Patent Description:
This invention pertains to analyzers and methods for automatically performing microscopic cell analysis tasks, such as counting blood cells in biological samples. More specifically, the present disclosure relates to single use devices, apparatus and methods used to count red blood cells, white blood cells and platelets, and measurements related to these particles.

There are a variety of methods for enumerating particles, such as blood cells, in a biological sample. Determining the number of cells per unit volume in a sample provides the physician important diagnostic information. The most elementary method of counting cells consists of introducing a diluted biological sample into a hemocytometer and examining it with a microscope. A hemocytometer is a device with an optically clear chamber having a known depth, typically <NUM> microns, and ruled markings to define a unit volume, typically. A uniform mixture of diluted whole blood, for example, may be introduced into the hemocytometer by capillary action to form a monolayer. Using a microscope to visualize the diluted sample, cells of different types can be counted manually in a limited number of marked areas. Counts are aggregated to compute the number of cells per unit volume. This manual method is time consuming, tedious, and requires a skilled technician to operate the microscope and to recognize the various types of cells, and is prone to error. Its accuracy is limited by the number of cells counted and the uniformity of the monolayer formed by introduction of the diluted sample.

Consequently, automated methods, such as impedancemetry (Coulter principle US Patent #<NUM>,<NUM>,<NUM>) and flow cytometry, have been developed for rapid counting, sizing, and classification of a relatively large number of cells for diagnostic tests such as the Complete Blood Count (CBC), sometimes referred to a CBC with a five part differential. These automated methods also have shortcomings. The analyzers are relatively large and expensive and require skilled operators for their use and maintenance. Such analyzers are typically available only in centralized laboratories. Blood samples are collected in special containers having an anticoagulant to keep the blood from clotting while being transported to the lab. This process adds costs and risk of erroneous results from transport, handling, labeling and transcription, as well as a time delay in obtaining the results. These analyzers also flag or reject in excess of <NUM>% of the tested samples for further review by a manual differential. Only highly skilled technicians can perform a manual differential. A flag is commonly generated by impedance or flow cytometry counters because the impedance or scatter profiles of a population of cells are ambiguous. Microscopic imaging analysis is not susceptible to the same ambiguities as impedancemetry and flow cytometry, and thus is used as a reference method. Similarly, automated imaging analysis have a much lower flag rate.

The CBC generally includes measures of white blood cells (leukocytes) per unit volume (WBC), red blood cells (erythrocytes) per unit volume (RBC), platelets (thrombocytes) per unit volume (PLT), hematocrit (HCT) or packed cell volume (PCV), hemoglobin (HGB), and measurements related to red cells including mean corpuscular volume (MCV), mean corpuscular hemoglobin (MCH), mean corpuscular hemoglobin content (MCHC), and red cell distribution width (RDW). A diagnostic test sometimes referred to as a "CBC with differential", or "CBC with five part diff", will also include neutrophil granulocytes (NEU), Lymphocytes (LYM), Monocytes (MON), Eosinophil granulocytes (EO) and Basophil granulocytes (BASO) per unit volume or as a percentage of the white blood cells (WBC). The CBC with differential also may include counts of Immature Cells (IC), atypical lymphocytes, nucleated Red Blood Cells (nRBC), and Reticulocytes (RETIC) per unit volume of the blood sample.

The CBC provides a panel of blood cell measurements that can be used to diagnose a wide variety of abnormal conditions, such as anemia or infection, or to monitor a patient's treatment, such as chemotherapy. Because of its usefulness, the CBC analysis is one of the most commonly performed diagnostic tests in medicine, but patients typically wait a day or more for results. If microscopic cell analysis could be performed in a portable, easy-to-use, analyzer close to the patient, results could have a more immediate impact in improving patient care. A simple system able to provide the CBC in the physician's office, or at bedside, or in the Critical Care Unit (CCU) or Intensive Care Unit (ICU), or in the hospital emergency room within a few minutes and using a drop of blood from a finger-stick, could have enormous impact on the delivery and affordability of health care.

Recent patent documents have described simpler devices than centralized lab hematology analyzers for performing cell analysis of blood samples. In <CIT>, issued to Larsen, the applicant, provides technology for performing a flow-cell analysis of blood cells in a single use disposable cartridge. Larsen describes means for taking an exact amount of blood sample, diluting the amount of blood with a precise volume of diluent, and mixing the blood with the diluent to obtain a homogeneous solution. Larsen utilizes a single use cartridge to flow a measured amount of the mixture of sample and diluent through an orifice at a rate of several thousand particles per second, and counts, sizes, and classifies the particles for analysis in accordance with the Coulter principle. Because Larsen's disclosure is directed to the analysis of a small sample of whole blood, errors in metering various volumes or in the mixing or sampling steps can significantly impact the accuracy of the results.

<CIT>et al. describes a system for analyzing a blood sample with a mobile electronic device having a camera. The sample preparation process for each test requires accurate measurement of <NUM>µL of whole blood to be mixed with <NUM>µL phosphate buffered saline and <NUM>µL of nucleic acid stain. Ten (<NUM>) µL of this diluted mixed sample are then loaded into a cell counting chamber with precise channel height of <NUM> and are imaged by a digital camera. A separate cell counting chamber is needed for analysis of red cells, white cells, and hemoglobin, and each test should be performed separately. Accuracy of the final result is not only dependent on the accurate measurements of the various sample preparation steps, including the precise metering of the sample and diluent, but also on the precise fabrication of the counting chambers. Maintaining uniformity and consistency of the <NUM> pm dimension of the channel height in a disposable cartridge is difficult to achieve in a low cost device.

<CIT>et al. describes a method for determining cell volume of red blood cells, which seeks to avoid the errors associated with diluting, mixing, and sampling, by analyzing a sample of substantially undiluted whole blood. In theory this approach has appeal, but the handling of undiluted whole blood is challenging. The cells are so numerous (for example <NUM>,<NUM>,<NUM> red cells in <NUM> pL) that their distribution can be impacted by contact with the surfaces of a disposable cartridge. Additionally, in order to image cells in this overcrowded environment, the imaging chamber should have a depth of only a few microns to prevent the overlapping of cells, and it should be fabricated accurately, because it determines the volume of the blood sample being analyzed.

Therefore a compact, accurate method of performing microscopic cell analysis using digital camera imaging of a diluted sample, which does not require accurate measurement of the diluent volume, or require accurate or precise dimensions of an imaging chamber, is highly desirable.

<CIT> discloses a method, kit and system for imaging a blood sample, in which a monolayer of a suspension of blood cells is imaged with a microscope.

<CIT> discloses a dual sample cartridge and method for characterizing particles in liquid, in which a disposable cartridge for single-use analysis is used for receiving and holding first and second liquid samples. Blood samples partly or fully constituting first and second liquid samples in a first cavity and a second cavity, respectively, may be diluted and prepared for analysis in a mixing chamber. The samples are analyzed by impedance sizing, i.e. the Coulter Principle, through an orifice in a wall of the mixing chamber. A conductive liquid forms an electrical connection from a first electrode in the mixing chamber to a second electrode in a collection chamber. Changes in impedance of the electrical connection originating from cells passing in a liquid flow through the orifice can be recorded for counting and sizing of the cells.

<CIT> discloses a microscopy system and a method for analyzing fluids in flow, in which a microfluidic cartridge receives fluids and agents to form a mixture and an imaging zone receives the mixture, an illumination unit in a microscopy system captures images of elements of the mixture flowing through the imaging zone.

In accordance with the invention there is provided a method of counting and analyzing biological particles in whole blood and a single-use cartridge for counting and analyzing biological particles in whole blood, as defined by the appended claims.

An objective of the present invention is to provide an apparatus that can provide counts of cells or other particles of a biological sample per unit volume without requiring an operator having specialized knowledge or specialized skills. Another objective of the present invention is to provide an easy-to-use analyzer that can perform all of the measurements of the CBC in a few minutes. Another object of the invention is to provide an analyzer to perform a CBC on a small finger stick sample. Another objective of the present invention is to provide a method for determining the concentration of particles in a diluted biological sample that does not require accurate measurement of a volume of diluent or reagent mixed with the sample. Another objective of the present invention is to provide ready-to-use reagents and diluent for use in performing the microscopic analysis of a biological sample that do not require preparation, mixing or measurement by the user. Another object of the invention is to create a substantially homogenous monolayer of cells of a diluted sample in a single use disposable device and to perform a CBC analysis in a few minutes. Another objective is to provide a sample collection device that can easily be operated by a user to obtain a biological sample for analysis. Yet another objective is to provide all of the fluidic components of a CBC analyzer in a single-use device, so as to prevent cross contamination between samples and to avoid the need for cleaning and washing of fluidic components of an analyzer. Another objective of the present invention is to provide internal monitoring of the critical process steps of counting cells, so that a potentially erroneous result can be flagged. Still another objective is to provide a method of performing the CBC on a sample immediately after collecting it, and to eliminate transport of the sample to a laboratory or storage of the sample. Some or all of these and/or other objectives or advantages may be accomplished by embodiments of the invention as provided for in the appended claims.

A further object of the invention is to provide a hematology analyzer that performs a CBC using imaging technology instead of the Coulter principle of flow cytometry. Another object of the invention is to provide a hematology analyzer that utilizes a single use disposable imaging chamber. Another object of the invention is to provide a substantially homogenous monolayer of cells and platelets of diluted whole blood in their unrestrained state incontradistiction to cells smeared or syrayed on a glass slide, wherein the cells are mechanically deformed or distorted or flattened, or cells that are sprayed or deposited on a glass slide and fixed. Another object of the invention is to provide an imaging based hematology analyzer that flags samples at a lower rate than hematology analyzers that use impedancemetry or flow cytometry.

The disclosure provides improved methods, systems, and devices for performing counts and measurements of particles in a biological sample. Aspects of the disclosure are directed to determining the concentration of one or more types of particles of a biological sample and providing the result as the number of such particles per unit volume in a few minutes. The particles may be any mass suspended in a liquid that can be recognized by optical inspection using an automated microscope and image analysis techniques well known in the art. Examples of particles include, but are not limited to, blood cells, platelets, sperm, bacteria, spores, and inorganic particles.

While embodiments of the present invention can be used in many applications to count particles suspended in a liquid, the present disclosure will demonstrate benefits of the invention in performing the Complete Blood Count (CBC) or CBC with differential on human or animalblood samples as defined above. The present disclosure describes a single-use test cartridge for use with an apparatus that includes an automated microscope for analyzing cells in a biological sample. The test cartridge is used to collect a biological sample. For example the user can prick the finger of a patient and obtain a whole blood sample and collect the resulting drop of blood in the test cartridge. The user can accomplish this by holding the test cartridge beneath the hanging drop from the patient's finger and then bringing it closer until the drop contacts an input port or sample cup on the test cartridge. In an alternate embodiment, the user may take a blood sample intravenously and transfer it to the test cartridge using a plastic bulb pipette. In one example the single-use test cartridge includes an input port adapted to accept a variety of sources of biological samples including a direct sample, capillary tube, or transfer pipette. In another example, the test cartridge could draw a sample into it by capillary action. The test cartridge may also include a closure that the user applies to cover the input port after the sample has been collected into the test cartridge. The closure may be part of the test cartridge or a separate device. The user may apply the closure manually or the apparatus may automatically move the closure to cover the input port when the test cartridge is docked to the apparatus. The closure provides a physical barrier to avoid subsequent contact with any excess sample on the surface of the test cartridge. The closure has a vent to provide an air path to the input port to allow the liquid sample to move within the test cartridge if a vacuum is applied, as will be described below.

Within the test cartridge, the input port is connected by an input channel to a metering chamber capable of precisely separating a small volume of the sample from the unmeasured sample. As an example, the collected sample volume may be <NUM>-<NUM>µL, of which the metering chamber separates out or isolates <NUM> - <NUM>µL for measurement. If a finger stick sample is utilized, a sample volume less than <NUM>µL will minimize the risk of hemolysis and the risk of dilution by interstitial fluids. The metering chamber can be a section of a fluid channel, a cavity, or a pass-through conduit within a valve, or another volumetric shape that can be reproducibly fabricated to contain a predetermined volume of the biological sample in the range of <NUM> to <NUM>µL. Injection molding, compression molding, etching or other processes known to those skilled in the making of lab-on-a-chip or microfluidic devices can be utilized to manufacture the metering chamber.

In one example, the metering chamber is combined with a rotary valve structure by molding a pass-through conduit in the cylindrical stem of the rotary valve. As an example a pass-through conduit having a cylindrical cross section with <NUM> diameter and a length of <NUM>, has an internal volume of approximately <NUM>µL. The pass-through conduit is initially filled with the biological sample by providing a fluid communication path between the input port and input channel, the pass-through conduit, and a vacuum channel. A vacuum applied to the vacuum channel pulls the sample into the pass-through conduit. Alternatively the biological sample can be pulled into the pass-through conduit by capillary action. Once the biological sample has completely filled the pass-through conduit, the cylindrical stem of the rotary valve is rotated until the pass-through conduit is no longer connected to the input channel or the vacuum channel, thus separating or isolating the sample volume contained in the pass-through conduit. Alternatively, a rotary face seal valve, a slide valve, or a fixed volume in the test cartridge could be used to isolate a small volume of the sample.

Further, elements of the test cartridge include a prepackaged liquid reagent or alternatively, a chamber for storing a liquid reagent, together with a mixing chamber, an imaging chamber, and fluid channels through which the sample and liquid reagent may be moved. In one example, after the biological sample has filled the pass-through conduit, the rotary valve is positioned so that the pass-through conduit is placed in fluid communication with both a liquid reagent and the mixing chamber. Empirical studies have determined that a volume of liquid reagent or diluent or stain (referred to hereafter as "diluent/reagent") that is in excess of <NUM>-times the volume of the pass-through conduit is sufficient to wash out the entire isolated sample. In one example, the diluent/reagent is a combination of diluent and stain and is supplied in a volume to provide a dilution ratio of about <NUM>:<NUM>. Therefore forty times the volume of the metering chamber can be used to push the isolated sample out of the pass-through conduit and into the mixing chamber, where the sample is uniformly mixed with the diluent/reagent, and then transferred into the imaging chamber.

The single use test cartridge contains an imaging chamber, through which an automated microscope can acquire images of cells in the mixture of diluent/reagent and sample. In one embodiment of the present invention, the isolated sample volume is diluted with a known volume of diluent/reagent, whereby the dilution ratio is established. The volume of the diluent/reagent may be determined by measuring it, for example, by monitoring its flow in a fluid channel of known dimensions with a camera or other fluid sensor such as optical reflective/transmitted or ultrasonic, or by temporarily metering it into a known volume chamber and then using only that known volume for sample dilution. According to this embodiment, the cells in a known volume of the diluted sample are counted, and because the dilution ratio is known, the cell counts per unit volume of the blood sample can be determined. The volume of the diluted sample can be determined by filling an imaging chamber of known volume with the diluted sample. The volume of the imaging chamber may be known by using highly reproducible manufacturing processes, or by measuring each test cartridge at time of manufacture and encoding sizing parameters in the package labeling. Alternatively, a measured amount of the diluted sample can be transferred into an imaging chamber of unknown volume and all the cells in the chamber are counted. A measured amount of the diluted sample can be determined by monitoring its flow from the mixing chamber into a fluid channel of known dimensions by a camera, and isolating a segment. The segment, in turn, is moved into the imaging chamber.

In a preferred embodiment, the isolated sample volume is transferred to the mixing chamber and then to the imaging chamber. According to this embodiment, neither the dilution ratio nor the volume of the diluent needs to be known. The size of the imaging chamber is chosen to ensure that the entire volume of the isolated sample and the diluent/reagent can be contained within the imaging chamber, but the exact dimensions or volume of the chamber do not need to be known. The depth of the imaging chamber should be small enough to prevent the cells from overlapping at the chosen dilution ratio when the cells settle to the bottom. This depth is preferably between about <NUM> and <NUM>. In one embodiment, the depth of the imaging chamber is <NUM> and the ratio of the diluent/reagent to the isolated sample is <NUM> to <NUM>. The width of the imaging chamber is chosen to provide uniform filling by the different cell sizes and smooth flow without forming voids or crowding of cells. The length of the imaging chamber is calculated based on the depth and width parameters to provide the volume needed to accommodate the entire isolated sample at the chosen dilution ratio, and to provide a safety margin. The shape of the imaging chamber may further be chosen to match the field of view of the digital camera or to facilitate capture of multiple images or to maintain a uniform distribution of cells.

We have found that if the shape of the imaging chamber is square or rectangular having a ratio of length to width of <NUM>:<NUM>, the cells will not uniformly fill the imaging chamber. If the mixture of sample and diluent/reagent is uniform when it enters the imaging chamber, the cells will tend to bunch and crowd, particularly near the sides or edges, and when they settle, the layer on the bottom of the imaging chamber will not be homogenous. It is important to obtain a substantially homogenous monolayer of cells in the imaging chamber, as this facilitates the counting of all the cells. We have found that if the width and depth of the imaging chamber are small compared to the length, the cells remain substanially uniformly distributed. Desirably, the length-to-width ratio of the imaging chamber is greater than <NUM>:<NUM>. In various embodiments of the present invention, the shape of an imaging chamber may be serpentine, helical, or castellated according to the form factor of the test cartridge. In all of these cases the width and depth are small compared to the length so that the cells due not aggregate on the sides or corners of the imaging chamber, and the layer of cells settling to the bottom of the imaging chamber is substantially homogenous. Those skilled in the art will recognize that other geometries for the imaging chamber, which maintain the distribution of cells when the mixed solution of sample and diluent/reagent is transferred into the imaging chamber may also be utilized.

The design goal of the imaging chamber is to contain all the cells from the original metered chamber and the diluent/reagent in a uniform manner and without significant cell overlap when the cells settle to the bottom of the imaging chamber. The dilution ratio combined with the depth of the imaging chamber can be chosen to minimize the overlapping. As an illustrative example, an imaging chamber may have a width between. <NUM> and <NUM>, a depth from <NUM> to <NUM>, and the dilution ratio may be from <NUM>:<NUM> to <NUM>:<NUM>.

Materials, which contact the cells outside of the imaging chamber, may be chosen to have surface properties to minimize cell adherence. Liquid reagents, which may include a surfactant or cell sphering agent to facilitate cell analysis, may also advantageously minimize red cells being lost during transfer or being overlapped in the imaging chamber. The volume of liquid reagent and the flow velocity may also be chosen to improve the likelihood of transferring every cell from the metering or mixing chamber to the imaging chamber and insuring that the distribution of the cells remains uniform. Yeh-Chan Ahn describes the complex convective diffusion phenomena that is created in a serpentine microchannel which has a varying curvature (See <NPL>). Particles, or in our case, cells which are in suspension and moving through such a microchannel tend to segregate according to their size, density, channel shape and flow velocity. Secondary flow from the serpentine geometry can create vortices as the channel curves causing the cells to be re-mixed into the center of the flow at certain fill velocities. This re-mixing helps maintain a near uniform distribution of the cells as the fluid fills the microchannel. In one embodiment, we have found that a serpentine path that is <NUM> wide with turning inside diameter of <NUM> and an outside diameter of <NUM>, a depth of <NUM>. <NUM>, a length of <NUM>, and an effective fill speed of about 2µL/s insures that the flow of cells remains uniform.

It should be noted that the time to count every cell is directly related to the volume of the metered chamber, and that this creates a trade-off in overall performance. Manufacturing highly reproducible metering chambers is challenging for very small volumes. However, while it may be easier and more reproducible to manufacture a metering chamber with a 5µL volume than one with a 1µL volume, it would potentially take five times longer to count every cell, and analyze them, in a <NUM> uL volume of sample than a <NUM> uL sample volume. Embodiments of the present invention can provide a solution to this dilemma. By ensuring that the sample and diluent/reagent are well mixed and that a proper dilution ratio is chosen, and by utilizing a serpentine shaped imaging chamber where the length is large compared to the width and depth, the pattern of cells across the imaging chamber is relatively uniform and reproducible. Under these conditions, the layer of cells settling to the bottom of the imaging chamber will be a substantially homogenous monolayer. As a result, instead of imaging the entire layer and counting every cell, one can take representative images or frames that are statistically derived to accurately account for every cell. Thus, within the allowable error for the final result(s), every cell is included in the analysis, whether by actual image or by statistical representation. As an illustrative example, the camera may take up to <NUM>,<NUM> images at 20X in order to scan the entire imaging chamber. Alternatively, every tenth frame could be taken to obtain a statistical representation. Another option would be to divide the imaging chamber into segments and count the cells in every other segment or every third segment and so on. Another alternative to decrease the imaging time would be to scan the entire imaging chamber at 10x/<NUM> numerical aperture (NA) or 4x/<NUM>. 1NA to obtain the total WBC and RBC total counts, and then take images at higher power (20X. 04NA or higher) to obtain the higher-resolution detail needed for counting platelets, reticulocytes, and performing the WBC differential.

Embodiments of the present invention can achieve accurate results independent of the many factors that have impacted the accuracy of results in the prior art. For example, the volume of the diluent/reagent and the dilution ratio do not impact the results, so long as all the cells from the metered sample volume are transferred to the imaging chamber and are not overlapping or crowded, and presented for analysis. Similarly the representativeness of a selected portion of the mixture of sample and reagent, and the homogeneity of the portion, which directly affect the accuracy of results by prior art methods, need have no impact on embodiments of the present invention. Most importantly, the depth and uniformity of the imaging chamber, which has been difficult or expensive to control in other prior art efforts, need not impact the accuracy of results according to embodiments of the present invention.

The present disclosure further describes a cell analyzer that is small and easy to use. The cell analyzer accepts the test cartridge and carries out all the steps of the cell analysis without further input from the user. In one embodiment, the test cartridge contains all diluents and reagents needed to perform a CBC analysis of the patient sample placed in it. In this embodiment, the cell analyzer has fluid handling components including positive and negative pressure sources that interface with the test cartridge when it is placed into the analyzer. One or more connections are made between the analyzer and the cartridge to place these pressure sources into fluid communication with channels in the cartridge to provide a motive force to move liquids within the cartridge. The cell analyzer also has a mechanical valve driver for operating a valve in the test cartridge for controlling the movements of fluids in the test cartridge. When the test cartridge is placed in the analyzer, the mechanical valve driver is connected to a valve indexer to provide means for operating the valve in the test cartridge. The cell analyzer includes a mechanism for release of the diluent/reagent that are stored on board the test cartridge. The cell analyzer further includes fluid control logic to automatically control movement of the fluids in the test cartridge by activating the positive and negative pressure or displacement sources and operating the mechanical valve driver according to pre-programmed sequences. The cell analyzer may include a process monitoring camera positioned to acquire digital images of the movement of fluids in the cartridge. Information from the process monitoring camera can be used to provide feedback for the fluid control logic or for monitoring critical steps.

The present disclosure also provides devices and methods for managing and/or monitoring the sample collection and preparation process to ensure accurate results. In applications where the present invention is used to perform a CBC analysis, if too much time lapses between obtaining the blood sample and completing sample dilution and staining within the test cartridge, the blood may clot or the cells may settle resulting in erroneous results. In one embodiment of the present invention that mitigates this risk, the test cartridge is placed on the analyzer in a slide-out tray which initiates process monitoring within the analyzer. The blood sample is added to the cartridge by dispensing a free-hanging drop, or by using a capillary tube that is inserted into the test cartridge or by transferring a sample and depositing it with a pipette. Immediately after the sample has been added to the cartridge, the user presses "Run Sample" to initiate the test sequence. Because the cartridge is controlled by the analyzer, the time to collect the sample is known and can be short enough to avoid the need for anticoagulant coating or mixing the blood sample.

In an alternate embodiment that allows the sample to be collected several minutes before processing, an anticoagulant, such as K2 or K3 EDTA, is provided. This may be achieved by coating the sample input cup with anticoagulant, by use of a capillary tube coated with anticoagulant for a finger-stick sample, or by sampling from an evacuated blood collection tube such as a Becton Dickenson Vacutainer® containing anticoagulant. To manage cell settling, the test cartridge according to this embodiment has a timing indicator which is initiated when the input port is opened or the blood sample is introduced. The timing indicator can be a color-changing chemical reaction, a time delayed thermal reaction, an analog or digital timer, or other means known in the art. When the user loads the test cartridge into the analyzer, the timing indicator is read and if needed, the sample is mixed before proceeding. If too much time has lapsed the sample can be rejected to avoid producing erroneous results.

In yet another embodiment that facilitates remote sample collection, the test cartridge is docked to a carrier system. The carrier system is a handheld or portable device used to facilitate a portion, or all, of the sample preparation steps. After blood is added to the test cartridge using any of the above mentioned methods, the carrier system according to this embodiment draws the blood into the cartridge, meters the sample, performs quality checks, and completes the sample preparation to present the cells for image analysis. The carrier system would then either eject the test cartridge for the user to transfer to the imaging analyzer, or the carrier system could be docked to the imaging analyzer for an automated handoff. In this embodiment anticoagulant coatings are not needed and there is no risk of cell settling because the critical steps are initiated as soon as the sample is placed in the test cartridge.

Combinations of the workflow devices and methods are also contemplated in the present disclosure. By way of example, a simple carrier system could incorporate a digital timer and a mechanism able to meter the sample, but not perform quality checks or full sample preparation. These additional steps would be done by the cell analyzer.

The cell analyzer contains an automated microscope including an objective lens, focusing mechanism, bright-field and/or fluorescent light sources or both, filters, a dichroic mirror and a digital camera. In some embodiments, the cell analyzer may further include an illumination source and photometric detector for measuring light transmission at one or multiple wavelengths for measuring the concentration of an analyte in the sample. For example, the test cartridge can include a photometric chamber which is in fluid communication with the input port by means of a fluidic channel, and through which the sample can be transferred for photometric analysis, such as a hemoglobin measurement.

By way of example, to measure hemoglobin, the cell analyzer may have an illumination source consisting of two light emitting diodes (LEDs) providing excitation at wavelengths of <NUM> and <NUM>. The light path for the LEDs and a photometric detector are approximately <NUM>" diameter. The <NUM> LED may be selected for absorbance measurement because of an isobestic point of oxyhemoglobin (O2Hb) and deoxyhemoglobin (RHb). Also at <NUM>, the slope of the O2Hb and RHb curves are very low, resulting in minimal variation with varying oxygen saturation (sO2) levels. Furthermore, the carboxyhemoglobin (COHb) curve is also close to this isobestic point, resulting in very little effect from COHb. An <NUM> LED can measure the background scatter effects caused by RBCs, WBCs, lipids, etc. This is particularly important when taking measurements on whole blood. This measurement may also be performed on lysed blood, with or without a reagent for converting the hemoglobin to a single form, such as reduced hemoglobin, methemoglobin, azidemethemoglobin or cyanomethemogloin. In the case of a conversion to a single form of hemoglobin, a different peak wavelength for absorption measurement may be used, such as <NUM> or <NUM>.

Disclosed and contemplated aspects also include an example of a test cartridge that is not preloaded with reagents, and instead, is coupled to a reagent supply module contained on board the cell analyzer. The user loads the reagent supply module into the cell analyzer where it is utilized for multiple test cartridges. When the reagent supply module is exhausted or expires, the cell analyzer alerts the user and will not perform additional tests until the reagent supply module is exchanged. The reagent supply module includes a cradle for receiving the test cartridge, a vessel for holding a liquid diluent/reagent, a diluent delivery pump in fluid communication with the vessel, and a diluent/reagent output port constructed to interface with the test cartridge when the cartridge is in the cradle. In one example the size of the vessel is of sufficient capacity to provide diluent/reagents to dilute several samples (<NUM>-<NUM>) with a reagent to sample ratio of <NUM>: <NUM> to about <NUM>: <NUM>. The diluent/reagent supply module may include a self-priming mechanism for priming the liquid reagent and eliminating air bubbles. 'The reagent supply module may further include a chamber for collecting waste diluent/reagent from the priming process.

In another embodiment contemplated in the present disclosure, a small measured volume of whole blood may be mixed manually with an imprecise amount of diluent/reagent in a sample preparation device. For instance, the known volume of sample and imprecise diluent/reagent may be put into a sample tube and gently rocked back and forth a few times. The entire mixed volume is then transferred by using a transfer pipette or similar device to a test cartridge having an imaging chamber sufficiently large to contain the entire mixed volume. According to embodiments of the present invention, if all of the cells in the imaging chamber are counted (either directly or by statistical sampling), then the concentration of cells per unit volume can be determined, without one needing to know the volume of the diluent/reagent, the dilution ratio, or the volume of the mixed sample in the imaging chamber, or the volume of the imaging chamber occupied by the mixture. One drawback to this embodiment is the practical difficulty in measuring a small volume of sample, e.g. <NUM> uL. If a large volume of sample is chosen, such as <NUM> uL, it will take a longer time to count all the cells and it will require a relatively large imaging chamber. In the case of a <NUM> uL sample size and a dilution ratio of <NUM>:<NUM>, an imaging chamber of <NUM> uL would be required. An alternative embodiment would be to take a <NUM> uL sample and mix it with a precise volume of diluent, and then taking a portion of the mixture and transferring it into an imaging chamber sufficiently large to contain the portion of mixture. If every cell of the mixture is counted, the number of cells per unit volume can be easily determined, since the dilution ratio is known.

Diluent/reagents that are preloaded in the test cartridge, or are provided in a separate sample preparation device, or by a supply module are in a ready-to-use format. For a CBC analysis, the reagents may include a membrane-permeable dye, such as Acridine Orange to differentially stain the DNA and RNA of cells in whole blood. Other stains known to those skilled in the art, such as cyanine dyes, can also be used to stain the blood cells. In an alternative arrangement, the stain may be provided in a dry reagent form together with a diluent that is mixed with the dry reagent as needed. Multiple stains can be included in a combination reagent. In one embodiment, the reagents may include an antibody conjugated to a detectable label that targets specific cells or specific antigens associated with cells. The detectable label may be a dye, a fluorescent dye, quantum dot, colloidal metal such as gold, silver, or platinum or other detectable constructs known in the art. The detectable label can also be used to detect a cell-specific antibody, such as CD3, CD4, CD14, CD16, CD19, CD34, CD45, CD56, or any other of the enumerated Cluster of Differentiation markers. The detectable label can also be used to detect bacterial or parasitic pathogens, platelets, recirculating tumor cells, leukemic cells, stem cells or any combination of these.

In other embodiments the liquid reagent may contain a surfactant such as polysorbate or sodium dodecyl sulfate (SDS), an anticoagulant such as EDTA, and/or a sphering agent such a zwitterionic detergent to provide isovolumetric reshaping of the red blood cells to facilitate cell size measurement and computation of the mean corpuscular volume (MCV).

Systems according to the invention can exhibit better quantitative accuracy than manual microscope analyses using a manual hemocytomer or similar device, which tend to be limited by variability in sample preparation and limited counting statistics. In embodiments of the present invention, sample preparation is improved by removing critical operator fluid handling steps and by automation of all dilution steps. Because every cell and platelet is counted in the entire metered volume of sample, any error in the sample dilution is irrelevant.

Systems according to the invention can also save time that would otherwise be allocated to manual hemocytometer slide preparation, setup time, and microscope focusing, which can limit the number of blood samples that can be analyzed. Automation can greatly increase the rate of image acquisition and analysis, allowing for more cells to be analyzed and counted. This can improve the counting statistics and overall precision of the system.

Systems according to the invention can also extend the capabilities of cell counting methods by enabling CBC point-of-care testing, i.e. near patient testing, to permit immediate clinical decisions to be made. Personnel having a relatively low skill level can operate the systems. The analyzers can be engineered to be inexpensively manufactured and easily serviced, allowing them to be more readily deployed at point-of-care sites, such as at the patient's bedside, in physician's offices, and at emergency sites.

In the following description, various embodiments of the present invention are described with reference to the following drawings, in which:.

<FIG> illustrates test cartridge <NUM> being positioned to collect a drop of blood <NUM> from a patient's finger. The test cartridge is held beneath the hanging drop <NUM>, so that it contacts the input port <NUM> of the test cartridge <NUM>. The input port <NUM> comprises a recessed area or opening that may be coated with an anticoagulant and have surface treatment or features such as small columns to increase surface retention to collect and hold the blood sample. In an alternate embodiment, the blood sample <NUM> may be collected intravenously and introduced to input port <NUM> by a transfer pipette or capillary tube. The transfer pipette or capillary may contain an anticoagulant coating according to the desired workflow. The volume of blood or other biological sample placed in input port <NUM> is sufficient to visually fill the recessed sample area, but is unmeasured.

<FIG> shows test cartridge <NUM> with closure <NUM> shown in the open position to provide access to input port <NUM>. Closure <NUM> is adapted to slide relative to the test cartridge <NUM> and may have detent or other positioning features that facilitate placing it in different positions. After the biological sample has been collected into input port <NUM>, closure <NUM> may be moved to the position shown in <FIG> to cover the input port <NUM>. The closure <NUM> may be moved by the user prior to inserting it into the analyzer as shown in <FIG>. Alternatively, closure <NUM> may be moved by an operation within the cell analyzer. Alternate embodiments of closure <NUM> may include graphics, identifying information, or instructions to the user. While the closure <NUM> is illustrated as a sliding component, other means of closing the input port <NUM> are contemplated including a cap that hinges upward, a small surface cover that swivels away from and returns to cover the input port <NUM>, or an adhesive component that sticks to the input port <NUM> or area surrounding it. In all cases the closure <NUM> includes a vent or air path to the input port to allow the blood sample to move into the test cartridge <NUM>.

<FIG> is a cut-away view of an illustrative cell analyzer <NUM> with test cartridge <NUM> positioned so that the operator can introduce it into the analyzer. From the outside of the cell analyzer <NUM>, one can see the housing <NUM>, a user-interface screen <NUM>, a printer <NUM>, and a cartridge loading door <NUM>. When the cartridge loading door <NUM> is opened, the test cartridge <NUM> can be placed on a cradle <NUM> of x-y stage <NUM>, configured to receive test cartridge <NUM> from the user. The cradle <NUM> provides mechanical alignment of the cartridge to facilitate connections that are made between the analyzer and the cartridge. For example, a mechanical presser foot <NUM> may be placed in contact with a flexible surface on the test cartridge to provide mechanical pressure onto packaged, on-board reagents. Some embodiments of the cell analyzer <NUM> may utilize a reagent supply module <NUM> as further described with reference to <FIG>. Reagent supply module <NUM> may be installed on x-y stage <NUM> and has a receiving area <NUM> (see <FIG>) to provide alignment of the test cartridge <NUM> with the reagent module <NUM>.

A valve driver <NUM> can be positioned to operate a rotary valve on the test cartridge. A vacuum/pressure pump <NUM> supplies negative or positive pressure to a manifold <NUM>, which interfaces with the test cartridge <NUM> when it is placed in the cell analyzer as described below. The cell analyzer <NUM> further includes system controller <NUM> to control movement of the fluids in the test cartridge by activating the vacuum/pressure pump <NUM>, moving the mechanical presser foot <NUM>, or operating the valve driver <NUM> according to pre-programmed sequences. Monitoring camera <NUM>, positioned to acquire digital images of the fluids in the cartridge, provides feedback for the system controller <NUM>. Monitoring light source <NUM> may be a ring illuminator that surrounds the lens of the monitoring camera <NUM>. Information from the monitoring camera <NUM> is used to provide feedback for controlling movement of liquids, for positioning the rotary valve, and for confirming critical steps.

Also shown in <FIG> are the components that comprise the automated microscope of the cell analyzer <NUM>. At the base of the analyzer, bright-field light source <NUM> provides illumination through the test cartridge to the objective lens <NUM>, operatively coupled to focusing mechanism <NUM>. At the top of the analyzer, fluorescent light source <NUM> provides illumination through dichroic mirror <NUM> to provide fluorescent excitation of the sample. At the rear of the analyzer, digital camera <NUM> captures images of the test cartridge <NUM> and transmits them to image processor/computer <NUM>. In some embodiments, the cell analyzer may further include a photometric light source <NUM> and photometric detector <NUM> for measuring light transmission at one or multiple wavelengths in a chamber in test cartridge <NUM>, such as for measuring hemoglobin, as is more fully explained below.

<FIG> shows an illustrative test cartridge <NUM> of the type that includes liquid reagents stored in a blister pack <NUM> for conducting a test. The test cartridge <NUM> has an input port <NUM> for receiving a sample, a passive mixing chamber <NUM> for mixing the sample with diluent/reagent, and an imaging chamber <NUM> for capturing images of the cells in the mixture of sample and diluent/reagent for analysis. In this embodiment, photometric chamber <NUM> may be filled with whole blood to make optical absorbance measurements to determine concentrations of certain analytes in the sample, such as hemoglobin. A rotary valve <NUM> provides fluidic connections between various fluidic channels, vents, and ports, including sample driver port <NUM>, vent <NUM> and mixture driver port <NUM> as will be described in <FIG>.

<FIG> shows an illustrative test cartridge <NUM> of the type that does not include on-board diluent/reagents. Many of the functional components are identical to those illustrated with reference to test cartridge <NUM>, but instead of on-board diluent/reagents, test cartridge <NUM> has a reagent input port <NUM> adapted to be connected to an external source of diluent/reagent. Test cartridge <NUM> may be used in embodiments in which diluent/reagents that are needed for an analysis may be too costly to package individually or may require refrigerated storage. In such an embodiment, diluent/reagent may be provided from a source within cell analyzer <NUM> or from a reagent supply module.

<FIG> shows an illustrative reagent supply module <NUM> positioned to receive test cartridge <NUM>. The reagent supply module <NUM> includes a receiving area <NUM> for docking the test cartridge <NUM>, and contains a vessel for holding the diluent/reagent, a reagent metering pump adapted to pump the diluent/reagent, and a reagent output port <NUM>. The reagent output port <NUM> is constructed with a suitable shape and/or elastomeric materials to insure a liquid-tight connection to reagent input port <NUM> on the test cartridge <NUM>, when the test cartridge is docked to the reagent supply module <NUM>. Reagent supply module <NUM> has an opening <NUM> suitably sized to allow monitoring camera <NUM> (<FIG>) to image the rotary valve <NUM>. Additionally a window <NUM> in the reagent supply module <NUM> is constructed to align with the photometric chamber <NUM> in the test cartridge. Window <NUM> allows the photometric light source <NUM> and photometric detector <NUM> (<FIG>) to make optical absorbance measurements on the fluid within photometric chamber <NUM>.

In one embodiment, the size of the vessel within reagent supply module <NUM> is of sufficient capacity to provide diluent/reagents to dilute and/or stain from ten to about one-hundred samples with a diluent/reagent to sample ratio of <NUM>:<NUM> to about <NUM>:<NUM>. The reagent supply module <NUM> further can include a self-priming mechanism for priming the liquid reagent and eliminating air bubbles. In such an embodiment, the reagent supply module <NUM> may include a chamber for collecting waste reagent from the priming process. Once the test cartridge <NUM> is docked with the reagent supply module <NUM> the combined pieces perform the same functions as test cartridge <NUM> except that the reagent supply module <NUM> replaces the blister pack <NUM>. Inside cell analyzer <NUM> the vacuum/pressure pump <NUM> makes connections through manifold <NUM> to sample driver port <NUM> and mixture driver port <NUM>. The interfaces between the manifold <NUM> and these ports are constructed with a suitable shape and/or elastomeric material to ensure an airtight connection so that system controller <NUM> can control movement of the fluids in the test cartridge (see <FIG>). In such an embodiment the presser foot <NUM> is not needed.

The only volume that is measured precisely is the metered volume of the original biological sample. Various means for metering a small volume of liquid are well known in the art. Two devices that are well suited for low cost, single use applications according to the present invention are shown in <FIG> shows the face of a cylindrical valve stem <NUM> of a rotary face valve. Metering chamber <NUM> is formed in the face by highly precise manufacturing processes such as injection molding. The chamber <NUM> is narrow and tubular in shape and centered in the face of the cylindrical stem <NUM>. A slot <NUM> in the top of stem <NUM> acts as a valve indexer to indicate the position of the valve stem <NUM>. Also formed in the face of valve stem <NUM> is an auxiliary connector <NUM>, which has a circular shape. When assembled into the rotary valve <NUM> (<FIG> and <FIG>), metering chamber <NUM> is able to connect between ports in the valve which are <NUM> degrees apart, while auxiliary connector <NUM> connects between other ports which are <NUM> degrees apart. As will be explained with reference to <FIG>, system controller <NUM> is able to control movement of the fluids by rotating valve stem <NUM> and by positioning the valve according to the valve indexer <NUM> according to preprogrammed sequences. Thus in a first position, the metering chamber <NUM> can be connected to the input port <NUM> (<FIG> and <FIG>) and filled with the biological sample, and then by rotating valve stem <NUM>, the volume contained within metering chamber <NUM> can be isolated and transferred for analysis.

<FIG> is a side view of a valve stem <NUM>' with a metering chamber formed as a pass-through conduit <NUM> in the tapered seat of valve stem <NUM>'. Pass-through conduit <NUM> is able to connect with fluidic channels in rotary valve <NUM> which are <NUM> degrees apart. Also shown in <FIG> is auxiliary fluidic connector <NUM>', which provides connections to adjacent fluidic channels which are <NUM> degrees apart.

When assembled in the rotary valve <NUM> (<FIG> and <FIG>) having a tapered seat to receive valve stem <NUM>', pass-through conduit <NUM> can be connected to input port <NUM> (<FIG> and <FIG>), filled with the biological sample, and then by rotating valve stem <NUM>', the volume of sample contained within pass-through conduit <NUM> can be isolated and transferred for analysis. <FIG> also shows auxiliary fluidic connector <NUM>', which provides fluidic connections to adjacent fluidic channels on the test cartridge according to the position of the valve indexer <NUM>'. It will be appreciated that the rotary face valve of <FIG> and the tapered seat valve of <FIG> are alternate embodiments for isolating sample and controlling fluidic paths. Therefore, in the descriptions that follow references to metering chamber <NUM> in a rotary face valve will be equally applicable to pass-through conduit <NUM> in a tapered seat valve.

Now turning our attention to <FIG>, and with reference to <FIG>, a sequence of operations will be illustrated that enable cell analyzer <NUM> to perform automated microscopic cell analysis on a biological sample without skilled operator interactions. In <FIG> a sample is shown deposited into input port <NUM>, which is in fluid communication with rotary valve <NUM>. As illustrated in <FIG>, the stem <NUM> (<FIG>) of rotary valve <NUM> is in a first position wherein the metering chamber <NUM> (<FIG>) is aligned with the sample input port <NUM> and the sample driver port <NUM>. A vacuum, supplied by the analyzer to sample driver port <NUM>, draws the sample from the input port <NUM> into the metering chamber <NUM> and into the photometric chamber <NUM>. When the photometric chamber <NUM> has been filled with sample, the system controller <NUM> (<FIG>) collects absorbance data from the undiluted sample using the photometric light source <NUM> (<FIG>) and photometric detector <NUM> (<FIG>). As will be understood by those skilled in the art, suitable choice of optical wavelengths and chamber geometry and analysis of the light passing through the biological sample can be used to determine concentrations of certain analytes in the sample such as hemoglobin.

By illustration and with reference to <FIG>, cartridge <NUM> is shown with a diluent/reagent contained in a blister pack <NUM>. When rotary valve <NUM> positioned such that the metering chamber <NUM> is aligned with the input port <NUM> and photometric chamber <NUM>, auxiliary connector <NUM> provides a fluid communication path between the blister pack <NUM> and vent <NUM>. When pressure is applied to the blister pack <NUM> by presser foot <NUM> (<FIG>), diluent/reagent is released and flushed through auxiliary connecter <NUM> thereby priming the channels and removing air bubbles through vent <NUM>.

<FIG> shows rotary valve <NUM> turned counterclockwise <NUM> degrees to a second position, which isolates a predetermined amount of sample in the metering chamber <NUM>. In this second position the stem <NUM> of rotary valve <NUM> is positioned such that the metering chamber <NUM> is in fluid communication with blister pack <NUM> and the serpentine imaging chamber <NUM>.

In <FIG>, the rotary valve <NUM> is shown in the same position as in <FIG> but following operation of the presser foot <NUM> which applies pressure to the blister pack <NUM>. As illustrated by the shaded area, the diluent/reagent from blister pack <NUM> and the isolated sample <NUM> from the metering chamber <NUM> are transferred into the imaging chamber <NUM>. A minimum volume of reagent of three times the volume of the pass-through conduit <NUM> is needed to flush the entire sample from the rotary valve <NUM>. According to the analysis being conducted, a sufficient volume of the reagent is pushed through the rotary valve <NUM> to completely wash out the isolated sample and to achieve the approximate dilution ratio desired.

In <FIG> the rotary valve <NUM> is shown turned counterclockwise <NUM> degrees from its previous position shown in <FIG> to its third position, wherein auxiliary connector <NUM> is aligned with mixture driver port <NUM> and imaging chamber <NUM>. Vacuum/pressure pump <NUM> of cell analyzer <NUM> (<FIG>) supplies pressure to mixture driver port <NUM> and pushes all of the mixture of sample and diluent/reagent from the imaging chamber <NUM> into passive mixing chamber <NUM>. As the mixture enters passive mixing chamber <NUM>, air within the chamber is vented through vent port <NUM>. Once all of the mixture of sample and diluent/reagent has been transferred to the passive mixing chamber <NUM>, vacuum/pressure pump <NUM> applies a controlled vacuum to mixture driver port <NUM> such that the mixture is pulled back into the imaging chamber <NUM>. A preprogrammed sequence of pushing the mixture into the passive mixing chamber <NUM> and pulling it back into the imaging chamber <NUM> is repeated to achieve a final mixture <NUM> that is free from cell clumping and overlapping after the cells settle to the bottom of the imaging chamber <NUM>. In the final movement of the mixture <NUM>, it is positioned entirely within the imaging chamber <NUM> as illustrated in <FIG>. We have found that that in most instances, pushing the sample and diluent/reagent into mixing chamber <NUM> and pulling it out is sufficient to provide a uniform mixture. Further, the mixture remains substantially uniform when it is transferred into serpentine imaging chamber <NUM>. It should also be noted that the mixing chamber <NUM> could be located at the beginning of the imaging chamber <NUM>.

<FIG> illustrates the final step of the sample preparation sequence. At this point in the preprogrammed sequence, the entire final mixture <NUM> has been withdrawn from the passive mixing chamber <NUM> and is positioned in the imaging chamber <NUM>. When this position is achieved, the rotary valve <NUM> is rotated counterclockwise approximately <NUM> degrees to the position shown in <FIG>, whereby it is not in fluid communication with any fluidic channel in rotary valve <NUM>, thereby blocking further fluid communication with the imaging chamber <NUM> so that no further movement of the final mixture <NUM> can take place.

<FIG> shows a cross section of the passive mixing chamber <NUM>. The chamber is referred to as "passive" because as illustrated, it does not contain any active mixing element such as a bead or spin-bar. Such devices may be used in some embodiments, but we have found that an adequately sized chamber as depicted in <FIG> is simpler and provides excellent mixing of the sample and reagent. In operation the diluent/reagent and sample <NUM> are driven by vacuum/pressure pump <NUM> (<FIG>) and enter and exit the chamber through mixing chamber opening <NUM>. As liquid enters the chamber, air within the chamber escapes through vent port <NUM>. The cross section of passive mixing chamber <NUM> illustrates wall geometry that increases smoothly in size from the bottom to the top such that the mixture entering from below expands into a larger volume. The chamber <NUM> may have asymmetrical sloped walls <NUM> and <NUM> to promote mixing of the sample and reagent and for removing bubbles from the mixture. After all of the mixture is in the chamber, air bubbles may be introduced to the chamber by vacuum/pressure pump <NUM> through mixing chamber opening <NUM>. These air bubbles further promote mixing and subsequently escape through vent port <NUM>. The choice of materials used to fabricate the passive mixing chamber <NUM> should take into consideration the wetting properties of the specific <NUM> diluent/reagent(s) being utilized in the test cartridge <NUM>. The properties of the material, among other requirements, should ensure that liquid surface tension will pull back all of the liquid in contact with the side walls of the chamber when the vacuum/pressure pump <NUM> empties the chamber through mixing chamber opening <NUM>.

<FIG> illustrates test cartridge <NUM> which comprises an imaging chamber <NUM> having at one end a sample input port <NUM>, and at the opposite end a vent <NUM>. A user of test cartridge <NUM> collects a small known volume of whole blood and mixes it manually with a diluent/reagent in a separate single-use sample preparation device (not shown). Once mixed, the entire mixed volume is injected into sample input port <NUM> at a controlled rate, such that the cells uniformly fill the imaging chamber. Air escapes through vent <NUM>, allowing the sample and diluent/reagent mixture to fill the imaging chamber <NUM>. The form of the imaging chamber is essentially the same as the imaging chamber as described above and shown in <FIG>, except that the volume of the imaging chamber must be sufficient to include all of the mixture of sample and diluent/reagent. Test cartridge <NUM> can be placed into analyzer <NUM> (<FIG>) to count every cell in the mixture of sample and diluent/reagent and for analysis beginning at step <NUM> of <FIG> as described below.

Turning our attention to <FIG> we will now describe the overall operation of cell analyzer <NUM> configured to provide a "CBC with Differential" analysis with reference to the test cartridge <NUM> illustrated in <FIG> and cell analyzer <NUM> illustrated in <FIG>. To obtain the blood sample from a patient presented at box <NUM>, the user first obtains a new test cartridge <NUM> at box <NUM> and opens it to expose the input port <NUM>. Blood from a finger prick is applied as illustrated in <FIG> at box <NUM> and the input port <NUM> is covered. The user inserts the test cartridge into the cell analyzer <NUM> at box <NUM>. The test cartridge is moved into the analyzer where mechanical and fluid connections are made between the analyzer and the cartridge as described above with reference to <FIG>. As a first step of analysis, the sample is drawn into the metering chamber passing through and into photometric chamber <NUM> (<FIG>). Absorbance of the blood is measured at box <NUM>. Data from absorbance measurements are used to determine hemoglobin concentration. At box <NUM> sample in the metering chamber <NUM> is imaged using monitoring camera <NUM> and analyzed to confirm that the metering chamber was properly filled at box <NUM>. If an error is detected the analysis is terminated at box <NUM> and the user is alerted to the error and instructed to remove the cartridge and reject the test.

If the pass-through conduit <NUM> is correctly filled the diluent/reagent channel is primed at box <NUM> as described above with reference to <FIG>. Rotary valve <NUM> is then turned to the position shown in <FIG> to isolate the sample and to allow diluent/reagent to wash the metered volume of blood out of the pass-through conduit <NUM> at box <NUM> while being imaged by monitoring camera <NUM>. The transfer continues until the monitoring camera <NUM> confirms that diluent/reagent plus sample has almost filled the imaging chamber as illustrated in <FIG>.

Once a sufficient volume of diluent/reagent is transferred, rotary valve <NUM> is positioned as shown in <FIG> and the total volume of sample and diluent/reagent is mixed at box <NUM>. At box <NUM> the entire volume <NUM> is transferred to the imaging chamber and rotary valve <NUM> is positioned as shown in <FIG>. Note that by transferring the entire volume of mixed sample <NUM>, all of the metered volume of blood from the original sample plus the unmetered volume of diluent/reagent is positioned in the imaging chamber at box <NUM>.

If test cartridge <NUM> is used, it is inserted into cell analyzer <NUM> and analysis begins at step <NUM>. Analysis of test cartridge <NUM> or <NUM> continues at step <NUM> when the x-y stage <NUM> moves the test cartridge <NUM> to obtain bright-field and fluorescent images of the entire imaging chamber <NUM> at box <NUM>. In an alternate embodiment, objective lens <NUM> and/or digital camera <NUM> are moved and test cartridge <NUM> remains stationary. In yet another embodiment objective lens <NUM> has sufficient field of view to capture the entire imaging chamber <NUM> without movement. Two digital images of each physical frame of the imaging chamber are transferred to image processor/computer <NUM> at box <NUM>. One image, taken with bright-field optics, can be compared to the other image taken with fluorescent optics to identify red blood cells, white blood cells and platelets. Further analysis of the white cell sizes and internal structure can identify sub-types of white cells using pattern recognition.

At box <NUM> comparison of the bright-field and fluorescent images can differentiate mature red cells from reticulocytes and nucleated red blood cells. By dividing each cell count by the known volume of the metering chamber <NUM>, the concentration (cells per unit volume) can be determined. By using a sphering agent the planar sizes of red cells can be transformed into mean corpuscular volume (MCV). Combining the red blood cell count with MCV and the volume of the metering chamber <NUM> allows the calculation of hematocrit (HCT) and red cell distribution width (RDW). Further calculations using the separately measured HGB from box <NUM>, combined with the RBC count gives mean corpuscular hemoglobin (MCH), and mean corpuscular hemoglobin content (MCHC).

At box <NUM> the measured results are compared with previously defined limits and ranges for the particular patient population and determination is made whether the results are within or outside normal expected ranges. According to this determination results within normal ranges are reported in box <NUM> and results that are outside the normal ranges are reported in box <NUM>.

As noted above, another embodiment of the invention is to perform a CBC on a known or measured volume of diluted sample. In this embodiment, every cell and platelet in the known volume of diluted sample is counted. If the volume of the diluted sample and the dilution ratio is known, the number of cells and platelets per unit volume of sample can be determined. A hematology analyzer can be provided to perform the CBC on a known volume of diluted sample, utilizing a single use disposable test cartridge. The length and depth of the imaging chamber will depend upon the dilution ratio and the volume of the known diluted sample. For instance, a <NUM> uL sample of whole blood may be diluted <NUM> to <NUM> producing <NUM> uL of diluted sample. <NUM> uL of the diluted sample may then be taken to be analyzed. Every cell and platelet in the diluted sample is counted, either directly or by statistical representation. The <NUM> uL of known diluted volume corresponds to. <NUM> uL of whole blood. The volume of the imaging chamber must be at least <NUM> uL in order to contain all of the known volume of diluted sample.

The dilution ratio must be sufficient to prevent crowding or overlapping when the cells settle to the bottom of the imaging chamber. The dilution ratio also depends on the depth of the imaging chamber as explained above. The volume of diluted blood must be sufficient to contain enough white cells to be significantly representative of the whole blood sample. For example, the average number of white cells in whole blood of a healthy patient would be approximately <NUM> per microliter. <NUM> uL of whole blood, there would be about <NUM> white cells. However, in a sick patient, or one being treated with chemotherapy, the white cell count could be as low as <NUM> white cells per microliter. In this case, the number of white cells in a. 4uL diluted sample would be about <NUM> cells, which maybe an inadequate number of white cells to be clinically significant. In this case, a larger volume of diluted sample may be desirable. However, the time to image and count every cell in the known volume of diluted sample increases as the volume of the diluted sample increases.

The hematology analyzer utilized to perform a CBC on a known diluted volume of sample will comprise an automated microscope for imaging the cells in the imaging chamber of a test cartridge, similar to the one described above and shown in <FIG>, except that it need not have a presser foot and valve driver. In one embodiment, the dilution step may be performed manually with pipettes and a mixing tube or beaker, and outside of the analyzer, in which case the dilution ratio will be known. A known volume of the mixture may be deposited in a sample cup <NUM> <FIG> on a test cartridge <NUM> having a serpentine imaging chamber <NUM>. The sample cup may be in fluid communication to the imaging chamber <NUM> by a channel <NUM> at one end of the imaging chamber <NUM>. At the opposite end of the serpentine chamber <NUM> is a vent hole <NUM>. When the test cartridge is inserted into the analyzer, the vent hole <NUM> interfaces with the vacuum/pressure source of the analyzer. The diluted sample is drawn into and positioned within the imaging chamber <NUM>, when a vacuum is applied at the vent hole <NUM>, such that its entire volume will be located within the imaging chamber. The diluted sample may also be pushed back into the sample cup by pressure applied at the vent hole and then pulled back into and positioned in the imaging chamber for the purposes of mixing the diluted sample, similar to the way described above with reference to the mixing chamber <NUM> in <FIG>. The sample cup may be of the same shape and format as the mixing chamber <NUM> in <FIG> to facilitate mixing if this is required. For instance, if the known volume of diluted sample is deposited in the sample cup and the test cartridge is not inserted in the analyzer for cell analysis immediately, the cells in the diluted sample may settle to the bottom of the sample cup. In this case, mixing may be necessary. Once the diluted sampled is positioned in the imaging chamber, the analyzer may perform a CBC on the diluted sample as described above.

Alternatively, a measured volume of sample and a measured volume of diluent/reagent may be mixed manually, and a portion of the mixture having a known volume may be inserted, at a controlled flow rate to prevent crowding and insure a uniform distribution of cells, into a test cartridge having a serpentine imaging chamber as illustrated in <FIG>. The dimensions of the serpentine path are chosen in accordance with the dilution ratio, the known volume of the mixture, and the guidelines set forth above. Every cell in the known volume of the mixture may be counted and analyzed as set forth above.

In another embodiment, the dilution and sample preparation step and may be performed by an analyzer utilizing a probe for aspirating a whole blood sample, a shear or face valve for isolating a predetermined volume of sample, a supply of diluent/stain, a syringe pump for metering and dispensing a known amount of diluent/stain in a mixing bowl for mixing the sample and diluent/stain, solenoid rocker valves or pinch valves for controlling the movements of fluids, vacuum and pressure sources, and a disposable single use test cartridge. The shear valve is in fluidic communication with the analyzer probe that aspirates blood samples. A sample is drawn through the probe and into the shear valve, which may be turned, trapping a predetermined amount of sample. The shear valve is further turned to a position where it is in fluidic communication with a pressure source and the mixing bowl. The isolated blood sample is pushed into the mixing bowl by the pressure source. The syringe pump is in fluidic communication with diluent/stain supply and the mixing bowl. The syringe pump dispenses a predetermined amount of diluent/stain into the mixing bowl. The blood sample and diluent/stain can be mixed in the bowl by pushing air through the probe and bubbling the air through the mixture. When mixed, a portion of the mixture may be drawn into a metering chamber of known volume and in fluidic communication with the mixing bowl. Optical edge detecting sensors are used to control the flow of the mixture into the metering chamber. The test cartridge illustrated in <FIG> is used as a single use disposable cartridge with the hematology analyzer. It is inserted into the analyzer such that the channel <NUM> <FIG> at one end of the serpentine imaging chamber <NUM> interfaces with, and is in fluidic communication with, the metering chamber. A vacuum is applied to the opposite end of the serpentine path through vent hole <NUM>, <FIG>, and the portion of the diluted sample in the metering chamber is drawn into, and positioned in, the imaging chamber, at a contolled rate to prevent crowding and to insure uniform distribution of the cells, for CBC analysis as described above. The dimensions of the serpentine path will depend upon the dilution ratio, the volume of the portion of the mixture and the guidelines noted above. One drawback to this arrangement is that the shear valve, metering chamber, mixing bowl, metering chamber, and connecting fluid channels must be flushed between every sample. Such analyzers also require frequent calibration and maintenance.

In another embodiment, the dilution step and metering step maybe performed with a test cartridge having a mixing bowl and diluted sample cup on the test cartridge. The analyzer includes a sampling probe, diluent/stain reservoir, precise diluter syringe pump, and wash station. In this case, the probe may be attached to a transfer arm mounted on the base of cell analyzer <NUM> <FIG>, which can move vertically in the z direction with respect to stage <NUM> <FIG>. The transfer arm can move horizontally along a linear axis such that it can be vertically aligned with the wash station or the diluent/reagent reservoir, or sample container. A schematic of the analyzer is illustrated in <FIG>. The dilution step is as follows. The probe <NUM> <FIG> moves along its linear axis <NUM> until it is aligned vertically with the diluent/stain reservoir <NUM>. It then moves downward in the vertical direction until the tip of the probe is submerged in the diluent/stain <NUM>. It then aspirates a known amount of diluent/stain, e.g. <NUM> uL. The probes moves upward and horizontally along axis <NUM> until it is aligned with the sample container <NUM>. After aspirating <NUM> uL of air, it moves downward in the vertical direction until the tip of the probe is well submerged in the sample in sample container <NUM>. The analyzer then aspirates <NUM> uL of sample, such as whole blood, from the sample container, after which the probe is moved upward and above the sample container, where it aspirates another <NUM> uL slug of air. The probe then moves along the linear axis <NUM> until it is aligned vertically with the mixing bowl <NUM> <FIG> on test cartridge <NUM>. The probe is then lowered vertically until the tip of the probe is just above the bottom of the mixing bowl <NUM>. The analyzer then dispenses the blood sample and the diluent/stain into the mixing bowl <NUM> on the test cartridge <NUM>. This sequence of steps insures that the entire aspirated blood sample is flushed out of the probe by the diluent/stain reagent and into the mixing bowl. The analyzer may mix the blood and diluent mechanically such as by moving back and forth along its axis <NUM> or by bubbling air through the mixture, or by aspirating the mixture and redispensing it into the mixing bowl, or by other methods. After the sample and diluent/stain are mixed, the analyzer aspirates <NUM> uL of the mixture. This corresponds to. <NUM> uL of undiluted sample. The probe is then moved upwards and moved along the linear axis <NUM> <FIG> until the probe is aligned with the diluted sample reservoir <NUM> <FIG>. The probe is lowered and the <NUM> uL mixture of sample and diluent/stain is dispensed into sample cup <NUM> <FIG>, which is in fluidic communication with one end of the serpentine path <NUM> through channel <NUM>. The mixture may be pulled through the serpentine path of imaging chamber <NUM> at a controlled rate by a vacuum source on the analyzer, which interfaces with vent hole <NUM> on the opposite end of the imaging chamber from the sample cup <NUM>. Alternatively, after the sample is dispensed, the probe may be positioned into vent hole <NUM>, which may also contain a sealing o-ring, and the analyzer aspirates air through the probe at a controlled rate, such as <NUM> uL per second, to prevent crowding and to insure a uniform distribution of cells. The analyzer positions the entire mixture of sample and diluent/stain in the imaging chamber <NUM>. The dimensions of the serpentine path depend upon the dilution ratio, the volume of the mixture, and the considerations noted above. Another variation would be to utilize a test cartridge without the sample cup, in which case the probe, after it has aspirated the <NUM> uL of diluted sample, may interface directly with the fluidic channel <NUM> and dispense the mixture at a controlled rate directly into the serpentine path of imaging chamber <NUM>.

The probe may be washed at the wash station <NUM> <FIG> after aspirating or dispensing blood or diluent/stain or the mixture of sample and diluent/stain to eliminate any solution adhering to the side of the probe. Although this process is not described above, those skilled in the art relating to chemistry analyzers or X-Y dispensing fluid mechanisms will understand the practices and procedures for doing so.

One advantage to this embodiment is the elimination of the shear valve and fluidic tubing and flushing them as well as interconnecting fluidic channels from sample to sample. It also reduces and may eliminate the need for pinch and/or solenoid valves.

The analyzer may process samples in parallel by performing the CBC imaging analysis on the known diluted sample in the imaging chamber of one test cartridge, while the analyzer is simultaneously diluting another sample and depositing it in the imaging chamber of a second test cartridge. This can be done to increase analyzer throughput.

<FIG> shows images that were collected using test devices according to the present invention. A fluorescent stain Acridine Orange (AO) was used to differentially stain DNA and RNA of cells in a whole blood sample. The visual images of <FIG> were obtained using an Olympus 20X x <NUM> NA objective lens <NUM> and a Basler <NUM> MP digital camera <NUM>. Excitation of the bright-field images in the second column was provided by white light bright-field source <NUM>. Excitation of the fluorescent images in the third column was a <NUM> blue fluorescent light source <NUM>.

White blood cells have significant RNA and DNA and therefore can be seen in the fluorescent images having green and orange structures. The size and shape of the green nuclear structure and overall size of the white cells can be used to differentiate them into sub-groups identified by name in the first column. Notably the basophil and eosinophil sub-groups of white cells have characteristic features in the bright-field image due to the presence of large granules in the cytoplasm. Therefore embodiments of the present invention make use of both bright-field and fluorescent image analysis to differentiate sub-groups of white cells.

Platelets also take up the AO stain but the size of a platelet is significantly smaller than any white cell and can therefore be differentiated. Because red cells lose their nucleus as they mature, they do not have nuclear material to take up the AO stain. Consequently the red cells can be identified as the objects that appear in the bright-field and cannot be seen in the fluorescent field. The immature red cells, called reticulocytes and the nucleated red blood cells (nRBC) have attributes of red cells but also show small levels of fluorescence. Embodiments of the present invention make use of these combined attributes to identify and sub-group red blood cells.

Table <NUM> illustrates a comparison of CBC parameters obtained according to the present invention and from an automated hematology analyzer.

Claim 1:
A method of counting and analyzing biological particles in whole blood, including red cells, white cells, and platelets, utilizing a cell analyzer with image processing software, diluent and stain, and a test cartridge (<NUM>, <NUM>) having an imaging chamber (<NUM>), the method comprising:
a) introducing a sample (<NUM>) of the whole blood into the test cartridge (<NUM>, <NUM>);
b) separating a known amount of sample (<NUM>) from a remaining amount of the sample with a sample metering valve in the test cartridge (<NUM>, <NUM>);
c) mixing the known amount of sample (<NUM>) in the test cartridge (<NUM>, <NUM>) with an amount of diluent in the cartridge that is sufficient to form a substantially uniform mixture of sample and diluent;
d) transferring the mixture into the imaging chamber of the test cartridge to form a monolayer of red cells, white cells, and platelets;
e) capturing one or more digital images of the monolayer of red cells, white cells, and platelets in the imaging chamber (<NUM>) that are selected to be statistically representative of the number and distribution of biological particles in the imaging chamber (<NUM>); and
f) deriving a quantitative characterization of at least one aspect of the distribution of the red cells in the monolayer in the imaging chamber, at least one aspect of the distribution of the white cells in the monolayer in the imaging chamber, and at least one aspect of the distribution of the platelets in the monolayer in the imaging chamber (<NUM>) based on the images captured in the step of capturing.