the surface of the capture element  174 . The capture antibodies can be configured to interact with the detector antibodies to capture PCT bound to the detector antibody, producing a localized accumulation of the detector antibody and their conjugated colored particle. In some embodiments, the capture antibodies can be adsorbed on the surface of the capture element  174 . 
     As described above with reference to the detection antibodies, the capture antibodies can include procalcitonin human antibodies including monoclonal anti-PCT antibody 14A2cc, monoclonal anti-CT antibody 796, PP3, and the like. The immobilized capture antibodies can be configured to bind PCT molecules which have been previously bound to the detector antibodies (and their conjugated colored particles) in the conjugate element  173 . As a result, exposure of the capture element  174  to a sample of blood and/or other biofluid containing PCT previously flown through the conjugate element  173  can cause accumulation of the colored particles associated to capture antibodies that bound PCT molecules present in the sample. This accumulation of colored particles on the capture element  174  can be registered and quantified by one or more optical methods, to determine the concentration of PCT in the sample. For example, in some embodiments, the colored particles accumulated on capture element  174  can be determined by a standard lateral flow reader such as a commercially available Leelu reader (LUMOS diagnostics), configured to detect colored particles providing suitable optical sensitivity and dynamic range sufficient to cover a broad range of concentrations. 
     The LFA can include the control element  175  to capture detection antibodies not otherwise captured by the capture elements  174 . In other embodiments, the LFA need not include a control element. The wick  176  of an LFA configured for detection and quantification of PCT from blood and/or other biofluid samples can be a pad that disposed adjacent to and/or downstream of the capture element  174  (or the control element  175  if included). As described with reference to  FIG. 2 , the wick  176  can be configured to absorb or wick portions of the sample that have not been immobilized in or on the capture element  174  (and/or the control element  175  if included). 
     The Lateral flow assays (LFA) configured to test for PCT in blood and/or other biofluids as described above can detect PCT present in various samples including buffer solutions, serum, plasma and/or whole blood. More specifically, in some embodiments, the LFA can exhibit a dynamic range of detectable PCT of 0.2 ng/mL-2 ng/mL, and a sensitivity equal to or higher than 0.1 ng/mL in buffer and serum. In some embodiments, the LFA can exhibit a cutoff PCT concentration of 0.2 ng/mL and 0.5 ng/mL in buffer/serum. The total time required to obtain results using the LFA configured for PCT detection can be about 10 min. The LFA configured for PCT detection can remain relatively stable during accelerated stability tests conducted at 37 C, without significant conjugate release and flow through the lateral flow strip. 
     While tests of serum lactate and/or serum PCT concentrations are described above, it should be understood that testing blood (e.g., whole blood or other suitable portions of blood) would produce similar or substantially the same results. While lactate biomarkers and PCT biomarkers are described above, it should be understood that they have been presented by way of example only and not limitation. In some implementations, the rapid testing device (e.g., the LFA  170 A) can be configured to test for any suitable biomarker associated with and/or otherwise indicative of sepsis and/or any other infectious or disease condition. Moreover, it should be understood that the rapid testing device  170  and/or the LFA  170 A (and/or any other suitable flow-based assay) can be used in conjunction with any of the fluid transfer devices described herein with reference to specific embodiments. 
     Aptamers 
     In some implementations, the rapid testing device  170  can be an LFA (e.g., the LFA  170 A) configured to use aptamers to test for any suitable biomarker associated with sepsis and/or any other infectious condition. Aptamers are single-stranded DNA or RNA molecules that can selectively bind to corresponding targets with high affinity and specificity. These single stranded molecules consist of a variable region comprising 20-40 bases in the middle end flanked with two constant regions at each end comprising binding sites. Aptamers can fold into secondary structures and three-dimensional shapes owing to intermolecular hybridization. The equilibrium dissociation constant of aptamer-target binding in the 1 pico Molar (pM) to 1 nano Molar (nM) range. Aptamers have similar affinities as antibodies to target molecules and can be generated against desired target such as toxic small molecules, non-immunogenic targets or single molecules which are not binding to antibodies. Additionally, aptamers can be reversibly denaturized by heat or chemicals which is not possible for antibodies. 
     Aptamers are analogous to antibodies in the range of target recognition and variety of applications. The use of aptamers, however, may present advantages over the use of antibodies including, for example, fabrication via in vitro processes that rely on easily controlled and highly reproducible chemical reactions, in contrast to the complex experiments required to derive antibodies from bacteria, cell culture, and/or animal cells (including human cells), ability to bind targets that are not recognized by antibodies such as ions, small molecules, complex multi-active site molecules, proteins, bacteria cells, viruses, and/or cancer cells, capability to be massively amplified in a short time by the polymerase chain reaction (PCR), ease of modification to introduce functional moieties (e.g., fluorophores, quenchers, and nanomaterials), stability under harsh conditions, and safety use on in vivo applications owing to their non-immunogenic characteristics. In some instances, aptamers can improve transport properties allowing cell specific targeting and improved tissue penetration. 
     Aptamers can be tailored to specific targets obtained through systematic evolution of ligands by exponential enrichment (SELEX) process. This process includes three major steps: library generation, selection, and amplification. In the first step, a random library is designed and synthesized by a combinatorial chemical synthesis technique to produce oligonucleotides comprising the variable region with 20-40 bases flanked by the upstream and downstream primer binding sites at each end. The resulting library can contain 10 12 -10 15  ssDNA or RNA sequences. In the second step, the target molecule is incubated with the library for several minutes in the presence of a binding buffer. Aptamers will bind to the target and form aptamer-target complexes, and non-specific sequences will remain in the binding buffer. The aptamer-target complexes can be collected and washed several times with washing buffer. The aptamers can then be separated from the aptamer-target complexes by treatment with an elution buffer. The selection step can include counter-selection procedure in which the target is replaced for analogs, and the nucleic acid sequences that bind to the analogs are excluded. In the third step, the sequences eluded in the second step are amplified by PCR, in the case of DNA, and by reverse transcriptase (RT)-PCR for RNA, to produce a sub-library to use on a second round of SELEX process. The procedure can be repeated several rounds until producing aptamers with high specificity for the target. 
     When affinities of the sequences bound to the target are saturated, they are sent to the clone and sequence, following the identification of aptamer sequences that bind the target with high sensitivity and specificity. Several techniques can be used in order to improve the separation of unbound sequences from aptamer-target complexes. For example, in some instances the selection of aptamers can include nitrocellulose membrane filtration-based SELEX, affinity chromatography and magnetic bead-based SELEX, capillary electrophoresis and/or microfluidic-based SELEX. Nitrocellulose membrane filtration-based SELEX uses nitrocellulose membranes to retain the complexes of aptamer-target and remove unbound oligonucleotide sequences based on size Multiple pores of micron size on the surface of the membrane allow DNA or RNA oligonucleotides to pass through and the protein to be trapped on the membrane. The material is then amplified by the PCR or RT-PCR for the next round of the fabrication. Affinity chromatography and magnetic bead-based SELEX uses Agarose beads packed onto a column as stationary phase. Magnetic beads are also used for the immobilization of the target through a physical interaction or chemical reaction between a specific tag and its ligand on the beads. Capillary electrophoresis and microfluidic based SELEX are used to improve separation speed, resolution, and capacity with minimal sample dilution. In this method, unbound nucleotides are separated from aptamer-target complexes due to their differences in electrophoretic mobility in an electric field. The aptamer can be obtained by the migration speeds of the mixture of target, ligand or target-ligand complexes. Capillary electrophoresis-based SELEX can be used to select the aptamer in a few rounds compare to other methods. Microfluidic-based SELEX is a technique is a n automated and miniaturized platform that enables aptamer selection on a chip. To carry out the selection process automatically, the system includes several modules with micropumps, microvalves, reservoir manifolds, waste chambers, and PCR chambers. Other methods including atomic force microscopy, high-throughput sequencing, graphene oxide, crosslinking by UV, flow cytometry and surface plasmon resonance (SPR) can be used in connection with the SELEX process. These methods are used to enrich the selection measures and to improve efficiency of aptamer selection. 
     Aptamers applications include in vivo therapeutics, molecular bio sensor, target capture, drug delivery, new drug development, hazard detection, environmental monitoring, clinical diagnosis, biomarkers discovery and food inspection. Aptamers are used as recognition elements for analytical tools including electrochemical and fluorescent biosensors, colorimetric assays, surface plasmon resonance assays and amplification techniques. 
     Detection 
     In some instances, the rapid testing device  170  (e.g., the LFA  170 A and/or any other suitable rapid testing device) can be configured to present test results that can be detected and/or assessed by a human (e.g., a doctor, nurse, technician, etc.) via visual inspection. For example, a doctor, nurse, technician, etc. can visually inspect the capture element  174  of the LFA  170 A to determine if a strip is present along the capture element  174 . In addition, the control element  175  of the LFA  170 A can be visually inspected to verify the performance of the test. In some such instances, visual inspection by a human can be relatively simple to implement and may not use additional equipment to provide qualitative results (e.g., a positive or a negative test result). 
     In other instances, the LFA  170 A can be configured to output test results, which in turn, can be received, inspected, analyzed, interpreted, etc. by one or more electronic devices (e.g., the electronic device  190  shown in  FIG. 1 ). For example, in some instances, a portable strip reader can be used to read, scan, and/or assess the strip(s) along the capture element  174  and/or the control element  175 . The strip reader can include a camera, scanner, reader, and/or the like that can use a complementary metal-oxide semiconductor (CMOS) device, a charge-coupled device (CCD), and/or any other suitable detection device or camera to detect the strip(s). In some implementations, the strip reader can be configured to define data or a digital representation of test results (strips), which can be qualitative, semi-quantitative, and/or quantitative. For example, a capture element intensity can be proportional to concentration of the analyte, thereby allowing for quantification of the analyte. In some instances, the strip reader can be configured to read, scan, and/or identify the presence of one or more strips as well as the intensity of the one or more strips, thereby providing both qualitative and quantitative data. In some implementations, the electronic device  190  can be integrated into/onto the rapid testing device  170  or it can be a stand-alone device into which the rapid testing device  170  and/or one or more cartridges (e.g., one or more portions of the rapid testing device  170 ) can be inserted for reading and analysis. 
     In some embodiments, the strip reader can be configured to provide the qualitative and/or quantitative data as an input into the electronic device  190 , which can analyze, process, and/or otherwise use the data to produce one or more qualitative and/or quantitative test results. The electronic device  190  can be any suitable hardware-based computing device configured to receive, process, define, and/or store data such as, for example, one or more diagnostic test results, test standards against which to measure results data, predetermined and/or predefined treatment plans, patient profiles, disease profiles, etc. In addition, the electronic device  190  can be configured to send and/or receive data via a wired or wireless connection or network. In some embodiments, the electronic device  190  can be, for example, a mobile electronic device (e.g., a smartphone, a tablet, a laptop, and/or any other mobile or wearable device), a personal computer (PC), a workstation, a server device or a distributed network of server devices, a virtual server or machine, a virtual private server and/or the like that is executed and/or run as an instance or guest on a physical server or group of servers, and/or any other suitable device. In some implementations, the electronic device  190  can be configured to provide a graphic and/or digital representation of the test results produced by the rapid testing device  170 . In addition, in some implementations, based on data associated with and/or representing the test results, the electronic device  190  can be configured to determine and graphically or digitally present one or more diagnoses, one or more treatment plans, one or more simulations, and/or any other suitable data associated with the bodily fluid sample, the patient, and/or the medical treatment of the patient. 
     As described above, in some implementations, the transfer device  105  can be configured transfer the first amount of bodily fluid to the rapid testing device  170  and at least some of the second amount of bodily fluid to one or more of the optional fluid collection devices  195 . For example, the second or sampling portion of the transfer device  105  can include and/or can be in fluid communication with an outlet or port, which can allow the second amount of bodily fluid to be transferred out of the second or sampling portion of the transfer device  105 . In some instances, the one or more optional fluid collection devices  195  can be physically and/or fluidically coupled to the transfer device  105  (e.g., via the outlet or port) to receive at least some of the second amount of bodily fluid. 
     In some embodiments, the optional fluid collection device(s)  195  can be any suitable device(s) for at least temporarily containing a bodily fluid. For example, a fluid collection device  195  can include, but is not limited to, any suitable vessel, container, reservoir, bottle, adapter, dish, vial, syringe, device, diagnostic and/or testing machine, and/or the like. In some embodiments, a fluid collection device can be substantially similar to or the same as known sample containers such as, for example, a Vacutainer® (manufactured by Becton Dickinson and Company (BD)), a BacT/ALERT® SN or BacT/ALERT® FA (manufactured by Biomerieux, Inc.), and/or any suitable reservoir, vial, microvial, microliter vial, nanoliter vial, container, microcontainer, nanocontainer, and/or the like. In some embodiments, a fluid collection device can be substantially similar to or the same as any of the sample reservoirs described in U.S. Pat. No. 8,197,420 entitled, “Systems and Methods for Parenterally Procuring Bodily-Fluid Samples with Reduced Contamination,” filed Dec. 13, 2007 (“the &#39;420 patent”), the disclosure of which is incorporated herein by reference in its entirety. 
     In some embodiments, the fluid collection device  195  can be devoid of contents prior to receiving a sample volume of bodily fluid. For example, in some embodiments, the fluid collection device  195  or reservoir can define and/or can be configured to define or produce a vacuum, suction, and/or negative pressure condition such as, for example, a vacuum-based collection tube (e.g., a Vacutainer®), a syringe, and/or the like. In some implementations, the fluid collection device  195  can be physically and/or fluidically coupled to the transfer device  105  (e.g., the outlet or port) such that the negative pressure conditions within the fluid collection device  195  facilitate withdrawal of bodily fluid from the patient, and into or through one or more portions of the transfer device  105 , as described in further detail herein with reference to specific embodiments. 
     In some embodiments, the fluid collection device  195  can include any suitable additives, culture media, substances, enzymes, oils, fluids, and/or the like. For example, the fluid collection device  195  can be a sample or culture bottle including, for example, an aerobic or anaerobic culture medium. The sample or culture bottle can be configured to receive a bodily fluid sample, which can then be tested (e.g., after incubation via in vitro diagnostic (IVD) tests, and/or any other suitable test) for the presence of, for example, Gram-Positive bacteria, Gram-Negative bacteria, yeast, fungi, and/or any other organism. In some instances, if such a test of the culture medium yields a positive result, the culture medium can be subsequently tested using nucleic acid-based systems (e.g., a PCR-based system(s), hybridization probe(s), nucleic acid amplification test(s) (NAATs), etc.) to identify a specific organism. In some embodiments, a sample reservoir can include, for example, any suitable additive or the like in addition to or instead of a culture medium. Such additives can include, for example, heparin, citrate, ethylenediaminetetraacetic acid (EDTA), oxalate, sodium polyanethol sulfonate (SPS), and/or the like. In some embodiments, the fluid collection device  195  can include any suitable additive or culture media and can be evacuated and/or otherwise devoid of air. 
     While “culture medium” is described above as a substance configured to react with organisms in a bodily fluid (e.g., microorganisms such as bacteria) and “additive” is described above as a substance configured to react with portions of the bodily fluid (e.g., constituent cells of blood, blood, synovial fluid, etc.), it should be understood that a sample reservoir can include any suitable substance, liquid, solid, powder, lyophilized compound, gas, etc. Moreover, when referring to an “additive” within a sample reservoir, it should be understood that the additive could be a culture medium, such as an aerobic culture medium and/or an anaerobic culture medium contained in a culture bottle, an additive and/or any other suitable substance or combination of substances contained in a culture bottle and/or any other suitable reservoir such as those described above. That is to say, the embodiments described herein can be used with any suitable fluid reservoir or the like containing any suitable substance or combination of substances. 
     In some implementations, the second amount of bodily fluid contained in the second or sampling portion of the transfer device  105  and/or contained in the optional one or more fluid collection devices  195  can be used as a biological sample in one or more tests, assays, and/or diagnostic procedures. In some instances, sequestering the first amount of bodily fluid from the second amount of bodily fluid can sequester contaminants or the like in the first amount of bodily fluid and/or in the sequestration portion of the transfer device  105 . The sequestering, in turn, can leave the second amount of bodily fluid substantially free of contaminants. Accordingly, the second portion or amount of bodily fluid can be used in one or more tests such as blood culture tests and/or the like, which may be relatively sensitive to contaminants (e.g., can produce adulterated results due to the presence of contaminants). In this manner, the system  100  can be configured to procure the first amount of bodily fluid, which can be used in testing that has relatively low sensitivity to contamination, and the second amount of bodily fluid, which can be used in testing that has a relatively high sensitivity to contamination. In some instances, the testing of the first amount of bodily fluid can provide relatively quick initial results that can inform one or more treatment options, while the testing of the second amount of bodily fluid can provide more detailed test results that typically take longer to develop. Thus, for time sensitive disease conditions (e.g., sepsis), the initial results from testing the first amount of bodily fluid can allow a doctor or physician to provide rapid initial treatment while the more detailed testing of the second amount of bodily fluid is being performed. 
       FIG. 3  is a schematic illustration of a fluid transfer and assay system  200 , according to an embodiment. The fluid transfer and assay system  200  (also referred to herein as “system”) can include at least a fluid transfer device  205  and a rapid diagnostic testing device  270 . In addition, the system  200  can include at least one fluid collection device  295  that can be physically and/or fluidically coupled to the fluid transfer device  205 . 
     The fluid transfer device  205  (also referred to herein as “transfer device”) can be any suitable shape, size, and/or configuration. In some implementations, the transfer device  205  can be configured to withdraw bodily fluid (e.g., blood) from a patient and into and/or through the transfer device  205 . In addition, the transfer device  205  can be configured to transfer at least some of the withdrawn bodily fluid to one or more other devices, reservoirs, containers, vials, machines, tests, assays, etc., such as the rapid diagnostic testing device  270  and/or one or more fluid collection devices  295 . 
     The transfer device  205  includes a housing  210  and an actuator  250 . The housing  210  of the device  205  can be any suitable shape, size, and/or configuration. For example, in some embodiments, the housing  210  can have a size that is at least partially based on an initial amount or volume of bodily fluid configured to be transferred into and/or sequestered within a portion of the housing  210 . In some embodiments, the housing  210  can have a size and/or shape configured to increase the ergonomics and/or ease of use associated with the device  205 . Moreover, in some embodiments, one or more portions of the housing  210  can be formed of a relatively transparent material configured to allow a user to visually inspect and/or verify a flow of bodily fluid through at least a portion of the housing  210 . 
     The housing  210  has and/or forms an inlet  212  and an outlet  213  and defines at least one fluid flow path  215  therebetween. The inlet  212  can be any suitable inlet, opening, port, stopcock, lock (e.g., a Luer lock), seal, coupler, valve (e.g. one-way, check valve, duckbill valve, umbrella valve, and/or the like), tubing, conduit, etc. The inlet  212  is configured to fluidically couple the housing  210  to a bodily fluid source (e.g., a patient). For example, the inlet  212  can be coupled to a lumen-containing device that is configured to be percutaneously disposed in a patient (e.g., a butterfly needle, intravenous (IV) catheter, peripherally inserted central catheter (PICC), midline, intermediary lumen-containing device, and/or the like). Thus, fluid can be transferred between the housing  210  and the patient via the inlet  212  and any lumen-containing device(s) coupled therebetween. More particularly, the transfer device  205  can be configured to transfer bodily fluid from the patient and/or any other bodily fluid source, through the inlet  212  (and/or any lumen-containing device coupled thereto), and into the housing  210  via the inlet  212 , as described in further detail herein. 
     As shown in  FIG. 3 , the housing  210  defines one or more fluid flow paths  215  between the inlet  212  and the outlet  213 . As described in further detail herein, the transfer device  205  and/or the housing  210  can be configured to transition between any number of states, operating modes, and/or configurations to selectively control bodily fluid flow through the one or more fluid flow paths  215 . Moreover, the transfer device  205  and/or the housing  210  can be configured to transition automatically (e.g., based on pressure differential, time, electronically, saturation of a membrane, an absorbent and/or barrier material, etc.) or via intervention (e.g., user intervention, mechanical intervention, or the like). 
     The outlet  213  is in fluid communication with the one or more fluid flow paths  215  and is configured to selectively receive a flow of bodily fluid from the inlet  212  (via the fluid flow paths  215 ). The outlet  213  can be any suitable outlet, opening, port, stopcock, lock, seal, coupler, valve, tubing, conduit, etc. configured to physically and/or fluidically coupled to any suitable device coupled to the outlet  213  such as, for example, the fluid collection device  295  (e.g., a fluid or sample reservoir, syringe, evacuated container, culture bottle, etc.). In some embodiments, the outlet  213  can be monolithically formed with the fluid collection device  295 . In other embodiments, the outlet  213  can be at least temporarily coupled to the fluid collection device  295  via an adhesive, a resistance fit, a mechanical fastener, a threaded coupling, a piercing or puncturing arrangement, any number of mating recesses, and/or any other suitable coupling or combination thereof. For example, in some embodiments, the outlet  213  can include and/or can be coupled to a fluid transfer adapter such as those described in U.S. Pat. No. 10,123,783 entitled, “Apparatus and Methods for Disinfection of a Specimen Container,” filed Mar. 2, 2015 (“the &#39;783 patent”), and/or can be coupled to a fluid transfer device such as those described in U.S. Patent Publication No. 2015/0342510 entitled, “Sterile Bodily-Fluid Collection Device and Methods,” filed Jun. 2, 2015 (“the &#39;510 publication”), the disclosure of each of which is incorporated herein by reference in its entirety. In such embodiments, the fluid transfer adapter can be coupled to and/or can receive a portion of the fluid collection device  295  and can establish fluid communication between the outlet  213  and the fluid collection device  295 . In still other embodiments, the outlet  213  can be operably coupled to the fluid collection device  295  via an intervening structure (not shown in  FIG. 3 ), such as sterile tubing and/or the like. 
     In some embodiments, the arrangement of the outlet  213  can be such that the outlet  213  is physically and/or fluidically sealed prior to coupling to the fluid collection device  295 . In some embodiments, the outlet  213  can be transitioned from a sealed configuration to an unsealed configuration in response to being coupled to the fluid collection device  295  and/or in response to a negative pressure differential between an environment within the outlet  213  and/or housing  210  and an environment within the fluid collection device  295 . 
     The fluid collection device  295  can be any suitable device for at least temporarily containing a bodily fluid, such as, for example, any of those described in detail above with reference to the fluid collection device  195  (e.g., an evacuated container, a sample reservoir, a syringe, a culture bottle, etc.). In some embodiments, the fluid collection device  295  can be a sample reservoir that includes a vacuum seal that maintains negative pressure conditions (vacuum conditions) inside the sample reservoir, which in turn, can facilitate withdrawal of bodily fluid from the patient, through the transfer device  205 , and into the sample reservoir, via a vacuum or suction force. In embodiments in which the fluid collection device  295  is an evacuated container or the like, the user can couple the fluid collection device  295  to the outlet  213  to initiate a flow of bodily fluid from the patient and into the device  205  such that a first or initial portion of the flow of bodily fluid is transferred into and/or sequestered, for example, by the rapid diagnostic testing device  270 , and a second or subsequent portion of the flow of bodily fluid bypasses and/or is otherwise diverted away from the rapid diagnostic testing device  270  and into the fluid collection device  295  (e.g., via the outlet  213 ), as described in further detail herein. 
     The actuator  250  of the device  205  is at least partially disposed within the housing  210  and is configured to control, direct, and/or otherwise facilitate a selective flow of fluid through at least a portion of the housing  210  and/or at least a portion of the one or more fluid flow paths  215 . The actuator  250  can be any suitable shape, size, and/or configuration. In some embodiments, the actuator  250  can be a member or device configured to transition between two or more states (e.g., at least a first state and a second state). For example, the actuator  250  can be a valve, plunger, seal, membrane, bladder, flap, plate, rod, switch, and/or the like. The actuator  250  can be actuated and/or transitioned between any number of states (e.g., at least a first state and a second state) in any suitable manner. For example, transitioning the actuator  250  can include activating, pressing, moving, translating, rotating, switching, sliding, opening, closing, and/or otherwise reconfiguring the actuator  250 . 
     In some implementations, the actuator  250  can be configured to transition between at least the first and the second state in response to a manual actuation by the user (e.g., manually exerting a force on a button, slider, plunger, switch, valve, rotational member, conduit, etc.). In other implementations, the actuator  250  can be configured to automatically transition between at least the first state and the second state in response to a pressure differential (or lack thereof), a change in potential or kinetic energy, a change in composition or configuration (e.g., a portion of an actuator could at least partially dissolve or transform), and/or the like. In still other implementations, the actuator  250  can be mechanically and/or electrically actuated or transitioned (e.g., via a motor, a spring-release mechanism, and/or the like) based on a predetermined time, volume of bodily fluid received, volumetric flow rate of a flow of bodily fluid, flow velocity of a flow of bodily fluid, etc. While examples of actuators and/or ways in which an actuator can transition are provided, it should be understood that they have been presented by way of example only and not limitation. 
     In the embodiment shown in  FIG. 3 , the actuator  250  can be configured to selectively establish fluid communication between the inlet  212  and the rapid diagnostic testing device  270  when in a first state and to selectively establish fluid communication between the inlet  212  and the outlet  213  when in a second state. When in the first state, the actuator  250  can be configured to allow bodily fluid to from the inlet  212 , through at least a portion of the fluid flow path  215  and to or into the rapid diagnostic testing device  270 . In some embodiments, the actuator  250  can be configured to sequester, separate, isolate, and/or otherwise prevent fluid communication between the outlet  213  and inlet  212 , at least a portion of the fluid flow path  215 , and/or the rapid diagnostic testing device  270 . When in the second state, the actuator  250  can be configured to allow a subsequent volume of bodily fluid (e.g., a volume of bodily fluid after the initial volume of bodily fluid) to be transferred from the inlet  212 , through at least a portion of the fluid flow path  215 , and to the outlet  213  (and/or the fluid collection device  295  fluidically coupled to the outlet  213 ), as described in further detail herein. In addition, when in the second state, the actuator  250  can be configured to sequester, separate, isolate, and/or otherwise prevent fluid communication between the rapid diagnostic testing device  270  and the inlet  212 , the outlet  213 , and/or at least a portion of the fluid flow path  215 , as described in further detail herein. 
     The rapid diagnostic testing device  270  (also referred to herein as “rapid testing device” or simply “testing device”) can be any suitable shape, size, and/or configuration. In some embodiments, the rapid testing device  270  can be removably coupled to the transfer device  205  or any suitable portion thereof (e.g., an inlet portion, an outlet portion, a sequestration portion, a sampling portion, and/or any other suitable portion). In other embodiments, the rapid testing device  270  can be integrated into the transfer device  205 . For example, the transfer device  205  and the rapid testing device  270  can be unitarily or monolithically formed and/or otherwise integrated. In still other embodiments, the transfer device  205  can include and/or can form a port, adapter, and/or receiving portion to which the rapid testing device  270  can be coupled or into which the rapid testing device  270  can be inserted to establish fluid communication therebetween. In some such embodiments, coupling the rapid testing device  270  to the transfer device  205  can be operable to transition one or more flow controllers, valves, septa, ports, seals, etc. from a closed or sealed state to an open state to allow fluid communication between the transfer device  205  and the testing device  270 . 
     In some implementations, the rapid testing device  270  can be configured to receive the first amount of bodily fluid from the transfer device  205  and to use the first amount of bodily fluid to perform one or more tests, assays, and/or diagnostic procedures. The rapid testing device  270  can be any suitable testing device. For example, the rapid testing device  270  can be an LFA or the like, as described in detail above with reference to the LFA  170 A shown in  FIG. 2 . In some implementations, the testing device  270  can be an LFA configured to test for the presence of specific analytes or biomarkers that can provide information used to diagnose a patient condition such as, for example, sepsis and/or any other disease state. For example, the LFA can be configured to test for lactate and/or PCT biomarkers, which can be indicators of sepsis. In other embodiments, the testing device can be an LFA configured to test for any of the target analytes and/or biomarkers described above with reference to the LFA  170 A shown in  FIG. 2 . 
     In some instances, the rapid testing device  270  can be configured to output test results associated with testing the volume of bodily fluid transferred from the transfer device  205  while the transfer device  205  and/or the actuator  250  is in the first state. The test results (indicated in  FIG. 3  by the arrow labelled “Output”) can be detected and/or assessed by a human via visual inspection, and/or can be detected and/or assessed by one or more electronic devices (e.g., the electronic device  290 ). In some instances, the test results output by the rapid testing device  270  can be qualitative, semi-quantitative, and/or quantitative. Accordingly, the rapid testing device  270  can be structurally and/or functionally similar to or the same as the rapid testing device  170  described in detail above and therefore, is not described in further detail herein. 
     As described above, the system  200  can be used to procure one or more volumes of bodily fluid from a patient, which can be used in one or more tests, assays, and/or diagnostic procedures. For example, in some instances, a user such as a doctor, physician, nurse, phlebotomist, technician, etc. can manipulate the device  205  to establish fluid communication between the inlet  212  and the bodily fluid source (e.g., a vein of a patient, cerebral spinal fluid (CSF) from the spinal cavity, urine collection, and/or the like). As a specific example, in some instances, the inlet  212  can be coupled to and/or can include a needle or the like that can be manipulated to puncture the skin of the patient and to insert at least a portion of the needle in the vein of the patient, thereby placing the inlet  212  in fluid communication with the bodily fluid source (e.g., the vein, an IV catheter, a PICC, etc.). 
     In some instances, the actuator  250  can be in a first state when the inlet  212  is placed in fluid communication with the bodily fluid source (e.g., the portion of the patient), such that at least a portion of the fluid flow path  215  establishes fluid communication between the inlet  212  and the rapid testing device  270  (and/or a portion of the device  205  to which the rapid testing device  270  is coupled). As such, the transfer device  205  can be configured to transfer an initial volume of bodily fluid from the bodily fluid source (e.g., the patient) to the rapid testing device  270 . In some implementations, the initial volume of bodily fluid can flow to the rapid testing device  270  passively (e.g., without user intervention and/or transitioning of one or more components) in response to a positive pressure associated with the vasculature of the patient and/or in response to any of the fluid transfer methods described in U.S. Patent Publication No. 2018/0353117 entitled, “Fluid Control Devices and Methods of Using the Same,” filed Jun. 11, 2018 (“the &#39;117 publication”), the disclosure of which is incorporated herein by reference in its entirety. 
     In other implementations, the transfer device  205  and/or a portion thereof can be configured to produce a negative pressure differential (e.g., a partial vacuum, a suction force, and/or the like) within at least a portion of the fluid flow path  215  that can initiate and/or sustain a flow of the initial volume of bodily fluid from the bodily fluid source and to the rapid testing device  270 . For example, in some instances, the actuator  250  can be stored in a third state (e.g., a storage state) prior to use and can be transitioned from the storage state to the first state to initiate the flow of the initial volume of bodily fluid. In such instances, the transitioning of the actuator  250  can generate a negative pressure that can draw the bodily fluid from the inlet  212  and to the rapid testing device  270 . In some such implementations, the actuator  250  can be transitioned to generate a negative pressure differential in a manner similar to and/or substantially the same as any of those described in U.S. Pat. No. 8,535,241 entitled, “Fluid Diversion Mechanism for Bodily-Fluid Sampling,” filed Oct. 22, 2012 (“the &#39;241 patent”); U.S. Pat. No. 9,060,724 entitled, “Fluid Diversion Mechanism for Bodily-Fluid Sampling,” filed May 29, 2013 (“the &#39;724 patent”); U.S. Pat. No. 9,155,495 entitled, “Syringe-Based Fluid Diversion Mechanism for Bodily-Fluid Sampling,” filed Dec. 2, 2013 (“the &#39;495 patent”); U.S. Patent Publication No. 2016/0361006 entitled, “Devices and Methods for Syringe Based Fluid Transfer for Bodily-Fluid Sampling,” filed Jun. 23, 2016 (“the &#39;006 publication”); and/or U.S. Provisional Patent Application Ser. No. 62/802,999 entitled, “Devices and Methods for Bodily Fluid Collection and Distribution,” filed Feb. 8, 2019 (“the &#39;999 application”), the disclosure of each of which is incorporated herein by reference in its entirety. In still other implementations, the initial volume of bodily fluid can flow to the rapid testing device  270  in response to a negative pressure differential generated by the fluid collection device  295 , as described in further detail herein with reference to other embodiments. 
     The initial volume of bodily fluid can be any suitable volume of bodily fluid, such as any of the volumes or amounts described above. For example, in some instances, the transfer device  205  can remain in the first state or configuration until a predetermined and/or desired volume (e.g., the initial volume) of bodily fluid is transferred to the rapid testing device  270 . In some embodiments, the initial volume can be associated with and/or at least partially based on a desired volume sufficient for the rapid testing device  270  to perform one or more tests or assays. In other embodiments, the initial volume of bodily fluid can be associated with and/or at least partially based on an amount or volume of bodily fluid that is equal to or greater than a volume associated with the fluid flow path defined between the bodily fluid source and the rapid testing device  270 . In still other embodiments, the transfer device  205  can be configured to transfer a flow of bodily fluid (e.g., the initial volume) into the rapid testing device  270  until a pressure differential between the rapid testing device  270  and the inlet  212  or the bodily fluid source is brought into substantial equilibrium and/or is otherwise reduced below a desired threshold. 
     In some implementations, the rapid testing device  270  can initiate a test and/or assay of or on the initial volume of bodily fluid when the initial volume is transferred into, for example, a sample element or the like (e.g., the sample element  171 ). In some instances, the rapid testing device  270  can be configured to provide one or more solutions, buffers, mixtures, additives, and/or the like that can be mixed or combined with the initial volume. In this manner, the initial volume of bodily fluid (whether alone or mixed with additional components) can flow through the rapid testing device  270  (e.g., an LFA as described above with reference to  FIG. 2 ), which in turn, can perform one or more tests or assays on the initial volume. For example, in some instances, the rapid testing device  270  can be an LFA configured to test for the presence of lactate and/or PCT, as described in detail above. Moreover, once the test or assay is complete, the rapid testing device  270  can be configured to output a test result, which can be detected and/or assessed by a human and/or one or more electronic devices, as described in detail above. 
     After the initial volume of bodily fluid is transferred and/or diverted into the rapid testing device  270 , the transfer device  205  can be transitioned from the first state or configuration to a second state or configuration. For example, in some embodiments, the actuator  250  can be transitioned from its first state to its first state when the initial volume of bodily fluid is transferred into the rapid testing device  270 , which in turn, places the transfer device  205  in its second state. In some embodiments, the arrangement of the transfer device  205  can be such that the transfer device  205  cannot transition to the second state prior to collecting the initial volume in the rapid testing device  270 . 
     In some embodiments, the arrangement of the transfer device  205 , the actuator  250 , and/or the rapid testing device  270  can be such that a flow of bodily fluid into the rapid testing device  270  substantially stops or slows in response to receiving the initial volume. In some instances, the user can visually inspect a portion of the device  205  and/or housing  210  to determine that the initial volume of bodily fluid is disposed in the rapid testing device  270  and/or that the flow of bodily fluid into the rapid testing device  270  has slowed or substantially stopped. In some embodiments, the user can exert a force on the actuator  250  and/or can otherwise actuate the actuator  250  to transition the actuator  250  from its first state to its first state. In other embodiments, the actuator  250  can be transitioned automatically (e.g., without user intervention). Moreover, in some implementations, the device  205  and/or actuator  250  can be transitioned from the first state to the second state while the rapid testing device  270  is performing the test(s) or assay(s) on the initial volume of bodily fluid. Said another way, the rapid testing device  270  can perform the assay on the initial volume of bodily fluid while the device  205  is used to transfer one or more subsequent volumes of bodily fluid (e.g., in one or more parallel processes or the like). 
     In some embodiments, the transitioning of the actuator  250  from its first state to its second state (e.g., placing the transfer device  205  in its second state or configuration) can sequester, isolate, separate, and/or retain the initial volume of the bodily fluid in the rapid testing device  270 . Said another way, the actuator  250  can sequester and/or isolate the rapid testing device  270  from the inlet  212 , the outlet  213 , and one or more portions of the fluid flow path  215 . As described in further detail herein, in some instances, contaminants such as, for example, dermally residing microbes or the like dislodged during the venipuncture event, other external sources of contamination, colonization of catheters and PICC lines that are used to collect samples, and/or the like can be entrained and/or included in the initial volume of the bodily fluid. Thus, such contaminants are sequestered in the initial volume. Moreover, the arrangement of the rapid testing device  270  can be such that the tests and/or assays performed by the rapid testing device  270  are not susceptible to such contamination, which means that the accuracy of the test results output by the rapid testing device  270  is not affected by such contamination, as described in detail above. 
     In addition to sequestering the rapid testing device  270  from the inlet  212 , the outlet  213 , and at least a portion of the fluid flow path  215 , placing the actuator  250  in its second state also establishes fluid communication between the inlet  212  and the outlet  213  via at least a portion of the fluid flow path  215 . For example, in some embodiments, transitioning the actuator  250  from its first state to its second state can, for example, open or close a port or valve, move one or more seals, move or remove one or more obstructions, define one or more portions of a flow path, and/or the like. 
     In some implementations, the fluid collection device  295  can be fluidically coupled to the outlet  213  at any time prior to and/or at the same time as the actuator  250  being transitioned from the first state to the second state. As described above, the fluid collection device  295  can be any suitable reservoir, container, and/or device configured to receive a volume of bodily fluid. For example, the fluid collection device  295  can be an evacuated reservoir or container that defines a negative pressure and/or can be a syringe that can be manipulated to produce a negative pressure. In some instances, coupling the outlet  213  to the fluid collection device  295  selectively exposes at least a portion of the fluid flow path  215  to the negative pressure and/or suction force within the fluid collection device  295 . Thus, in response to the negative pressure and/or suction force, one or more subsequent volume(s) of the bodily fluid can flow from the inlet  212 , through at least a portion of the fluid flow path  215 , through the outlet  213 , and into the fluid collection device  295 . As described above, sequestering the initial volume of bodily fluid (e.g., in the rapid testing device  270 ) prior to collecting or procuring one or more subsequent volumes of bodily fluid reduces and/or substantially eliminates an amount of contaminants in the one or more subsequent volumes. Accordingly, the subsequent volumes of bodily fluid can be used in one or more tests such as blood culture tests and/or the like, which may be relatively sensitive to contaminants (e.g., can produce adulterated results due to the presence of contaminants). In this manner, the system  200  can be configured to procure the initial volume of bodily fluid, which can be used in testing that has relatively low sensitivity to contamination, and the subsequent volume(s) of bodily fluid, which can be used in testing that has a relatively high sensitivity to contamination. In some instances, the testing of the initial volume of bodily fluid (e.g., by the rapid testing device  270 ) can provide relatively quick initial results that can inform one or more treatment options, while the testing of the subsequent volume(s) of bodily fluid can provide more detailed test results that typically take longer to develop. 
       FIG. 4  is a schematic illustration a fluid transfer and assay system  300 , according to an embodiment. The fluid transfer and assay system  300  (also referred to herein as “system”) can include at least a fluid transfer device  305  and a rapid diagnostic testing device  370 . In some implementations, the system  300  can include at least one fluid collection device  395  that can be physically and/or fluidically coupled to the fluid transfer device  305 . Portions and/or aspects of the fluid transfer device  305 , the rapid diagnostic testing device  370 , and/or the fluid collection device  395  can be similar to and/or substantially the same as the fluid transfer devices  105  and/or  205 , the rapid diagnostic testing devices  170  (and/or the LFA  170 A) and/or  270 , and/or the fluid collection devices  195  and/or  295 , respectively, described in detail above with reference  FIG. 3 . Accordingly, such portions and/or aspects are not described in further detail herein. 
     The fluid transfer device  305  (also referred to herein as “transfer device”) can be any suitable shape, size, and/or configuration. In some implementations, the transfer device  305  can be configured to withdraw bodily fluid (e.g., blood) from a patient and into and/or through the transfer device  305 . In addition, the transfer device  305  can be configured to transfer at least some of the withdrawn bodily fluid to one or more other devices, reservoirs, containers, vials, machines, tests, assays, etc., such as the rapid diagnostic testing device  370  and/or one or more fluid collection devices  395 . 
     The transfer device  305  includes a housing  310 , a flow controller  340 , and an actuator  350 . The housing  310  of the device  305  can be any suitable shape, size, and/or configuration. For example, in some embodiments, the housing  310  can be similar to and/or the substantially the same as the housing  210  described above with reference to  FIG. 3 . Specifically, the housing  310  has and/or forms an inlet  312  and an outlet  313  and defines at least one fluid flow path  315  therebetween. The inlet  312  can be any suitable inlet or port and can be configured to establish fluid communication between the housing  310  to a bodily fluid source (e.g., a patient). The outlet  313  can be any suitable outlet or port and can be configured to establish fluid communication between the housing  310  and the fluid collection device  395 . Moreover, the fluid collection device  395  can be similar to or substantially the same as the fluid collection device  295  and thus, is not described in further detail herein. The one or more fluid flow paths  315  defined by the housing  310  extends between the inlet  312  and the outlet  313  and can selectively establish fluid communication therebetween, as described in further detail herein. 
     The housing  310  can differ from the housing  210 , however, by including, forming, and/or coupling to a sequestration chamber  330 . As described in further detail herein, the sequestration chamber  330  is selectively in fluid communication with the fluid flow path  315 . In addition, the sequestration chamber  330  includes, is coupled to, and/or is otherwise in fluid communication with the rapid diagnostic testing device  370 . The sequestration chamber  330  can be configured to (1) receive a flow and/or volume of bodily fluid from the inlet  312 , (2) sequester (e.g., separate, segregate, contain, retain, isolate, etc.) at least a portion of the flow and/or volume of bodily fluid therein, and (3) transfer at least a portion of the flow and/or volume of bodily fluid into the rapid diagnostic testing device, as described in further detail herein. 
     The sequestration chamber  330  can have any suitable arrangement such as, for example, those described herein with respect to specific embodiments. For example, in some embodiments, the sequestration chamber  330  can be at least partially formed by the housing  310 . In other embodiments, the sequestration chamber  330  can be a reservoir placed and/or disposed within a portion of the housing  310 . In other embodiments, the sequestration chamber  330  can be formed and/or defined by a portion of the fluid flow path  315 . That is to say, the housing  310  can define one or more lumens and/or can include one or more lumen defining device(s) configured to receive an initial flow or volume of bodily fluid from the inlet  312 , thereby forming and/or functioning as the sequestration chamber  330 . While examples of a sequestration chamber are described herein, it should be understood that the transfer device  305  and/or the housing  310  can have a sequestration chamber arranged in any suitable manner and therefore, the sequestration chamber  330  is not intended to be limited to those shown and described herein. 
     The sequestration chamber  330  can have any suitable volume and/or fluid capacity. For example, in some embodiments, the sequestration chamber  330  can have a volume and/or fluid capacity between about 0.1 mL and about 5.0 mL. In some embodiments, the sequestration chamber  330  can have a volume measured in terms of an amount of bodily fluid (e.g., the initial or first amount of bodily fluid) configured to be transferred in the sequestration chamber  330 . For example, in some embodiments, the sequestration chamber  330  can have a volume sufficient to receive an initial volume of bodily fluid as small as a microliter or less of bodily fluid (e.g., a volume as small as 20 drops of bodily fluid, 10 drops of bodily fluid, 5 drops of bodily fluid, a single drop of bodily fluid, or any suitable volume therebetween). In other embodiments, the sequestration chamber  330  can have a volume sufficient to receive an initial volume of bodily fluid up to, for example, about 5.0 mL, 10.0 mL, 15.0 mL, 20.0 mL, 30.0 mL, 40.0 mL, 50.0 mL, or more. In some embodiments, the sequestration chamber  330  can have a volume that is equal to at least some of the volumes of one or more lumen(s) placing the sequestration chamber  330  in fluid communication with the bodily fluid source (e.g., a combined volume of a lumen of a needle, the inlet  312 , and at least a portion of the fluid flow path  315 ). In still other embodiments, the sequestration chamber  330  can have a volume that is based at least in part on a desired volume of bodily fluid used in or by the rapid diagnostic testing device  370 . 
     As shown in  FIG. 4 , the device  305  includes the flow controller  340 , which is at least partially disposed within the housing  310  and is configured to control, direct, and/or otherwise facilitate a selective flow of fluid through at least a portion of the housing  310 , at least a portion of the fluid flow path  315 , and/or at least a portion of the sequestration chamber  330 . In this context, the flow of fluids, for example, can be a liquid such as water, oil, dampening fluid, bodily fluid, and/or any other suitable liquid, and/or can be a gas such as air, oxygen, carbon dioxide, helium, nitrogen, ethylene oxide, and/or any other suitable gas. 
     The flow controller  340  can be any suitable shape, size, and/or configuration. In some embodiments, the flow controller  340  can be, for example, a valve, a membrane, a diaphragm, a bladder, a plunger, a piston, a bag, a pouch, and/or any other suitable member having a desired stiffness, flexibility, and/or durometer, or any suitable combination thereof. In some embodiments, the flow controller  340  can be, for example, a restrictor, a vent, an absorbent member, a selectively permeable member (e.g., a fluid impermeable barrier or seal that at least selectively allows the passage of air or gas therethrough), a port, a junction, an actuator, and/or the like, or any suitable combination thereof. In some embodiments, the flow controller  340  can be similar to or substantially the same as any of those described in the &#39;117 publication; U.S. Patent Publication No. 2019/0076074 entitled, “Fluid Control Devices and Methods of Using the Same,” filed Sep. 12, 2018 (“the &#39;074 publication”); U.S. patent application Ser. No. 16/426,380 entitled, “Fluid Control Devices and Methods of Using the Same,” filed May 30, 2019 (“the &#39;380 application”); and/or U.S. Provisional Patent Application Ser. No. 62/816,477 entitled, “Fluid Control Devices and Methods of Using the Same,” filed Mar. 11, 2019 (“the &#39;477 application”), the disclosure of each of which is incorporated herein by reference in its entirety. 
     In some embodiments, the transfer device  305  can be configured to selectively transfer a volume of bodily fluid to the sequestration chamber  330  or to the outlet  313  based at least in part on a pressure differential between two or more portions of the transfer device  305 . For example, a pressure differential can result from fluidically coupling the outlet  313  to the fluid collection device  395 , which can define and/or can be configured to produce a negative pressure (e.g., an evacuated reservoir, a syringe, a pressure charged canister, and/or other source or potential energy to create a vacuum or pressure differential). In other embodiments, the pressure differential can result from a change in volume and/or temperature. In still other embodiments, the pressure differential can result from at least a portion of the transfer device  305 , the housing  310 , the actuator  350 , and/or portions of the fluid flow path  315  being evacuated and/or charged (e.g., the sequestration chamber  330  and/or any other suitable portion). In some embodiments, the pressure differential can be established automatically or via direct or indirect intervention (e.g., by the user). 
     In some embodiments, the flow controller  340  can be configured to facilitate air (or other fluid) displacement through one or more portions of the transfer device  305 , which in some instances, can allow for or result in a pressure differential and/or pressure equalization across one or more portions of the housing  310 . Moreover, a flow of a fluid (e.g., gas and/or liquid) resulting from a pressure differential can be selectively controlled via the flow controller  340 . For example, the flow controller  340  can be configured to transition between one or more operating states or conditions to control the fluid flow. In some embodiments, the flow controller  340  can be a member or device formed of an absorbent or semi-permeable material configured to selectively allow fluid flow therethrough. For example, such an absorbent material can be transitioned from a first state in which the material allows a flow of gas (e.g., air) therethrough but prevents a flow of liquid (e.g., bodily fluid) therethrough, to a second state in which the material substantially prevents a flow of gas and liquid therethrough (e.g., the flow controller  340  can be a selectively permeable blood barrier), as described in detail in the &#39;117 publication and/or the &#39;380 application. 
     In some embodiments, the flow controller  340  can be configured to transition from a first state to a second state in response to a negative pressure differential and/or suction force exerted on at least a portion of the flow controller  340 . For example, the flow controller  340  can include one or more valves, membranes, diaphragms, and/or the like. For example, the flow controller  340  can be in a first state prior to using the device  305  (e.g., a storage or non-use state) and in response to the outlet  313  being fluidically coupled to the fluid collection device  395  (e.g., a collection device defining or configured to define a negative pressure and/or suction force), the flow controller  340  can be transitioned to a second state. In some embodiments, the flow controller  340  can be a bladder configured to transition or “flip” from a first state to a second state in response to a negative pressure differential and/or suction force exerted on a surface of the bladder, as described in detail in the &#39;380 application and/or the &#39;477 application. 
     In some embodiments, a size, shape, arrangement, and/or constituent material of the flow controller  340  can be configured and/or otherwise selected such that the flow controller  340  transitions from the first state to the second state in a predetermined manner and/or with a predetermined or desired rate. In some instances, controlling a rate at which the flow controller  340  transitions from the first state to the second state can, in turn, control and/or modulate a rate of bodily fluid flow into the sequestration chamber  330  and/or a magnitude of a suction force generated in the sequestration chamber  330  that is operable in drawing the initial volume of bodily fluid into the sequestration chamber  330 . Although not shown in  FIG. 4 , in some embodiments, the housing  310  and/or the flow controller  340  can include any suitable member, feature, opening, etc., configured to modulate a suction force exerted on or through the flow controller  340 , which in turn, can modulate the rate at which the flow controller  340  transitions from the first state to the second state. In some instances, controlling a rate at which the flow controller  340  transitions and/or a magnitude of a pressure differential and/or suction force generated within the sequestration chamber  330  can reduce, for example, hemolysis of a blood sample and/or a likelihood of collapsing a vein (e.g., which is particularly important when procuring bodily fluid samples from fragile patients). In some instances, modulating the transitioning of the flow controller  340  and/or the pressure differential generated in the sequestration chamber  330  can at least partially control an amount or volume of bodily fluid transferred into the sequestration chamber  330  (i.e., can control a volume of the initial amount of bodily fluid). 
     In some embodiments, the flow controller  340  can include any suitable combination of devices, members, and/or features. It should be understood that the flow controllers included in the embodiments described herein are presented by way of example and not limitation. Thus, while specific flow controllers are described herein, it should be understood that fluid flow can be controlled through the transfer device  305  by any suitable manner. 
     The actuator  350  of the device  305  is at least partially disposed within the housing  310  and is configured to control, direct, and/or otherwise facilitate a selective flow of fluid through at least a portion of the housing  310  and/or at least a portion of the one or more fluid flow paths  315 . The actuator  350  can be any suitable shape, size, and/or configuration. In some embodiments, the actuator  350  can be a member or device configured to transition between any number of states and in any suitable manner. In addition, the actuator  350  can be actuated in any suitable manner (e.g., user actuation, automatic actuation, mechanical actuation, electronic actuation, chemical actuation, and/or the like). For example, the actuator  350  can be the similar to and/or substantially the same as any of those described above with reference to the actuator  250 . 
     In the embodiment shown in  FIG. 4 , the actuator  350  can be configured to selectively establish fluid communication between the inlet  312  and the sequestration chamber  330  when in a first state and to selectively establish fluid communication between the inlet  312  and the outlet  313  when in a second state. When in the first state, the actuator  350  can be configured to allow bodily fluid to from the inlet  312 , through at least a portion of the fluid flow path  315  and to or into the sequestration chamber  330 . In some embodiments, the actuator  350  can be configured to sequester, separate, isolate, and/or otherwise prevent fluid communication between the outlet  313  and inlet  312 , at least a portion of the fluid flow path  315 , and/or the sequestration chamber  330 . When in the second state, the actuator  350  can be configured to allow a subsequent volume of bodily fluid (e.g., a volume of bodily fluid after the initial volume of bodily fluid) to be transferred from the inlet  312 , through at least a portion of the fluid flow path  315 , and to the outlet  313  (and/or the fluid collection device  395  fluidically coupled to the outlet  313 ), as described in further detail herein. In addition, when in the second state, the actuator  350  can be configured to sequester, separate, isolate, and/or otherwise prevent fluid communication between the sequestration chamber  330  and the inlet  312 , the outlet  313 , and/or at least a portion of the fluid flow path  315 . In the embodiment shown in  FIG. 4 , the transfer device  305  is such that the actuator  350  and the flow controller  340  collectively control the flow of fluid (e.g., a gas and/or a liquid) through the device, as described in further detail herein. 
     The rapid diagnostic testing device  370  (also referred to herein as “rapid testing device” or simply “testing device”) can be any suitable shape, size, and/or configuration. In some embodiments, the rapid testing device  370  can be removably coupled to the transfer device  305  or any suitable portion thereof. For example, in the embodiment shown in  FIG. 4 , the rapid testing device  370  can be at least fluidically coupled to the sequestration chamber of the transfer device  305 . In other embodiments, the rapid testing device  370  can be integrated into the transfer device  305  such that the rapid testing device  370  is in fluid communication with the sequestration chamber  330 . For example, the transfer device  305  and the rapid testing device  370  can be unitarily or monolithically formed and/or otherwise integrated. In still other embodiments, the housing  310  can include and/or can form a port, adapter, and/or receiving portion to which the rapid testing device  370  can be coupled or into which the rapid testing device  370  can be inserted to establish fluid communication between the rapid testing device  370  and the sequestration chamber  330 . 
     In some such embodiments, coupling the rapid testing device  370  to the transfer device  305  can be operable to transition one or more flow controllers, valves, septa, ports, seals, etc. from a closed or sealed state to an open state to allow fluid communication between the transfer device  305  and the testing device  370 . Although not shown in  FIG. 4 , in some embodiments, the transfer device  305  can include a second actuator and/or the like that can be manipulated to establish fluid communication between the sequestration chamber  330  and the rapid testing device  370 . In other embodiments, the actuator  350  can be transitioned to establish fluid communication between the sequestration chamber  330  and the rapid testing device  370 . 
     In some implementations, the rapid testing device  370  can be configured to receive the first amount of bodily fluid from the transfer device  305  and to use the first amount of bodily fluid to perform one or more tests, assays, and/or diagnostic procedures. The rapid testing device  370  can be any suitable testing device. For example, the rapid testing device  370  can be an LFA or the like, as described in detail above with reference to the LFA  170 A shown in  FIG. 2 . In some implementations, the testing device  370  and/or aspects or portions thereof can be substantially similar to the rapid testing devices  170  and/or  270  described in detail above. Accordingly, the rapid testing device  370  and/or aspects or portions thereof is/are not described in further detail herein. 
     As described above, the system  300  can be used to procure one or more volumes of bodily fluid from a patient, which can be used in one or more tests, assays, and/or diagnostic procedures. For example, in some instances, a user such as a doctor, physician, nurse, phlebotomist, technician, etc. can manipulate the device  305  to establish fluid communication between the inlet  312  and the bodily fluid source (e.g., a vein of a patient, cerebral spinal fluid (CSF) from the spinal cavity, urine collection, and/or the like), as described above. In some instances, the actuator  350  can be in a first state when the inlet  312  is placed in fluid communication with the bodily fluid source (e.g., the portion of the patient), such that at least a portion of the fluid flow path  315  establishes fluid communication between the inlet  312  and the sequestration chamber  330 . 
     As such, the transfer device  305  can be configured to transfer an initial volume of bodily fluid from the bodily fluid source (e.g., the patient) to the rapid testing device  370 . More specifically, in the embodiment shown in  FIG. 4 , once the inlet  312  is placed in fluid communication with the bodily fluid source (e.g., the portion of the patient), the outlet  313  can be fluidically coupled to the fluid collection device  395 . As described above, in some embodiments, the fluid collection device  395  can be any suitable reservoir, container, and/or device configured to receive a volume of bodily fluid. For example, the fluid collection device  395  can be an evacuated reservoir or container that defines a negative pressure and/or can be a syringe that can be manipulated to produce a negative pressure. In some instances, coupling the outlet  313  to the fluid collection device  395  selectively exposes at least a portion of the fluid flow path  315  to the negative pressure and/or suction force within the fluid collection device  395 . In some implementations, the actuator  350  can be in the first state such that the outlet  313  is sequestered from the inlet  312 . In addition, when the actuator  350  is in the first state, the outlet  313  can be in fluid communication with the flow controller  340  (e.g., via a portion of the fluid flow path  315 ). The flow controller  340  can similarly be in its first state when the fluid collection device  395  is coupled to the outlet  313 . 
     In embodiments in which the flow controller  340  is a selectively permeable member or membrane, the arrangement of the flow controller  340  and the actuator  350  can be such that a flow of air or gas is allowed to pass through the flow controller  340  between the outlet  313  and the sequestration chamber  330 . In such embodiments, this arrangement results in at least a portion of the negative pressure differential or suction force generated by the fluid collection device  395  being transferred into and/or through the sequestration chamber  330 , which in turn, can be operable in drawing the initial volume of bodily fluid from the bodily fluid source, through the inlet  312  and at least a portion of the fluid flow path  315 , and into the sequestration chamber  330 , as described in detail in the &#39;117 publication and/or the &#39;380 application. 
     Alternatively, in embodiments in which the flow controller  340  is a diaphragm, flap, valve, sleeve, etc., the arrangement of the flow controller  340  and the actuator  350  can be such that a portion and/or surface of the flow controller  340  is in fluid communication with the outlet  313  (e.g., via a portion of the fluid flow path  315 ). As such, the negative pressure and/or suction force can be exerted on the portion and/or surface of the flow controller  340 , which in turn, can be operable to transition the flow controller  340  from its first state, in which the sequestration chamber  330  has a first volume, to its second state, in which the sequestration chamber  330  has a second volume, greater than the first volume. The sequestration chamber  330  can be such that the increase in volume results in a decrease in pressure within the sequestration chamber  330 , thereby generating a negative pressure differential operable to draw bodily fluid into the sequestration chamber  330 . Thus, in such embodiments, the initial volume of bodily fluid can be drawn into the sequestration chamber  330  in response to the transitioning of the flow controller  340  (e.g., the increase in volume of the sequestration chamber  330  as a result of the flow controller  340  transitioning from the first state to the second state), as described in detail in the &#39;380 application and/or the &#39;477 application. 
     The initial volume of bodily fluid can be any suitable volume of bodily fluid, such as any of the volumes or amounts described above. For example, in some instances, the transfer device  305  can remain in the first state or configuration until a predetermined and/or desired volume (e.g., the initial volume) of bodily fluid is transferred to the sequestration chamber  330 . In some embodiments, the initial volume can be associated with and/or at least partially based on a volume of the sequestration chamber  330  or a portion thereof (e.g., a volume sufficient to fill the sequestration chamber  330  or a desired portion of the sequestration chamber  330 ). In some embodiments, the initial volume can be associated with and/or at least partially based on a desired volume sufficient for the rapid testing device  370  to perform one or more tests or assays. In other embodiments, the initial volume of bodily fluid can be associated with and/or at least partially based on an amount or volume of bodily fluid that is equal to or greater than a volume associated with the fluid flow path defined between the bodily fluid source and the sequestration chamber  330 . In still other embodiments, the transfer device  305  can be configured to transfer a flow of bodily fluid (e.g., the initial volume) into the sequestration chamber  330  until a pressure differential between the sequestration chamber  330  and the inlet  312  or the bodily fluid source is brought into substantial equilibrium and/or is otherwise reduced below a desired threshold. 
     In some embodiments, the transfer device  305  can be configured to transfer a flow of bodily fluid (e.g., the initial volume) into the sequestration chamber  330  until the flow controller  340  is transitioned to its second configuration. Said another way, in some embodiments, transferring the initial volume of bodily fluid into the sequestration chamber  330  can be operable to place the flow controller  340  in its second state or configuration. For example, in embodiments in which the flow controller  340  is a selectively permeable member, transferring the initial volume of bodily fluid into the sequestration chamber  330  can be such that at least a portion of the initial volume wets and/or saturates the flow controller  340 , which in turn, places the flow controller  340  in its second state, as described in detail in the &#39;117 application and/or the &#39;380 application. In embodiments in which the flow controller  340  is a diaphragm and/or the like, the transferring of the initial volume into the sequestration chamber  330  can substantially coincide with the flow controller  340  being placed in its second state and/or configuration (e.g., in response to the negative pressure produced by the fluid collection device  395 ), as described in detail in the &#39;380 application and/or the &#39;477 application. Moreover, in the embodiment shown in  FIG. 4 , the arrangement of the flow controller  340  is such that when in its second state and/or configuration, the flow controller  340  sequesters and/or fluidically isolates the sequestration chamber  330  from the outlet  313  such that the negative pressure and/or suction force produced by the fluid collection device  395  no longer acts on or through the sequestration chamber  330 . 
     In some implementations, at least a portion of the initial volume of bodily fluid can be transferred from the sequestration chamber  330  and into the rapid testing device  370  when the flow controller  340  is in its second state and prior to the actuator being transitioned from its first state to its second state. In some embodiments, the actuator  350  is configured to sequester the sequestration chamber  330  from the inlet  313 , the outlet  315 , and at least a portion of the fluid flow path  315 . In such embodiments, the portion of the initial volume of bodily fluid can be transferred from the sequestration chamber  330  prior to transitioning the actuator  350  from its first state to its second state, during the transitioning, and/or after transitioning the actuator  350  from its first state to its second state. In some implementations, the transferring of the portion of the initial volume can be automatic. In other implementations, the transferring of the portion of the initial volume can be in response to one or more user inputs and/or the like. 
     In some embodiments, transferring the portion of the initial volume of bodily fluid into the rapid testing device  370  can initiate a test and/or assay of or on the portion of the initial volume of bodily fluid, as described in detail above with reference to the rapid testing device  270 . Moreover, the rapid testing device  370  can be configured to perform any suitable test and/or assay. For example, the rapid testing device  370  can be an LFA configured to test for the presence of lactate and/or PCT, as described in detail above. Moreover, once the test or assay is complete, the rapid testing device  370  can be configured to output a test result, which can be detected and/or assessed by a human and/or one or more electronic devices, as described in detail above. 
     In some embodiments, the transitioning of the actuator  350  from its first state to its second state (e.g., placing the transfer device  305  in its second state or configuration) can sequester, isolate, separate, and/or retain the initial volume of the bodily fluid in the sequestration chamber  330  and/or the rapid testing device  370 . Said another way, the actuator  350  can sequester and/or isolate the sequestration chamber  330  from the inlet  312 , the outlet  313 , and one or more portions of the fluid flow path  315 . In some instances, sequestering the initial volume of bodily fluid in the sequestration chamber  330  can also sequester contaminants in the initial volume. Moreover, the arrangement of the rapid testing device  370  can be such that the tests and/or assays performed by the rapid testing device  370  are not susceptible to such contamination, which means that the accuracy of the test results output by the rapid testing device  370  is not affected by such contamination, as described in detail above. 
     In addition to sequestering the sequestration chamber  330  from the inlet  312 , the outlet  313 , and at least a portion of the fluid flow path  315 , placing the actuator  350  in its second state (and having the flow controller  340  in its second state) also establishes fluid communication between the inlet  312  and the outlet  313  via at least a portion of the fluid flow path  315 . For example, in some embodiments, transitioning the actuator  350  from its first state to its second state can, for example, open or close a port or valve, move one or more seals, move or remove one or more obstructions, define one or more portions of a flow path, and/or the like. Thus, in response to the negative pressure and/or suction force generated by the fluid collection device  395 , one or more subsequent volume(s) of the bodily fluid can flow from the inlet  312 , through at least a portion of the fluid flow path  315 , through the outlet  313 , and into the fluid collection device  395 . As described above, sequestering the initial volume of bodily fluid (e.g., in the rapid testing device  370 ) prior to collecting or procuring one or more subsequent volumes of bodily fluid reduces and/or substantially eliminates an amount of contaminants in the one or more subsequent volumes. Accordingly, the system  300  can be configured to procure the initial volume of bodily fluid, which can be used in rapid testing that has relatively low sensitivity to contamination, and the subsequent volume(s) of bodily fluid, which can be used in testing that has a relatively high sensitivity to contamination, as described above with reference to the systems  100  and/or  200 . 
       FIGS. 5A and 5B  are schematic illustrations a fluid transfer and assay system  400 , according to an embodiment, and shown in a first state and a second state, respectively. The fluid transfer and assay system  400  (also referred to herein as “system”) can include at least a fluid transfer device  405  and a rapid diagnostic testing device  470 . Portions and/or aspects of the fluid transfer device  405  and/or the rapid diagnostic testing device  470  can be similar to and/or substantially the same as the fluid transfer devices  105 ,  205 , and/or  305 , and/or the rapid diagnostic testing devices  170  (and/or the LFA  170 A),  270  and/or  370 , respectively, described in detail above. Accordingly, such portions and/or aspects are not described in further detail herein. 
     The fluid transfer device  405  (also referred to herein as “transfer device”) can be any suitable shape, size, and/or configuration. In some implementations, the transfer device  405  can be configured to withdraw bodily fluid (e.g., blood) from a patient and into and/or through the transfer device  405 . In addition, the transfer device  405  can be configured to transfer at least some of the withdrawn bodily fluid to one or more other devices, reservoirs, containers, vials, machines, tests, assays, etc., such as the rapid diagnostic testing device  470  and/or one or more fluid collection devices (not shown in  FIGS. 5A and 5B ). 
     The transfer device  405  includes at least a housing  410  and an actuator  450 . The housing  410  of the device  405  can be any suitable shape, size, and/or configuration. For example, in some embodiments, the housing  410  can be similar to and/or the substantially the same as the housings  210  and/or  310  described above. Specifically, the housing  410  has and/or forms an inlet  412  and an outlet  413  and can define at least one fluid flow path therebetween (not shown in  FIGS. 5A and 5B ). The inlet  412  can be any suitable inlet or port and can be configured to establish fluid communication between the housing  410  to a bodily fluid source (e.g., a patient). The outlet  413  can be any suitable outlet or port and can be configured to establish fluid communication between the housing  410  and a fluid collection device (not shown in  FIGS. 5A and 5B ), such as any of those described in detail above. The one or more fluid flow paths defined by the housing  410  extend between the inlet  412  and the outlet  413  and can selectively establish fluid communication therebetween, as described in further detail herein. 
     As described above with reference to the housing  310 , the housing  410  shown in  FIGS. 5A and 5B  includes, forms, and/or couples to a sequestration chamber  430  configured to be selectively placed in fluid communication with the fluid flow path and/or at least the inlet  412 . In addition, the sequestration chamber  430  includes, is coupled to, and/or is otherwise configured to be placed in fluid communication with the rapid diagnostic testing device  470 . The sequestration chamber  430  can have any suitable shape, size, and/or configuration. For example, in some embodiments, the sequestration chamber  430  can have a volume and/or fluid capacity between about 0.1 mL and about 5.0 mL. In some embodiments, the sequestration chamber  430  can have a volume measured in terms of an amount of bodily fluid (e.g., the initial or first amount of bodily fluid) configured to be transferred into the sequestration chamber  430  and/or configured to be tested by the rapid diagnostic testing device  470 . In some embodiments, the sequestration chamber  430  and/or at least a portion thereof can be substantially similar in at least form and/or function to the sequestration chamber  330  described above with reference to  FIG. 4 . Thus, portions and/or aspects of the sequestration chamber  430  are not described in further detail herein. 
     In the embodiment shown in  FIGS. 5A and 5B , at least a portion of the sequestration chamber  430  can include an absorbent and/or hydrophilic material  431 . In addition, the sequestration chamber  430  includes a sampling portion  435  and a vent  424 . The absorbent material  431  can be disposed within a portion of the sequestration chamber  430 . For example, one or more inner surfaces of the sequestration chamber  431  can be lined with and/or formed by the absorbent material  431 . As shown in  FIGS. 5A and 5B , the arrangement of the sequestration chamber  430  can be such that a sampling portion  435  of the sequestration chamber  430  is downstream of the absorbent material  431  (e.g., relative to a portion of the sequestration chamber  430  is temporarily fluidically coupled to the inlet  412 . In this manner, the absorbent material  431  can be configured to receive and/or absorb a first portion or part of an initial volume of bodily fluid transferred into the sequestration chamber  430 . In some implementations, the absorbent material  431  can become saturated after absorbing a predetermined amount or volume of bodily fluid such that any additional amount or volume of bodily fluid transferred into the sequestration chamber  430  can flow into the sampling portion  435 . As described in further detail herein, the sampling portion  435  of the sequestration chamber  430  can be placed in fluid communication with the rapid diagnostic testing device  470  to transfer a part of the initial volume of bodily fluid disposed in the sampling portion  435  into the rapid diagnostic testing device  470 . 
     The vent  424  is coupled to the housing  410  and/or the sequestration chamber  430  and is in fluid communication with an internal volume of the sequestration chamber  430 . The vent  424  can be configured to vent and/or otherwise allow a flow of air or gas out of the sequestration chamber  430  as the initial volume of bodily fluid is transferred into the sequestration chamber  430 . In some implementations, venting air or gas out of the sequestration chamber  430  (e.g., via the vent  424 ) can reduce an amount of pressure within the sequestration chamber  430  that may otherwise limit and/or impede the flow of bodily fluid into the sequestration chamber  430 . In some implementations, venting air or gas through the vent  424  can allow for a negative pressure differential that can facilitate the transfer of the initial volume of bodily fluid into the sequestration chamber  430 . While the absorbent material  431  and the vent  424  are shown in  FIGS. 5A and 5B  as being separate components, in other embodiments, the absorbent material  431  can form one or more vents configured to vent the sequestration chamber  430  as well as being configured to absorb a first part or portion of the initial volume. For example, the absorbent material  431  can form one or more walls or one or more portions of a wall of the sequestration chamber  430 . 
     The actuator  450  of the device  405  can be any suitable shape, size, and/or configuration. In some embodiments, the actuator  450  and/or aspects or portions thereof can be similar to and/or substantially the same as the actuators  150 ,  250 , and/or  350  described in detail above. In some embodiments, the actuator  450  can be at least partially disposed within and/or partially formed by the housing  410 . As described above, the actuator  450  can be configured to control, direct, and/or otherwise facilitate a selective flow of fluid through at least a portion of the housing  410  and/or at least a portion of the one or more fluid flow paths. In some embodiments, the actuator  450  can be a member or device configured to transition between any number of states (e.g., two, three, four, or more) and in any suitable manner (e.g., user actuation, automatic actuation, mechanical actuation, electronic actuation, chemical actuation, and/or the like). 
     More particularly, in the embodiment shown in  FIGS. 5A and 5B , the actuator  450  can be configured to transition between a first state in which the inlet  412  is in fluid communication with the sequestration chamber  430  ( FIG. 5A ) and a second state in which the inlet  412  is in fluid communication with the outlet  413  ( FIG. 5B ). In some embodiments, the actuator  450  can be configured to sequester, separate, isolate, and/or otherwise prevent fluid communication between the outlet  413  and inlet  412  and/or the outlet  413  and the sequestration chamber  430  when in the first state. Conversely, in the second state, the actuator  450  can be configured to allow a subsequent volume of bodily fluid (e.g., a volume of bodily fluid after the initial volume of bodily fluid) to be transferred from the inlet  412 , through one or more fluid flow paths (not shown in  FIGS. 5A and 5B ) and to the outlet  413  (and/or a fluid collection device fluidically coupled to the outlet  413 ). In addition, when in the second state, the actuator  450  can be configured to sequester, separate, isolate, and/or otherwise prevent fluid communication between the sequestration chamber  430  and the inlet  412 , the sequestration chamber  430  and the outlet  413 , and/or the sequestration chamber  430  and at least a portion of the fluid flow path extending between the inlet  412  and the outlet  413 . As such, the actuator  450  can be structurally and/or functionally similar to the actuators  150 ,  250 , and/or  350  described in detail above. 
     The rapid diagnostic testing device  470  (also referred to herein as “rapid testing device” or simply “testing device”) can be any suitable shape, size, and/or configuration. In some embodiments, the rapid testing device  470  can be removably coupled to the transfer device  405  or any suitable portion thereof. For example, in the embodiment shown in  FIGS. 5A and 5B , the rapid testing device  470  can be configured to engage or couple to the housing  410  and/or sequestration chamber  4350  such that the rapid testing device  470  is placed in fluid communication with the sampling portion  435  of the sequestration chamber  430 . In some embodiments, the housing  410  can include and/or can form a port, adapter, and/or receiving portion to which the rapid testing device  470  can be coupled or into which the rapid testing device  470  can be inserted to establish fluid communication between the rapid testing device  470  and the sampling portion  435  of the sequestration chamber  430 . Moreover, in the embodiment shown in  FIGS. 5A and 5B , transitioning the actuator  450  from its first state to its second state can establish fluid communication between the sequestration chamber  430  and the rapid testing device  470  (e.g., via one or more flow controllers, valves, septa, ports, seals, aligned flow paths, and/or other suitable member or device for establishing fluid communication). In some embodiments, transitioning the actuator  450  from its first state to its second state can establish fluid communication between the sequestration chamber  430  and the rapid testing device  470 . 
     In some implementations, the rapid testing device  470  can be configured to receive the first amount of bodily fluid from the sampling portion  435  of the sequestration chamber  430  and to use the first amount of bodily fluid to perform one or more tests, assays, and/or diagnostic procedures. The rapid testing device  470  can be any suitable testing device. For example, the rapid testing device  470  can be an LFA or the like, as described in detail above with reference to the LFA  170 A shown in  FIG. 2 . In some implementations, the testing device  470  and/or aspects or portions thereof can be substantially similar to the rapid testing devices  170 ,  270 , and/or  370  described in detail above. Accordingly, the rapid testing device  470  and/or aspects or portions thereof is/are not described in further detail herein. 
     The system  400  can be used to procure one or more volumes of bodily fluid from a patient, which can be used in one or more tests, assays, and/or diagnostic procedures. As described above, for example, the inlet  412  can be placed in fluid communication with a bodily fluid source. In some instances, the actuator  450  can be in a first state when the inlet  412  is placed in fluid communication with the bodily fluid source (e.g., the portion of the patient), thereby establishing fluid communication between the inlet  412  and the sequestration chamber  430  and sequestering the outlet  413  from the inlet  412 , as shown in  FIG. 5A . As such, the transfer device  405  can be configured to transfer an initial volume of bodily fluid from the bodily fluid source (e.g., the patient) to the rapid testing device  470 . In some implementations, the initial volume of bodily fluid can flow to and/or into the sequestration chamber  430  in response to a pressure differential between the sequestration chamber  430  and the inlet  412  and/or the bodily fluid source. In some embodiments, the vent  424  can be configured to allow a flow of air or gas out of the sequestration chamber  430 , which can facilitate the flow of the initial volume of bodily fluid into the sequestration chamber  430 . In some embodiments, the vent  424  can be configured to vent the sequestration chamber  430  in a manner similar to the vents and/or the like described, for example, in the &#39;117 publication. 
     The initial volume of bodily fluid can be any suitable volume of bodily fluid, such as any of the volumes or amounts described above. More specifically, in the embodiment shown in  FIGS. 5A and 5B , the initial volume of bodily fluid can be sufficient to saturate and/or wet (or substantially saturate and/or wet) the absorbent material  431  disposed in the sequestration chamber  430  and to fill (or substantially fill) the sampling portion  435  of the sequestration chamber  430 . In some embodiments, the filling of the sequestration chamber  430  can be serial in that the flow of the initial volume of bodily fluid is first absorbed by the absorbent material  431  until the absorbent material  431  is saturated and then a remaining portion of the initial volume of bodily fluid can flow into and/or fill the sampling portion  435  of the sequestration chamber  430 . In some implementations, serially filling the sequestration chamber  430  can be such that the portion of the initial volume of bodily fluid (e.g., a first portion) can contain contaminants (e.g., associated with and/or resulting from a venipuncture event, fluidically coupling one or more components, and/or the like), while the portion of the initial volume of bodily fluid (e.g., a second portion) can contain a reduced amount of contaminants and/or can be substantially free of contaminants. In some instances, once the initial volume of bodily fluid is transferred into the sequestration chamber  430 , the flow of bodily fluid can stop and/or a pressure differential can be substantially equalized that can slow or stop the flow of bodily fluid. 
     In some embodiments, after transferring the initial volume of bodily fluid into the sequestration chamber  430 , the actuator  450  can be transitioned from its first state ( FIG. 5A ) to its second state ( FIG. 5B ). For example, in some embodiments, the actuator  450  can be moved, slid, switched, rotated, and/or otherwise transitioned relative to the inlet  412  and the outlet  413 . In some embodiments, transitioning and/or moving the actuator  450  can include transitioning and/or moving at least a portion of the housing  410 . In other embodiments, the actuator  450  can be moved relative to the housing  410  (e.g., the housing  410  need not be transitioned and/or moved). 
     As shown in  FIG. 5B , transitioning the actuator  450  from the first state to the second state can establish fluid communication between the sampling portion  435  of the sequestration chamber  430  and the rapid testing device  470 , and can sequester the sequestration chamber  430  from the inlet  412 , the outlet  413 , and/or one or more portions of the fluid flow path therebetween. In some embodiments, the arrangement of the actuator  450  can be such that placing the actuator  450  in the second state results in and/or increases an air gap between a portion of the sequestration chamber  430  including the absorbent material  431  and a portion of the sequestration chamber  430  including, forming, and/or defining the sampling portion  435 . The air gap can facilitate the transfer of bodily fluid from the sampling portion  435  to the rapid testing device  470  (e.g., by allowing a desired relative pressure or pressure differential). In addition, in instances in which contaminants are contained in the portion of the initial volume absorbed by the absorbent material  431 , such an arrangement can ensure that only the portion of the initial volume disposed in the sampling portion  435  of the sequestration chamber  430  is transferred to the rapid testing device  470 . 
     At least a portion of the initial volume of bodily fluid can be transferred from the sampling portion  435  of the sequestration chamber  430  and into the rapid testing device  470  when the actuator  450  is transitioned from its first state to its second state. In some implementations, the transferring of the portion of the initial volume can be automatic. In other implementations, the transferring of the portion of the initial volume can be in response to one or more user inputs and/or the like. In some implementations, the placement of the actuator  450  in the second state can fluidically couple the rapid testing device  470  to the sampling portion  435  of the sequestration chamber  430 , thereby allowing the fluid transfer therebetween. 
     In some embodiments, transferring the portion of the initial volume of bodily fluid into the rapid testing device  470  can initiate a test and/or assay of or on the portion of the initial volume of bodily fluid, as described in detail above with reference to the rapid testing device  270 . In some instances, the system  400 , the transfer device  405 , and/or the rapid testing device  470  can be configured to provide a buffer  481  (or any other suitable solution) that can be mixed with the portion of the initial volume of bodily fluid, as shown in  FIG. 5B . The rapid testing device  470  can be configured to perform any suitable test and/or assay. For example, the rapid testing device  470  can be an LFA configured to test for the presence of lactate and/or PCT, as described in detail above. Moreover, once the test or assay is complete, the rapid testing device  470  can be configured to output a test result, which can be detected and/or assessed by a human and/or one or more electronic devices, as described in detail above with reference to the rapid testing devices  170 ,  270 , and/or  370 . 
     Transitioning the actuator  450  from its first state to its second state can sequester, isolate, separate, and/or retain the initial volume of the bodily fluid in the sequestration chamber  430  and/or the rapid testing device  470 . Said another way, the actuator  450  can sequester and/or isolate the sequestration chamber  430  from the inlet  412 , the outlet  413 , and one or more portions of the fluid flow path. In some instances, sequestering the initial volume of bodily fluid in the sequestration chamber  430  can also sequester contaminants in the initial volume (e.g., at least the portion of the initial volume absorbed by the absorbent material  431 ). Moreover, the arrangement of the rapid testing device  470  can be such that the tests and/or assays performed by the rapid testing device  470  are not susceptible to such contamination, which means that the accuracy of the test results output by the rapid testing device  470  is not affected by such contamination, as described in detail above. In other instances, having the first part or portion of the initial volume of bodily fluid received and/or absorbed by the absorbent material  431  can allow the rapid testing device  470  to perform one or more tests that may be at least partially sensitive to contaminants. 
     In addition, transitioning the actuator  450  to its second state establishes fluid communication between the inlet  412  and the outlet  413  via at least a portion of the fluid flow path disposed therebetween. For example, transitioning the actuator  450  from its first state to its second state can open or close a port or valve, move one or more seals, move or remove one or more obstructions, define one or more portions of a flow path, and/or the like. In some implementations, the outlet  413  can be placed in fluid communication with a fluid collection device prior to or after the actuator is placed in its second state. As described in detail above, the fluid collection device can define and/or can be configured to generate a negative pressure and/or suction force that can be operable to draw bodily fluid into the fluid collection device. Thus, in response to the negative pressure and/or suction force, one or more subsequent volume(s) of the bodily fluid can flow from the inlet  412 , through any suitable fluid flow path or portion thereof, through the outlet  413 , and into the fluid collection device. As described above, sequestering the initial volume of bodily fluid in the sequestration chamber  430  prior to collecting or procuring one or more subsequent volumes of bodily fluid reduces and/or substantially eliminates an amount of contaminants in the one or more subsequent volumes. Accordingly, the system  400  can be configured to procure the initial volume of bodily fluid, which can be used in one or more rapid testing processes, and the subsequent volume(s) of bodily fluid, which can be used in testing that has a relatively high sensitivity to contamination (e.g., blood culture testing), as described above with reference to the systems  100 ,  200 , and/or  300 . 
       FIGS. 6A-6D  are schematic illustrations of at least a portion of a fluid transfer and assay system  500 , according to an embodiment. The fluid transfer and assay system  500  (also referred to herein as “system”) can include at least a fluid transfer device  505  and a rapid diagnostic testing device  570 . Portions and/or aspects of the fluid transfer device  505  and/or the rapid diagnostic testing device  570  can be similar to and/or substantially the same as the fluid transfer devices  105 ,  205 ,  305 , and/or  405 , and/or the rapid diagnostic testing devices  170  (and/or the LFA  170 A),  270 ,  370 , and/or  470 , respectively, described in detail above. Accordingly, such portions and/or aspects are not described in further detail herein. 
     The fluid transfer device  505  (also referred to herein as “transfer device”) can be any suitable shape, size, and/or configuration. In some implementations, the transfer device  505  can be configured to withdraw bodily fluid (e.g., blood) from a patient and into and/or through the transfer device  505 . In addition, the transfer device  505  can be configured to transfer at least some of the withdrawn bodily fluid to one or more other devices, reservoirs, containers, vials, machines, tests, assays, etc., such as the rapid diagnostic testing device  570  and/or one or more fluid collection devices (not shown in  FIGS. 6A-6D ). The transfer device  505  and/or aspects or portions thereof can be substantially similar to any of the transfer devices  105 ,  205 ,  305 , and/or  405  described in detail above. Thus, the transfer device  505  is not described in further detail herein. 
     The rapid diagnostic testing device  570  (also referred to herein as “rapid testing device” or simply “testing device”) can be any suitable testing device. In some implementations, the testing device  570  and/or aspects or portions thereof can be substantially similar to the rapid testing devices  170  (and/or the LFA  170 A),  270 ,  370 , and/or  470  described in detail above. Accordingly, the rapid testing device  570  and/or aspects or portions thereof is/are not described in further detail herein. 
     In the embodiment shown in  FIGS. 6A-6D , the rapid testing device  570  can be an LFA or the like, as described in detail above with reference to the LFA  170 A shown in  FIG. 2 . The rapid testing device  570  includes a substrate  571  having any suitable configuration of capillary beds or the like, as described in detail above. In addition, the rapid testing device  570  includes a coupling member  578  that can be coupled to the substrate  571  via an attachment mechanism  579 . The coupling member  578  can be any suitable coupling member configured to establish fluid communication with an inner volume of the transfer device  505  in response to the rapid testing device  570  being coupled thereto. For example, as shown in  FIGS. 6A and 6B , the rapid testing device  570  and/or the coupling member  578  thereof can be configured to couple to the transfer device  505  via a port  525  (e.g., any suitable port, vent, coupler, opening, valve, junction, etc.). In some embodiments, the coupling member  578  can be, for example, a puncture member, needle, tube, and/or the like that can puncture and/or otherwise advance through the port  525 . In some embodiments, the coupling member  578  can be a capillary member or the like configured to transfer fluid via capillary action. In some embodiments, the port  525  can be self-healing allowing the port  525  to seal once the coupling portion  578  of the rapid testing device  570  is removed therefrom. In some embodiments, the port  525  and/or at least a portion of thereof can include and/or can form a vent similar to the vent  424 . 
     The attachment mechanism  579  can be any suitable member, mechanism, device, etc. configured to attach the coupling member  578  to the substrate  571 . In some embodiments, the attachment mechanism  579  can be configured to transition between two or more states or configuration to selectively place the coupling member  578  in fluid communication with a portion of the substrate  571  (e.g., a sample portion, element, and/or capillary bed). More particularly, the attachment mechanism  579  can be configured to transition between a first state and/or configuration ( FIGS. 6A-6C ) to a second state and/or configuration ( FIG. 6D ). 
     When in the first state, the rapid testing device  570  can be coupled to the transfer device  505  and the coupling portion  578  can establish fluid communication with the inner volume of the transfer device  505  (e.g., via the port  525 ). As shown in  FIG. 6B , the coupling member  578  can receive at least portion of the volume of bodily fluid disposed in the transfer device  505  (e.g., via capillary action, a pressure differential, and/or any other fluid transfer modality). As shown in  FIGS. 6C and 6D , once the coupling member  578  has received a desired volume of bodily fluid, the rapid testing device  570  can be decoupled from the transfer device  505  and the attachment mechanism  579  can be transitioned from its first state to its second state. 
     For example, in some embodiments, the attachment mechanism  579  can be a living hinge or the like that can be bent, folder, deformed, and/or otherwise reconfigured. When the attachment mechanism  579  is in the second state, the coupling member  578  can be in fluid communication with the portion of the substrate  571  (e.g., a sample portion, element, and/or capillary bed), as shown in  FIG. 6D . Thus, the volume of bodily fluid contained in the coupling member  578  can be transferred to the portion of the substrate  571 . In addition, in some implementations, when the attachment mechanism  579  is in the second state, a buffer  581  and/or any other suitable solution can be transferred to the substrate  571 . The buffer  581  can be transferred to the substrate  571  via the coupling member  578 , any suitable portion of the attachment mechanism  579 , and/or any other suitable portion of the rapid testing device  570 . As such, the buffer  581  can mix with the volume of bodily fluid and the mixture can flow along the substrate  571  for testing, as described in detail above. In some implementations, the rapid testing device  570  can be configured to test for the presence of lactate and/or PCT, which can be indicative of a patient condition such as sepsis. Moreover, once the test or assay is complete, the rapid testing device  570  can be configured to output a test result, which can be detected and/or assessed by a human and/or one or more electronic devices, as described in detail above with reference to the rapid testing devices  170 ,  270 ,  370 , and/or  470 . 
       FIGS. 7A-7D  are schematic illustrations a fluid transfer and assay system  600 , according to an embodiment. The fluid transfer and assay system  600  (also referred to herein as “system”) can include at least a fluid transfer device  605  and a rapid diagnostic testing device  670 . Portions and/or aspects of the fluid transfer device  605  and/or the rapid diagnostic testing device  670  can be similar to and/or substantially the same as the fluid transfer devices  105 ,  205 ,  305 ,  405 , and/or  505 , and/or the rapid diagnostic testing devices  170  (and/or the LFA  170 A),  270 ,  370 ,  470 , and/or  570 , respectively, described in detail above. Accordingly, such portions and/or aspects are not described in further detail herein. 
     The fluid transfer device  605  (also referred to herein as “transfer device”) can be any suitable shape, size, and/or configuration. In some implementations, the transfer device  605  can be configured to withdraw bodily fluid (e.g., blood) from a patient and into and/or through the transfer device  605 . In addition, the transfer device  605  can be configured to transfer at least some of the withdrawn bodily fluid to one or more other devices, reservoirs, containers, vials, machines, tests, assays, etc., such as the rapid diagnostic testing device  670  and/or one or more fluid collection devices (not shown in  FIGS. 7A-7D ). 
     The transfer device  605  includes at least a housing  610  and an actuator  650 . The housing  610  of the device  605  can be any suitable shape, size, and/or configuration. For example, in some embodiments, the housing  610  can be similar to and/or the substantially the same as the housings  210 ,  310 , and/or  410  described above. Specifically, the housing  610  has and/or forms an inlet  612  and an outlet  613  and can define a fluid flow path  615  therebetween. The inlet  612  can be any suitable inlet or port and can be configured to establish fluid communication between the housing  610  to a bodily fluid source (e.g., a patient). The outlet  613  can be any suitable outlet or port and can be configured to establish fluid communication between the housing  610  and a fluid collection device (not shown in  FIGS. 7A-7D ), such as any of those described in detail above. The fluid flow path  615  defined by the housing  610  extends between the inlet  612  and the outlet  613  and can selectively establish fluid communication therebetween, as described in further detail herein. 
     As described above with reference to the housing  410 , the housing  610  shown in  FIGS. 7A-7D  includes, forms, and/or couples to a sequestration chamber  630  configured to be selectively placed in fluid communication with the fluid flow path and/or at least the inlet  612 . In addition, the sequestration chamber  630  includes, forms, and/or defines a sampling portion  635  and a port  625 . The sequestration chamber  630  can have any suitable shape, size, and/or configuration. For example, in some embodiments, the sequestration chamber  630  and/or at least a portion thereof can be substantially similar in at least form and/or function to the sequestration chambers  330  and/or  430  described in detail above. Thus, portions and/or aspects of the sequestration chamber  630  are not described in further detail herein. 
     The port  625  is coupled to the housing  610  and/or the sequestration chamber  630  and is in fluid communication with an internal volume of the sequestration chamber  630 . More specifically, as shown in  FIGS. 7A-7D , the port  625  is included in and/or coupled to the housing  610  and in fluid communication with the sampling portion  635  of the sequestration chamber  630 . In some embodiments, the port  625  and/or at least a portion thereof can be configured to vent and/or otherwise allow a flow of air or gas out of the sequestration chamber  630  as the initial volume of bodily fluid is transferred into the sequestration chamber  630 , as described in detail above with reference to the vent  424 . The sampling portion  635  of the sequestration chamber  630  can be placed in fluid communication with the rapid diagnostic testing device  670  to transfer a part of the initial volume of bodily fluid disposed in the sampling portion  635  into the rapid diagnostic testing device  670 . In the embodiment shown in  FIGS. 7A-7D , for example, the rapid diagnostic testing device  670  can be placed in fluid communication with the sampling portion  635  via the port  625  and/or any other suitable port, as described above with reference to the port  525  shown in  FIGS. 6A and 6B . 
     The actuator  650  of the device  605  can be any suitable shape, size, and/or configuration. In some embodiments, the actuator  650  and/or aspects or portions thereof can be similar to and/or substantially the same as the actuators  150 ,  250 ,  350 , and/or  450  described in detail above. In some embodiments, the actuator  650  can be at least partially disposed within and/or partially formed by the housing  610 . As described above, the actuator  650  can be configured to control, direct, and/or otherwise facilitate a selective flow of fluid through at least a portion of the housing  610  and/or at least a portion of the one or more fluid flow paths. The actuator  650  can be any suitable member(s) or device(s) configured to transition between any number of states (e.g., two, three, four, or more) and in any suitable manner (e.g., user actuation, automatic actuation, mechanical actuation, electronic actuation, chemical actuation, and/or the like). 
     More particularly, in the embodiment shown in  FIGS. 7A-7D , the actuator  650  includes a first member  651  and a second member  660 . The first member  651  of the actuator  650  can be any suitable shape, size, and/or configuration. The first member  651  can be a plunger or the like having at least one seal  652  (e.g., disposed at an end portion of the first member  651 ). In some embodiments, the end portion of the first member  651  can, for example, separate and/or at least partially define the sampling portion  635  of the sequestration chamber  630 . For example, the sampling portion  635  of the sequestration chamber  630  can be disposed on one side of the end portion of the first member  651  while the remaining portion of the sequestration chamber  630  is disposed on the opposite side of the end portion of the first member  651 . Moreover, the arrangement of the seal  652  can be such that the seal  652  engages and/or contacts an inner surface of the housing  610  to form and/or define a substantially fluid tight seal therebetween. The first member  651  also includes one or more valves, ports, openings, channels, selectively permeable members, and/or the like (referred to herein as “valve  653 ”) configured to establish selective fluid communication between the sampling portion  635  of the sequestration chamber  635  and the remaining portions of the sequestration chamber  630 , as described in further detail herein. 
     The second member  660  of the actuator  650  can be any suitable shape, size, and/or configuration. For example, in the embodiment shown in  FIGS. 7A-7D , the second member  660  can be disposed about and/or on at least a portion of the first member  651 . The second member  660  includes a set of seals  661 . More particularly, the second member  660  can include a set of three seals. As shown, the second member  660  can have a first end portion and a second end portion opposite the first end portion. The first end portion of the second member  660  includes an outer seal  661  configured to engage and/or contact an inner surface of the housing  610  to define a substantially fluid tight seal therebetween. In addition, the first end portion of the second member  660  includes an inner seal  661  configured to engage and/or contact a portion of the first member  651  to define a substantially fluid tight seal therebetween. The second end portion of the second member  660  includes an outer seal  661  configured engage and/or contact an inner surface of the housing to define a substantially fluid tight seal therebetween. 
     As shown in  FIGS. 7A-7D , the arrangement of the first member  651  and the second member  660  of the actuator is such that a portion of the sequestration chamber  630  (e.g., the portion other than the sampling portion  635 ) is disposed and/or defined between, for example, the end portion of the first member  651  and the first end portion of the second member  660 . In addition, the second member  660  is configured to at least partially define the fluid flow path  615  between the first end portion and the second end portion of the second member  660 . Thus, the first end portion of the second member  660  and the seals  661  included in the first end portion, sequester and/or fluidically isolate the sequestration chamber  630  from the fluid flow path  615 . 
     The actuator  650  is configured to transition between at least a first state, a second state, and a third state. As shown in  FIGS. 7A-7D , the end portion of first member  651  and the seal  652  included therein are disposed on and maintained on a first side of the inlet  612  and a first side of the outlet  613 , regardless of the state of the actuator  650 . Similarly, the second end portion of the second member  660  and the seal member  661  included therein are disposed on and maintained on a second side of the inlet  612  (opposite the first side) and a second side of the outlet  613  (opposite the first side), regardless of the state of the actuator  650 . The first end portion of the second member  660  and the seal members  661  disposed therein, however, are configured to be (i) disposed on the second side of the inlet  612  and the first side of the outlet  613  when the actuator  650  is in the first state and the second state ( FIGS. 7A and 7B ) and (ii) disposed on the first side of the inlet  612  and the first side of the outlet  613  when the actuator  650  is in the third state ( FIGS. 7C and 7D ). Thus, the arrangement of the actuator  650  is such that transitioning the actuator  650  can selectively direct and/or divert a flow of fluid between (i) the inlet  612  and the sequestration chamber  630  and (ii) the inlet  612  and the outlet  613  via the fluid flow path  615 , as described in further detail herein. 
     The rapid diagnostic testing device  670  (also referred to herein as “rapid testing device” or simply “testing device”) can be any suitable testing device. For example, the rapid testing device  670  can be an LFA or the like, as described in detail above with reference to the LFA  170 A shown in  FIG. 2 . In some implementations, the testing device  670  and/or aspects or portions thereof can be substantially similar to the rapid testing devices  170 ,  270 ,  370 , and/or  470  described in detail above. Accordingly, the rapid testing device  670  and/or aspects or portions thereof is/are not described in further detail herein. 
     As shown in  FIG. 7D , the rapid testing device  670  can be configured to engage or couple to the housing  610  via the port  625 . In some embodiments, for example, the port  625  can be a valve, coupler, and/or any suitable reconfigurable member or device configured to (i) vent air or gas from the sequestration chamber  630 , as described above with reference to the vent  424 , and (ii) receive a portion of the rapid testing device  670  to place the rapid testing device  670  in fluid communication with the sampling portion  635  of the sequestration chamber  630 . For example, the rapid testing device  670  can include a coupling member  678  that can establish fluid communication with the sampling portion  635  of the sequestration chamber  630  when the rapid testing device  670  is coupled thereto. In some embodiments, the coupling member  678  can be, for example, a puncture member, needle, tube, capillary, and/or the like that can puncture and/or otherwise advance through the port  625 . In some embodiments, the coupling member  678  can be substantially similar to the coupling member  578  described above with reference to  FIGS. 6A-6D . In some embodiments, the port  625  can be self-healing allowing the port  625  to seal once the coupling portion  678  of the testing device  670  is removed therefrom. As shown in  FIG. 7D , the coupling portion  678  of the testing device  670  can be coupled to a substrate  671  of the testing device  670  (e.g., coupled directly to the substrate  671  and/or coupled via an attachment mechanism such as the attachment mechanism  579 ). In this manner, the coupling portion  678  can transfer a volume of bodily fluid from the sampling portion  635  of the sequestration chamber  630  into the testing device  670 . In response, the testing device  670  can use the volume of bodily fluid to perform one or more tests, assays, and/or diagnostic procedures. 
     The system  600  can be used to procure one or more volumes of bodily fluid from a patient, which can be used in one or more tests, assays, and/or diagnostic procedures. As described above, for example, the inlet  612  can be placed in fluid communication with a bodily fluid source. The actuator  650  can be in a first state when the inlet  612  is placed in fluid communication with the bodily fluid source (e.g., the portion of the patient), thereby establishing fluid communication between the inlet  612  and the sequestration chamber  630  and sequestering the outlet  613  from the inlet  612 , as shown in  FIG. 7A . Moreover, when the actuator  650  is in the first state, the end portion of the first member  651  can be near or adjacent to the first side of the inlet  612  and the first end portion of the second member  660  can be near or adjacent to the second side of the inlet  612 . In this manner, the portion of the sequestration chamber  630  defined between the first member  651  and the second member  660  can have a first volume. 
     In some instances, once the inlet  612  is placed in fluid communication with the bodily fluid source, the actuator  650  can be transitioned from its first state to its second state. For example, as shown in  FIG. 7B , the first member  651  can be transitioned or moved relative to the inlet  612  and the second member  660 , which in turn, increases a volume of the portion of the sequestration chamber  630  disposed between the first member  651  and the second member  660 . In addition, the transitioning and/or movement of the first member  651  can reduce a volume of the sampling portion  635  of the sequestration chamber  630 , and the arrangement of the port  625  can be such that air or gas contained in the sampling portion  635  can be allowed to escape and/or flow out of the sampling portion  635 . The end portion of the first member  651  can be configured to limit and/or substantially prevent a flow of air from the sampling portion  635  of the sequestration chamber  630  into the remaining portion of the sequestration chamber  630  such that the increase in the volume within the remaining portion of the sequestration chamber  630  results in a negative pressure differential operative in drawing the initial volume of bodily fluid from the bodily fluid source, through the inlet  612 , and into the sequestration chamber  630 , as shown in  FIG. 7B . 
     The initial volume of bodily fluid can be any suitable volume of bodily fluid, such as any of the volumes or amounts described above. In some implementations, once the initial volume of bodily fluid is transferred into the sequestration chamber  630 , the flow of bodily fluid can stop and/or a pressure differential can be substantially equalized that can slow or stop the flow of bodily fluid. In such implementations, the actuator  650  can then be transitioned from its second state to its third state. In other implementations, the transitioning of the actuator  650  through the three states can be a substantially continuous transition. In such implementations, the initial volume of bodily fluid can be a volume of bodily fluid that is transferred into the sequestration chamber  630  as the actuator  650  is transitioned from its first state to its second state, and continuing to transition the actuator  650  from its second state to its third state can be operable in stopping the flow into the sequestration chamber  630 . 
     The actuator  650  can be transitioned from its second state to its third state when the initial volume of bodily fluid is contained in the sequestration  630 . As shown in  FIG. 7C , transitioning the actuator  650  to the third state can include transitioning and/or moving the second member  660  relative to the inlet  612  and the first member  651  of the actuator  650 . The transitioning and/or moving of the second member  660  transitions and/or moves the first end portion of the second member from the second side of the inlet  612  to the first side of the inlet  612 , thereby sequestering and/or fluidically isolating the sequestration chamber  630  from the inlet  612 . Moreover, the transitioning and/or moving of the second member  660  relative to the first member  651  can decrease a volume of the portion of the sequestration chamber  630  disposed therebetween. In some implementations, the decrease in the volume of the portion of the sequestration chamber  630  results in an increase in pressure that can be operable in transitioning the valve  653  from a closed state to an open state, thereby allowing at least some of the initial volume of bodily fluid to be transferred into the sampling portion  635  of the sequestration chamber  630 , as shown in  FIG. 7C . 
     As shown in  FIG. 7D , the rapid testing device  670  can be coupled to the housing  610  and/or can otherwise be placed in fluid communication with the sampling portion  635  of the sequestration chamber  630  (e.g., via the coupling member  678 ). Accordingly, at least a portion of the bodily fluid can be transferred from the sampling portion  635  of the sequestration chamber  630  and into the rapid testing device  670 . In some implementations, the transferring of the portion of the initial volume can be automatic. In other implementations, the transferring of the portion of the initial volume can be in response to one or more user inputs and/or the like (e.g., via the actuator  650  and/or any other suitable actuation mechanism or the like not shown in  FIGS. 7A-7D ). In some embodiments, transferring the portion of the initial volume of bodily fluid into the rapid testing device  670  can initiate a test and/or assay of or on the portion of the initial volume of bodily fluid, as described in detail above with reference to the rapid testing device  270 . Although not shown in  FIGS. 7A-7D , in some instances, the system  600 , the transfer device  605 , and/or the rapid testing device  670  can be configured to provide a buffer (or any other suitable solution) that can be mixed with the portion of the initial volume of bodily fluid. The rapid testing device  670  can be configured to perform any suitable test and/or assay. For example, the rapid testing device  670  can be an LFA configured to test for the presence of lactate and/or PCT, as described in detail above. Moreover, once the test or assay is complete, the rapid testing device  670  can be configured to output a test result, which can be detected and/or assessed by a human and/or one or more electronic devices, as described in detail above with reference to the rapid testing devices  170 ,  270 ,  370 , and/or  470 . 
     As described above, transitioning the actuator  650  from its second state to its third state can sequester, isolate, separate, and/or retain the initial volume of the bodily fluid in the sequestration chamber  630  and/or the rapid testing device  670 , which in turn, can also sequester contaminants in the initial volume. Moreover, the arrangement of the rapid testing device  670  can be such that the tests and/or assays performed by the rapid testing device  670  are not susceptible to such contamination, which means that the accuracy of the test results output by the rapid testing device  670  is not affected by such contamination, as described in detail above. 
     As shown in  FIGS. 7C and 7D , transitioning the actuator  650  from its second state to its third state establishes fluid communication between the inlet  612  and the outlet  613  via the fluid flow path  615  disposed between the first end portion and the second end portion of the second member  660  of the actuator  650 . More particularly, when the actuator  650  is in its third state, the first end portion of the second member  660  is disposed on the first side of the inlet  612  and the second end portion of the second member  660  is disposed on the second side of the outlet  613 . In other words, both the inlet  612  and the outlet  613  are disposed between the first end portion and the second end portion of the second member  660 . Thus, the fluid flow path  615  can establish fluid communication between the inlet  612  and the outlet  613  when the actuator  650  is in the third state. 
     In some implementations, the outlet  613  can be placed in fluid communication with a fluid collection device (not shown in  FIGS. 7A-7D ) prior to or after the actuator  650  is placed in its third state. As described in detail above, the fluid collection device can define and/or can be configured to generate a negative pressure and/or suction force that can be operable to draw bodily fluid into the fluid collection device. Thus, in response to the negative pressure and/or suction force, one or more subsequent volume(s) of the bodily fluid can flow from the inlet  612 , through the fluid flow path  615 , through the outlet  613 , and into the fluid collection device. As described above, sequestering the initial volume of bodily fluid in the sequestration chamber  630  prior to collecting or procuring one or more subsequent volumes of bodily fluid reduces and/or substantially eliminates an amount of contaminants in the one or more subsequent volumes. Accordingly, the system  600  can be configured to procure the initial volume of bodily fluid, which can be used in rapid testing that has relatively low sensitivity to contamination, and the subsequent volume(s) of bodily fluid, which can be used in testing that has a relatively high sensitivity to contamination, as described above with reference to the systems  100 ,  200 ,  300 , and/or  400 . 
       FIGS. 8 and 9A-9D  illustrate a fluid transfer and assay system  700 , according to an embodiment. The fluid transfer and assay system  700  (also referred to herein as “system”) can include at least a fluid transfer device  705  and a rapid diagnostic testing device  770 . Portions and/or aspects of the fluid transfer device  705  and/or the rapid diagnostic testing device  770  can be similar to and/or substantially the same as the fluid transfer devices  105 ,  205 ,  305 ,  405 ,  505 , and/or  605 , and/or the rapid diagnostic testing devices  170  (and/or the LFA  170 A),  270 ,  370 ,  470 ,  570 , and/or  670 , respectively, described in detail above. Accordingly, such portions and/or aspects are not described in further detail herein. 
     The fluid transfer device  705  (also referred to herein as “transfer device”) can be any suitable shape, size, and/or configuration. In some implementations, the transfer device  705  can be configured to withdraw bodily fluid (e.g., blood) from a patient and into and/or through the transfer device  705 . In addition, the transfer device  705  can be configured to transfer at least some of the withdrawn bodily fluid to one or more other devices, reservoirs, containers, vials, machines, tests, assays, etc., such as the rapid diagnostic testing device  770  and/or one or more fluid collection devices (not shown in  FIGS. 8 and 9A-9D ). 
     The transfer device  705  includes at least a housing  710  and an actuator  750 . The housing  710  of the device  705  can be any suitable shape, size, and/or configuration. For example, in some embodiments, the housing  710  can be similar to and/or the substantially the same as at least the housing  610  described above. Specifically, the housing  710  has and/or forms an inlet  712  and an outlet  713  and can define a fluid flow path  715  therebetween. The inlet  712  can be any suitable inlet or port and can be configured to establish fluid communication between the housing  710  to a bodily fluid source (e.g., a patient). The outlet  713  can be any suitable outlet or port and can be configured to establish fluid communication between the housing  710  and a fluid collection device (not shown in  FIGS. 8-9D ), such as any of those described in detail above. The fluid flow path  715  defined at least in part by the housing  710  extends between the inlet  712  and the outlet  713  and can selectively establish fluid communication therebetween, as described in further detail herein. 
     As described above with reference to at least the housing  610 , the housing  710  shown in  FIGS. 8-9D  includes, forms, and/or couples to a sequestration chamber  730  configured to be selectively placed in fluid communication with the fluid flow path and/or at least the inlet  712 . In addition, the housing defines an opening  721  and/or a port configured to receive a portion of the rapid diagnostic testing device  770 , as described in further detail herein. The sequestration chamber  730  can have any suitable shape, size, and/or configuration. For example, in some embodiments, the sequestration chamber  730  and/or at least a portion thereof can be substantially similar in at least form and/or function to the sequestration chambers  330 ,  430 , and/or  630  described in detail above. Thus, portions and/or aspects of the sequestration chamber  730  are not described in further detail herein. 
     The actuator  750  of the device  705  can be any suitable shape, size, and/or configuration. In some embodiments, the actuator  750  and/or aspects or portions thereof can be similar to and/or substantially the same as the actuators  150 ,  250 ,  350 ,  450 , and/or  650  described in detail above. In some embodiments, the actuator  750  can be at least partially disposed within and/or partially formed by the housing  710 . As described above, the actuator  750  can be configured to control, direct, and/or otherwise facilitate a selective flow of fluid through at least a portion of the housing  710  and/or at least a portion of the one or more fluid flow paths. The actuator  750  can be any suitable member(s) or device(s) configured to transition between any number of states (e.g., two, three, four, or more) and in any suitable manner (e.g., user actuation, automatic actuation, mechanical actuation, electronic actuation, chemical actuation, and/or the like). 
     More particularly, as shown in  FIGS. 9A-9D , the actuator  750  includes a first member  751 , a second member  760 , and a third member  765 . The first member  751  of the actuator  750  can be any suitable shape, size, and/or configuration. For example, the first member  751  can be similar in at least form and/or function to the first member  651  of the actuator  650 , described in detail above. The first member  751  includes at least one seal  752  disposed at a first end portion of the first member  751 . The arrangement of the seal  752  can be such that the seal  752  engages and/or contacts an inner surface of the housing  710  to form and/or define a substantially fluid tight seal therebetween. 
     The first end portion of the first member  751  also includes a port  725  that is in fluid communication with a sampling channel  735 . In some embodiments, for example, the port  725  can be a valve, coupler, and/or any suitable reconfigurable member or device configured to (i) vent and/or allow a flow of air or gas out of the sampling channel  735  and (ii) receive a portion of the rapid testing device  770  to place the rapid testing device  770  in fluid communication with the sampling channel  735 , as described above with reference to the port  625 . The sampling channel  735  is disposed in and/or defined by the first member  751 . For example, in some embodiments, the first member  751  can have a hollow elongate portion that defines the sampling channel  735 . Moreover, such a portion of the first member  751  can define and/or can have an opening, port, valve, selectively permeable member, and/or the like configured to place the sampling channel  735  in selective fluid communication with the sequestration chamber  730 . In some embodiments, while the sampling channel  735  is included in and/or defined by the first member  751  of the actuator  750 , the sampling channel  735  can be similar in at least form and/or function to the sampling portion  635  of the sequestration chamber  630 , described above with reference to  FIGS. 7A-7D . 
     As shown in  FIGS. 9A-9D , the first member  751  also includes an engagement member  755  disposed at or on a second end portion of the first member  751 , opposite the first end portion. The engagement member  755  can be any suitable shape, size, and/or configuration. For example, in some embodiments, the engagement member  755  can be a protrusion, tab, button, knob, and/or any other suitable engagement member. The engagement member  755  is configured to selectively engage a portion of the third member  765  of the actuator  750  to direct and/or at least partially control a relative movement between the first member  751 , the second member  760 , and/or the third member  765 , as described in further detail herein. 
     The second member  760  of the actuator  750  can be any suitable shape, size, and/or configuration. As shown in  FIGS. 9A-9D , the second member  760  can be disposed about and/or on at least a portion of the first member  751 . The second member  760  includes a set of seals  761 . As shown, the second member  760  can includes a first end portion having an inner seal  761  and an outer seal  761 , and a second end portion opposite the first end portion having an outer seal  761 . In this manner, the second member  760  can be similar to and/or substantially the same as the second member  660  of the actuator  650 . Accordingly, the second member  760  and/or aspects or portions thereof are not described in further detail herein. 
     The third member  765  can be any suitable shape, size, and/or configuration. In some embodiments, the third member  765  can be included in and/or can form a portion of the housing  710  and/or an exterior portion of the transfer device  705 . For example, as shown in  FIGS. 9A-9D , at least a portion of the housing  710 , first member  751 , and second member  760  can be disposed within a portion of the third member  765 . More particularly, the third member  765  can be a substantially hollow cylinder or the like having an open end and a substantially closed end. The substantially closed end includes and/or defines a detent, recess, opening, and/or engagement structure (referred to herein as “engagement structure  766 ”). The engagement structure  766  can be in contact with and/or can otherwise selectively engage the engagement member  755  of the first member  751 . For example, as described in further detail herein, the engagement member  755  can be configured to engage and/or contact the engagement structure  766 , which in turn, can result in the first member  751  and the third member  765  being moved collectively and/or concurrently as the actuator  750  is transitioned between two or more states or configurations. Moreover, a portion of the transitioning of the actuator  750  can result in the engagement member  755  disengaging and/or moving relative to the engagement structure  766 , which in turn, can result in the first member  751  being moved relative to the third member  765  (or vice versa), as described in further detail herein. 
     As shown in  FIGS. 9A-9D , the arrangement of the first member  751  and the second member  760  of the actuator is such that the sequestration chamber  730  is disposed and/or defined between, for example, the first end portion of the first member  751  and the first end portion of the second member  760 . In addition, the second member  760  is configured to at least partially define the fluid flow path  715  between the first end portion and the second end portion of the second member  760 . Thus, the first end portion of the second member  760  and the seals  761  included in the first end portion, sequester and/or fluidically isolate the sequestration chamber  730  from the fluid flow path  715 . 
     The actuator  750  is configured to transition between at least a first state, a second state, a third state, and a fourth state. As shown in  FIGS. 9A-9D , the first end portion of first member  751  and the seal  752  included therein are disposed on and maintained on a first side of the inlet  712  and a first side of the outlet  713 , regardless of the state of the actuator  750 . Similarly, the second end portion of the second member  760  and the seal member  761  included therein are disposed on and maintained on a second side of the inlet  712  (opposite the first side) and a second side of the outlet  713  (opposite the first side), regardless of the state of the actuator  750 . The first end portion of the second member  760  and the seal members  761  disposed therein, however, are configured to be (i) disposed on the second side of the inlet  712  and the first side of the outlet  713  when the actuator  750  is in the first state ( FIG. 9A ), the second state ( FIG. 9B ), and the third state ( FIG. 9C ), and (ii) disposed on the first side of the inlet  712  and the first side of the outlet  713  when the actuator  750  is in the fourth state ( FIG. 9D ). Thus, the arrangement of the actuator  750  is such that transitioning the actuator  750  can selectively direct and/or divert a flow of fluid between (i) the inlet  712  and the sequestration chamber  730  and (ii) the inlet  712  and the outlet  713  via the fluid flow path  715 , as described in further detail herein. 
     The rapid diagnostic testing device  770  (also referred to herein as “rapid testing device” or simply “testing device”) can be any suitable testing device. For example, the rapid testing device  770  can be an LFA or the like, as described in detail above with reference to the LFA  170 A shown in  FIG. 2 . In some implementations, the testing device  770  and/or aspects or portions thereof can be substantially similar to the rapid testing devices  170 ,  270 ,  370 ,  470 ,  570 , and/or  670  described in detail above. Accordingly, the rapid testing device  770  and/or aspects or portions thereof is/are not described in further detail herein. 
     As shown in  FIG. 9D , the rapid testing device  770  includes a coupling member  778  that is coupled to and/or at least in fluid communication with a substrate  771  of the testing device  770  (e.g., coupled directly to the substrate  771  and/or coupled via an attachment mechanism such as the attachment mechanism  579 ). The coupling member  778  can be at least partially inserted through the opening  721  of the housing  710  to establish fluid communication with the sampling channel  735  when the rapid testing device  770  is coupled the transfer device  705 . For example, the coupling member  778  can be a puncture member, needle, tube, capillary, and/or the like that can puncture and/or otherwise advance through the port  725 . In some embodiments, the substrate  771  and the coupling member  778  can be substantially similar to the substrates  571  and/or  671 , and the coupling members  578  and/or  678  described in detail above. Thus, the substrate  771  and the coupling member  778  (and/or aspects or portions thereof) are not described in further detail herein. 
     The system  700  can be used to procure one or more volumes of bodily fluid from a patient, which can be used in one or more tests, assays, and/or diagnostic procedures. As described above, for example, the inlet  712  can be placed in fluid communication with a bodily fluid source. The actuator  750  can be in a first state when the inlet  712  is placed in fluid communication with the bodily fluid source (e.g., the portion of the patient), thereby establishing fluid communication between the inlet  712  and the sequestration chamber  730  and sequestering the outlet  713  from the inlet  712 , as shown in  FIG. 9A . Moreover, when the actuator  750  is in the first state, the first end portion of the first member  751  can be near or adjacent to the first side of the inlet  712  and the first end portion of the second member  760  can be near or adjacent to the second side of the inlet  712 . In this manner, the sequestration chamber  730  defined between the first member  751  and the second member  760  can have a first volume. 
     In some instances, once the inlet  712  is placed in fluid communication with the bodily fluid source, the actuator  750  can be transitioned from its first state to its second state. For example, as shown in  FIG. 9B , a user can exert a force on the third member  765  that can be operative to move the third member  765  relative to the housing  710 . As described above, the arrangement of the engagement member  755  of the first member  751  and the engagement structure  766  of the third member  765  is such that movement of the third member  765  relative to the housing  710  results in a similar movement of the first member  751 . The movement of the first member  751  is also relative to the second member  760  (e.g., the second member  760  is not yet moved), which in turn, increases a volume of the sequestration chamber  730  disposed between the first member  751  and the second member  760 . In addition, the transitioning and/or movement of the first member  751  can reduce a volume within the housing  710  on a side of the first member  751  opposite the sequestration chamber  730 , and the opening  721  can be such that air or gas contained therein can be allowed to escape and/or flow out of the sampling channel  735 . Thus, the transitioning of the actuator  750  from its first state ( FIG. 9A ) to its second state ( FIG. 9B ) can result in a negative pressure differential being generated within the sequestration chamber operative in drawing the initial volume of bodily fluid from the bodily fluid source, through the inlet  712 , and into the sequestration chamber  730 , as described in detail above with reference to the sequestration chamber  630 . Moreover, the initial volume of bodily fluid can be any suitable volume of bodily fluid, such as any of the volumes or amounts described above. 
     The actuator  750  can be transitioned from its second state ( FIG. 9B ) to its third state ( FIG. 9C ) when the initial volume of bodily fluid is contained in the sequestration  730 . As described above with reference to the transfer device  605 , the transitioning of the actuator  750  from the second state to the third state can be in response to the initial volume of bodily fluid being disposed in the sequestration chamber  730 , in response to an equalization of one or more pressure differentials, in response to a given point in a continuous process of transitioning the actuator  750  from the first to the fourth state, and/or the like. In some instances, the transitioning can be automatic or in response to an applied force. 
     As shown in  FIG. 9C , transitioning the actuator  750  to the third state can include transitioning and/or moving the first member  751  and the third member  765  an additional amount relative to the housing  710  and the second member  760 . More specifically, when in the third state, the first member  751  can be placed in a position relative to the second member  760  such that an opening, port, valve, etc. (referred to herein as “opening  754 ”) is placed in fluid communication with the sequestration chamber  730  and/or the inlet  712 , as shown in  FIG. 9C . In this manner, a volume of bodily fluid can be transferred into the sampling channel  735  defined by the first member  751 . As described above, in some embodiments, the port  725  can be configured to vent the sampling channel  735  to facilitate the flow of bodily fluid into the sampling channel  735 . 
     With a volume of bodily fluid contained in the sampling channel  735 , the actuator  750  can be transitioned from its third state ( FIG. 9C ) to its fourth state ( FIG. 9D ). More specifically, in some implementations, the third member  765  and the second member  760  can be moved relative to the housing  710 , while the first member  751  is maintained in a substantially fixed position relative to the housing  710 . Said another way, the third member  765  and the second member  760  are moved together and relative to the first member  751 . 
     As shown in  FIG. 9D , the engagement member  755  is disengaged from and/or moved relative to the engagement surface  766  when the actuator  750  is transitioned to the fourth state. In some embodiments, the engagement member  755  and/or the engagement surface  766  can be sized and/or configured to maintain contact and/or engagement until a desired and/or predetermined force is exerted that is sufficient to overcome a force maintaining the engagement (e.g., a friction force, a force sufficient to elastically and/or plastically deform the engagement member  755  and/or the engagement surface  766 , and/or any other suitable force). In other words, the third member  765  can be moved relative to the first member  751  when a force satisfies a criterion and/or is greater than a threshold amount of force. 
     The second member  760  of the actuator  750  is moved with and in the same direction as the third member  765  when the actuator  750  is transitioned to the fourth state. As shown in  FIG. 9D , the transitioning and/or moving of the second member  760  transitions and/or moves the first end portion of the second member  760  from the second side of the inlet  712  to the first side of the inlet  712 , thereby sequestering and/or fluidically isolating the sequestration chamber  730  from the inlet  712 . Moreover, the transitioning and/or moving of the second member  760  relative to the first member  751  can place the opening  754  of the first member  751  on an opposite side of the inner seal  561  included in or on the first end portion of the second member  760 , which in some instances, can allow the sampling channel  735  to be vented, as described in further detail herein. 
     As shown in  FIG. 9D , the rapid testing device  770  can be coupled to the housing  710  and/or can otherwise be at least partially inserted into and/or through the opening  721  of the housing  710  to allow the coupling member  778  to establish fluid communication with the sampling channel  735  (e.g., via the port  725 ). Accordingly, at least a portion of the bodily fluid can be transferred from the sampling channel  735  and into the rapid testing device  770 , as described in detail above with reference to the rapid testing devices  470 ,  570 , and/or  670 . In some embodiments, transferring the volume of bodily fluid from the sampling channel  735  into the rapid testing device  770  can initiate a test and/or assay of or on the portion of the initial volume of bodily fluid, as described in detail above with reference to the rapid testing device  270 . Moreover, in some instances, venting the sampling channel  735  via the opening  754  can allow for a desired pressure differential within the sampling channel  735  that can facilitate the transfer of bodily fluid from the sampling channel  735  and into the rapid testing device  770 . The rapid testing device  770  can be configured to perform any suitable test and/or assay (e.g., a test for the presence of lactate and/or PCT), such as any of those described in detail above. Moreover, once the test or assay is complete, the rapid testing device  770  can be configured to output a test result, which can be detected and/or assessed by a human and/or one or more electronic devices, as described in detail above with reference to the rapid testing devices  170 ,  270 ,  370 ,  470 ,  570 , and/or  670 . 
     As described above, transitioning the actuator  750  from its third state to its fourth state can sequester, isolate, separate, and/or retain the initial volume of the bodily fluid in the sequestration chamber  730  and/or the rapid testing device  770 , which in turn, can also sequester contaminants in the initial volume. Moreover, the arrangement of the rapid testing device  770  can be such that the tests and/or assays performed by the rapid testing device  770  are not susceptible to such contamination, which means that the accuracy of the test results output by the rapid testing device  770  is not affected by such contamination, as described in detail above. 
     As shown in  FIG. 9D , transitioning the actuator  750  from its third state to its fourth state establishes fluid communication between the inlet  712  and the outlet  713  via the fluid flow path  715  disposed between the first end portion and the second end portion of the second member  760  of the actuator  750 . When the actuator  750  is in its fourth state, the first end portion of the second member  760  is disposed on the first side of the inlet  712  and the second end portion of the second member  760  is disposed on the second side of the outlet  713 , as described in detail above with reference to the actuator  650 . 
     In some implementations, the outlet  713  can be placed in fluid communication with a fluid collection device (not shown in  FIGS. 8-9D ) prior to or after the actuator  750  is placed in its fourth state. As described in detail above, the fluid collection device can define and/or can be configured to generate a negative pressure and/or suction force that can be operable to draw bodily fluid into the fluid collection device. Thus, in response to the negative pressure and/or suction force, one or more subsequent volume(s) of the bodily fluid can flow from the inlet  712 , through the fluid flow path  715 , through the outlet  713 , and into the fluid collection device. As described above, sequestering the initial volume of bodily fluid in the sequestration chamber  730  prior to collecting or procuring one or more subsequent volumes of bodily fluid reduces and/or substantially eliminates an amount of contaminants in the one or more subsequent volumes. Accordingly, the system  700  can be configured to procure the initial volume of bodily fluid, which can be used in rapid testing that has relatively low sensitivity to contamination, and the subsequent volume(s) of bodily fluid, which can be used in testing that has a relatively high sensitivity to contamination, as described above with reference to the systems  100 ,  200 ,  300 ,  400 , and/or  600 . 
       FIGS. 10, 11, and 12A-12D  illustrate a fluid transfer and assay system  800 , according to an embodiment. The fluid transfer and assay system  800  (also referred to herein as “system”) can include at least a fluid transfer device  805  and a rapid diagnostic testing device  870 . Portions and/or aspects of the fluid transfer device  805  and/or the rapid diagnostic testing device  870  can be similar to and/or substantially the same as the fluid transfer devices  105 ,  205 ,  305 ,  405 ,  505 ,  605 , and/or  705 , and/or the rapid diagnostic testing devices  170  (and/or the LFA  170 A),  270 ,  370 ,  470 ,  570 ,  670 , and/or  770 , respectively, described in detail above. Accordingly, such portions and/or aspects are not described in further detail herein. 
     The fluid transfer device  805  (also referred to herein as “transfer device”) can be any suitable shape, size, and/or configuration. In some implementations, the transfer device  805  can be configured to withdraw bodily fluid (e.g., blood) from a patient and into and/or through the transfer device  805 . In addition, the transfer device  805  can be configured to transfer at least some of the withdrawn bodily fluid to one or more other devices, reservoirs, containers, vials, machines, tests, assays, etc., such as the rapid diagnostic testing device  870  and/or one or more fluid collection devices (not shown in  FIGS. 10, 11, and 12A-12D ). 
     The transfer device  805  includes at least a housing  810  and an actuator  850 . The housing  810  of the device  805  can be any suitable shape, size, and/or configuration. For example, in some embodiments, the housing  810  can be similar to and/or the substantially the same as any of the housings  210 ,  310 ,  410 ,  510 ,  610 , and/or  710  described above. Specifically, the housing  810  has and/or forms an inlet  812  and an outlet  813 . The housing  810  can form and/or can define an actuator chamber  814 , a fluid flow path  815 , and a sequestration chamber  830 . The inlet  812  can be any suitable inlet or port and can be configured to establish fluid communication between the housing  810  to a bodily fluid source (e.g., a patient). As shown in  FIG. 11 , the inlet  812  is in fluid communication with the actuator chamber  814 , which in turn, is in fluid communication with the fluid flow path  815  and the sequestration chamber  830 . The outlet  813  can be any suitable outlet or port and can be configured to establish fluid communication between the housing  810  and a fluid collection device (not shown in  FIGS. 10-12D ), such as any of those described in detail above. The outlet  813  is in fluid communication with the fluid flow path  815 . In addition, the outlet  813  is configured to be in selective fluid communication with the sequestration chamber  830  via a flow controller  840 , as described in further detail herein. 
     The sequestration chamber  830  can be configured to receive a flow and/or volume of bodily fluid from the inlet  812  and to sequester (e.g., separate, segregate, contain, retain, isolate, etc.) at least a portion of the flow and/or volume of bodily fluid within the sequestration chamber  830 , as described in further detail herein. The sequestration chamber  830  can have any suitable shape, size, and/or configuration. For example, in some embodiments, the sequestration chamber  830  and/or at least a portion thereof can be substantially similar in at least form and/or function to the sequestration chambers  330 ,  430 ,  630 , and/or  730  described in detail above. Thus, portions and/or aspects of the sequestration chamber  830  are not described in further detail herein. 
     The flow controller  840  is at least partially disposed within the housing  810  and is configured to control, direct, and/or otherwise facilitate a selective flow of fluid through at least a portion of the housing  810 , at least a portion of the fluid flow path  815 , and/or at least a portion of the sequestration chamber  830 . The flow controller  840  can be configured to facilitate fluid displacement through one or more portions of the housing  810 , which in some instances, can allow for or result in a pressure differential and/or pressure equalization across one or more portions of the housing  810 . In this context, the flow of fluids, for example, can be a liquid such as water, oil, dampening fluid, bodily fluid, and/or any other suitable liquid, and/or can be a gas such as air, oxygen, carbon dioxide, helium, nitrogen, ethylene oxide, and/or any other suitable gas. 
     The flow controller  840  can be any suitable shape, size, and/or configuration. In some embodiments, the flow controller  840  can be similar to and/or substantially the same as the flow controller  340  described in detail above with reference to  FIG. 4 . For example, the flow controller  840  can be configured to transition from a first state to a second state in response to a pressure differential, suction force, contact with and/or a flow of bodily fluid, and/or the like. More specifically, in the embodiment shown in  FIGS. 10-12D , the flow controller  840  can be a member or device formed of an absorbent or semi-permeable material configured to be permeable to a flow of a gas or air and impermeable to a flow of a liquid (e.g., blood or other bodily fluid) when in a first state and configured to be impermeable to both gases and liquids when in a second state. Accordingly, the flow controller  840  and/or aspects or portions thereof are not described in further detail herein. 
     The actuator  850  of the device  805  can be any suitable shape, size, and/or configuration. For example, the actuator  850  can be any suitable member(s) or device(s) configured to transition between any number of states (e.g., two, three, four, or more) and in any suitable manner (e.g., user actuation, automatic actuation, mechanical actuation, electronic actuation, chemical actuation, and/or the like). In some embodiments, the actuator  850  and/or aspects or portions thereof can be similar to and/or substantially the same as the actuators  150 ,  250 ,  350 ,  450 ,  650 , and/or  750  described in detail above. As shown in  FIG. 11 , the actuator  850  forms and/or includes a rod that is at least partially movably disposed in a portion of the actuator chamber  814  of the housing  810 . In addition, the actuator  850  includes a set of seals  852  disposed at predetermined positions along a length of the actuator  850  (or rod) that can allow the actuator  850  to control, direct, and/or otherwise facilitate a selective flow of fluid through at least a portion of the housing  810 . As described in further detail herein, the actuator  850  includes a set of four seals  852  that are disposed at desired positions along a length of the actuator  850  (or rod) to selectively control fluid flow from the inlet  812  and into at least one of the sequestration chamber  830 , the rapid diagnostic testing device  870 , and/or the fluid flow path  815 . Moreover, the arrangement of the seals  852  can also allow the actuator  850  to sequester the sequestration chamber  830 , the rapid diagnostic testing device  870 , and/or the fluid flow path  815  as the actuator  850  is transitioned between two or more states. 
     While the rapid testing devices included in the previous embodiments have be shown and/or described as being coupled to the housing  810 , in the embodiment shown in  FIGS. 10-12D , the rapid testing device  870  is disposed within and/or integrated into the housing  810 . The rapid diagnostic testing device  870  (also referred to herein as “rapid testing device” or simply “testing device”) can be any suitable testing device. For example, the rapid testing device  870  and/or aspects or portions thereof can be substantially similar to the rapid testing devices  170 ,  270 ,  370 ,  470 ,  570 ,  670 , and/or  770  described in detail above. In some implementations, the rapid testing device  870  can be an LFA or the like, as described in detail above with reference to the LFA  170 A shown in  FIG. 2 . 
     For example, as shown in  FIG. 11 , the rapid testing device  870  includes at least a sample element  872  disposed on an end portion of a substrate  871 , a conjugate element  873  disposed on the substrate  871  downstream of the sample element  872 , a capture element  874  disposed on the substrate  871  downstream of the conjugate element  873 , and a control element  875  disposed on the substrate  871  downstream of the capture element  874 . The rapid testing device  870  can be disposed within the housing  810  such that the capture element  874  and the control element  875  can be viewed from outside of the housing  810  via a viewing opening  819  or the like. Moreover, the housing  810  and/or the rapid testing device  870  includes and/or is coupled to a buffer actuator  880  that contains a volume of a buffer solution  881 . In some embodiments, the buffer actuator  880  can be a blister pack, a frangible or pierceable container, a reservoir including one or more reconfigurable portions (e.g., one or more valves or flow controllers), and/or the like. The buffer actuator  880  can be actuated to provide the sample element  872  of the rapid testing device  870  with a flow of the buffer solution  881 , which in turn, can mix with the volume of bodily fluid transferred to the sample element  872 , as described in further detail herein. 
     The system  800  can be used to procure one or more volumes of bodily fluid from a patient, which can be used in one or more tests, assays, and/or diagnostic procedures. As described above, for example, the inlet  812  can be placed in fluid communication with a bodily fluid source. The actuator  850  can be in a first state when the inlet  812  is placed in fluid communication with the bodily fluid source (e.g., the portion of the patient), thereby establishing fluid communication between the inlet  812  and the sequestration chamber  830 , as shown in  FIG. 11 . More specifically, when the actuator  850  is in the first state, the inlet  812  and the sequestration chamber  830  can be in fluid communication with a portion of the actuator chamber  814  defined between two of the seals  852  of the actuator  850 . For example, a first seal  852  disposed at or near an end portion of the actuator  850  (e.g., an end seal) can be disposed within the actuator chamber  814  in a position between the rapid testing device  870  and the sequestration chamber  830  and a second seal  852  adjacent to (or closest to) the first or end seal  852  can be disposed within the actuator chamber  814  between the inlet  812  and the fluid flow path  815 . In this manner, when the actuator  850  is in the first state, the inlet  812  is in fluid communication with the sequestration chamber  830 , as shown in  FIG. 11 . 
     In the embodiment shown in  FIGS. 10-12D , once the inlet  812  is placed in fluid communication with the bodily fluid source (e.g., the portion of the patient), the outlet  813  can be fluidically coupled to a fluid collection device, such as any of those described herein. For example, the fluid collection device can be any suitable reservoir, container, and/or device configured to receive a volume of bodily fluid. In some embodiments, the fluid collection device can be an evacuated reservoir or container that defines a negative pressure and/or can be a syringe that can be manipulated to produce a negative pressure. As such, coupling the fluid collection device to the outlet  813  selectively exposes at least a portion of the fluid flow path  815  to the negative pressure and/or suction force within the fluid collection device. 
     The actuator  850  is configured to be in the first state when the fluid collection device is fluidically coupled to the outlet  813 . As shown in  FIG. 12A , the fluid flow path  815  is in fluid communication with a portion of the actuator chamber  814  defined between the seal  852  (e.g., second from the bottom) disposed between the inlet  812  and the fluid flow path  815  and an adjacent seal  852  (e.g., third from the bottom) disposed on an opposite side of the fluid flow path  815 . In this manner, the fluid flow path  815  places the outlet  813  in fluid communication with a portion of the actuator chamber  814  that is sequestered and/or fluidically isolated by the seals  852  disposed on either side of the fluid flow path  815 . As described above, the outlet  813  and/or the fluid flow path  815  is also in fluid communication with the flow controller  840 , which can be in its first state when the fluid collection device is coupled to the outlet  813 . 
     The arrangement of the flow controller  840  (e.g., the selectively permeable member) can be such that a flow of air or gas is allowed to pass through the flow controller  840  between the outlet  813  (and/or fluid flow path  815 ) and the sequestration chamber  830 , while a flow of liquid (e.g., bodily fluid) is not allowed to pass through the flow controller  840 . As a result, at least a portion of the negative pressure differential or suction force generated by the fluid collection device can be transferred into and/or through the sequestration chamber  830 , which in turn, can be operable in drawing the initial volume of bodily fluid from the bodily fluid source, through the inlet  812 , a portion of the actuator chamber  814  defined between the two corresponding seals  852 , and into the sequestration chamber  830 , as described in detail above with reference to the transfer device  305 . 
     The initial volume of bodily fluid can be any suitable volume of bodily fluid, such as any of the volumes or amounts described above. For example, in some instances, the actuator  850  and/or the transfer device  805  can remain in the first state or configuration until a predetermined and/or desired volume (e.g., the initial volume) of bodily fluid is transferred to the sequestration chamber  830 . In some embodiments, the initial volume can be associated with and/or at least partially based on a volume of the sequestration chamber  830  or a portion thereof (e.g., a volume sufficient to fill the sequestration chamber  830  or a desired portion of the sequestration chamber  830 ). In some embodiments, the transfer device  805  can be configured to transfer a flow of bodily fluid (e.g., the initial volume) into the sequestration chamber  830  until the flow controller  840  is transitioned to its second configuration. Said another way, in some embodiments, transferring the initial volume of bodily fluid into the sequestration chamber  830  can be operable to place the flow controller  840  in its second state or configuration. For example, transferring the initial volume of bodily fluid into the sequestration chamber  830  can be such that at least a portion of the initial volume wets and/or saturates the flow controller  840 , which in turn, places the flow controller  840  in its second state, as described in detail above with reference to the flow controller  340 . As shown in  FIGS. 12A and 12B , the initial volume of bodily fluid can be sufficient to substantially fill the sequestration chamber  830  such that at least a portion of the initial volume is disposed within the actuator chamber  814  between the two seals  852  (e.g., the two lowest seals  852 ). 
     The flow controller  840  sequesters and/or fluidically isolates the sequestration chamber  830  from the outlet  813  when the flow controller  840  is transitioned to its second state and/or configuration. As such, the negative pressure and/or suction force produced by the fluid collection device no longer acts on or through the sequestration chamber  830 . In some instances, this can allow a pressure differential between the sequestration chamber  830  and the inlet  812  to be substantially equalized and/or to be reduced below a desired threshold. In some instances, the pressure equalization can be such that a flow of bodily fluid into the sequestration chamber  830  stops. 
     The actuator  850  can be transitioned from its first state ( FIGS. 11 and 12A ) to its second state ( FIGS. 12B and 12C ) after the initial volume of bodily fluid is contained in the sequestration  830 , thereby transitioning the transfer device  805  from its first state to its second state. As described above with reference to the transfer device  605 , the transitioning of the actuator  850  from the first state to the second state can be in response to the initial volume of bodily fluid being disposed in the sequestration chamber  830 , in response to an equalization of one or more pressure differentials, and/or the like. In some instances, the transitioning can be automatic or in response to an applied force (e.g., as indicated by the arrow in  FIG. 12B ). 
     As shown in  FIG. 12B , when in the second state or configuration, the actuator  850  can be disposed within the actuator chamber  814  such that the seals  852  are in desired positions relative to the rapid testing device  870 , the sequestration chamber  830 , the inlet  812 , and the fluid flow path  815 . For example, the sequestration chamber  830  is in fluid communication with a portion of the actuator chamber  814  disposed between a seal  852  positioned between the rapid testing device  870  and the sequestration chamber  830  and a seal  852  positioned between the sequestration chamber  830  and the inlet  812 . As such, when the flow controller  840  is in its second state and the actuator  850  is transitioned to its second state, the sequestration chamber  830  is sequestered and/or fluidically isolated from other portions of the transfer device  805  (see e.g.,  FIGS. 12B-12D ). Said another way, the actuator  850  (and the flow controller  840 ) can sequester and/or isolate the sequestration chamber  830  from the inlet  812 , the outlet  813 , the fluid flow path  815 , and the rapid testing device  870 . In some instances, sequestering the initial volume of bodily fluid in the sequestration chamber  830  can also sequester contaminants in the initial volume. 
     As shown in  FIG. 12C , when in the second state or configuration, the actuator  850  also establishes fluid communication between the inlet  812  and the outlet  813  via the fluid flow path  815  and a portion of the actuator chamber  814 . For example, in some embodiments, the inlet  812  and the fluid flow path  815  are each in fluid communication with a portion of the actuator chamber  814  disposed between a corresponding pair of the seals  852  (e.g., a top pair of seals  852 ). Thus, in response to the negative pressure and/or suction force generated by the fluid collection device, one or more subsequent volume(s) of the bodily fluid can flow from the inlet  812 , through the portion of the actuator chamber  814  and the fluid flow path  815 , through the outlet  813 , and into the fluid collection device (not shown). As described above, sequestering the initial volume of bodily fluid in the sequestration chamber  830  prior to collecting or procuring one or more subsequent volumes of bodily fluid reduces and/or substantially eliminates an amount of contaminants in the one or more subsequent volumes. 
     As shown in  FIG. 12C , when the actuator  850  is in the second state or configuration, the rapid testing device  870  is in fluid communication with a portion of the actuator chamber  814  disposed between a corresponding pair of seals  852  (e.g., an end pair), which can allow a portion of the initial volume of bodily fluid disposed within the actuator chamber  814  between the pair of seals  852  to be transferred into or onto the sample element  872  of the rapid testing device  870 . As shown in  FIG. 12D , the transfer device  805  can be transitioned from its second state to a third state by manipulating and/or engaging the buffer actuator  880  to transition the buffer actuator  880  from its first state to its second state to transfer at least a portion of the buffer solution  881  contained therein into or onto the sample element  872 . For example, the buffer actuator  880  can include a frangible portion that can be broken and/or punctured in response applied by a user on the buffer actuator  880 . As shown in  FIG. 12D , the rapid testing device  870  and/or the housing  810  can include a puncture member  882  or the like that can be configured to break, puncture, and/or otherwise open the buffer solution. In such embodiments, the puncture member  882  can define a lumen that can be in fluid communication with the sample element  872 . Thus, the force applied on the buffer actuator  880  can be operable to transfer at least a portion of the buffer solution  881  into and/or onto the sample element  872 . Moreover, with volume of bodily fluid also transferred to the sample element  872 , the bodily fluid and the buffer solution  881  can begin to mix. 
     In some embodiments, the mixing of the bodily fluid and the buffer solution  881  in or on the sample element  872  can initiate a test and/or assay of or on the bodily fluid, as described in detail above with reference to the rapid testing device  270 . Moreover, the rapid testing device  870  can be configured to perform any suitable test and/or assay. In some embodiments, the buffer solution  881  can be based at least in part on the test being performed. For example, in some instances, the rapid testing device  870  can be configured to test for the presence of lactate and/or PCT, as described in detail above. Moreover, once the test or assay is complete, the rapid testing device  870  can be configured to output a test result, which can be detected and/or assessed. For example, in some instances, a human may observe the capture element  874  and/or the control element  875  via the viewing opening  819  defined by the housing  810 . In other embodiments, an electronic device can perform one or more scans of the capture element  874  and/or the control element  875  via the viewing opening  819 . In other embodiments, one or more electronic devices can be integrated and/or disposed in the housing  810  and the capture element  874  and/or the control element  875  need not be observed by a human. 
     As described in detail above, in some implementations, the arrangement of the rapid testing device  870  can be such that the tests and/or assays performed by the rapid testing device  870  are not susceptible to such contamination, which means that the accuracy of the test results output by the rapid testing device  870  is not affected by contamination that may be contained in the initial volume of bodily fluid, as described in detail above. Accordingly, the system  800  can be configured to procure the initial volume of bodily fluid, which can be used in rapid testing that has relatively low sensitivity to contamination, and the subsequent volume(s) of bodily fluid, which can be used in testing that has a relatively high sensitivity to contamination, as described above with reference to the systems  100 ,  200 ,  300 ,  400 ,  600 , and/or  700 . 
       FIGS. 13-16  illustrate at least a portion of a fluid transfer and assay system  900 , according to an embodiment. The fluid transfer and assay system  900  (also referred to herein as “system”) can include at least a fluid transfer device  905  and a rapid diagnostic testing device  970 . Portions and/or aspects of the system  900  can be similar to and/or substantially the same as the systems (or devices)  100 ,  200 ,  300 ,  400 ,  500 ,  600 ,  700 , and/or  800  described in detail above. Accordingly, such portions and/or aspects are not described in further detail herein. 
     The fluid transfer device  905  (also referred to herein as “transfer device”) can be any suitable shape, size, and/or configuration. In some implementations, the transfer device  905  can be configured to withdraw bodily fluid (e.g., blood) from a patient and into and/or through the transfer device  905 . In addition, the transfer device  905  can be configured to transfer at least some of the withdrawn bodily fluid to one or more other devices, reservoirs, containers, vials, machines, tests, assays, etc., such as the rapid diagnostic testing device  970  and/or one or more fluid collection devices (not shown in  FIGS. 13-16 ). In some implementations, the transfer device  905  and/or aspects or portions thereof can be substantially similar to any of the transfer devices  105 ,  205 ,  305 ,  405 ,  505 ,  605 ,  705 , and/or  805  described in detail above. 
     For example, the transfer device  905  includes at least a housing  910  and an actuator  950 . The housing  910  has and/or forms an inlet  912  and an outlet  913 . The inlet  912  can be any suitable inlet or port and can be configured to establish fluid communication between the housing  910  to a bodily fluid source (e.g., a patient). The outlet  913  can be any suitable outlet or port and can be configured to establish fluid communication between the housing  910  and a fluid collection device (not shown in  FIGS. 13-16 ), such as any of those described in detail above. In addition, the housing  910  includes and/or defines a port  925  that can be configured to establish fluid communication between at least a portion of the housing  910  and/or one or more reservoirs or chambers disposed therein and, for example, the rapid diagnostic testing device  970 . In some embodiments, the port  925  can be substantially similar in at least form and/or function to the port  525  described above with reference to  FIGS. 6A-6D . In this manner, the housing  910  and/or portions or aspects thereof can be similar to and/or the substantially the same as any of the housings  210 ,  310 ,  410 ,  510 ,  610 ,  710 , and/or  810  described above and thus, is/are not described in further detail herein. 
     The actuator  950  is at least partially disposed within the housing  910 . The actuator  950  of the device  905  can be any suitable shape, size, and/or configuration. For example, the actuator  950  can be a member or device configured to transition between two or more states to control, direct, and/or otherwise facilitate a selective flow of fluid through at least a portion of the housing  910 . Moreover, the actuator  950  can be actuated and/or transitioned between any number of states in any suitable manner. In the embodiment shown in  FIGS. 13-16 , the actuator  950  can be transitioned between at least a first state and a second state. When in the first state, the actuator  950  can be configured to allow an initial volume bodily fluid to from the inlet  912  into an initial or first portion of the housing  910  such as a sequestration chamber or the like described in detail above with reference to the sequestration chambers  330 ,  430 ,  630 ,  730 , and/or  830 . In some embodiments, the actuator  950  can be configured to sequester, separate, isolate, and/or otherwise prevent fluid communication between the outlet  913  and the inlet  912 , and/or the outlet  913  and the initial or first portion of the housing  910  when in the first state. When in the second state, the actuator  950  can be configured to allow a subsequent volume of bodily fluid (e.g., a volume of bodily fluid after the initial volume of bodily fluid) to be transferred from the inlet  912 , through at least a portion of the housing  910  (e.g., a second portion) and to the outlet  913  (and/or the fluid collection device fluidically coupled to the outlet  913 ). In addition, when in the second state, the actuator  950  can be configured to sequester, separate, isolate, and/or otherwise prevent fluid communication between the initial or first portion of the housing  910  and the inlet  912 , the outlet  913 , and/or one or more other portions of the housing  910 . In this manner, the actuator  950  and/or portions or aspects thereof can be substantially similar to any of the actuators  250 ,  350 ,  450 ,  650 ,  750 , and/or  850  described in detail above and thus, is/are not described in further detail herein. 
     The rapid diagnostic testing device  970  (also referred to herein as “rapid testing device” or simply “testing device”) can be any suitable testing device. For example, the testing device  970  and/or aspects or portions thereof can be substantially similar to the rapid testing devices  170 ,  270 ,  370 ,  470 ,  570 ,  670 ,  770 , and/or  870  described in detail above. In some implementations, the rapid testing device  970  can be an LFA or the like, as described in detail above with reference to the LFA  170 A shown in  FIG. 2 . For example, the rapid testing device  970  includes at least a sample element  972  disposed on an end portion of a substrate  971 , a conjugate element  973  disposed on the substrate  971  downstream of the sample element  972 , a capture element  974  disposed on the substrate  971  downstream of the conjugate element  973 , and a control element  975  disposed on the substrate  971  downstream of the capture element  974 . 
     The rapid testing device  970  also includes a housing  983  configured to contain and/or house at least a portion of the rapid testing device  970  and a testing device actuator  986  configured to selectively establish fluid communication between the rapid testing device  970  and the housing  910 . In some embodiments, the rapid testing device  970  can be configured as a substantially modular device that can be coupled to and/or attached to any suitable fluid transfer device, tubing, reservoir, mechanism, transfer adapter, etc. In some implementations, the modular arrangement of the testing device  970  can allow the transfer device  905  and the testing device  970  to be manufactured and/or shipped independently and coupled and/or assembled at a point of use. In some implementations, the modular arrangement of the testing device  970  can allow various versions of the testing device  970  to be compatible with the transfer device  905 , with each version of the testing device  970  being configured to perform a different test or assay. Said another way, the modular arrangement of the testing device  970  can allow different versions of the testing device  970  to test for different biomarkers while maintaining substantially the same form factor and/or compatibility. 
     As shown in  FIGS. 14-16 , the housing  983  can be any suitable shape, size, and/or configuration. In some embodiments, the housing  983  of the testing device  970  can be configured to be coupled to a portion of the housing  910  of the transfer device  905 . The housing  983  includes, houses, and/or defines a vent  985  configured to allow a flow of air or gas out of the housing  983 . As described in detail above with reference to the transfer devices, in some implementations, venting the housing  983  of the testing device  970  can facilitate a flow of fluid through the testing device  970  (e.g., along the substrate  971 ). In addition, the housing  983  includes and/or defines a viewing opening  984 . As shown in  FIGS. 14 and 15 , the testing device  970  can be disposed within the housing  983  such that at least the capture element  974  and/or the control element  975  are visible and/or detectable via the viewing opening  984 . 
     The testing device actuator  986  is movably coupled to the housing  983  of the testing device  970  and is configured to be transitioned between a first state and a second state to establish fluid communication between the transfer device  905  and the testing device  905 . For example, in some embodiments, the testing device actuator  986  can be a spring loaded button or the like that can include a puncture member  987 . The testing device  970  and/or the housing  983  of the testing device  970  can include and/or can form a septum  988 . In addition, the testing device actuator  986  can be aligned with the septum  988 . In some implementations, the testing device actuator  986  can be configured such that the puncture member  987  is disposed on a first side of the septum  988  and within the housing  983  of the testing device  970  when the testing device actuator  986  is in a first state (see e.g.,  FIG. 15 ) and the puncture member  987  extends through the septum  988  and outside of the housing  983  of the testing device  970  when the testing device actuator  986  is in a second state (not shown in  FIGS. 13-16 ). 
     The testing device  970  and/or the housing  983  thereof is configured to couple to the housing  910  of the transfer device  905  such that the testing device actuator  986  is substantially aligned with the port  925  included in and/or formed by the housing  910 . As such, when the testing device actuator  986  is transitioned to its second state, the puncture member  987  can extend through the septum  988  of the testing device  970  and through the port  925  of the transfer device  905  to establish fluid communication therebetween. In this manner, the puncture member  987  can receive at least portion of the initial volume of bodily fluid disposed in the transfer device  905  (e.g., via capillary action, a pressure differential, and/or any other fluid transfer modality). As shown in  FIG. 15 , the puncture member  987  is in fluid communication with the portion of the substrate  971  such as, for example, the sample element  972 . Thus, a flow of bodily fluid can be transferred from a portion of the transfer device  905  (e.g., a portion of the housing, a sequestration chamber, and/or the like) to the sample element  972 . 
     Although not shown in  FIGS. 13-16 , in some implementations, the testing device  970  can be configured to convey a buffer solution or the like to the sample element  972  in conjunction with the volume of bodily fluid (e.g., as described above with reference to the testing device  870 ). In such implementations, the buffer solution can mix with the volume of bodily fluid and the mixture can flow along the substrate  971  for testing, as described in detail above. In some implementations, the rapid testing device  970  can be configured to test for the presence of lactate and/or PCT, which can be indicative of a patient condition such as sepsis. Moreover, once the test or assay is complete, the rapid testing device  970  can be configured to output a test result, which can be detected and/or assessed. For example, in some instances, a human may observe the capture element  974  and/or the control element  975  via the viewing opening  984  defined by the housing  983  of the testing device  970 . In other embodiments, an electronic device can perform one or more scans of the capture element  974  and/or the control element  975  via the viewing opening  984 . In other embodiments, one or more electronic devices can be integrated and/or disposed in the housing  910  and the capture element  974  and/or the control element  975  need not be observed by a human. 
     In addition to transferring a volume of bodily fluid to the rapid testing device  970 , in some instances, the transfer device  905  can be configured to transfer one or more subsequent volumes of bodily fluid to any suitable device, reservoir, test, etc. coupled to the outlet  913 . Accordingly, the system  900  can be configured to procure the initial volume of bodily fluid, which can be used in rapid testing (e.g., that has relatively low sensitivity to contamination), and the subsequent volume(s) of bodily fluid, which can be used in subsequent testing (e.g., that has a relatively high sensitivity to contamination), as described above with reference to the systems  100 ,  200 ,  300 ,  400 ,  600 ,  700 , and/or  800 . 
       FIGS. 17-20  illustrate various examples of fluid transfer and assay systems and/or devices according to different embodiments. For example,  FIG. 17  illustrates a fluid transfer and assay system  1000  (also referred to herein as “system”). The system  1000  can be substantially similar in form and/or function to the system  900  described above with reference to  FIGS. 13-16 . While the port  925  of the transfer device  905  is shown in  FIG. 14  as being disposed at or near an end portion of the housing  910 , in the embodiment shown in  FIG. 17 , a transfer device included in the system  1000  can include and/or form a port disposed near or adjacent to an inlet thereof. In this manner, a flow of bodily fluid through a rapid testing device that is coupled to the transfer device of the system  1000  can be in a substantially opposite direction relative to a flow of bodily fluid through, for example, the rapid testing device  970  described above with reference to  FIGS. 13-17 . 
       FIG. 18  illustrates a fluid transfer and assay system  1100  (also referred to herein as “system”). In this embodiment, the system  1100  includes an “in-line” rapid diagnostic testing device. For example, in some embodiments, the system  1100  can include an in-line rapid diagnostic testing device that is included in and/or coupled to and inlet tubing, an outlet tubing, and/or any other suitable portion of the system  1100 . In some implementations, the in-line rapid testing device included in the system can receive a flow of bodily fluid and can perform a test or assay as described in detail above. Moreover, in some instances, the in-line rapid testing device can include one or more flow through or bypass mechanisms or the like (e.g., an automatic or manually actuated mechanism) that can allow a flow of bodily fluid through the in-line rapid testing device after it receives an initial volume of bodily fluid. Thus, the in-line rapid testing device can perform one or more tests or assays on an initial volume of bodily fluid while a subsequent volume of bodily fluid continues to flow through the system  1100 . 
       FIG. 19  illustrates a fluid transfer and assay system  1200  (also referred to herein as “system”). In this embodiment, the system  1200  includes a fluid transfer device that is configured as a syringe. In some embodiments, the syringe can be, for example, a standard syringe configured to withdraw a volume of bodily fluid. In other embodiments, the syringe can be, for example, a syringe configured to withdraw and sequester an initial volume of bodily fluid prior to withdrawing a “sample volume” of bodily fluid. For example, such a syringe can be similar to and/or substantially the same as any of those described in the &#39;495 patent and/or the &#39;006 publication incorporated by reference above. As shown in  FIG. 19 , the system  1200  can include a rapid diagnostic testing device that can be coupled to any suitable portion of the syringe to be placed in fluid communication with an inner volume thereof. In embodiments in which the syringe is configured to withdraw and sequester an initial volume of bodily fluid, the rapid testing device can couple to the syringe such that fluid communication is established between the sequestered portion of the syringe and the rapid testing device. In this manner, the system  1200  can be similar to at least the systems  300 ,  400 ,  600 ,  700 , and/or  800  described in detail above. 
       FIG. 20  illustrates a fluid transfer and assay system  1300  (also referred to herein as “system”). In this embodiment, the system  1300  includes a fluid transfer device that is fluidically coupled to, for example, a syringe. As described above with reference at least the systems  200 ,  300 , and  800 , the system  1300  can include a fluid transfer device that is configured to withdraw an initial volume of bodily fluid into a sequestration chamber and configured to withdraw a subsequent volume of bodily fluid in response to, for example, a negative pressure differential produced by a fluid collection device or the like. While some of the embodiments are described herein as being coupled to an evacuated container (e.g., a Vacutainer® or the like), the embodiment shown in  FIG. 20  is configured to be coupled to a syringe that can be manipulated to produce a negative pressure differential. Moreover, the fluid transfer device shown in  FIG. 20  is configured to be coupled to a rapid testing device such as any of those described herein. In this manner, the system  1300  can be similar in at least form and/or function to any of the systems described in detail herein. 
     While various embodiments have been described above, it should be understood that they have been presented by way of example only, and not limitation. For example, while some of the embodiments are described herein as being used for procuring bodily fluid for one or more assays, tests, and/or the like, it should be understood that the embodiments are not limited to such a use. Any of the embodiments and/or methods described herein can be used to transfer a flow of bodily fluid to any suitable device that is placed in fluid communication therewith. Thus, while specific examples are described herein, the devices, methods, and/or concepts are not intended to be limited to such specific examples. 
     While the embodiments have been particularly shown and described, it will be understood that various changes in form and details may be made. Where schematics and/or embodiments indicate certain components arranged in certain orientations or positions, the arrangement of components may be modified. Although various embodiments have been described as having particular features, concepts, and/or combinations of components, other embodiments are possible having any combination or sub-combination of any features, concepts, and/or components from any of the embodiments described herein. 
     The specific configurations of the various components can also be varied. For example, the size and specific shape of the various components can be different from the embodiments shown, while still providing the functions as described herein. In some embodiments, varying the size and/or shape of such components may reduce an overall size of the device and/or may increase the ergonomics of the device without changing the function of the device. In some embodiments, the size and/or shape of the various components can be specifically selected for a desired or intended usage. For example, in some implementations, a device configured for use with or on seemingly healthy adult patients can be configured to procure a first amount of bodily fluid while a device configured for use with or on, for example, very sick patients and/or pediatric patients can be configured to procure a second amount of bodily fluid that is less than the first volume. Thus, it should be understood that the size, shape, and/or arrangement of the embodiments and/or components thereof can be adapted for a given use unless the context explicitly states otherwise. 
     The embodiments described herein and/or portions thereof can include components formed of one or more parts, features, structures, etc. When referring to such components it should be understood that the components can be formed by a singular part having any number of sections, regions, portions, and/or characteristics, or can be formed by multiple parts or features. For example, when referring to a structure such as a wall or chamber, the structure can be considered as a single structure with multiple portions, or as multiple, distinct substructures or the like coupled to form the structure. Thus, a monolithically constructed structure can include, for example, a set of substructures. Such a set of substructures may include multiple portions that are either continuous or discontinuous from each other. A set of substructures can also be fabricated from multiple items or components that are produced separately and are later joined together (e.g., via a weld, an adhesive, or any suitable method). 
     Any of the embodiments described herein can be used in conjunction with any suitable diagnostic testing device or machine, rapid diagnostic testing device, assay device (e.g., a lateral flow assay device), and/or the like. Any of the embodiments described herein can include and/or can be used in conjunction with any suitable fluid transfer device, fluid collection device, and/or fluid storage device such as, for example, a sample reservoir, vessel, container, bottle, adapter, dish, vial, syringe, and/or device (including, for example, micro- and/or nano-configurations thereof). Moreover, any of the embodiments described herein can incorporate, can include, and/or can be used in conjunction with any suitable fluid transfer device, transfer adapter, and/or component thereof such as any of the devices and/or components described in the &#39;420 patent, the &#39;783 patent, the &#39;510 publication, the &#39;117 publication, the &#39;241 patent, the &#39;724 patent, the &#39;495 patent, the &#39;006 publication, the &#39;999 application, the &#39;074 publication, the &#39;380 application, and/or the &#39;477 application, the disclosures of which are incorporated herein by reference in their entireties. 
     While some of the embodiments described above include a flow controller and/or actuator that physically and/or mechanically sequesters one or more portions of a fluid transfer device, in other embodiments, a fluid transfer device need not physically and/or mechanically sequester one or more portions of the fluid transfer device. For example, in some embodiments, an actuator such as any of those described herein can be transitioned from a first state in which an initial volume of bodily fluid can flow from an inlet to a sequestration chamber or portion, to a second state in which (1) the sequestration chamber or portion is physically and/or mechanically sequestered and (2) the inlet is in fluid communication with an outlet of the fluid transfer device. In other embodiments, however, an actuator and/or any other suitable portion of a fluid transfer device can transition from a first state in which an initial volume of bodily fluid can flow from an inlet to a sequestration chamber or portion, to a second state in which the inlet is placed in fluid communication with the outlet without physically and/or mechanically sequestering (or isolating) the sequestration chamber or portion. When such a transfer device is in the second state, one or more features and/or geometries of the transfer device can result in a preferential flow of bodily fluid from the inlet to the outlet and the initial volume of bodily fluid can be retained in the sequestration chamber or portion without physically and/or mechanically being sequestered or isolated. 
     Although not shown, any of the devices described herein can include an opening, port, coupler, septum, Luer-Lok, gasket, valve, threaded connecter, standard fluidic interface, etc. (referred to for simplicity as a “port”) in fluid communication with the sequestration chamber. In some such embodiments, the port can be configured to couple to and/or accept any suitable device, reservoir, pressure source, testing device, etc. For example, in some embodiments, the port can be configured to couple to any of the rapid diagnostic testing devices described herein. In some embodiments, the port can be coupled to a negative pressure source such as an evacuated container, a pump, a syringe, and/or the like to collect a portion or the full volume of the bodily fluid in the sequestration chamber, channel, reservoir, etc. and can use that volume of bodily fluid (e.g., the pre-sample volume) for additional clinical and/or in vitro diagnostic testing purposes. In some embodiments, the sequestration chamber can be configured with the addition of rapid diagnostic testing components integrated into the chamber (e.g., any of the rapid diagnostic testing devices described herein) allowing at least a portion of the initial volume of bodily fluid to be used for that test. In still other embodiments, the sequestration chamber and/or a rapid testing device coupled to or forming a portion of the sequestration chamber can be designed, sized, and configured to be removable and compatible with testing equipment and/or specifically accessible for other types of bodily fluid tests commonly performed on patients with suspected conditions (e.g., the rapid diagnostic testing devices described herein configured to test for sepsis and/or the like). In some embodiments, a port (or the like) can be coupled to any suitable pressure source or infusion device configured to infuse at least a portion of the initial volume of bodily fluid sequestered in the sequestration chamber back into the patient and/or bodily fluid source (e.g., in the case of pediatric patients, very sick patients, patients having a low blood volume, and/or the like). 
     While some embodiments described herein include a rapid diagnostic testing device that is coupled to or inserted into a portion of a fluid transfer device to receive a volume of bodily fluid for testing, in other embodiments, rapid diagnostic testing device can be integrated into one or more portions of a transfer device. For example, any of the embodiments described herein can include an integrated transfer and assay device such as the device(s) described above with reference to the system  800 . While the rapid testing device  870  is shown as being disposed or housed within the housing  810 , in other embodiments, a rapid testing device can form and/or can be at least temporarily coupled to an outer portion of a fluid transfer device. 
     Although not shown, in some embodiments, a fluid transfer device can include one or more lumen, channels, flow paths, etc. configured to selectively allow for a “bypass” flow of bodily fluid, where an initial amount or volume of bodily fluid can flow from the inlet, through the lumen, cannel, flow path, etc. to bypass the sequestration chamber (or rapid testing device), and into the collection device. In some embodiments, the fluid transfer device can include an actuator having, for example, at least three states—a first in which bodily fluid can flow from the inlet to the sequestration chamber (or rapid testing device), a second in which bodily fluid can flow from the inlet to the outlet after the initial volume is sequestered in the sequestration chamber, and a third in which bodily fluid can flow from the inlet, through the bypass flow path, and to the outlet. In other embodiments, the transfer device can include a first actuator configured to transition the device between a first and second state, as described in detail above with reference to specific embodiments, and can include a second actuator configured to transition the device to a bypass configuration or the like. In still other embodiments, the transfer device can include any suitable device, feature, component, mechanism, actuator, controller, etc. configured to selectively place the fluid transfer device in a bypass configuration or state. 
     While some methods are described herein as including steps recited in a certain order, in other embodiments, the ordering of certain events and/or procedures in any of the methods or processes described herein may be modified and such modifications are in accordance with the variations of the invention. Additionally, certain events and/or procedures may be performed concurrently in a parallel process when possible, as well as performed sequentially as described above. Certain steps may be partially completed or may be omitted before proceeding to subsequent steps. 
     For example, while some devices are described herein as transitioning from a first state to a second state in a discrete operation or the like, it should be understood that the devices described herein can be configured to automatically and/or passively transition from the first state to the second state and that such a transitioning may occur over a period of time. In other words, the transitioning from the first state to the second state may, in some instances, be relatively gradual. For example, in some instances, as a last portion of an initial volume of bodily fluid is transferred into a device (e.g., an initial or sequestration portion thereof), the device can begin to transition from the first state to the second state. In some instances, the rate of change when transitioning from the first state to the second state can be selectively controlled to achieve one or more desired characteristics associated with the transition. Moreover, in some such instances, the inflow of the last portion of the initial volume can limit and/or substantially prevent bodily fluid already disposed in the initial or sequestration portion from escaping therefrom. Accordingly, while the transitioning from the first state to the second state may occur over a given amount of time, the initial or sequestration portion of the device can nonetheless sequester the initial volume of bodily fluid disposed therein. 
     Some embodiments and/or methods described herein include one or more electronic devices configured to perform one or more processes included in and/or associated with the fluid transfer and/or rapid diagnostic testing systems and methods described herein. The electronic device(s) described herein (e.g., the electronic device  190 ) can be any suitable hardware-based computing device configured to receive, process, define, and/or store data such as, for example, one or more diagnostic test results, test standards against which to measure results data, predetermined and/or predefined treatment plans, patient profiles, disease profiles, etc. In some instances, the electronic device(s) can receive data associated with a diagnostic test, assay, and/or the like (e.g., the rapid testing device  170 ) and can be configured to analyze, process, and/or otherwise use the data to produce one or more qualitative and/or quantitative test results associated with the tests. In some instances, such a test can be, for example, a test for sepsis and/or any other disease condition. 
     Examples of electronic devices and/or components thereof are provided below. While certain devices and/or components are described, it should be understood that they have been presented by way of example only, and not limitation. Any other suitable electronic devices and/or an electronic having any other suitable components that are capable of performing the processes, procedures, and/or methods described herein may be used. 
     The electronic device(s) described herein can be, for example, a mobile electronic device (e.g., a smartphone, a tablet, a laptop, and/or any other mobile or wearable device), a PC, a workstation, a server device or a distributed network of server devices, a virtual server or machine, a virtual private server and/or the like that is executed and/or run as an instance or guest on a physical server or group of servers, and/or any other suitable device. In some implementations, the electronic device(s) can be configured to provide a graphic and/or digital representation of the test results produced by any of the rapid testing devices described herein. In addition, in some implementations, based on data associated with and/or representing test results, the electronic device(s) can be configured to determine and graphically or digitally present one or more diagnoses, one or more treatment plans, one or more simulations, and/or any other suitable data associated with the bodily fluid sample, the patient, and/or the medical treatment of the patient. 
     The components of the electronic device(s) can be contained within a single housing or machine or can be distributed within and/or between multiple physical machines, virtual machines, and/or any combination thereof. In some embodiments, the electronic device(s) can be stored, run, executed, and/or otherwise implemented in a cloud-computing environment. In some embodiments, the electronic device(s) can include and/or can be collectively formed by a client or mobile device (e.g., a smartphone, a tablet, a wearable device, and/or the like) and a server or host device(s), which can be in communication via one or more networks. Moreover, the electronic device(s) and/or any of the components thereof can be included, housed, and/or integrated in any of the fluid transfer devices and/or rapid diagnostic testing devices described herein, or any suitable combination thereof. 
     The electronic device(s) included in the embodiments described herein can include at least a memory, a processor, and a communication interface. The memory, the processor, and the communication interface can be connected and/or electrically coupled (e.g., via a system bus or the like) such that electric and/or electronic signals may be sent between the memory, the processor, and the communication interface. The electronic device(s) can also include and/or can otherwise be operably coupled to a database and/or one or more user interfaces or input/output (I/O) devices, as described in further detail herein. 
     In some embodiments, a memory can be, for example, a random access memory (RAM), a memory buffer, a hard drive, a read-only memory (ROM), an erasable programmable read-only memory (EPROM), an electrically erasable programmable read-only memory (EEPROM), a flash memory, and/or the like, or suitable combinations thereof. In some implementations, the memory can be physically housed and/or contained in or by the electronic device(s) or can be operatively coupled to the electronic device(s) and/or at least the processor thereof. In such implementations, the memory can be, for example, included in and/or distributed across one or more devices such as, for example, server devices, cloud-based computing devices, network computing devices, and/or the like. The memory can be configured to store, for example, one or more software modules and/or code that can include instructions that can cause the processor to perform one or more processes, functions, and/or the like (e.g., processes, functions, etc. associated with storing, analyzing, and/or presenting data associated with the fluid transfer and/or rapid diagnostic testing systems and methods described herein). 
     The memory and/or at least a portion thereof can include and/or can be in communication with one or more data storage structures such as, for example, one or more databases and/or the like. A database can be any suitable data storage structure(s) such as, for example, a table, a repository, a relational database, an object-oriented database, an object-relational database, a structured query language (SQL) database, an extensible markup language (XML) database, and/or the like. In some embodiments, the database can be disposed in a housing, rack, and/or other physical structure including at least the memory, the processor, and/or the communication interface. In other embodiments, the electronic device(s) can include and/or can be operably coupled to any number of databases. In some implementations, the database can be configured to store data associated with the fluid transfer and/or rapid diagnostic testing systems and methods described herein. 
     In some embodiments, a processor can be a hardware-based integrated circuit (IC) and/or any other suitable processing device configured to run or execute a set of instructions and/or code stored, for example, in the memory. For example, the processor can be a general purpose processor, a central processing unit (CPU), an accelerated processing unit (APU), an application specific integrated circuit (ASIC), a network processor, a front end processor, a field programmable gate array (FPGA), a programmable logic array (PLA), and/or the like. The processor can be in communication with the memory (and any other component of the electronic device) via any suitable interconnection, system bus, circuit, and/or the like. The processor can include any number of engines, processing units, cores, etc. configured to execute code, instructions, modules, processes, and/or functions associated with the fluid transfer and/or rapid diagnostic testing systems and methods described herein. 
     In some embodiments, a communication interface can be any suitable hardware-based device in communication with the processor and the memory and/or any suitable software stored in the memory and executed by the processor. In some implementations, the communication interface can be configured to communicate with a network and/or any suitable device in communication with the network. The communication interface can include one or more wired and/or wireless interfaces, such as, for example, a network interface card (NIC), universal serial bus (USB) card, and/or any other suitable communication and/or peripheral card or device. For example, in some implementations, the NIC can include, for example, one or more Ethernet interfaces, optical carrier (OC) interfaces, asynchronous transfer mode (ATM) interfaces, one or more wireless radios (e.g., a WiFi® radio, a Bluetooth® radio, Near Field Communication (NFC) radios, etc.), and/or the like. In some implementations, the communication interface can be configured to send data to and/or receive data from (e.g., via one or more networks) any suitable portion or device included in the fluid transfer and/or assay devices and/or systems described herein, one or more peripheral components (e.g., a reader, scanner, camera, analyzer, detector, I/O device, etc.), a user or client device (e.g., a smartphone, a tablet, a wearable electronic device, a PC, etc.), and/or the like. 
     In some implementations, a network can be any type of network(s) such as, for example, a local area network (LAN), a wireless local area network (WLAN), a virtual network such as a virtual local area network (VLAN), a wide area network (WAN), a metropolitan area network (MAN), a worldwide interoperability for microwave access network (WiMAX), a telephone network (such as the Public Switched Telephone Network (PSTN) and/or a Public Land Mobile Network (PLMN)), an intranet, the Internet, an optical fiber (or fiber optic)-based network, a cellular network, and/or any other suitable network. Moreover, the network and/or one or more portions thereof can be implemented as a wired and/or wireless network. For example, the network can include one or more networks of any type such as, for example, a wired or wireless LAN and the Internet. In some implementations, the network can be any suitable combination of devices connected and/or otherwise placed in communication via a wired or wireless connection (e.g., a USB connection, an Ethernet connection, a WiFi network, a Bluetooth network, an NFC network, and/or the like). 
     In some embodiments, a user interface can be a display or screen such as, for example, a cathode ray tube (CRT) monitor, a liquid crystal display (LCD) monitor, a light emitting diode (LED) monitor, and/or the like. In some instances, the display can be a touch sensitive display or the like (e.g., the touch sensitive display of a smartphone, tablet, wearable device, PC, and/or the like). In some instances, the display can provide a user interface for a software application (e.g., a mobile application, a PC application, an internet web browser, and/or the like) that can allow the user to manipulate the electronic device(s). In some implementations, the user interface can include any suitable type of human-machine interface device, human-computer interface device, a batch interface, graphical user interface (GUI), and the like. In some implementations, the user interface can be any other suitable user interface and/or input/output (I/O) device(s) such as, for example, a holographic display, a wearable device such as a contact lens display, an optical head-mounted display, a virtual reality display, an augmented reality display, a mouse, a keyboard, and/or the like, or combinations thereof. Accordingly, the electronic device(s) described herein can receive, process, define, and/or store data such as, for example, one or more diagnostic test results, test standards against which to measure results data, predetermined and/or predefined treatment plans, patient profiles, disease profiles, etc. In addition, the electronic device(s) can present (e.g., on the display thereof) one or more qualitative and/or quantitative test results associated with any of the rapid diagnostic testing methods described herein (e.g., rapid diagnostic tests for sepsis and/or any other disease condition). 
     Some embodiments described herein relate to a computer storage product with a non-transitory computer-readable medium (e.g., memories or one or more memories) having instructions or computer code thereon for performing various computer-implemented operations. The computer-readable medium (or processor-readable medium) is non-transitory in the sense that it does not include transitory propagating signals per se (e.g., a propagating electromagnetic wave carrying information on a transmission medium such as space or a cable). The media and computer code (also can be referred to as code) may be those designed and constructed for a specific purpose or purposes. Examples of non-transitory computer-readable media include, but are not limited to, magnetic storage media such as hard disks, floppy disks, and magnetic tape; optical storage media such as Compact Disc/Digital Video Discs (CD/DVDs), Compact Disc-Read Only Memories (CD-ROMs), and holographic devices; magneto-optical storage media such as optical disks; carrier wave signal processing modules; and hardware devices that are specially configured to store and execute program code, such as ASICs, ROM devices, RAM devices, and/or Programmable Logic Devices (PLDs). Other embodiments described herein relate to a computer program product, which can include, for example, the instructions and/or computer code discussed herein. 
     Some embodiments and/or methods described herein can be performed by software (executed on hardware), hardware, or a combination thereof. Hardware modules may include, for example, a general-purpose processor, a CPU, an FPGA, an ASIC, and/or the like. Software modules (executed on hardware) can be expressed in a variety of software languages (e.g., computer code), including C, C++, Java™, Ruby, Visual Basic™, Python™, and/or other object-oriented, procedural, or other programming language and development tools. Examples of computer code include, but are not limited to, micro-code or micro-instructions, machine instructions, such as produced by a compiler, code used to produce a web service, and files containing higher-level instructions that are executed by a computer using an interpreter. For example, embodiments may be implemented using imperative programming languages (e.g., C, FORTRAN, etc.), functional programming languages (Haskell, Erlang, etc.), logical programming languages (e.g., Prolog), object-oriented programming languages (e.g., Java, C++, etc.) or other suitable programming languages and/or development tools, and/or combinations thereof (e.g., Python™). Additional examples of computer code include, but are not limited to, control signals, encrypted code, and compressed code.