Patent Publication Number: US-9426979-B2

Title: Apparatus for oxygenation and perfusion of tissue for organ preservation

Description:
CROSS-REFERENCE TO RELATED APPLICATIONS 
     The present application is a continuation-in-part of U.S. patent application Ser. No. 14/459,773, filed Aug. 14, 2014, which is a continuation of U.S. patent application Ser. No. 13/420,962, filed Mar. 15, 2012 (now U.S. Pat. No. 8,835,158), which claims priority to and the benefit of U.S. Provisional Application Ser. No. 61/541,425, filed Sep. 30, 2011, and U.S. Provisional Application Ser. No. 61/452,917, filed Mar. 15, 2011, each of which is incorporated herein by reference in its entirety. 
    
    
     BACKGROUND 
     The current invention generally relates to devices, systems, and methods that are configured to oxygenate and/or perfuse a bodily tissue for the extracorporeal preservation of the tissue, and more specifically, to such devices, systems, and methods that are configured to facilitate self-purging of excess fluid and that are configured for a programmed sequence of pumping oxygen for oxygenation of the perfusate and for perfusion of the tissue that helps to minimize usage of oxygen and/or a power source. 
     One known technique for preserving a bodily tissue for transplantation is nonperfused or static cold storage. Such cold storage, however, limits the period of viability of the bodily tissue, which can be attributable to insufficient levels of oxygen in the storage carrier to meet the tissue&#39;s metabolic need. Another known technique for preserving a bodily tissue for transplantation includes the use of hypothermic perfusion devices. The portability of such known devices is limited, however, because such known devices are large and require a significant volume of compressed gas and electrical power. Furthermore, such known devices are very complex, which can lead to increased manufacturing costs. 
     Therefore, a need exists for an improved device for the extracorporeal preservation of bodily tissue that is compact for improved portability, that reduces the need for at least one of an amount of oxygen and a power source, and that has a simplified system for oxygenating a perfusate and for perfusing the bodily tissue. 
     SUMMARY OF THE INVENTION 
     An apparatus according to an embodiment is configured to oxygenate and perfuse a bodily tissue for extracorporeal preservation of the bodily tissue. The apparatus includes a pneumatic system, a pumping chamber, and an organ chamber. The pneumatic system is configured for the controlled delivery of fluid to and from the pumping chamber based on a predetermined control scheme. The predetermined control scheme can be, for example, a time-based control scheme or a pressure-based control scheme. The pumping chamber is configured to diffuse a gas into a perfusate and to generate a pulse wave for moving the perfusate through a bodily tissue. The organ chamber is configured to receive the bodily tissue and the perfusate. The organ chamber is configured to substantially automatically purge excess fluid from the organ chamber to the pumping chamber. The pumping chamber is configured to substantially automatically purge excess fluid from the pumping chamber to an area external to the apparatus. 
    
    
     
       BRIEF DESCRIPTION OF THE DRAWINGS 
         FIG. 1  is a schematic illustration of an apparatus according to an embodiment. 
         FIG. 2  is a perspective view of an apparatus according to an embodiment. 
         FIG. 3  is a side view of the apparatus of  FIG. 2 . 
         FIG. 4  is a cross-sectional view of the apparatus of  FIG. 2  taken along line Y-Y, with a portion of a pneumatic system removed. 
         FIG. 5  is a cross-sectional view of a lid assembly of the apparatus of  FIG. 2  taken along line X-X (shown in  FIG. 3 ). 
         FIG. 6  is an exploded perspective view of a lid assembly of the apparatus of  FIG. 2 . 
         FIG. 7  is a top view of a portion of a lid assembly and a pneumatic system of the apparatus of  FIG. 2 . 
         FIG. 8  is a schematic illustration of a pneumatic system and a pumping chamber of the apparatus of  FIG. 2 . 
         FIG. 9  is a schematic illustration of a pneumatic system and a pumping chamber of an apparatus according to an embodiment. 
         FIG. 10  is a front perspective view of an apparatus according to an embodiment. 
         FIG. 11  is a rear perspective view of the apparatus of  FIG. 10 . 
         FIG. 12  is a front perspective view of the apparatus of  FIG. 10  with the lid cover, one of the clamps, and the organ chamber removed. 
         FIG. 13  is a side view of the apparatus of  FIG. 10 . 
         FIG. 14  is a cross-sectional view of the apparatus of  FIG. 10  taken along line W-W (shown in  FIG. 10 ). 
         FIG. 15  is a cross-sectional view of the apparatus of  FIG. 10  taken along line V-V (shown in  FIG. 13 ). 
         FIG. 16A  is an enlarged cross-sectional view of the portion of  FIG. 14  identified by the line  16 A. 
         FIG. 16B  is an enlarged cross-sectional view of a portion of an apparatus according to an embodiment. 
         FIG. 17  is a component diagram of a control system according to an embodiment. 
         FIG. 18  is a flow diagram of a method for calculating organ flow rate and organ resistance according to an embodiment. 
         FIG. 19  is a perspective view of an apparatus according to an embodiment. 
         FIG. 20  is a cross-sectional view of the apparatus of  FIG. 19  taken along line U-U (shown in  FIG. 19 ). 
         FIG. 21A  is a cross-sectional view of a lid assembly of the apparatus of  FIG. 19  taken alone line T-T (shown in  FIG. 19 ). 
         FIG. 21B  is an enlarged cross-sectional view of a portion of the lid assembly of the apparatus of  FIG. 21A . 
         FIG. 22  is a top perspective view of a portion of the lid assembly of the apparatus of  FIG. 19 . 
         FIG. 23  is a side perspective view of the portion of the lid assembly of  FIG. 22 . 
         FIG. 24  is a cross-sectional view of the portion of the lid assembly of  FIG. 22  taken along line S-S (shown in  FIG. 22 ). 
         FIG. 25  is a top perspective view of a portion of the lid assembly of the apparatus of  FIG. 19 . 
         FIG. 26  is a bottom perspective view of the portion of the lid assembly of  FIG. 25 . 
         FIGS. 27A-27C  are bottom perspective views of the lid assembly, a coupling mechanism, and a canister of the apparatus of  FIG. 19  in a first configuration, a second configuration, and a third configuration, respectively. 
         FIGS. 28A-28C  are top perspective views of the lid assembly and the coupling mechanism of the apparatus of  FIG. 19  in a first configuration, a second configuration, and a third configuration, respectively. 
         FIG. 29  is a front view of the canister of the apparatus of  FIG. 19 . 
         FIG. 30  is a front view of a canister according to an embodiment. 
         FIG. 31  is a perspective view of the canister of  FIG. 30  and a bodily tissue. 
         FIG. 32  is a perspective view of the apparatus of  FIG. 19 . 
         FIG. 33  is a front view of a carrier assembly for use with the apparatus of  FIG. 19 . 
         FIG. 34  is a perspective view of an active lid assembly. 
         FIG. 35  is a bottom view of the active lid assembly of  FIG. 34 . 
         FIG. 36  is a perspective view of a static lid assembly. 
         FIG. 37  is a bottom view of the static lid assembly of  FIG. 36 . 
         FIG. 38  is a perspective view of an organ transport container. 
         FIG. 39  is a perspective view of the organ transport container of  FIG. 38  with the top portion removed. 
         FIG. 40  is a bottom view of the organ transport container of  FIG. 38 . 
         FIG. 41  is a side view of a transporter unit with the lid removed. 
         FIG. 42  is a top view of the transporter unit of  FIG. 41  with the lid removed. 
         FIG. 43  is a perspective view of the transporter unit of  FIG. 41  with the lid attached. 
     
    
    
     DETAILED DESCRIPTION 
     Devices, systems and methods are described herein that are configured to oxygenate and/or perfuse a bodily tissue for the extracorporeal preservation of the tissue. More specifically, described herein are devices, systems, and methods that are configured to oxygenate a perfusate and to perfuse the bodily tissue with the oxygenated perfusate in a portable device, thereby extending the viability of the tissue over a longer period of time. Such extracorporeal preservation of tissue is desirable, for example, for transportation of an organ to be transplanted from a donor to a recipient. In another example, such extracorporeal preservation of tissue is desirable to preserve the bodily tissue over a period of time as scientific research is conducted, such as research to test the efficacy of a particular course of treatment on a disease of the tissue over the period of time. 
     In some embodiments, a device is configured to self-purge excess fluid (e.g., liquid and/or gas). For example, in some embodiments, a device includes a lid assembly in which at least a portion of the lid assembly is inclined with respect to a horizontal axis. The inclined portion of the lid assembly is configured to facilitate the flow of fluid towards a purge port disposed at substantially the highest portion of a chamber of the lid assembly. In this manner, excess fluid can escape the device via the purge port. Also in this manner, when excess liquid is expelled from the device via the purge port, an operator of the device can determine that any excess gas has also been purged from the device, or at least from within an organ chamber of the device, because the gas is lighter than the liquid and will move towards and be expelled via the purge port before excess liquid. 
     In some embodiments, a device is configured to pump oxygen through a pumping chamber to oxygenate a perfusate and to perfuse a bodily tissue based on a desired control scheme. For example, in some embodiments, the device includes a pneumatic system configured to deliver oxygen to the pumping chamber on a time-based control scheme. The pneumatic system can be configured to deliver oxygen to the pumping chamber for a first period of time. The pneumatic system can be configured to vent oxygen and carbon dioxide from the pumping chamber for a second period of time subsequent to the first period of time. In another example, in some embodiments, the device includes a pneumatic system configured to deliver oxygen to the pumping chamber on a pressure-based control scheme. The pneumatic system can be configured to deliver oxygen to the pumping chamber until a first threshold pressure is reached within the pumping chamber. The pneumatic system can be configured to vent oxygen and carbon dioxide from the pumping chamber until a second threshold pressure is reached within the pumping chamber. In some embodiments, a power source of the device is in use when oxygen is being delivered to the pumping chamber and is not in use when oxygen and carbon dioxide are being vented from the pumping chamber. In this manner, the device is configured to help minimize usage of the power source, and thus the device can prolong the period of time a bodily tissue is extracorporeally preserved within the device before the power source is depleted. Such an improvement increases the time available for transporting the bodily tissue from a donor to a recipient. Such an improvement also facilitates the long term preservation of the bodily tissue, such as for a period of scientific research. 
     In some embodiments, a device is configured to provide a suitable environment to grow, transport, and/or store a bodily tissue. Accordingly, devices, systems and methods described herein can be used to provide growth conditions that improve the efficiency and/or reproducibility of tissue growth; monitor and modulate tissue growth in response to experimentally identified conditions and/or conditions that mimic a natural growth environment; evaluate tissue growth to determine suitability for transplantation; provide safety features to monitor and/or control sterility, and/or to manage the process of matching a tissue with an intended recipient (e.g., by monitoring and/or tracking the source or identity of the cells that were introduced into the reactor for regeneration); and/or to provide structural or functional features on a substitute tissue that are useful during the transplantation procedure to help make structural and functional connections to the recipient body. These and other aspects are described herein and are useful both to optimize the growth of individual tissues, and also to manage a large scale process of tissue growth and development that involves tracking and producing different tissues (e.g., organs). For example, tissue development (e.g., based on speed and/or tissue quality) may be significantly influenced (and improved in some cases) by changing the growth conditions during development. Accordingly, devices, systems and methods described herein can be used to change tissue growth conditions one or more times during development in response to one or more parameters or cues described herein (e.g., based on predetermined time intervals, levels of one or more variables, images, etc., or combinations thereof). 
     As used in this specification, the singular forms “a,” “an” and “the” include plural referents unless the context clearly dictates otherwise. Thus, for example, the term “a fluid” is intended to mean a single fluid or a combination of fluids. 
     As used herein, “a fluid” refers to a gas, a liquid, or a combination thereof, unless the context clearly dictates otherwise. For example, a fluid can include oxygen, carbon dioxide, or another gas. In another example, a fluid can include a liquid. Specifically, the fluid can be a liquid perfusate. In still another example, the fluid can include a liquid perfusate with a gas, such as oxygen, mixed therein or otherwise diffused therethrough. 
     As used herein, “bodily tissue” refers to any tissue of a body of a donor, including tissue that is suitable for being transplanted into a recipient and tissue that is suitable for being used in scientific research. Bodily tissue can include, for example, muscle tissue, such as, for example, skeletal muscle, smooth muscle, or cardiac muscle. Specifically, bodily tissue can include a group of tissues forming an organ, such as, for example, the skin, lungs, cochlea, heart, bladder, liver, kidney, or other organ. In another example, bodily tissue can include nervous tissue, such as a nerve, the spinal cord, or another component of the peripheral or central nervous system. In still another example, bodily tissue can include a group of tissues forming a bodily appendage, such as an arm, a hand, a finger, a thumb, a foot, a toe, or another bodily appendage. 
     An apparatus  10  according to an embodiment is schematically illustrated in  FIG. 1 . The apparatus  10  is configured to oxygenate a perfusate (not shown) received in a pumping chamber  14  of the apparatus. The apparatus  10  includes a valve  12  configured to permit a fluid (e.g., oxygen) to be introduced into a first portion  16  of the pumping chamber  14 . A membrane  20  is disposed between the first portion  16  of the pumping chamber  14  and a second portion  18  of the pumping chamber. The membrane  20  is configured to permit the flow of a gas between the first portion  16  of the pumping chamber  14  and the second portion  18  of the pumping chamber through the membrane. The membrane  20  is configured to substantially prevent the flow of a liquid between the second portion  18  of the pumping chamber  14  and the first portion  16  of the pumping chamber through the membrane. In this manner, the membrane can be characterized as being semi-permeable. 
     The membrane  20  is disposed within the pumping chamber  14  along an axis A 1  that is transverse to a horizontal axis A 2 . Said another way, the membrane  20  is inclined, for example, from a first side  22  to a second side  24  of the apparatus  10 . As such, as described in more detail below, a rising fluid in the second portion  18  of the pumping chamber  14  will be directed by the inclined membrane  20  towards a port  38  disposed at the highest portion of the pumping chamber  14 . The port  38  is configured to permit the fluid to flow from the pumping chamber  14  into the atmosphere external to the apparatus  10 . In some embodiments, the port  38  is configured for unidirectional flow, and thus is configured to prevent a fluid from being introduced into the pumping chamber  14  via the port (e.g., from a source external to the apparatus  10 ). In some embodiments, the port  38  includes a luer lock. 
     The second portion  18  of the pumping chamber  14  is configured to receive a fluid. In some embodiments, for example, the second portion  18  of the pumping chamber  14  is configured to receive a liquid perfusate. The second portion  18  of the pumping chamber  14  is in fluid communication with an adapter  26 . The adapter  26  is configured to permit movement of the fluid from the pumping chamber  14  to a bodily tissue T. For example, in some embodiments, the pumping chamber  14  defines an aperture (not shown) configured to be in fluidic communication with a lumen (not shown) of the adapter  26 . The adapter  26  is configured to be coupled to the bodily tissue T. The adapter  26  can be coupled to the bodily tissue T in any suitable manner. For example, in some embodiments, the adapter  26  is configured to be sutured to the bodily tissue T. In another example, the adapter  26  is coupleable to the bodily tissue T via an intervening structure, such as silastic or other tubing. In some embodiments, at least a portion of the adapter  26 , or the intervening structure, is configured to be inserted into the bodily tissue T. For example, in some embodiments, the lumen of the adapter  26  (or a lumen of the intervening structure) is configured to be fluidically coupled to a vessel of the bodily tissue T. 
     In some embodiments, the adapter  26  is configured to support the bodily tissue T when the bodily tissue T is coupled to the adapter. For example, in some embodiments, the adapter  26  includes a retention mechanism (not shown) configured to be disposed about at least a portion of the bodily tissue T and to help retain the bodily tissue T with respect to the adapter. The retention mechanism can be, for example, a net, a cage, a sling, or the like. In some embodiments, the apparatus  10  includes a basket (not shown) or other support mechanism configured to support the bodily tissue T when the bodily tissue T is coupled to the adapter  26  or otherwise received in the apparatus  10 . 
     An organ chamber  30  is configured to receive the bodily tissue T and a fluid. In some embodiments, the apparatus  10  includes a port  34  that is extended through the apparatus  10  (e.g., through the pumping chamber  14 ) to the organ chamber  30 . The port  34  is configured to permit fluid (e.g., perfusate) to be introduced to the organ chamber  30 . In this manner, fluid can be introduced into the organ chamber  30  as desired by an operator of the apparatus. For example, in some embodiments, a desired amount of perfusate is introduced into the organ chamber  30  via the port  34 , such as before disposing the bodily tissue T in the organ chamber  30  and/or while the bodily tissue T is received in the organ chamber. In some embodiments, the port  34  is a unidirectional port, and thus is configured to prevent the flow of fluid from the organ chamber  30  to an area external to the organ chamber through the port. In some embodiments, the port  34  includes a luer lock. The organ chamber  30  may be of any suitable volume necessary for receiving the bodily tissue T and a requisite amount of fluid for maintaining viability of the bodily tissue T. In one embodiment, for example, the volume of the organ chamber  30  is approximately 2 liters. 
     The organ chamber  30  is formed by a canister  32  and a bottom portion  19  of the pumping chamber  14 . In a similar manner as described above with respect to the membrane  20 , an upper portion of the organ chamber (defined by the bottom portion  19  of the pumping chamber  14 ) can be inclined from the first side  22  towards the second side  24  of the apparatus. In this manner, as described in more detail below, a rising fluid in the organ chamber  30  will be directed by the inclined upper portion of the organ chamber towards a valve  36  disposed at a highest portion of the organ chamber. The valve  36  is configured to permit a fluid to flow from the organ chamber  30  to the pumping chamber  14 . The valve  36  is configured to prevent flow of a fluid from the pumping chamber  14  to the organ chamber. The valve  36  can be any suitable valve for permitting unidirectional flow of the fluid, including, for example, a ball check valve. 
     The canister  32  can be constructed of any suitable material. In some embodiments, the canister  32  is constructed of a material that permits an operator of the apparatus  10  to view at least one of the bodily tissue T or the perfusate received in the organ chamber  30 . For example, in some embodiments, the canister  32  is substantially transparent. In another example, in some embodiments, the canister  32  is substantially translucent. The organ chamber  30  can be of any suitable shape and/or size. For example, in some embodiments, the organ chamber  30  can have a perimeter that is substantially oblong, oval, round, square, rectangular, cylindrical, or another suitable shape. 
     In use, the bodily tissue T is coupled to the adapter  26 . The pumping chamber  14  is coupled to the canister  32  such that the bodily tissue T is received in the organ chamber  30 . In some embodiments, the pumping chamber  14  and the canister  32  are coupled such that the organ chamber  30  is hermetically sealed. A desired amount of perfusate is introduced into the organ chamber  30  via the port  34 . The organ chamber  30  can be filled with the perfusate such that the perfusate volume rises to the highest portion of the organ chamber. The organ chamber  30  can be filled with an additional amount of perfusate such that the perfusate flows from the organ chamber  30  through the valve  36  into the second portion  18  of the pumping chamber  14 . The organ chamber  30  can continue to be filled with additional perfusate until all atmospheric gas that initially filled the second portion  18  of the pumping chamber  14  rises along the inclined membrane  20  and escapes through the port  38 . Because the gas will be expelled from the pumping chamber  14  via the port  38  before any excess perfusate is expelled (due to gas being lighter, and thus more easily expelled, than liquid), an operator of the apparatus  10  can determine that substantially all excess gas has been expelled from the pumping chamber when excess perfusate is released via the port. As such, the apparatus  10  can be characterized as self-purging. When perfusate begins to flow out of the port  38 , the apparatus  10  is in a “purged” state (i.e., all atmospheric gas initially within the organ chamber  30  and the second portion  18  of the pumping chamber  14  has been replaced by perfusate). When the purged state is reached, the operator can close both ports  34  and  38 , preparing the apparatus  10  for operation. 
     Oxygen (or another suitable fluid, e.g., gas) is introduced into the first portion  16  of the pumping chamber  14  via the valve  12 . A positive pressure generated by the introduction of oxygen into the pumping chamber  14  causes the oxygen to be diffused through the semi-permeable membrane  20  into the second portion  18  of the pumping chamber. Because oxygen is a gas, the oxygen expands to substantially fill the first portion  16  of the pumping chamber  14 . As such, substantially the entire surface area of the membrane  20  between the first portion  16  and the second portion  18  of the pumping chamber  14  is used to diffuse the oxygen. The oxygen is diffused through the membrane  20  into the perfusate received in the second portion  18  of the pumping chamber  14 , thereby oxygenating the perfusate. 
     In the presence of the positive pressure, the oxygenated perfusate is moved from the second portion  18  of the pumping chamber  14  into the bodily tissue T via the adapter  26 . For example, the positive pressure can cause the perfusate to move from the pumping chamber  14  through the lumen of the adapter  26  into the vessel of the bodily tissue T. The positive pressure is also configured to help move the perfusate through the bodily tissue T such that the bodily tissue T is perfused with oxygenated perfusate. 
     After the perfusate is perfused through the bodily tissue T, the perfusate is received in the organ chamber  30 . In this manner, the perfusate that has been perfused through the bodily tissue T is combined with perfusate previously disposed in the organ chamber  30 . In some embodiments, the volume of perfusate received from the bodily tissue T following perfusion combined with the volume of perfusate previously disposed in the organ chamber  30  exceeds a volume (e.g., a maximum fluid capacity) of the organ chamber  30 . A portion of the organ chamber  30  is flexible and expands to accept this excess volume. The valve  12  can then allow oxygen to vent from the first portion  16  of the pumping chamber  14 , thus, reducing the pressure in the pumping chamber  14 . As the pressure in the pumping chamber  14  drops, the flexible portion of the organ chamber  30  relaxes, and the excess perfusate is moved through the valve  36  into the pumping chamber  14 . The cycle of oxygenating perfusate and perfusing the bodily tissue T with the oxygenated perfusate can be repeated as desired. 
     An apparatus  100  according to an embodiment is illustrated in  FIGS. 2-7 . The apparatus  100  is configured to oxygenate a perfusate and to perfuse a bodily tissue for extracorporeal preservation of the bodily tissue. The apparatus  100  includes a lid assembly  110 , a canister  190 , and a coupling mechanism  250 . 
     The lid assembly  110  is configured to facilitate transportability of the apparatus. The lid assembly  110  includes a handle  112  and a lid  120 . The handle  112  is configured to be grasped, e.g., by a hand of a person transporting the apparatus  100 . The handle  112  is coupled to the lid  120 . The handle  112  can be coupled to the lid  120  using any suitable mechanism for coupling. For example, the handle  112  can be coupled to the lid  120  with at least one screw (e.g., screw  114  as shown in  FIG. 2 ), an adhesive, a hook and loop fastener, mating recesses, or the like, or any combination of the foregoing. An upper portion  122  of the lid  120  defines a chamber  124  configured to receive components of a pneumatic system  200  and a control system  500 , each of which is described in more detail below. A bottom portion  116  of the handle  112  is configured to substantially enclose a top of the chamber  124  defined by the lid  120 . 
     The lid assembly  110  defines a pumping chamber  125  configured to receive a gas, such as oxygen, from the pneumatic system  200 , to facilitate diffusion of the oxygen into a perfusate (not shown) and to facilitate movement of the oxygenated perfusate into a bodily tissue (not shown). Although the apparatus  100  is described herein as being configured for use with oxygen, any suitable gas may be used with apparatus  100  instead of or in addition to oxygen. A top of the pumping chamber  125  is formed by a lower portion  128  of the lid  120 . A bottom of the pumping chamber  125  is formed by an upper surface  134  of a base  132  of the lid assembly  110 . 
     As illustrated in an exploded perspective view in  FIG. 6 , the lid assembly  110  includes a first gasket  142 , a membrane  140 , and a membrane frame  144 . The membrane  144  is disposed within the pumping chamber  125 . The first gasket  142  is disposed between the membrane  140  and the lid  120  such that the first gasket is engaged with an upper surface  141  of the membrane  140  and the lower portion  128  of the lid. The first gasket  142  is configured to seal a perimeter of a first portion  127  of the pumping chamber  125  formed between the lower portion  128  of the lid  120  and the upper surface  141  of the membrane  140 . In other words, the first gasket  142  is configured to substantially prevent lateral escape of the oxygen from the first portion  127  of the pumping chamber  125  to a different portion of the pumping chamber. In the embodiment illustrated in  FIG. 6 , the first gasket  142  has a perimeter substantially similar in shape to a perimeter defined by the membrane  140  (e.g., when the membrane is disposed on the membrane frame  148 ). In other embodiments, however, a first gasket can have another suitable shape for sealing a first portion of a pumping chamber configured to receive oxygen from a pneumatic system. 
     The first gasket  142  can be constructed of any suitable material. In some embodiments, for example, the first gasket  142  is constructed of silicone, an elastomer, or the like. The first gasket  142  can have any suitable thickness. For example, in some embodiments, the first gasket  142  has a thickness within a range of about 0.1 inches to about 0.15 inches. More specifically, in some embodiments, the first gasket  142  has a thickness of about 0.125 inches. The first gasket  142  can have any suitable level of compression configured to maintain the seal about the first portion  142  of the pumping chamber  125  when the components of the lid assembly  110  are assembled. For example, in some embodiments, the first gasket  142  is configured to be compressed by about 20 percent. In some embodiments, the first gasket  142  can provide a leak-proof seal under operating pressures up to 5 pounds per square inch (psi). 
     The membrane  140  is configured to permit diffusion of the gas from the first portion  127  of the pumping chamber  125  through the membrane to a second portion  129  of the pumping chamber, and vice versa. The membrane  140  is configured to substantially prevent a liquid (e.g., the perfusate) from passing through the membrane. In this manner, the membrane  140  can be characterized as being semi-permeable. A membrane frame  144  is configured to support the membrane  140  (e.g., during the oxygenation and perfusing of the bodily tissue). The membrane frame  144  can be a substantially ring-like structure with an opening at its center. As shown in  FIG. 5 , at least a portion of the membrane  140  is disposed (e.g., wrapped) about at least a portion of the membrane frame  144 . In some embodiments, the membrane  140  is stretched when it is disposed on the membrane frame  144 . The membrane  140  is disposed about a lower edge of the membrane frame  144  such that the membrane  140  is engaged with a series of protrusions (e.g., protrusion  145  shown in  FIG. 5 ) configured to help retain the membrane with respect to the membrane frame  144 . At least a portion of the series of protrusions on the lower edge of the membrane frame  144  are configured to be received in a recess  147  defined by the upper surface  134  of the base  132 . As such, the membrane  140  is engaged between the membrane frame  144  and the base  132 , which facilitates retention of the membrane with respect to the membrane frame. In some embodiments, the first gasket  142  also helps to maintain the membrane  140  with respect to the membrane frame  144  because the first gasket is compressed against the membrane. 
     As best illustrated in  FIG. 4 , the membrane  140  is disposed within the pumping chamber  125  at an angle with respect to a horizontal axis A 3 . In this manner, the membrane  140  is configured to facilitate the movement of fluid towards a highest portion of the pumping chamber  125 , as described in more detail herein. 
     The membrane  140  can be of any suitable size. For example, in some embodiments, the upper surface  141  of the membrane  140  can be about 15 to about 20 square inches. More specifically, in some embodiments, the upper surface  141  of the membrane  140  can be about 19 square inches. In another example, the membrane  140  can have any suitable thickness. In some embodiments, for example, the membrane  140  is about 0.005 inches to about 0.010 inches thick. More specifically, in some embodiments, the membrane is about 0.0075 inches thick. The membrane  140  can be constructed of any suitable material. For example, in some embodiments, the membrane is constructed of silicone, plastic, or another suitable material. In some embodiments, the membrane is flexible. As illustrated in  FIG. 6 , the membrane  140  can be substantially seamless. In this manner, the membrane  140  is configured to be more resistant to being torn or otherwise damaged in the presence of a flexural stress caused by a change pressure in the pumping chamber due to the inflow and/or release of oxygen. 
     The lid  120  includes a purge port  106  disposed at the highest portion of the second portion  129  of the pumping chamber  125 , as shown in  FIG. 4 . In some embodiments, the port  106  is disposed at the highest portion of the pumping chamber  125  as a whole. In other words, the highest portion of the second portion  129  of the pumping chamber  125  can be the highest portion of the pumping chamber  125 . The purge port  106  is configured to permit movement of a fluid from the pumping chamber  125  to an area external to the apparatus  100 . The purge port  106  can be similar in many respects to a port described herein (e.g., port  38 , described above, and/or purge ports  306 ,  706 , described below). The purge port  106  can be any suitable mechanism for permitting movement of the fluid from the pumping chamber  125  into the atmosphere external to the apparatus  100 , including, but not limited to, a luer lock fitting. The purge port  106  can include a cap (not shown) coupled to the port via a retaining strap. 
     In some embodiments, the lid  120  is transparent, either in its entirety or in part (e.g. in the vicinity of the purge port  106 ). This permits a user to readily view a fluid therein (e.g., any gas bubbles) and to confirm completion of purging of excess fluid (e.g., the gas bubbles). 
     Referring to  FIG. 4 , and as noted above, the upper surface  134  of the base  132  forms the bottom portion of the pumping chamber  125 . The upper surface  134  of the base  132  is inclined from a first end  102  of the apparatus  100  to a second end  104  of the apparatus. Said another way, the upper surface  134  lies along a plane having an axis different than the horizontal axis A 3 . Because each of the first gasket  142 , the membrane  140 , and the membrane frame  144  are disposed on the upper surface  134  of the base  132 , each of the first gasket, the membrane, and the membrane frame are similarly inclined from the first end  102  of the apparatus  100  towards the second end  104  of the apparatus. In this manner, the base  132  is configured to facilitate movement of a fluid towards the highest portion of the pumping chamber  125 . The angle of incline of these components may be of any suitable value to allow fluid (e.g., gas bubbles, excess liquid) to flow towards the purge port  106  and exit the pumping chamber  125 . In some embodiments, the angle of incline is approximately in the range of 1°-10°, in the range of 2°-6°, in the range of 2.5°-5°, in the range of 4°-5° or any angle of incline in the range of 1°-10° (e.g., approximately 1°, 2°, 3°, 4°, 5°, 6°, 7°, 8°, 9°, 10°). 
     As illustrated in  FIG. 4 , a valve  138  is disposed at approximately the highest portion of the lower surface  136  of the base  132 . The valve  138  is moveable between an open configuration and a closed configuration. In its open configuration, the valve  138  is configured to permit movement of a fluid from an organ chamber  192 , which is defined by the canister  190  and a lower surface  136  of the lid assembly  110 , to the pumping chamber  125  via the valve. Specifically, the valve  138  is configured to permit fluid to move from the organ chamber  192  into the second portion  129  of the pumping chamber  114 . In this manner, an excess amount of fluid within the organ chamber  192  can overflow through the valve  138  and into the pumping chamber  125 . In its closed configuration, the valve  138  is configured to substantially prevent movement of a fluid from the pumping chamber  125  to the organ chamber  192  via the valve. The valve  138  is moved from its closed configuration to its open configuration when a pressure in the organ chamber  192  is greater than a pressure in the pumping chamber  125 . In some embodiments, the valve  138  is moved from its open position to its closed position when a pressure in the pumping chamber  125  is greater than a pressure in the organ chamber  192 . The valve  138  can be biased towards its closed configuration. In some embodiments, one or more additional valves (not shown) are disposed at other locations of the base  132 . In some embodiments, an additional valve (not shown) is located at approximately the lowest portion of the lower surface  136  of the base  132 . 
     As illustrated in  FIGS. 4 and 6 , in some embodiments, the valve  138  is a ball check valve. In its closed configuration, a spherical ball of the valve  138  is disposed on a seat of the valve. In its open configuration, the ball is lifted off of the seat of the valve  138 . The ball of the valve  138  has a near neutral buoyancy. As such, the ball of the valve  138  will neither sink nor rise merely because it is in the presence of a fluid (e.g., the perfusate, oxygen, or another fluid). The ball of the valve  138  is configured to rise off of the seat of the valve when the pressure in the organ chamber  192  is greater than the pressure in the pumping chamber  125 . In some embodiments, a protrusion  151  of the lid  120  is extended downwardly over the valve  138  to prevent the ball from rising too high above the seat such that the ball could be laterally displaced with respect to the seat. In some embodiments, the ball of the valve  138  is configured to return to the seat of the valve when the pressure in the pumping chamber is greater than the pressure in the organ chamber. In some embodiments, the ball of the valve  138  is biased towards the seat of the valve by a spring (not shown) extended from the lid  120 . The seat of the valve  138  can be conically tapered to guide the ball into the seat and to facilitate formation of a positive seal when stopping flow of fluid from the pumping chamber  125  to the organ chamber  192 . 
     The base  132  is coupled to the lid  120 . In some embodiments, a rim  139  of the base  132  and a rim  121  of the lid  120  are coupled together, e.g., about a perimeter of the pumping chamber  125 . The base  132  and the lid  120  can be coupled using any suitable mechanism for coupling including, but not limited to, a plurality of screws, an adhesive, a glue, a weld, another suitable coupling mechanism, or any combination of the foregoing. A gasket  148  is disposed between the base  132  and the lid  120 . The gasket  148  is configured to seal an engagement of the base  132  and the lid  120  to substantially prevent fluid in the pumping chamber  125  from leaking therebetween. In some embodiments, the gasket  148  is an O-ring. 
     The base  132  defines a lumen  135  configured to be in fluid communication with a lumen  174  of an organ adapter  170 , described in more detail below. The base  132  is configured to permit oxygenated perfusate to move from the pumping chamber  125  through its lumen  135  into the lumen  174  of the organ adapter  170  towards the organ chamber  192 . In this manner, the lumen  135  of the base  132  is configured to help fluidically couple the pumping chamber  125  and the organ chamber  192 . 
     The organ adapter  170  is configured to substantially retain the bodily tissue with respect to the apparatus  100 . The organ adapter  170  can be similar in many respects to an adapter described herein (e.g., adapter  26 , described above, and/or adapter  770 , described below). The organ adapter  170  includes a handle portion  178 , an upper portion  172 , and a protrusion  180 , and defines the lumen  174  extended therethrough. The upper portion  172  of the organ adapter  170  is extended from a first side of the handle portion  178 . The protrusion  180  of the organ adapter  170  is extended from a second side of the handle portion  178  different than the first side of the handle portion. At least a portion of the protrusion  180  is configured to be inserted into the bodily tissue. More specifically, at least a portion of the protrusion  180  is configured to be inserted into a vessel (e.g., an artery, a vein, or the like) of the bodily tissue. In some embodiments, the protrusion  180  is configured to be coupled to the bodily tissue via an intervening structure, such as silastic or other tubing. 
     As illustrated in  FIG. 4 , at least a portion of the protrusion  180  includes a series of tapered steps such that a distal end  181  of the protrusion is narrower than a proximal end  183  of the protrusion. In this manner, the protrusion  180  is configured to be inserted into a range of vessel sizes. For example, the protrusion  180  can be configured to be received in a bodily vessel having a diameter within the range of about 3 millimeters to about 8 millimeters. In this manner, the protrusion  180  is configured to deliver the fluid (e.g., the oxygenated perfusate) from the pumping chamber  125  to the vessel of the bodily tissue via the lumen  174  defined by the organ adapter  170 . The vessel of the bodily tissue can be sutured to the protrusion  180  of the adapter  170 . 
     The organ adapter  170  includes a first arm  182  having a first end portion  185  and a second arm  184  having a second end portion  187 . The first and second arms  182 ,  184  are configured to facilitate retention of the bodily tissue with respect to the organ adapter  170 . A retention mechanism (not shown) is configured to be attached, coupled, or otherwise disposed about each of the first and second arms  182 ,  184 . The retention mechanism can be any suitable retention mechanism described above with respect to the apparatus  10 , including, for example, a net, a cage, a sling, or the like. A middle portion of the retention mechanism is configured to be disposed about at least a portion of the bodily tissue coupled to the protrusion  180  of the adapter  170 . End portions of the retention mechanism are configured to be disposed about each of the first and second arms  182 ,  184  of the organ adapter  170 . The first end portion  185  of the first arm  182  and the second end portion  187  of the second arm  184  are each configured to facilitate retention of the end portions of the retention mechanism with respect to the first and second arms, respectively. For example, as shown in  FIG. 4 , each of the first and second end portions  185 ,  187  of the first and second arms  182 ,  184 , respectively, defines a shoulder portion configured to help prevent the end portions of the retention mechanism from being inadvertently removed from the first or second arm, respectively. 
     The upper portion  172  of the organ adapter  170  is configured to couple the organ adapter to the base  132 . The upper portion  172  of the organ adapter is configured to be received by the lumen  135  defined by the base. The upper portion  172  includes a first projection  176  and a second projection (not shown) spaced apart from the first projection. The projections  176  of the organ adapter  170  are configured to be received by the lumen  135  of the base  132  in opposing spaces between a first protrusion  154  and a second protrusion  156  (shown in  FIG. 5 ) disposed within the lumen of the base. Once the upper portion  172  is received in the lumen  135  of the base  132 , the organ adapter  170  can be rotated approximately ninety degrees such that its first projection  176  and its second projection sit on a shoulder  155 ,  157  defined by the protrusions  154 ,  156  of the base, respectively. The organ adapter  170  can be rotated in either a clockwise or a counterclockwise direction to align its projections with the shoulders of the protrusions of the base  132 . Similarly, the organ adapter  170  can be rotated in either the clockwise or the counterclockwise direction to unalign its projections with the shoulders of the protrusions of the base  132 , such as for decoupling of the adapter from the base. Said another way, the organ adapter  170  can be configured to be coupled to the base  132  with a bayonet joint. The handle portion  178  is configured to facilitate coupling and decoupling of the organ adapter  170  and the base  132 . For example, the handle portion  178  is configured to be grasped by a hand of an operator of the apparatus  100 . As shown in  FIG. 6 , the handle portion  178  is substantially disc-shaped, and includes a series of recesses configured to facilitate grasping the handle portion with the operator&#39;s hand. 
     A gasket  188  is disposed about the upper portion  172  of the organ adapter  170  between the handle portion  178  of the adapter and the base  132 . The gasket  188  is configured to substantially prevent a fluid from flowing between the pumping chamber  125  and the organ chamber  192  within a channel formed between an outer surface of the upper portion  172  of the organ adapter  170  and an inner surface of the lumen  135  of the base  132 . In some embodiments, the gasket  188  is compressed between the organ adapter  170  and the base  132  when the organ adapter is coupled to the base. 
     In some embodiments, at least a portion of the lid assembly  110  is configured to minimize flexure of the portion of the lid assembly, such as may occur in the presence of a positive pressure (or pulse wave) caused by introduction of oxygen into the pumping chamber  125  and/or of oxygenated perfusate into the organ chamber  192 . For example, as illustrated in  FIG. 6 , the upper portion  122  of the lid  120  includes a plurality of ribs  126  configured to minimize flexure of the lid  120  when oxygen is pumped through the pumping chamber  125 . In other words, the plurality of ribs  126  structurally reinforces the lid  120  to help prevent the lid  120  from flexing. The plurality of ribs  126  are extended from a top surface of the lid  120  in a substantially parallel configuration. In another example, the lower portion  128  of the lid  120  can include a plurality of ribs (not shown) configured to reinforce the top of the pumping chamber  125  to help prevent flexure of the top of the pumping chamber  125  during pumping of oxygen through the lid assembly  110 . In yet another example, the base  132  is configured to substantially minimize flexure of the base, such as may occur in the presence of a positive pressure caused by the introduction of oxygen into the pumping chamber  125  and/or of oxygenated perfusate into the organ chamber  192 . As illustrated in  FIG. 6 , the base  132  includes a plurality of ribs  131  extended from its upper surface  134 . As illustrated in  FIG. 5 , the base  132  includes a plurality of ribs  133  extended from its lower surface  136 . Each of the plurality of ribs  131 ,  133  is configured to reinforce the base  132 , which helps to minimize flexure of the base. 
     The lid assembly  110  includes a fill port  108  configured to permit introduction of a fluid (e.g., the perfusate) into the organ chamber  192  (e.g., when the lid assembly is coupled to the canister  190 ). The fill port  108  can be similar in many respects another port described herein (e.g., port  34 , described above, and/or port  708 , described below). In the embodiment illustrated in  FIG. 4  and  FIG. 6 , the fill port  108  is formed by a fitting  107  coupled to the lid  120  and that defines a lumen  109  in fluidic communication with a lumen  143  in the first gasket  142 , which lumen  143  is in fluidic communication with a lumen  137  defined by the base  132 , which lumen  137  is in fluidic communication with the organ chamber  192 . The fitting  107  can be any suitable fitting, including, but not limited to, a luer lock fitting. The fill port  108  can include a cap (not shown) removably coupled to the port via a retaining strap. The cap can help prevent inadvertent movement of fluid, contaminants, or the like through the fill port  108 . 
     The lid assembly  110  is configured to be coupled to the canister  190 . The canister  190  can be similar in many respects to a canister described herein (e.g., canister  32 , described above, and/or canister  390 ,  790 ,  990 , described below). The canister includes a wall  191 , a floor  193 , and a compartment  194  defined on its sides by the wall and on its bottom by the floor. The compartment  194  can form a substantial portion of the organ chamber  192 . As shown in  FIG. 4 , at least a portion of the lid assembly  110  (e.g., the base  132 ) is configured to be received in the compartment  194  of the canister  190 . A gasket  152  is disposed between the base  132  and an inner surface of the wall  191  of the canister  190 . The gasket  152  is configured to seal the opening between the base  132  and the wall  191  of the canister  190  to substantially prevent flow of fluid (e.g., the perfusate) therethrough. The gasket  152  can be any suitable gasket, including, for example, an O-ring. In some embodiments, the canister  190  includes a port  196  disposed on the wall  191  of the canister. 
     The floor  193  of the canister  190  is configured to flex when a first pressure within the organ chamber  192  changes to a second pressure within the organ chamber, the second pressure different than the first pressure. More specifically, in some embodiments, the floor  193  of the canister  190  is configured to flex when a first pressure within the organ chamber  192  is increased to a second pressure greater than the first pressure. For example, the floor  193  of the canister  190  can be configured to flex in the presence of a positive pressure (or a pulse wave) generated by the pumping of the oxygenated perfusate from the pumping chamber  125  into the organ chamber  192 , as described in more detail below. In some embodiments, the floor  193  of the canister  190  is constructed of a flexible membrane. The floor  193  of the canister  190  can have any suitable thickness. For example, in some embodiments, the floor  193  of the canister  190  has a thickness of about 0.075 to about 0.085 inches. In some embodiments, the floor  193  of the canister  190  is about 0.080 inches thick. 
     The canister  190  can be configured to enable an operator of the apparatus  100  to view the bodily tissue when the bodily tissue is sealed within the organ chamber  192 . In some embodiments, for example, at least a portion of the canister  190  (e.g., the wall  191 ) is constructed of a transparent material. In another example, in some embodiments, at least a portion of the canister  190  (e.g., the wall  191 ) is constructed of a translucent material. In some embodiments, the canister  190  includes a window (not shown) through which at least a portion of the organ chamber  192  can be viewed. 
     As noted above, the coupling mechanism  250  is configured to couple the canister  190  to the lid assembly  110 . In the embodiment illustrated in  FIGS. 2-4 , the coupling mechanism  250  is a substantially C-shaped clamp. The clamp  250  includes a first arm  252  and a second arm  254 . The arms  252 ,  254  are configured to be disposed on opposite sides of the apparatus  100  about a lower rim of the lid  120  and an upper rim of the canister  190 . The arms  252 ,  254  of the clamp  250  are coupled at the first side  102  of the apparatus  100  by a hinge  256 . The clamp  250  is in an open configuration when the first arm  252  is movable with respect to the second arm  254  (or vice versa). The arms  252 ,  254  are configured to be coupled at a second side  104  of the apparatus  100  by a locking lever  258 . The clamp  250  is in a closed configuration when its arms  252 ,  254  are coupled at the second side  104  of the apparatus  100  by the locking lever  258 . In some embodiments, the clamp  250  is configured for a single use. More specifically, the clamp  250  can be configured such that when it is moved from its closed configuration to its open configuration, the clamp is prevented from being returned to its closed configuration. In other words, once an original seal formed by the clamp in its closed configuration is broken by opening the clamp, the clamp can no longer be resealed. In use, the clamp  250  being configured for a single use can help an operator of the apparatus  100  ensure that bodily tissue being preserved within the apparatus is free of tampering. In some embodiments, the clamp  250  remains coupled to one of the canister  190  or the lid  120  when the clamp is moved to its open configuration from its closed configuration. 
     Although the coupling mechanism  250  has been illustrated and described as being a clamp (and a band clamp specifically), in other embodiments, another suitable mechanism for coupling the canister  190  to the lid assembly  110  can be used. For example, the coupling mechanism  250  can be designed as a toggle clamp that is attached to the lid assembly  110 . The toggle clamp can be a toggle action clamp that is manually movable between undamped, center, and over-center (clamped) positions. Any suitable number of toggle clamps may be employed, such as one, two, three, four or more toggle clamps. 
     As noted above, the apparatus  100  is configured for controlled delivery of fluid (e.g., oxygen) from an external source (not shown) into the pumping chamber  125  of the lid assembly  110 . The external source can be, for example, an oxygen cylinder. In some embodiments, the pneumatic system  200  is configured for controlled venting of fluid (e.g., carbon dioxide) from the pumping chamber  125  to an area external to the apparatus  100  (e.g., to the atmosphere). The pneumatic system  200  is moveable between a first configuration in which the pneumatic system is delivering fluid to the pumping chamber  125  and a second configuration in which the pneumatic system is venting fluid from the pumping chamber  125 . The pneumatic system  200  includes a supply line  204 , a vent line  206 , a control line  208 , a valve  210 , a printed circuit board assembly (“PCBA”)  214 , and a power source  218 . 
     The supply line  204  is configured to transmit fluid from the external source to the valve  210 . A first end of the supply line  204  external to the lid  120  is configured to be coupled to the external source. A second end of the supply line  204  is configured to be coupled to the valve  210 . Referring to  FIGS. 6 and 7 , a portion of the supply line  204  between its first end and its second end is configured to be extended from an area external to the lid  120  through an opening  123  defined by the lid into the chamber  124  defined by the lid. In some embodiments, the supply line  204  is configured to transmit fluid to the valve  210  at a pressure of about 2 pounds per square inch (“p.s.i.”), plus or minus ten percent. 
     The vent line  206  is configured to transmit fluid (e.g., oxygen, carbon dioxide) from the valve  210  to an area external to the chamber  124  of the lid  120 . A first end of the vent line  206  is configured to be coupled to the valve  210 . In some embodiments, the second end of the vent line  206  is a free end such that the fluid is released into the atmosphere. A portion of the vent line  206  between its first end and its second end is configured to be extended from the valve  210  through the chamber  124  and the opening  123  defined by the lid  120  to the area external to the lid. 
     The control line  208  is configured to transmit fluid between the valve  210  and the pumping chamber  125  of the lid assembly  110 . A first end of the control line  208  is coupled to the valve  210 . A second end of the control line  208  is coupled to the pumping chamber  125 . In some embodiments, as shown in  FIG. 7 , the control line  208  is mechanically and fluidically coupled to the pumping chamber  125  by an adapter  209 . The adapter  209  can be any suitable mechanism for coupling the control line  208  to the pumping chamber  125 . In some embodiments, for example, the adapter  209  includes a male fitting on a first end of the adapter that is configured to be disposed in the second end of the control line  208  and threaded portion on a second end of the adapter configured to be received in a correspondingly threaded opening in the lower portion  128  of the lid  120 . When the pneumatic system  200  is in its first configuration, the control line  208  is configured to transmit fluid from the supply line  204  via the valve  210  to the pumping chamber  125 . When the pneumatic system  200  is in its second configuration, the control line  208  is configured to transmit fluid from the pumping chamber  125  to the vent line  206  via the valve  210 . Each of the foregoing lines (i.e., supply line  204 , vent line  206 , control line  208 ) can be constructed of any suitable material including, for example, polyurethane tubing. 
     The valve  210  is configured to control the flow of oxygen into and out of the pumping chamber  125 . In the embodiment illustrated in  FIG. 7 , the valve  210  is in fluidic communication with each of the supply line  204 , the vent line  206 , and the control line  208  via a first port, a second port, and a third port (none of which are shown in  FIG. 7 ), respectively. In this manner, the valve  210  is configured to receive the fluid from the supply line  204  via the first port. In some embodiments, the first port defines an orifice that is about 0.10 to about 0.60 mm in size. In other embodiments, the first port defines an orifice that is about 0.15 to about 0.50 mm in size, about 0.20 to about 0.40 mm in size, about 0.20 to about 0.30 mm in size, or about 0.25 to about 0.30 mm in size. Specifically, in some embodiments, the first port defines an orifice that is about 0.25 mm in size. The valve  210  is configured to deliver the fluid to the vent line  206  via the second port. Additionally, the valve  210  is configured to receive the fluid from and deliver the fluid to the control line  208  via the third port. Specifically, the valve  210  is movable between a first configuration and a second configuration. In its first configuration, the valve  210  is configured to permit the flow of fluid from the supply line  204  through the valve  210  to the control line  208 . As such, when the valve  210  is in its first configuration, the pneumatic system  200  is in its first configuration. In its second configuration, the valve  210  is configured to permit the flow of fluid from the control line  208  through the valve to the vent line  206 . As such, when the valve  210  is in its second configuration, the pneumatic system  200  is in its second configuration. 
     The valve  210  is in electrical communication with the power source  218 . In some embodiments, for example, the valve  210  is in electrical communication with the power source  218  via the PCBA  214 . In the embodiment illustrated in  FIGS. 6 and 7 , the PCBA  214  is disposed in the chamber  124  between the valve  210  and the power source  218 . In some embodiments, the PCBA  214  includes an electrical circuit (not shown) configured to electrically couple the power source  218  to the valve  210 . The power source  218  is configured to provide power to the valve  210  to enable the valve  210  to control the flow of oxygen. In some embodiments, the power source  218  is configured to provide power to the valve  210  to enable the valve to move between its first configuration and its second configuration. The power source can be any suitable source of power including, for example, a battery. More specifically, in some embodiments, the power source is a lithium battery (e.g., a Li/MnO 2  2/3A battery). In another example, the power source can be an AA, C or D cell battery. 
     The valve  210  can be any suitable mechanism for controlling movement of the fluid between the first port, the second port, and the third port (and thus the supply line  204 , vent line  206 , and the control line  208 , respectively). For example, in the embodiment illustrated in  FIG. 7 , the valve  210  is a solenoid valve. As such, in operation, the valve  210  is configured to convert an electrical energy received from the power source  218  to a mechanical energy for controlling the flow of oxygen therein. In some embodiments, for example, the valve  210  is configured to move to its first configuration when power is received by the valve from the power source  218 . In some embodiments, the valve  210  is configured to move to its second configuration when the valve is electrically isolated (i.e., no longer receiving power) from the power source  218 . In other words, the valve  210  is configured to deliver fluid (e.g., oxygen) to the pumping chamber  125  when the solenoid of the valve is energized by the power source  218 , and the valve is configured to vent fluid (e.g., oxygen, carbon dioxide) from the pumping chamber when the solenoid of the valve is not energized by the power source. In some embodiments, the valve  210  is biased towards its second (or venting) configuration (in which power is not being provided from the power source  218  to the valve). Because the power source  218  is configured to not be in use when the pneumatic system  200  is not delivering oxygen to the pumping chamber  125 , the usable life of the power source is extended, which enables the bodily tissue to be extracorporeally preserved within the apparatus  100  for a longer period of time. For example, in some embodiments, the solenoid of the valve  210  is configured to receive power from the power source  218  for about 20 percent of the total time the apparatus  100 , or at least the pneumatic system  200  of the apparatus, is in use. 
     In some embodiments, the flow of fluid from the supply line  204  to the valve  210  is substantially prevented when the valve is in its second configuration. In this manner, the flow of oxygen into the valve  210  from the supply line  204  is stopped while the valve is venting fluid from the pumping chamber  125 . As such, the overall oxygen use of the apparatus  100  is reduced. In other embodiments, when the valve  210  is in its second configuration, the fluid being transmitted into the valve from the supply line  204  is transmitted through the valve to the vent line  206  without entering the pumping chamber  125 . In this manner, the inflow of fluid from the supply line  204  to the valve  210  is substantially continuous. Accordingly, the flow of fluid from the valve  210  to the vent line  206  is also substantially continuous because the valve  210  is substantially continuously venting fluid from at least one of the supply line  204  and/or the control line  208 . 
     Referring to a schematic illustration of the pneumatic system and pumping chamber in  FIG. 8 , the pneumatic system  200  is configured to control a change in pressure within the pumping chamber  125  of the lid assembly  110 . In some embodiments, the pneumatic system  200  is configured to control the pressure within the pumping chamber  125  via the control line  208 . More specifically, the rate of flow of fluid between the valve  210  and the pumping chamber  125  via the control line  208  is determined by a control orifice  207  disposed within the control line. The control orifice  207  can be, for example, a needle valve disposed within the control line  208 . In some embodiments, the control orifice is about 0.10 to about 0.60 mm in size. In other embodiments, the first port defines an orifice that is about 0.15 to about 0.50 mm in size, about 0.20 to about 0.40 mm in size, about 0.20 to about 0.30 mm in size, or about 0.25 to about 0.30 mm in size. For example, in some embodiments, the control orifice  207  is about 0.25 mm in size. Because the rate of a change (e.g., rise, fall) in pressure within the pumping chamber  125  is based on the rate of flow of the fluid between the valve  210  and the pumping chamber  125  via the control line  208 , the pressure within the pumping chamber  125  is also determined by the size of the control orifice  207  in the control line  208 . 
     The pneumatic system  200  can be configured to move between its first configuration and its second configuration based on a predetermined control scheme. In some embodiments, the pneumatic system  200  is configured to move between its first configuration and its second configuration on a time-based control scheme. In some embodiments, the pneumatic system  200  is configured to move from its first configuration to its second configuration after a first period of time has elapsed. For example, the pneumatic system  200  can be configured to move from its first configuration to its second configuration after about 170 milliseconds. As such, the pneumatic system  200  is configured to deliver fluid (e.g., oxygen) to the pumping chamber  125  for the first time period (e.g., about 170 milliseconds). The pneumatic system  200  is configured to move from its second configuration to its first configuration after a second period of time has elapsed. For example, the pneumatic system  200  can be configured to move from its second configuration to its first configuration after being in its second configuration for about 700 milliseconds. As such, the pneumatic system  200  is configured to vent fluid (e.g. carbon dioxide) from the pumping chamber  125  for the second time period (e.g., about 700 milliseconds). The pneumatic system  200  is configured to alternate between its first configuration and its second configuration, and thus between delivering fluid into the pumping chamber  125  and venting fluid from the pumping chamber. 
     Although the pneumatic system  200  has been illustrated and described above as having a time-based control scheme, in some embodiments, the pneumatic system  200  is configured to move between its first configuration and its second configuration on a pressure based control scheme. In some embodiments, the pneumatic system  200  is configured to move from its first configuration to its second configuration when a pressure within the pumping chamber  125  reaches a first threshold pressure. For example, the pneumatic system  200  can be configured to move from its first configuration to its second configuration when the pressure within the pumping chamber  125  is about 20 mmHg (millimeters of mercury), about 25 mmHg, about 30 mmHg, about 35 mmHg, about 40 mmHg, about 45 mmHg or about 50 mmHg. The pneumatic system  200  can be configured to move from its second configuration to its first configuration when a pressure within the pumping chamber  125  reaches a second threshold pressure. For example, the pneumatic system  200  can be configured to move from its second configuration to its first configuration when the pressure within the pumping chamber  125  is about 0 mmHg, about 5 mmHg, about 10 mmHg or about 15 mmHg. Said another way, when the pressure within the pumping chamber  125  is increased from the second threshold pressure to the first threshold pressure, the valve  210  is switched from delivering fluid to the pumping chamber to venting fluid from the pumping chamber. Similarly, when the pressure within the pumping chamber  125  is decreased from the first threshold pressure to the second threshold pressure, the valve  210  is switched from venting fluid from the pumping chamber to delivering fluid to the pumping chamber. 
     Because the pneumatic system  200  is configured to alternate between its first configuration and its second configuration, the pneumatic system  200  can be characterized as being configured to deliver oxygen to the pumping chamber  125  via a series of intermittent pulses. In some embodiments, however, the pneumatic system  200  is configured to deliver oxygen to the pumping chamber  125  in a substantially constant flow. In still another example, the pneumatic system  200  can be configured to selectively deliver oxygen in each of a substantially constant flow and a series of intermittent pulses. In some embodiments, the pneumatic system  200  is configured to control the flow of fluid within the pumping chamber  125 , including the delivery of oxygen to the pumping chamber, in any combination of the foregoing control schemes, as desired by an operator of the apparatus  100 . 
     Although the pneumatic system  200  has been illustrated and described herein as controlling the change in pressure within the pumping chamber  125  via a control orifice disposed in the control line  208 , in other embodiments, a pneumatic system is configured to control the pressure within the pumping chamber via at least one control orifice disposed within at least one of the supply line and the vent line. Referring to  FIG. 9 , in some embodiments of a pneumatic system  220 , a larger control orifice  223  is disposed within the supply line  222 . In this manner, the pneumatic system  220  can permit a larger and/or quicker inflow of fluid from the supply line  222  to the pumping chamber, and thus can cause a quick pressure rise within the pumping chamber  228 . In another example, in some embodiments, a smaller control orifice  225  is disposed within the vent line  224 . In this manner, the pneumatic system  220  can restrict the flow of fluid venting through the vent line  224  from the pumping chamber  228 , and thus can cause a slower or more gradual decline in pressure within the pumping chamber. As compared to pneumatic system  200 , pneumatic system  220  can permit a shorter time period when the valve  210  is energized, thereby allowing power source  218  to operate the apparatus for a longer period. 
     In use, the bodily tissue is coupled to the organ adapter  170 . The lid assembly  110  is disposed on the canister  190  such that the bodily tissue is received in the organ chamber  192 . The lid assembly  110  is coupled to the canister  190 . Optionally, the lid assembly  110  and the canister  190  are coupled via the clamp  250 . A desired amount of perfusate is delivered to the organ chamber  192  via the fill port  108 . Optionally, a desired amount of perfusate can be disposed within the compartment  194  of the canister  190  prior to disposing the lid assembly  110  on the canister. In some embodiments, a volume of perfusate greater than a volume of the organ chamber  192  is delivered to the organ chamber such that the perfusate will move through the ball check valve  138  into the second portion  129  of the pumping chamber  125 . 
     A desired control scheme of the pneumatic system  200  is selected. Oxygen is introduced into the first portion  127  of the pumping chamber  125  via the pneumatic system  200  based on the selected control scheme. The pneumatic system  200  is configured to generate a positive pressure by the introduction of oxygen into the first portion  127  of the pumping chamber  125 . The positive pressure helps to facilitate diffusion of the oxygen through the membrane  140 . The oxygen is diffused through the membrane  140  into the perfusate disposed in the second portion  129  of the pumping chamber  125 , thereby oxygenating the perfusate. Because the oxygen will expand to fill the first portion  127  of the pumping chamber  125 , substantially all of an upper surface  141  of the membrane  140  which faces the first portion of the pumping chamber can be used to diffuse the oxygen from the first portion into the second portion  129  of the pumping chamber. 
     As the bodily tissue uses the oxygen, the bodily tissue will release carbon dioxide into the perfusate. In some embodiments, the carbon dioxide is displaced from the perfusate, such as when the pneumatic system  200  the oxygen is diffused into the perfusate because of the positive pressure generated by the pneumatic system. Such carbon dioxide can be diffused from the second portion  129  of the pumping chamber  125  into the first portion  127  of the pumping chamber  125 . Carbon dioxide within the first portion  127  of the pumping chamber is vented via the control line  208  to the valve  210 , and from the valve through the vent line  206  to the atmosphere external to the apparatus  100 . 
     The positive pressure also causes the membrane  140  to flex, which transfers the positive pressure in the form of a pulse wave into the oxygenated perfusate. The pulse wave generated by the pumping chamber is configured to facilitate movement of the oxygenated perfusate from the second portion  129  of the pumping chamber  125  into the bodily tissue via the organ adapter  170 , thus perfusing the bodily tissue. In some embodiments, the pumping chamber  125  is configured to generate a pulse wave that is an about 60 Hz pulse. In some embodiments, the pumping chamber  125  is configured to generate a pulse wave through the perfusate that is configured to cause a differential pressure within the organ chamber  192  to be within the range of about 0 mmHg to about 50.0 mmHg. More specifically, in some embodiments, the pumping chamber  125  is configured to generate a pulse wave through the perfusate that is configured to cause a differential pressure within the organ chamber  192  to be within the range of about 5 mmHg to about 30.0 mmHg. 
     At least a portion of the perfusate perfused through the bodily tissue is received in the organ chamber  192 . In some embodiments, the pulse wave is configured to flow through the perfusate disposed in the organ chamber  192  towards the floor  193  of the canister  190 . The floor  193  of the canister  190  is configured to flex when engaged by the pulse wave. The floor  193  of the canister  190  is configured to return the pulse wave through the perfusate towards the top of the organ chamber  192  as the floor  193  of the canister  190  is returned towards its original non-flexed position. In some embodiments, the returned pulse wave is configured to generate a sufficient pressure to open the ball check valve  138  disposed at the highest position in the organ chamber  192 . In this manner, the returned pulse wave helps to move the valve  138  to its open configuration such that excess fluid (e.g., carbon dioxide released from the bodily tissue and/or the perfusate) can move through the valve from the organ chamber  192  to the pumping chamber  125 . 
     The foregoing perfusion cycle can be repeated as desired. For example, in some embodiments, the pneumatic system  200  is configured to begin a perfusion cycle approximately every second based on a time-based control scheme. As such, the pneumatic system  200  is configured to power on to deliver oxygen to the pumping chamber  125  for several milliseconds. The pneumatic system  200  can be configured to power off for several milliseconds, for example, until time has arrived to deliver a subsequent pulse of oxygen to the pumping chamber  125 . Because the pneumatic system  200 , and the solenoid valve  210  specifically, is only powered on when needed to transmit a pulse of oxygen to the pumping chamber, the usable life of the power source  218  can be extended for a longer period of time. 
     An apparatus  300  according to an embodiment is illustrated in  FIGS. 10-16 . The apparatus  300  is configured to oxygenate a perfusate and to perfuse a bodily tissue for extracorporeal preservation of the bodily tissue. The apparatus  300  includes a lid assembly  310 , a canister  390 , and a coupling mechanism  450 . Unless stated otherwise, apparatus  300  can be similar in many respects (e.g., form and/or function) to the apparatus described herein (e.g., apparatus  10 ,  100 ,  700  (described below)), and can include components similar in many respects (e.g., form and/or function) to components of such apparatus. For example, the canister  390  can be similar to the canister  190 . 
     The lid assembly  310  includes a lid cover  314  (e.g., as shown in  FIG. 10 ) and a lid  320  (e.g., as shown in  FIG. 12 ). The lid cover  314  is coupled to the lid  320 . The lid cover  314  can be coupled to the lid  320  using any suitable mechanism for coupling. For example, the lid cover  314  can be coupled to the lid  320  with at least one of a screw, an adhesive, a hook and loop fastener, mating recesses, or the like, or any combination of the foregoing. A chamber  324  is formed between an upper portion  322  of the lid  320  and a bottom portion  316  of the lid cover  314 . The chamber  324  is configured to receive components of a pneumatic system (e.g., the pneumatic system  200  described above) and the control system  500  (described in detail below with respect to  FIG. 17 ). 
     The lid assembly  310  includes a first gasket  342 , a membrane  340 , and a membrane frame  344  disposed on the upper portion  322  of the lid  320 . The lid assembly  310  defines a pumping chamber  325  configured to receive oxygen from the pneumatic system  200 , to facilitate diffusion of the oxygen into a perfusate (not shown) and to facilitate movement of the oxygenated perfusate into a bodily tissue (not shown). A top of the pumping chamber  325  is formed by the membrane frame  344 . A bottom of the pumping chamber  325  is formed by an upper surface  334  of a base  332  of the lid assembly  310 . 
     One or more components of the lid assembly  310  (e.g., the lid  320  and/or the lid cover  314 ) can be transparent, either in its entirety or in part. Referring to  FIGS. 10 and 12 , the lid cover  314  includes a window (not shown), and the lid  320  includes a transparent portion  326  adjacent to, or at least in proximity to, a purge port  306 . The transparent portion  326  permits a user to view any excess fluid (e.g., in the form of gas bubbles) in the pumping chamber  325  and to confirm when the excess fluid has been purged from the pumping chamber  325 . 
     The first gasket  342  is disposed between the membrane  340  and the membrane frame  344  such that the first gasket is engaged with an upper surface  341  of the membrane  340 . The first gasket  342  is configured to seal a perimeter of a first portion  327  of the pumping chamber  325  formed between the membrane frame  344  and the upper surface  341  of the membrane  340 . In other words, the first gasket  342  is configured to substantially prevent lateral escape of oxygen from the first portion  327  of the pumping chamber  325  to a different portion of the pumping chamber. The first gasket  342  has a perimeter substantially similar in shape to a perimeter defined by the membrane  340  (e.g., when the membrane is disposed on the membrane frame  344 ). In other embodiments, however, a gasket can have another suitable shape for sealing the first portion  327  of the pumping chamber  325 . 
     The membrane  340  is configured to permit diffusion of gas (e.g., oxygen, carbon dioxide, etc.) from the first portion  327  of the pumping chamber  325  through the membrane to a second portion  329  of the pumping chamber, and vice versa. The membrane  340  is configured to substantially prevent a liquid (e.g., the perfusate) from passing through the membrane. In this manner, the membrane  340  can be characterized as being semi-permeable. The membrane frame  344  is configured to support the membrane  340  (e.g., during the oxygenation and perfusion of the bodily tissue). At least a portion of the membrane  340  is disposed (e.g., wrapped) about at least a portion of the membrane frame  344 . In some embodiments, the membrane  340  is stretched when it is disposed on the membrane frame  344 . The membrane  340  is disposed about a bottom rim of the membrane frame  344  such that the membrane  340  is engaged with a series of protrusions (e.g., the protrusions  345  shown in  FIG. 12 ) configured to help retain the membrane  340  with respect to the membrane frame  344 . The lid  320  and the membrane frame  344  are designed for oblique compression of the first gasket  342  therebetween. The lid  320  is designed such that the membrane  340 , when stretched and disposed on the membrane frame  344 , is virtually coplanar with a bottom portion  328  of the lid  320 , which is inclined from a first side of the apparatus  300  towards a second side of the apparatus  300  (i.e., towards the purge port  306 ). As such, excess fluid (e.g., gas bubbles, perfusate, etc.) is more effectively purged from the pumping chamber  325 , e.g., to prevent gas bubbles or the like from being trapped therein. 
     The pumping chamber  325  includes an obstruction free second portion  329 . The second portion  329  of the pumping chamber  325  is configured to receive fluid (e.g., the perfusate) from the canister  390 , as described in more detail below. The second portion  329  of the pumping chamber  325  is configured to contain the fluid for oxygenation of the fluid as oxygen is pumped into the first portion  327  of the pumping chamber  325  and permeated through the membrane  340  into the second portion  329  of the pumping chamber, thereby facilitating oxygenation of the fluid contained therein. In some embodiments, the lid  320  includes one or more purging structures, such as a lumen (not shown), configured to help avoid trapping of gas bubbles and/or other fluid at the membrane-lid interface. 
     Referring to  FIG. 14 , the base  332  includes return flow valves  338 A,  338 B. Each return flow valve  338 A,  338 B is configured to permit fluid to flow from the canister  390  into the pumping chamber  325 . The valves  338 A,  338 B each can be any suitable type of valve, including, for example, a ball check valve. Each valve  338 A,  338 B can include a return jet  360 A,  360 B, respectively, configured to focus fluid flowing from the canister  390  into the pumping chamber  325  onto the membrane  340 . Because the membrane  340  is inclined towards the purge port  306 , the focused flow of fluid from the return jets  360 A,  360 B onto the membrane  340  can help facilitate movement of the fluid towards the purge port  306 , thereby facilitating purging of excess fluid from the apparatus  300 . Although illustrated as being nozzle-shaped, other designs of the jets  360 A,  360 B are suitable. The jets  360 A,  360 B are also configured to enhance mixing of fluid (e.g., perfusate) within the pumping chamber  325 , which facilitates oxygenation of the fluid returning into the pumping chamber  325  from the canister  390 . 
     Although lid  320  and the membrane frame  344  are illustrated (e.g., in  FIG. 16A ) and described as being configured to obliquely compress the first gasket  342  therebetween, in some embodiments, an apparatus can include a lid and membrane frame configured to differently compress a gasket therebetween. For example, referring to  FIG. 16B , a lid  420  and a membrane frame  444  are configured to axially compress a first gasket  442 . In some embodiments, one or more additional purging structures can be formed on a bottom portion  428  of the lid  420 , such as a lumen (not shown), to prevent the trapping of gas bubbles and/or other fluid at the membrane-lid interface. 
     The coupling mechanism  450  is configured to couple the lid assembly  310  to the canister  390 . The coupling mechanism  450  can include a first clamp  312  and a second clamp  313  different than the first clamp. The first clamp  312  and the second clamp  313  can be disposed on opposing sides of the lid assembly  310 . Each of the clamps  312 ,  313  are configured to be disposed about a portion of a lower rim of the lid  320  and an upper rim of the canister  390 . The clamps  312 ,  313  are configured to be moved between a first, or open configuration in which the lid assembly  310  and the canister  390  are freely removable from each other, and a second, or closed, configuration in which the lid assembly  310  and the canister  390  are not freely removably from each other. In other words, in its second configuration, the handles  312 ,  313  of the coupling mechanism  450  are configured to lock the lid assembly  310  to the canister  390 . The clamps  312 ,  313  can be any suitable clamp, including, for example, a toggle clamp. 
     Referring to  FIG. 17 , the control system  500  includes a processor  502 , an organ chamber pressure sensor  506 , a pumping chamber pressure sensor  510 , a solenoid  514 , a display unit  518 , and a power source  520 . In some embodiments, the control system  500  includes additional components, such as, for example, components configured for wired or wireless network connectivity (not shown) for the processor  502 . 
     The control system  500  is described herein with reference to the apparatus  300 , however, the control system is suitable for use with other embodiments described herein (e.g., apparatus  10 ,  100 , and/or  700 ). The pumping chamber pressure sensor  510  is configured to detect the oxygen pressure in the pumping chamber  325 . Because the pumping chamber  325  is split into the first and second portions  327 ,  329 , respectively, by the semi-permeable membrane  340 , which is configured to undergo relatively small deflections, the oxygen pressure in the first portion  327  of the pumping chamber  325  is approximately equal to the fluid (e.g., perfusate) pressure in the second portion  329  of the pumping chamber  325 . Therefore, measuring the fluid pressure in either the first portion  327  or the second portion  329  of the pumping chamber  325  approximates the fluid pressure in the other of the first portion or the second portion of the pumping chamber  325 . 
     The organ chamber pressure sensor  506  is configured to detect the fluid pressure in the canister  390 . Each pressure sensor  506 ,  510  can be configured to detect the fluid pressure in real-time and permit instantaneous determination of small pressure changes. Examples of pressure sensors that can be used include, but are not limited to, analog pressure sensors available from Freescale (e.g., MPXV5010GP-NDD) and from Honeywell (e.g., HSC-MRNN001PGAA5). At least one of the pressure sensors  506 ,  510  can be configured to measure pressures between 0-1.0 psig with a 5 volt power supply. In some embodiments, at least one of the pressure sensors  506 ,  510  can be configured to detect pressure variations as small as 0.06 mmHg. The sensors  506 ,  510  can be placed in the chamber  324  at the same height to avoid pressure head measurement errors. 
     The solenoid  514  is disposed in the chamber  324 . The solenoid  514  is configured to control the opening and/or closing of one or more valves (not shown in  FIG. 17 ) for gas flow to and from the pumping chamber  325 . The solenoid  514  is operably connected to the power source  520  for optimal power management. 
     The display unit  518  is configured to display one or more parameters. Display parameters of the display unit  518  can include, for example, elapsed time of operation, operating temperature, organ flow rate, and/or organ resistance, which are key metrics for determining the overall health of the organ being transported by the apparatus  300 . Calculation of the organ flow rate and the organ resistance parameters are described in more detail below. The processor  502  is configured to receive information associated with the oxygen pressure in the pumping chamber  325  and in the canister  390  via the sensors  510 ,  506 , respectively. The processor  502  is configured to control operation of the solenoid  514 , to control the supply of power from the power source  520  to the solenoid  514 , and to display operating parameters on the display unit  518 . 
     The processor  502  is configured to calculate the organ flow rate and the organ resistance, as illustrated in  FIG. 18 . Organ flow rate is a measure of the organ&#39;s compliance to fluid flow therethrough (e.g. blood flow), and can be a significant indicator of organ viability. Organ resistance, on the other hand, is a measure of the organ&#39;s resistance to fluid flow therethrough, and is theoretically a function of the pressure drop across the organ. In some embodiments, the processor  502  is configured to evaluate such parameters (i.e., organ flow rate and/or organ resistance) continually and in real time. In some embodiments, the processor  502  is configured to periodically evaluate such parameters at predetermined time intervals. 
     Referring to  FIG. 18 , a flow chart of a method  600  for evaluating a parameter, such as organ flow rate and/or organ resistance, according to an embodiment is illustrated. The method  600  is described herein with respect to apparatus  300  and control unit  500 , however, can be performed by another apparatus described herein. At  602 , the number of beats/minute (bpm) is determined. As used herein, “beat” refers to a pressure increase caused by a first volume of fluid (e.g., oxygen from pneumatic system  200 ) being introduced (e.g., intermittently) into the pumping chamber  325 , which in turn causes a pressure wave that in turn causes a second volume of fluid (e.g., oxygenated perfusate) to be pumped or otherwise transferred from the pumping chamber  325  towards the canister  390  and/or an organ contained in the canister  390 . Determination of the bpm can be based on the frequency with which the solenoid  514  (under the control of processor  502 ) permits gas exchange via the control orifice. 
     Because the canister  390  is compliant (i.e., it has a flexible floor  393 ), the canister flexes with each “beat” and then returns to its starting position. As the canister  390  floor flexes, the canister accepts the second volume of fluid from the pumping chamber  325 , via flow through the organ (e.g., through vasculature of the organ, which can be coupled to an organ adapter in fluid communication with the pumping chamber  325 ). When the floor  393  of the canister  390  relaxes, the second volume of fluid returns to the pumping chamber  325  through the valves  338 A,  338 B. The canister  390  floor  393  flexing and relaxing process can be repeated for each beat. 
     As the second volume of fluid enters the canister  390 , pressure in the canister  390  (or more specifically, an organ chamber  392 , illustrated in  FIG. 14 , defined by the canister  390  and the lid assembly  310 ) rises and causes the canister  390  floor  393  to flex. This rise is pressure is measured by the organ chamber pressure sensor  506 . At  604 A, the rise in organ chamber pressure is calculated as a difference between the highest organ chamber pressure and lowest organ chamber pressure for each beat. In some embodiments, the organ chamber pressure is sampled at a rate significantly higher than the number of beats/minute (e.g. at 1 kHz for 60 bpm), such that multiple organ chamber pressure measurements are taken prior to performing the calculation of organ chamber pressure rise at  604 A. For example, in some embodiments, the organ chamber pressure is sampled at 610 Hz (i.e., 610 samples per second). 
     As described above, the floor  393  of the canister  390  is a thin plate configured to undergo small deformations, such that its deflection due to pressure/volume changes is linear and is a measure of the volumetric compliance (defined as volume displaced per unit pressure change) of the canister. In one embodiment, volumetric compliance of the canister  390  is known and preprogrammed into the processor  502 . In another embodiment, the processor  502  is configured to calculate volumetric compliance in real-time. At  606 , the volumetric change is calculated by multiplying the calculated rise in canister pressure with the known/estimated volumetric compliance of the canister  390 . 
     At  608 , the organ flow rate is calculated by dividing the calculated change in volume by the beat period (i.e., a time interval between consecutive beats, measured in units of time). An average of several consecutive values of organ flow rate or other calculated values can be displayed to minimize beat variations. For example, a moving average value can be displayed. 
     At  610 , the organ resistance is calculated. Organ resistance is expressed in units of pressure over organ flow rate, for example, mmHg/(mL/min). Organ flow rate is calculated as described above. The organ resistance is calculated by the processor  502  based upon the calculated canister pressure rise, calculated at  604 A, and a measured chamber pressure, at  604 B. The calculated canister pressure rise and measured chamber pressure can be based on substantially simultaneous and relatively high rate sampling of the pressure on each side of the organ (i.e. at both the organ chamber sensor  506  and the pumping chamber sensor  510 ). In some embodiments, the sampling rate is significantly higher than the number of beats per minute. For example, the pressures at the sensors  506 ,  510  can be sampled 1,000 times per second (1 kHz). At the start of the beat, the pressure on each side of the organ is approximately the same. Thus, the pressure drop across the organ is zero. As the oxygen pressure in the pumping chamber  325  rises, the pressure in the canister  390  rises at a slower rate. As the fluid subsequently returns to the pumping chamber  325  from the canister  390 , the two pressures drop to equilibrium. Thus, the pressure across the organ varies throughout each beat. For improved accuracy, pressure can be measured at a high rate and accumulated for each beat period. For example, the total pressure impulse for each beat can be integrated step-wise. In this manner, organ resistance is calculated at 610 Hz. Further averaging or other statistical analysis can be performed by the processor  502  to reduce error. Due to the low operating pressures of the apparatus, an organ&#39;s resistance to flow can be approximated by laminar flow, such that instantaneous flow rate is proportional to the instantaneous pressure drop. Calculations can be performed in real-time using direct pressure measurements. 
     An apparatus  700  according to an embodiment is illustrated in  FIGS. 19-29 . The apparatus  700  is configured to oxygenate a perfusate and to perfuse a bodily tissue for extracorporeal preservation of the bodily tissue. Unless stated otherwise, the apparatus  700  can be similar in many respects (e.g., form and/or function) to the apparatus described herein (e.g., apparatus  10 ,  100 ,  300 ), and can include components similar in many respects (e.g., form and/or function) to components of the apparatus described herein. The apparatus  700  includes a lid assembly  710 , a canister  790 , and a coupling mechanism  850 . 
     The lid assembly  710  defines a chamber  724  (see, e.g.,  FIG. 25 ) configured to receive components of a pneumatic system (not shown), such as the pneumatic system  200  described above, and/or a control system (not shown), such as the control system  500  described above. In some embodiments, the chamber  724  is formed by a lid  720  of the lid assembly  710 . In some embodiments, the chamber  724  can be formed between a lower portion  723  of the lid  720  and an upper portion  722  of the lid. 
     Referring to  FIGS. 20 and 21A , the lid assembly  710  defines a pumping chamber  725  configured to receive oxygen (e.g., from the pneumatic system), to facilitate diffusion of the oxygen into a perfusate (not shown) and to facilitate movement of the oxygenated perfusate into a bodily tissue (not shown). A top of the pumping chamber  725  is formed by a lower portion  728  of a membrane frame  744  of the lid assembly  710 . A bottom of the pumping chamber  725  is formed by an upper surface  734  of a base  732  of the lid assembly  710 . 
     As illustrated in  FIGS. 20-24 , the lid assembly  710  includes a first gasket  742 , a membrane  740 , and the membrane frame  744 . The membrane  740  is disposed within the pumping chamber  725  and divides the pumping chamber  725  into a first portion  727  and a second portion  729  different than the first portion. The first gasket  742  is disposed between the membrane  740  and the membrane frame  744  such that the first gasket is engaged with an upper surface  741  of the membrane  740  and a lower, perimeter portion of the membrane frame  744  (see, e.g.,  FIG. 24 ). The first gasket  742  is configured to seal a perimeter of the first portion  727  of the pumping chamber  725  formed between the lower portion  728  of the membrane frame  744  and the upper surface  741  of the membrane  740 . In other words, the first gasket  742  is configured to substantially prevent lateral escape of oxygen from the first portion  727  of the pumping chamber  725  to a different portion of the pumping chamber. In the embodiment illustrated in  FIG. 24 , the first gasket  742  has a perimeter substantially similar in shape to a perimeter defined by the membrane  740  (e.g., when the membrane is disposed on the membrane frame  744 ). In other embodiments, however, a first gasket can have another suitable shape for sealing a first portion of a pumping chamber configured to receive oxygen from a pneumatic system. 
     The first gasket  742  can be constructed of any suitable material. In some embodiments, for example, the first gasket  742  is constructed of silicone, an elastomer, or the like. The first gasket  742  can have any suitable thickness. For example, in some embodiments, the first gasket  742  has a thickness within a range of about 0.1 inches to about 0.15 inches. More specifically, in some embodiments, the first gasket  742  has a thickness of about 0.139 inches. The first gasket  742  can have any suitable level of compression configured to maintain the seal about the first portion  727  of the pumping chamber  725  when the components of the lid assembly  710  are assembled. For example, in some embodiments, the first gasket  742  is configured to be compressed by about 20 percent. 
     The membrane  740  is configured to permit diffusion of gas (e.g., oxygen) from the first portion  727  of the pumping chamber  725  through the membrane to the second portion  729  of the pumping chamber, and vice versa. The membrane  740  is configured to substantially prevent a liquid (e.g., the perfusate) from passing through the membrane. In this manner, the membrane  740  can be characterized as being semi-permeable. The membrane frame  744  is configured to support the membrane  740  (e.g., during the oxygenation of the perfusate and perfusion of the bodily tissue). The membrane frame  744  can have a substantially round or circular shaped perimeter. The membrane frame  744  includes a first port  749 A and a second port  749 B. The first port  749 A is configured to convey fluid between the first portion  727  of the pumping chamber and the pneumatic system (not shown). For example, the first port  749 A can be configured to convey oxygen from the pneumatic system to the first portion  727  of the pumping chamber  725 . The second port  749 B is configured to permit a pressure sensor line (not shown) to be disposed therethrough. The pressure sensor line can be, for example, polyurethane tubing. The ports  749 A,  749 B can be disposed at any suitable location on the membrane frame  744 , including, for example, towards a center of the membrane frame  744  as shown in  FIG. 21  A. Although the ports  749 A,  749 B are shown in close proximity in  FIG. 21  A, in other embodiments, the ports  749 A,  749 B can be differently spaced (e.g., closer together or further apart). 
     Referring to  FIGS. 22-24 , at least a portion of the membrane  740  is disposed (e.g., wrapped) about at least a portion of the membrane frame  744 . In some embodiments, the membrane  740  is stretched when it is disposed on the membrane frame  744 . The membrane  740  is disposed about a lower edge or rim of the membrane frame  744  and over at least a portion of an outer perimeter of the membrane frame  744  such that the membrane  740  is engaged with a series of protrusions (e.g., protrusion  745 ) configured to help retain the membrane with respect to the membrane frame. The membrane frame  744  is configured to be received in a recess  747  defined by the lid  720  (see, e.g.,  FIG. 21  A). As such, the membrane  740  is engaged between the membrane frame  744  and the lid  720 , which facilitates retention of the membrane with respect to the membrane frame. In some embodiments, the first gasket  742  also helps to maintain the membrane  740  with respect to the membrane frame  744  because the first gasket is compressed against the membrane between the membrane frame  744  and the lid  720 . 
     As illustrated in  FIG. 20 , the membrane  740  is disposed within the pumping chamber  725  at an angle with respect to a horizontal axis A 4 . In this manner, the membrane  740  is configured to facilitate movement of fluid towards a purge port  706  in fluid communication with the pumping chamber  725 , as described in more detail herein. The angle of incline of the membrane  740  can be of any suitable value to allow fluid (e.g., gas bubbles, excess liquid) to flow towards the purge port  706  and exit the pumping chamber  725 . In some embodiments, the angle of incline is approximately in the range of 1°-10°, in the range of 2°-6°, in the range of 2.5°-5°, in the range of 4°-5° or any angle of incline in the range of 1°-10° (e.g., approximately 1°, 2°, 3°, 4°, 5°, 6°, 7°, 8°, 9°, 10°). More specifically, in some embodiments, the angle of incline is approximately 5°. 
     The membrane  740  can be of any suitable size and/or thickness, including, for example, a size and/or thickness described with respect to another membrane herein (e.g., membrane  40 ,  140 ,  340 ). The membrane  740  can be constructed of any suitable material. For example, in some embodiments, the membrane is constructed of silicone, plastic, or another suitable material. In some embodiments, the membrane is flexible. As illustrated in  FIG. 23 , the membrane  740  can be substantially seamless. In this manner, the membrane  740  is configured to be more resistant to being torn or otherwise damaged in the presence of a flexural stress caused by a change in pressure in the pumping chamber due to the inflow and/or release of oxygen or another gas. 
     Referring to  FIG. 20 , the lid  720  includes the purge port  706  disposed at the highest portion of the pumping chamber  725  (e.g., at the highest portion or point of the second portion  729  of the pumping chamber  725 ). The purge port  706  is configured to permit movement of fluid from the pumping chamber  725  to an area external to the apparatus  700 . The purge port  706  can be similar in many respects to a purge port described herein (e.g., port  78 , purge ports  106 ,  306 ). 
     As noted above, the upper surface  734  of the base  732  forms the bottom portion of the pumping chamber  725 . Referring to  FIGS. 21A and 26 , a lower surface  736  of the base  732  forms an upper portion of an organ chamber  792 . The organ chamber  792  is formed by the canister  790  and the lower surface  736  of the base  732  when the lid assembly  710  is coupled to the canister  790 . A well  758  is extended from the lower surface  736  of the base  732  (e.g., into the organ chamber  792 ). The well  758  is configured to contain a sensor (not shown) configured to detect the temperature within the organ chamber  792 . The well  758  can be configured to substantially fluidically isolate the sensor from the organ chamber  792 , thereby preventing liquid (e.g., perfusate) from the organ chamber from engaging the sensor directly. In some embodiments, the sensor contained in the well  758  can be in electrical communication with a control unit (such as control unit  500 , described in detail above). 
     The lower surface  736  of the base  732  defines a first concavely inclined portion  751  and a second concavely inclined portion  753  different from the first portion  751 . Said another way, the portions of the base  732  forming each of the first portion  751  and the second portion  753  of the lower surface  736  lie along a plane having an axis different than the horizontal axis A 4 . For example, each of the first portion  751  and the second portion  753  of the base can be in the shape of an inverted cone. The portions of the lower surface  736  of the base forming the first and second portions  751 ,  753  can each be inclined with respect to the horizontal axis A 4  at an angle equal to or greater than about 5°. Each of the first portion  751  and the second portion  753  of the lower surface  736  of the base  732  define the highest points or portions (i.e., the peak(s)) of the organ chamber  792  when the apparatus  700  is in an upright position (as shown in  FIG. 20 ). In this manner, the base  732  is configured to facilitate movement of fluid towards the highest portion(s) of the organ chamber  792  as the organ chamber  792  is filled with fluid approaching a maximum volume or maximum fluid capacity of the organ chamber. 
     As illustrated in  FIG. 21A , valves  738 A,  738 B, respectively, are disposed at approximately the peak of each of the first portion  751  and the second portion  753 , respectively, of the base  732 . Because valves  738 A,  738 B are substantially similar in form and function, only valve  738 A is described in detail herein. The valve  738  is moveable between an open configuration and a closed configuration. In its open configuration, the valve  738 A is configured to permit movement of fluid from the organ chamber  792  to the pumping chamber  725  via the valve. Specifically, the valve  738 A is configured to permit fluid to move from the organ chamber  792  into the second portion  729  of the pumping chamber  725 . In this manner, an excess amount of fluid within the organ chamber  792  can overflow through the valve  738 A and into the pumping chamber  725 . In its closed configuration, the valve  738 A is configured to substantially prevent movement of fluid from the pumping chamber  725  to the organ chamber  792 , or vice versa, via the valve. The valve  738 A is moved from its closed configuration to its open configuration when a pressure in the organ chamber  792  is greater than a pressure in the pumping chamber  725 . In some embodiments, the valve  738 A is moved from its open position to its closed position when a pressure in the pumping chamber  725  is greater than a pressure in the organ chamber  792 . In some embodiments, the valve  738 A is biased towards its closed configuration. 
     The valve  738 A can be a ball check valve. The valve  738 A is moveable between a closed configuration in which a ball of the valve  738 A is disposed on a seat of the valve and an open configuration in which the ball is lifted off of the seat of the valve. The ball of the valve  738 A is configured to rise off of the seat of the valve when the pressure in the organ chamber  792  is greater than the pressure in the pumping chamber  725 . In some embodiments, the membrane  740  is positioned in proximity over the valve  738 A to prevent the ball from rising too high above the seat such that the ball could be laterally displaced with respect to the seat. The valves  738 A,  738 B can be similar in many respects to a valve described herein (e.g., valve  138 ,  338 A,  338 B). For example, the valves  738 A,  738 B can include a jet  760 A,  760 B, respectively, similar in form and/or function as the jets  360 A,  360 B described in detail above with respect to apparatus  300 . As such, the valves  738 A,  738 B are not described in more detail herein. 
     The base  732  is coupled to the lid  720 . In some embodiments, the base  732  and the lower portion  723  of the lid  720  are coupled together, e.g., about a perimeter of the pumping chamber  725  (see, e.g.,  FIGS. 21A and 25 ). The base  732  and the lid  720  can be coupled using any suitable mechanism for coupling including, but not limited to, a plurality of screws, an adhesive, a glue, a weld, another suitable coupling mechanism, or any combination of the foregoing. A gasket  748  is disposed between the base  732  and the lid  720  (see e.g.,  FIGS. 20 and 21  A). The gasket  748  is configured to seal an engagement of the base  732  and the lid  720  to substantially prevent fluid in the pumping chamber  725  from leaking therebetween. In some embodiments, the gasket  748  is an O-ring. The gasket  748  can be similar in many respects to a gasket described herein (e.g., gasket  148 ,  742 ). 
     The base  732  defines a lumen  735  configured to be in fluid communication with a lumen  774  of an organ adapter  770 , described in more detail below. The base  732  is configured to permit oxygenated perfusate to move from the pumping chamber  725  through its lumen  735  into the lumen  774  of the organ adapter  770  towards the organ chamber  792 . In this manner, the lumen  735  of the base  732  is configured to help fluidically couple the pumping chamber  725  and the organ chamber  792 . 
     The organ adapter  770  is configured to substantially retain the bodily tissue with respect to the apparatus  700 . The organ adapter  770  can be similar in many respects to an adapter described herein (e.g., adapter  26 , organ adapter  170 ). Referring to  FIG. 2  IB, the organ adapter  770  includes a handle portion  778 , an upper portion  772 , and a lower portion  780 , and defines the lumen  774  extended therethrough. The upper portion  772  of the organ adapter  770  is extended from a first side of the handle portion  778 . The lower portion  780  of the organ adapter  770  is extended from a second side of the handle portion  778  different than the first side of the handle portion. In some embodiments, the lower portion  780  is configured to be at least partially inserted into the bodily tissue. More specifically, at least a portion of the lower portion  780  is configured to be inserted into a vessel (e.g., an artery, a vein, or the like) of the bodily tissue. For example, the protrusion  780  can be configured to be at least partially received in a bodily vessel having a diameter within the range of about 3 millimeters to about 8 millimeters. In other embodiments, the lower portion  780  is configured to be coupled to the bodily tissue via an intervening structure (not shown in  FIG. 2  IB) to fluidically couple the lumen  774  of the organ adapter  770  to a vessel of the bodily tissue. The intervening structure can be, for example, silastic or other tubing. In this manner, the lower portion  780  is configured to deliver the fluid (e.g., the oxygenated perfusate) from the pumping chamber  725  to the vessel of the bodily tissue via the lumen  774  defined by the organ adapter  770 . The vessel of the bodily tissue can be sutured to the lower portion  780  of the adapter  770  and/or to the intervening structure (e.g., tubing). 
     The upper portion  772  of the organ adapter  770  is configured to couple the organ adapter to the base  732  of the lid assembly  710 . The upper portion  772  of the organ adapter is configured to be received by the lumen  735  defined by the base. The upper portion  772  includes a first projection  776 A and a second projection  776 B spaced apart from the first projection. The projections  776 A,  776 B of the organ adapter  770  are configured to be received by the lumen  735  of the base  732  in opposing spaces between a first protrusion  754  and a second protrusion  756  (shown in  FIG. 21B ) disposed within the lumen of the base. Once the upper portion  772  is received in the lumen  735  of the base  732 , the organ adapter  770  can be rotated approximately ninety degrees such that its first projection  776 A and its second projection sit on a shoulder  755 ,  757 , respectively, defined by the protrusions  754 ,  756 , respectively, of the base. The organ adapter  770  can be rotated in either a clockwise or a counterclockwise direction to align its projections  776 A,  776 B with the shoulders  755 ,  757  of the protrusions  754 ,  756  of the base  732 . Similarly, the organ adapter  770  can be rotated in either the clockwise or the counterclockwise direction to unalign its projections  776 A,  776 B with the shoulders  755 ,  757  of the protrusions  754 ,  756  of the base  732 , such as for decoupling of the adapter from the base. Said another way, the organ adapter  770  can be configured to be coupled to the base  732  with a bayonet joint. The handle portion  778  is configured to facilitate coupling and decoupling of the organ adapter  770  and the base  732 . For example, the handle portion  778  is configured to be grasped by a hand of an operator of the apparatus  700 . The handle portion  778  can be substantially disc-shaped, and includes a series of recesses configured to facilitate grasping the handle portion with the operator&#39;s hand and/or fingers. 
     In some embodiments, the upper portion  772  of the organ adapter  770  includes a set of protrusions spaced apart (e.g., vertically offset) from projections  776 A,  776 B. For example, as shown in  FIG. 21B , protrusions  111  A,  777 B are disposed at opposing portions of an outer perimeter of the upper portion  772  of the organ adapter  770 . The protrusions  111  A,  777 B can each be configured to be received in a recess  779 A,  779 B, respectively, defined by the base  732 . In some embodiments, the protrusions  111  A,  777 B are configured to retain a gasket  788  disposed about the upper portion  772  of the organ adapter  770  between the handle portion  778  of the adapter and the base  732 . The gasket  788  is configured to substantially prevent a fluid from flowing between the pumping chamber  725  and the organ chamber  792  within a channel formed between an outer surface of the upper portion  772  of the organ adapter  770  and an inner surface of the lumen  735  of the base  732 . In some embodiments, the gasket  788  is compressed between the organ adapter  770  and the base  732  when the organ adapter is coupled to the base. The gasket  788  can be similar in many respects to a gasket described herein (e.g., gasket  188 ,  742 ). 
     In some embodiments, at least a portion of the lid assembly  710  is configured to minimize flexure of the portion of the lid assembly, such as may occur in the presence of a positive pressure (or pulse wave) caused by introduction of oxygen into the pumping chamber  725  and/or of oxygenated perfusate into the organ chamber  792 . For example, as illustrated in  FIG. 21  A, an upper portion  722  of the lid  720  includes a plurality of ribs  726  configured to minimize flexure of the lid  720  in response to externally applied loads, for example, if an operator presses down on the lid  720 . In other words, the plurality of ribs  726  structurally reinforces the lid  720  to help prevent the lid  720  from flexing. In another example, as illustrated in  FIG. 22 , an upper portion of the membrane frame  744  can include ribs  746  configured to reinforce the top of the pumping chamber  725  to help prevent flexure of the top of the pumping chamber  725  during pumping of oxygen through the lid assembly  710 . In yet another example, the base  732  is configured to substantially minimize flexure of the base, such as may occur in the presence of a positive pressure caused by the introduction of oxygen into the pumping chamber  725  and/or of oxygenated perfusate into the organ chamber  792 . As illustrated in  FIG. 25 , the base  732  includes a plurality of ribs  731  extended from its upper surface. The plurality of ribs  731  is configured to reinforce the base  732 , which helps to minimize flexure of the base. The plurality of ribs (e.g., ribs  726 ,  746 , and/or  731 ) can be in any suitable configuration, including, for example, a circular configuration, a hub-and-spoke combination, a parallel configuration, or the like, or any suitable combination thereof. For example, as shown in  FIGS. 21  A,  22  and  25 , the plurality of ribs (e.g., ribs  726 ,  746 ,  731 ) are a combination of circular and hub-and-spoke configurations. 
     Referring to  FIG. 20 , the lid assembly  710  includes a fill port  708  configured to permit introduction of a fluid (e.g., the perfusate) into the organ chamber  792  (e.g., when the lid assembly  710  is coupled to the canister  790 ). The fill port  708  can be similar in many respects to a port described herein (e.g., port  74 , fill port  108 ). In the embodiment illustrated in  FIG. 20 , the fill port  708  includes a fitting  707  coupled to the lid  720  and defines a lumen  709  in fluidic communication with a lumen  737  defined by the base  732 , which lumen  737  is in fluidic communication with the organ chamber  792 . The fitting  707  can be any suitable fitting, including, but not limited to, a luer lock fitting. The fill port  708  can include a cap  705  removably coupled to the port. The cap  705  can help prevent inadvertent movement of fluid, contaminants, or the like through the fill port  708 . 
     The lid assembly  710  is configured to be coupled to the canister  790 . The lid assembly  710  includes handles  712 ,  713 . The handles  712 ,  713  are each configured to facilitate coupling the lid assembly  710  to the canister  790 , as described in more detail herein. Said another way, the handles  712 ,  713  are configured to move between a closed configuration in which the handles prevent the lid assembly  710  being uncoupled or otherwise removed from the canister  790 , and an open configuration in which the handles do not prevent the lid assembly  710  from being uncoupled or otherwise removed from the canister. The handles  712 ,  713  are moveably coupled to the lid  720 . Each handle  712 ,  713  can be pivotally coupled to opposing sides of the coupling mechanism  850  (described in more detail herein) disposed about the lid  720 . For example, each handle  712 ,  713  can be coupled to the coupling mechanism  850  via an axle (not shown). Each handle includes a series of gear teeth (not shown) configured to engage a series of gear teeth  719  (see, e.g.,  FIG. 25 ) disposed on opposing sides of the lid  720  as the handles  712 ,  713  each pivot with respect to the coupling mechanism  850 , thus causing rotation of the coupling mechanism  850 , as described in more detail herein. In some embodiments, the handles  712 ,  713  include webbing between each tooth of the series of gear teeth, which is configured to provide additional strength to the respective handle. In their closed configuration, the handles  712 ,  713  are substantially flush to the coupling mechanism  850 . In some embodiment, at least one handle  712  or  713  includes an indicia  713 B indicative of proper usage or movement of the handle. For example, as shown in  FIG. 28C , the handle  713  includes indicia (i.e., an arrow) indicative of a direction in which the handle portion can be moved. As also shown in  FIG. 28C , in some embodiments, the handles  712 ,  713  include a ribbed portion configured to facilitate a grip by a hand of an operator of the apparatus  700 . 
     The canister  790  can be similar in many respects to a canister described herein (e.g., canister  32 ,  190 ,  390 ). As shown in  FIG. 29 , the canister  790  includes a wall  791 , a floor (also referred to herein as “bottom”)  793 , and a compartment  794  defined on its sides by the wall and on its bottom by the floor. The compartment  794  can form a substantial portion of the organ chamber  792 . 
     As shown in  FIGS. 27A-27C , at least a portion of the canister  790  is configured to be received in the lid assembly  710  (e.g., the base  732 ). The canister  790  includes one or more protruding segments  797  disposed adjacent, or at least proximate, to an upper rim  795  of the canister. Each segment  797  is configured to protrude from an outer surface of the canister  790  wall  791 . The segments  797  are configured to help properly align the canister  790  with the lid assembly  710 , and to help couple the canister  790  to the lid assembly  710 . Each segment  797  is configured to be received between a pair of corresponding segments  721  of the lid  720 , as shown in  FIG. 27B . A length Li of the segment  797  of the canister  790  is substantially equivalent to a length L 2  (see, e.g.,  FIG. 27A ) of an opening  860  between the corresponding segments  721  of the lid  720 . In this manner, when the segment  797  of the canister  790  is received in the corresponding opening of the lid  720 , relative rotation of the canister  790  and lid  720  with respect to each other is prevented. The canister  790  can include any suitable number of segments  797  configured to correspond to openings between protruding segments  721  of the lid  720 . For example, in the embodiment illustrated in  FIG. 27B  (and also shown in  FIG. 29 ), the canister  790  includes ten segments  797 , each of which is substantially identical in form and function, spaced apart about the outer perimeter of the canister  790  adjacent the upper rim  795 . In other embodiments, however, a canister can include less than or more than ten segments. 
     A gasket  752  is disposed between the base  732  and the upper rim  795  of the wall  791  of the canister  790 . The gasket  752  is configured to seal the opening between the base  732  and the wall  791  of the canister  790  to substantially prevent flow of fluid (e.g., the perfusate) therethrough. The segments  797  of the canister  790  are configured to engage and compress the gasket  752  when the canister  790  is coupled to the lid  720 . The gasket  752  can be any suitable gasket, including, for example, an O-ring. 
     The floor  793  of the canister  790  is configured to flex when a first pressure within the organ chamber  792  changes to a second pressure within the organ chamber, the second pressure different than the first pressure. More specifically, in some embodiments, the floor  793  of the canister  790  is configured to flex outwardly when a first pressure within the organ chamber  792  is increased to a second pressure greater than the first pressure. For example, the floor  793  of the canister  790  can be configured to flex in the presence of a positive pressure (or a pulse wave) generated by the pumping of the oxygenated perfusate from the pumping chamber  725  into the organ chamber  792 , as described in detail above with respect to apparatus  100 . In some embodiments, the floor  793  of the canister  790  is constructed of a flexible membrane. The floor  793  of the canister  790  can have any suitable thickness T, including, for example, a thickness described above with respect to floor  193  of canister  190 . In some embodiments, the floor  793  has a thickness T equal to or greater than 0.100 inches. 
     The canister  790  can be configured to enable an operator of the apparatus  700  to view the bodily tissue when the bodily tissue is sealed within the organ chamber  792 . In some embodiments, for example, at least a portion of the canister  790  (e.g., the wall  791 ) is constructed of a clear or transparent material. In another example, in some embodiments, at least a portion of the canister  790  (e.g., the wall  791 ) is constructed of a translucent material. In yet another example, in some embodiments, a canister includes a window through which at least a portion of the organ chamber can be viewed. 
     As noted above, the coupling mechanism  850  is configured to couple the canister  790  to the lid assembly  710 . In the embodiment illustrated in  FIGS. 19-29 , the coupling mechanism  850  is a retainer ring. The retainer ring  850  is configured to be disposed about a lower rim of the lid  720  and the upper rim  795  of the canister  790 . An upper portion of the retainer ring  850  can be wrapped over a portion of the lid assembly  710  (e.g., an upper perimeter edge of the base  732 ), as shown in  FIG. 20 . In this manner, compression of gasket  752  is improved when the lid assembly  710  is coupled to the canister  790  by the retainer ring  850 , as described in more detail below. The retainer ring  850  can be of any suitable size for being disposed about the lid  720  and the canister  790 . For example, in some embodiments, the retainer ring  850  can be 22.35 cm (or about 8.80 inches) in diameter. 
     A plurality of segments  856  are extended from an inner surface of the retainer ring  850  at spaced apart locations about an inner perimeter of the retainer ring. Each segment of the plurality of segments  856  is configured to be aligned with a segment  721  of the lid  720  when the retainer ring  850  is coupled to the lid  720 , and the handles  712 ,  713  of the lid assembly  710  are in the open configuration. In some embodiments, as shown in  FIG. 27A , each segment of the plurality of segments  856  of the retainer ring  850  is configured to laterally abut an inner portion of an L-shaped portion of the corresponding segment  721  of the lid  720  when the retainer ring  850  is disposed on the lid assembly  710  and the handles  712 ,  713  of the lid assembly  710  are in the open configuration, which facilitates accurate alignment of the lid  720  and the retainer ring  850 . Accordingly, when the lid  720  and the retainer ring  850  are aligned and the handles  712 ,  713  of the lid assembly  710  are in the open configuration, the aligned segments  721  of the lid  720  and segments  856  of the retainer ring  850  collectively define the openings  860  configured to receive the segments  797  of the canister  790 , described above. 
     To couple, or otherwise secure, the canister  790  to the lid assembly  710  using the retainer ring  850 , the handles  712 ,  713  of the lid assembly are moved from their open configuration (see, e.g.,  FIGS. 27B and 28A ) through an intermediate configuration (see, e.g.,  FIG. 28B ) to their closed configuration (see, e.g.,  FIGS. 27C and 28C ). As the handles  712 ,  713  are moved from their open configuration towards their closed configuration, the retainer ring  850  is rotated in a first direction (as shown by arrow Ai in  FIG. 28B ) with respect to each of the canister  790  and the lid assembly  710 . Accordingly, as shown in  FIG. 27C , when the handles  712 ,  713  are in their closed configuration, the segments  856  of the retainer ring  850  are vertically aligned with the segments  797  of the canister  790 , e.g., such that each segment of the retainer ring is disposed beneath a corresponding segment  797  of the canister  790  when the apparatus  700  is in the upright position. Over-rotation of the retainer ring  850  with respect to the lid assembly  710  and the canister  790  is prevented by an outer edge of the L-shaped portion of the lid  720  segments  721 . To decouple the lid assembly  710  from the canister  790 , the handles  712 ,  713  are moved from their closed configuration to their open configuration, thus causing rotation of the retainer ring  850  relative to the lid assembly and the canister in a second direction opposite the first direction. During decoupling, over rotation of the retainer ring  850  with respect to the lid assembly  710  and the canister  790  is prevented because the segments  856  of the retainer ring will each laterally abut the inner portion of the L-shaped portion of the corresponding segment  721  of the lid  720 . 
     As noted above, the apparatus  700  is configured for controlled delivery of fluid (e.g., oxygen) from an external source (not shown) into the pumping chamber  725  of the lid assembly  710 . The external source can be, for example, an oxygen cylinder. In some embodiments, the apparatus  700  includes the pneumatic system, such as pneumatic system  200 , configured for controlled venting of fluid (e.g., carbon dioxide) from the pumping chamber  725  to an area external to the apparatus  700  (e.g., to the atmosphere). The pneumatic system  200  is moveable between a first configuration in which the pneumatic system is delivering fluid to the pumping chamber  725  and a second configuration in which the pneumatic system is venting fluid from the pumping chamber  725 . The pneumatic system  200  is described in detail above with respect to apparatus  100 . 
     In use, the bodily tissue is coupled to at least one of the organ adapter  770  or tubing configured to be coupled to the organ adapter. The organ adapter  770  can be coupled to the lid assembly  710 . Optionally, a desired amount of perfusate can be disposed within the compartment  794  of the canister  790  prior to disposing the lid assembly  710  on the canister. For example, in some embodiments, a perfusate line (not shown) is connected to the organ adapter  770  and the organ is flushed with perfusate, thereby checking for leaks and partially filling the canister  790  with perfusate. Optionally, when the canister  790  is substantially filled, the perfusate line can be disconnected. The lid assembly  710  is disposed on the canister  790  such that the bodily tissue is received in the organ chamber  792 . The lid assembly  710  is coupled to the canister  790 . Optionally, the lid assembly  710  and the canister  790  are coupled via the retainer ring  850 . Optionally, a desired amount of perfusate is delivered to the organ chamber  792  via the fill port  708 . In some embodiments, a volume of perfusate greater than a volume of the organ chamber  792  is delivered to the organ chamber such that the perfusate will move through the valves  738 A,  738 B into the second portion  729  of the pumping chamber  725 . 
     A desired control scheme of the pneumatic system  200  is selected. Oxygen is introduced into the first portion  727  of the pumping chamber  725  via the pneumatic system  200  based on the selected control scheme. The pneumatic system  200  is configured to generate a positive pressure by the introduction of oxygen into the first portion  727  of the pumping chamber  725 . The positive pressure helps to facilitate diffusion of the oxygen through the membrane  740 . The oxygen is diffused through the membrane  740  into the perfusate disposed in the second portion  729  of the pumping chamber  725 , thereby oxygenating the perfusate. Because the oxygen will expand to fill the first portion  727  of the pumping chamber  725 , substantially all of an upper surface  741  of the membrane  740  which faces the first portion of the pumping chamber can be used to diffuse the oxygen from the first portion into the second portion  729  of the pumping chamber. 
     As the bodily tissue uses the oxygen, the bodily tissue will release carbon dioxide into the perfusate. Such carbon dioxide can be diffused from the second portion  729  of the pumping chamber  725  into the first portion  727  of the pumping chamber  725 . Carbon dioxide within the first portion  727  of the pumping chamber is vented via a control line (not shown) to a valve (not shown), and from the valve through a vent line (not shown) to the atmosphere external to the apparatus  700 . 
     The positive pressure also causes the membrane  740  to flex, which transfers the positive pressure in the form of a pulse wave into the oxygenated perfusate. The pulse wave generated by the pumping chamber is configured to facilitate movement of the oxygenated perfusate from the second portion  729  of the pumping chamber  725  into the bodily tissue via the organ adapter  770  (and any intervening structure or tubing), thus perfusing the bodily tissue. In some embodiments, the pumping chamber  725  is configured to generate a pulse wave in a similar manner as pumping chamber  125 , described in detail above with respect to apparatus  100 . 
     At least a portion of the perfusate perfused through the bodily tissue is received in the organ chamber  792 . In some embodiments, the pulse wave is configured to flow through the perfusate disposed in the organ chamber  792  towards the floor  793  of the canister  790 . The floor  793  of the canister  790  is configured to flex when engaged by the pulse wave. The floor  793  of the canister  790  is configured to return the pulse wave through the perfusate towards the top of the organ chamber  792  as the floor  793  of the canister  790  is returned towards its original non-flexed position. In some embodiments, the returned pulse wave is configured to generate a sufficient pressure to open the valves  738 A,  738 B disposed at the highest positions in the organ chamber  792 . In this manner, the returned pulse wave helps to move the valves  738 A,  738 B to their respective open configurations such that excess fluid (e.g., carbon dioxide released from the bodily tissue and/or the perfusate) can move through the valves from the organ chamber  792  to the pumping chamber  725 . The foregoing perfusion cycle can be repeated as desired, including in any manner described above with respect to other apparatus described herein (e.g., apparatus  10 ,  100 ,  300 ). 
     Although the perfusion cycle has been described herein as including a substantially regular intermittent pulse of oxygen from the pneumatic system  200  to the pumping chamber  725 , in other embodiments, the pneumatic system  200  can be configured to deliver oxygen to the pumping chamber  725  at a different interval (e.g., flow interval), such as those variations described above with respect to apparatus  100  and pneumatic system  200 . 
     Although the lid assembly  710  has been illustrated and described as being configured for use with the canister  790 , in other embodiments, the lid assembly  710  can be configured for use with canisters having different configurations. For example, although the canister  790  has been illustrated and described herein as being of a certain size and/or shape, in other embodiments, a canister having any suitable dimensions can be configured for use with the lid assembly  710 . In some embodiments, for example, a first canister configured for use with the lid assembly  710  is dimensionally configured to accommodate a first type of bodily tissue, and a second canister configured for use with the lid assembly  710  is dimensionally configured to accommodate a second type of bodily tissue different than the first type of bodily tissue. For example, the canister  790  illustrated in  FIG. 29  and described herein with respect to apparatus  700  can be dimensioned to accommodate the first bodily tissue, such as a heart. The canister  790  can be, for example, a 2.7 liter cylindrical canister having a height greater than or substantially equal to a width of the floor  793 . For example, as shown in  FIG. 29 , the compartment  794  of the canister  790  can have a height Hi of about 15 cm (or about 5.91 inches) and a diameter Di of about 15 cm (note that diameter Di of the compartment  794  can be different from a diameter D 3  of the top rim  795  of the canister  790 , which can be about 20 cm (or about 7.87 inches)). Accordingly, when the canister  790  is coupled to the lid assembly  710 , the apparatus  700  can have an overall diameter of about 24 cm (or about 9.44 inches) and an overall height of about 22.3 cm (or about 8.77 inches). 
     In another embodiment, as illustrated in  FIG. 30 , a differently dimensioned canister  990  can be used with the lid assembly  710 . The canister  990  can be dimensioned to accommodate the second bodily tissue, such as a kidney. The canister  990  can be, for example, a 3.0 liter cylindrical canister having a wall  991  height less than a width of a floor  993  of the canister. For example, as shown in  FIG. 30 , the compartment  994  of the canister  990  can have a height H 2  less than the height Hi of canister  790  and a diameter D 2  greater than or equal to the diameter Di of canister  790 . The height H 2  and diameter D 2  of the compartment  994  can be such that the lid assembly  710  coupled to the canister  990  via the retainer ring  850  collectively have an overall height of about 16.5 cm (or about 6.48 inches) and a diameter of about 24 cm (or about 9.44 inches). It should be noted that although specific dimensions are described herein, in other embodiments, such dimensions can be different and still be within the scope of the invention. The thickness of the floor  993  of the canister  990  can be selected based on the height and width dimensions of the canister  990  to ensure that the floor  993  is configured to properly flex in the presence of the pulse wave, as described above, and may be the same as or different than the thickness of the floor  793  of canister  790 . The canister  990  includes a plurality of segments  997  protruding from an outer surface of the wall adjacent an upper rim  995  of the canister  990 . The plurality of segments  997  are configured to facilitate coupling the canister  990  to the lid assembly  710  and the retainer ring  850 , as described above with respect to the canister  790 . 
     Referring to  FIG. 31 , in some embodiments, an apparatus includes a basket  870  configured to be disposed in a compartment  994  of the canister  990 . The basket  870  is configured to support the bodily tissue (e.g., kidney K) within the compartment  994 . In some embodiments, for example, the basket  870  includes a bottom portion  872  on which the bodily tissue can be disposed. In some embodiments, the bottom portion  872  of the basket  870  is smooth. The bottom portion  872  can be slightly curved to accommodate curvature of the bodily tissue. In some embodiments, netting (not shown) can be used to retain the bodily tissue with respect to the basket  870  (e.g., when the bodily tissue is disposed on the bottom portion  872  of the basket  870 ). Arms  874 A,  874 B are disposed on a first side of the bottom portion  872  of the basket  870  opposite arms  876 A,  876 B disposed on a second side of the bottom portion of the basket. Each pair of arms  874 A,  874 B and  876 A,  876 B is extended vertically and terminates in a handle portion  875 ,  877 , respectively, that couples the upper end portions of the arms. 
     In some embodiments, as shown in  FIG. 31 , a shape of the outer perimeter of the bottom portion  872  of the basket  870  can substantially correspond to a shape of a perimeter of the canister  990 , such that outer edges of lower end portions of the arms  874 A,  874 B,  876 A,  876 B each abut an inner surface of the wall  991  of the canister. In this manner, lateral movement of the basket  871 , and thus of the bodily tissue supported thereon, is prevented, or at least restricted. The handle portions  875 ,  877  can be configured to engage the lower surface  736  of the base  732  of the lid assembly  710  when the basket  870  is received in the canister&#39;s  990  compartment  994  and the canister is coupled to the lid assembly  710 . In this manner, vertical movement of the basket  870  with respect to the canister  990  is prevented. 
     While various embodiments have been described above, it should be understood that they have been presented by way of example only, and not limitation. Where methods described above indicate certain events occurring in certain order, the ordering of certain events may be modified. For example, selecting the control scheme of the pneumatic system  200  can occur before the coupling the bodily tissue to the organ adapter  170 ,  770 . Additionally, certain of the events may be performed concurrently in a parallel process when possible, as well as performed sequentially as described above. Furthermore, although methods are described above as including certain events, any events disclosed with respect to one method may be performed in a different method according to the invention. Thus, the breadth and scope should not be limited by any of the above-described embodiments. 
     While the invention has been particularly shown and described with reference to specific embodiments thereof, it will be understood that various changes in form and details may be made. For example, although the valves  138 ,  738 A,  738 B disposed at the highest portion of the organ chamber  192 ,  792  have been illustrated and described herein as being a ball check valve, in other embodiments, a different type of valve configured to permit unidirectional flow of a fluid from the organ chamber into the pumping chamber can be included in the apparatus. For example, in some embodiments, an apparatus includes a different type of a check valve, such as a diaphragm check valve, a swing check valve, a life check valve, or the like. In another example, in some embodiments, an apparatus includes a valve that is different than a check valve. 
     Although the valve  210  of the pneumatic system  200  has been illustrated and described herein as being a solenoid valve, in other embodiments, the pneumatic system can include a different type of valve configured to control the flow of oxygen into the pumping chamber. 
     Although the valve  210  of the pneumatic system  200  has been illustrated and described herein as including three ports, in other embodiments, a valve of a pneumatic system can include a different number of ports. For example, in some embodiments, the valve includes one, two, four, or more ports. 
     Although the pneumatic systems (e.g., pneumatic system  200 ,  220 ) have been illustrated and described as including a specific number of control orifices (e.g., one control orifice  207  and two control orifices  223 ,  225 , respectively), in other embodiments, a pneumatic system can include any suitable number of control orifices. For example, a pneumatic system can include one, two, three, four, or more control orifices. 
     Although the lid assemblies described herein (e.g., lid assembly  110 ,  710 ) have been illustrated and described as being reinforced by a plurality of ribs (e.g., plurality of ribs  126 ,  131 ,  133 ,  726 ,  731 ) having a certain configuration (e.g., a parallel configuration or a combination circular/spoke and wheel configuration), in other embodiments, the lid assembly can include a plurality of ribs having a different orientation. For example, in another embodiment, any of the plurality of ribs can have a grid configuration, a diamond configuration, a herringbone configuration, a spoke and wheel configuration, another suitable configuration, or any combination of the foregoing configurations. Additionally, although lid assembly  110  has been illustrated and described herein as including a plurality of ribs (e.g., plurality of ribs  126 ,  131 ,  133 ) in a parallel configuration in a first direction, in other embodiments, the plurality of ribs can have a parallel configuration in a different direction. For example, although the plurality of ribs  131  are illustrated as having a parallel orientation in a first direction and the plurality of ribs  133  are illustrated as having a parallel orientation in a second direction substantially orthogonal to the first direction, in some embodiments, the plurality of ribs on each of an upper surface and a lower surface of a base can be oriented in a different manner. For example, in some embodiments, a plurality of ribs on an upper surface of a base have a parallel orientation in a first direction and a plurality of ribs on a lower surface of the base have a parallel orientation also in the first direction. 
     In another example, although the lid assemblies are illustrated and described herein (e.g., lid assembly  110 ,  710 ) have been illustrated and described as being reinforced by a plurality of ribs (e.g., plurality of ribs  126 ,  131 ,  133 ,  726 ,  731 ), in other embodiments, a lid assembly can include a different mechanism for reinforcement. 
     In some embodiments, an apparatus described herein can include components in addition to those described above. For example, referring to  FIG. 32 , in some embodiments, the apparatus  700  includes a base  796  configured to be coupled to the canister  790 . In some embodiments, the canister  790  and the base  796  are removably coupleable. The canister  790  can be coupled to the base using any suitable coupling mechanism, including, for example, a resistance fit, mating threads, an adhesive, or other suitable coupling mechanism. In the embodiment illustrated in  FIG. 32 , an upper surface of the base  796  defines a recess  798  configured to receive a bottom portion of the canister  790 . The base  796  is configured to provide stability to the canister  790  when the canister  790  is coupled thereto and/or received in the recess  798  of the base  796 . In other words, the base  796  is configured to help maintain the canister  790  in an upright position. In some embodiments, the base has a width substantially equal to an overall width of the lid assembly  710 . In this manner, the stability provided by the base  796  helps to off-set any top-heaviness imparted to the apparatus  700  by the lid assembly  710 . The base  796  is also configured to protect the floor  793  of the canister  790  when the floor  793  is flexed due to a pressure change within the organ chamber  792 , as described above. 
     In another example, the apparatus  700  can include a sterile carrier assembly  880 , as illustrated in  FIG. 33 . The carrier assembly  880  includes a top portion  882 , a bottom portion  884  and a plurality of latches  886  configured to couple the top portion  882  of the carrier assembly  880  to the bottom portion  884  of the carrier assembly  880 . The carrier assembly  880  is configured to receive the apparatus  700  (i.e., the coupled lid assembly  710 , retainer ring  850  and canister  790 ) in a compartment (not shown) defined by the top and bottom portions  882 ,  884  of the carrier assembly  880 . The carrier assembly  880  is configured to protect the apparatus  700  contained therein, including ensuring that the sterility of the apparatus  700  contained therein is not compromised when the apparatus  700  is removed from a sterile field. In this manner, the carrier assembly  880  facilitates transportability of the apparatus  700 . 
     In another example, in some embodiments, an apparatus described herein (e.g., apparatus  10 ,  100 ,  300 ,  700 ) includes at least one sensor (not shown) configured to detect information associated with the bodily tissue, such as a measurement associated with the bodily tissue. The apparatus can include a display configured to display an output based on the information detected by the at least one sensor. For example, in some embodiments, the lid  112  of the lid assembly  110  includes a display configured to display a message in real-time based on a measurement associated with the bodily tissue detected by the at least one sensor. 
     In certain embodiments the invention provides a transport system for preserving and transporting a biological sample such as an organ. The transport system may include an apparatus for containing the organ. The system may also include a sterile transport container configured to enclose the apparatus in a sterile environment. The system may further include a transporter including a power source. The transporter can be configured to receive the transport container and connect it to the power source. Optionally, the transporter can include a fluid container, such as an oxygen tank, with connections for providing fluid to the apparatus. 
     Such a system requires several fluid connectors and electrical connectors between the various system components to couple the power source and fluid source to the apparatus housing the organ. An object of the present invention is to facilitate quick and easy connections, which reduces user error and shortens the amount of time needed to prepare an organ for transport. 
     The invention provides quick-connect attachments (also known as “snap-and-go” connectors) between the organ preservation apparatus, the sterile transport container, and the transporter that includes temperature, power, and fluid supply and controls. To further reduce user error, each of the apparatus, container, and transporter have electrical and mechanical connectors configured to fit together and orient each piece in its proper alignment, described in greater detail below. 
     In certain embodiments of the invention, the system includes three modules: an apparatus for preserving an organ; a sterile container for creating a sterile barrier; and a transporter unit containing power and oxygen supply and insulation. The modules connect to each other via the quick connect snap-and-go mechanics. The apparatus drops into the container, and the container drops into the transporter. The connections themselves do not require any latching mechanisms themselves. They merely slide together or apart to mate and de-mate, and are held together by external forces. 
     For example, when the container is closed around the apparatus, latches that hold the top portion and bottom portion of the container together also hold the apparatus in place so that the appropriate connectors align. Likewise, when the container is inserted into the transporter, two mechanical latches or tabs are pushed open, allowing the snap-and-go connectors to align and connect. The latches hold the container in place within the transporter to secure the connectors. 
     In certain aspects, the invention provides a connection system for connecting components of an organ transport system. The system includes an organ transport container that has a top portion and a bottom portion. The top and bottom portions are configured to fit together to define an inner volume for containing an organ. The organ may be contained within a separate apparatus within the container, as described below. The container also includes a first mechanical connector and a first electrical connector. The system also includes a transporter, which may be connected to a power source. The transporter includes a transporter body sized and configured to receive the container. The transporter also includes a second mechanical connector and a second electrical connector. The transporter further includes a latch configured to secure the container in place within the transporter. According to the invention, when the transporter body is secured in the container by the latch, the transporter body and the container are configured to be oriented such that the electrical and mechanical connectors are aligned. 
     In embodiments, the system further includes an organ preservation apparatus sized and configured to fit within the organ transport container. The apparatus includes a canister and a lid assembly. The lid assembly has a third mechanical connector and a third electrical connector. The third mechanical connector is configured to connect with a fourth mechanical connector located within the inner volume of the container, thereby aligning the third electrical connector with a fourth electrical connector located within the inner volume of the container. When the top portion and bottom portion of the container are fit together, the apparatus is secured in place, thereby securing the alignment of the connectors. 
     In some embodiments, connecting pairs of mechanical connectors align and connect the corresponding electrical connectors. Each connecting pair of mechanical connectors may comprise a male connector and a female connector. In some embodiments the first and third mechanical connectors comprise female connectors, and the second and fourth mechanical connectors comprise male connectors. 
     In embodiments, the mechanical connectors comprise pneumatic passageways. The second mechanical connector may be coupled to a fluid source, which allows the series of connectors to form a fluid passageway from a fluid source to the organ preservation apparatus, such that the fluid source is in fluid communication with the lid assembly. The lid assembly may include a pumping chamber for pumping the fluid into a perfusate. The fluid may be, for example, oxygen. 
     In certain embodiments, each mechanical connector has a plurality of pneumatic passageways. One of the passageways may be a fluid supply port and at one of the passageways may be a fluid vent port. 
     In embodiments, when all electrical connections are made, the power source is in electrical communication with the lid assembly. The power source may be configured to power a valve to switch between a fluid-delivery configuration and a fluid-venting configuration of the pneumatic passageways. 
     In some embodiments, the latch secures the container in place when the container is inserted into the transporter. The latch may be configured to be manually released by a user for removing the container. 
       FIGS. 34 and 35  show a perspective view and a bottom view of an active lid assembly  810  for use with the present invention. The active lid assembly  810  is configured to oxygenate a perfusate in a pumping chamber (not shown), as has been described in greater detail above. The lid assembly  810  is referred to as “active” to differentiate it from a static lid assembly that does not include a fluid pumping mechanism. 
     Additional features of the active lid assembly  810  are visible in the bottom view shown in  FIG. 35 . A lumen  135  is configured to be in fluid communication with the organ adapter (not shown). A gasket  823 , such as an O-ring is disposed near the perimeter of the lid assembly  810  to facilitate a sealed connection with a canister (not shown). In the embodiment shown, the lid assembly  810  further includes an electrical connector  819 A and two mechanical connectors  804 A and  806 A. The connectors  819 A,  804 A, and  806 A are female ports for accepting corresponding male connectors on an organ transport container, described in greater detail below. The electrical connector  819 A can be any type of electrical connector known in the art such as a printed circuit board connector. In the active lid assembly  810 , mechanical connectors  804 A and  806 A are pneumatic passageways. Pneumatic passageways have channels formed within them for delivering or venting a fluid. In the active lid assembly  810 , mechanical connector  804 A is a fluid supply line for supplying a fluid such as oxygen to the lid assembly  810 , and mechanical connector  806 A is a vent line for venting a fluid such as carbon dioxide from the pumping chamber to an area external to the system. 
       FIGS. 36 and 37  show a perspective and bottom view of a static lid assembly  910 . The static lid assembly  910  is differentiated from the active lid assembly  810  in that static lid assembly  910  does not include a pumping chamber Like the active lid assembly  810 , however, the static lid assembly  910  includes a fill port  108  for introducing a fluid perfusate into the apparatus. The fill port can be similar to other ports described herein (e.g., port  74 , fill port  708 ). 
     The underside of the static lid assembly  910  is shown in  FIG. 37 . Static lid assembly  910  includes an electrical connector  819 A and two mechanical connectors  804 A and  806 A. Because the static lid assembly  910  does not include a pneumatic system, the mechanical connectors  804 A and  806 A in this embodiment do not include passageways for the introduction of a fluid or releasing a fluid. Instead, in the embodiment of the static lid assembly  910 , mechanical connectors  804 A and  806 A merely serve to receive their male counterparts on the organ transport container, and by doing so, help to align the electrical connector  819 A with its connection on the organ transport container. In another embodiment, mechanical connectors  804 A and  806 A include pneumatic passageways, but those passageways are merely plugged when used with a static lid assembly. 
       FIGS. 38-40  show multiple views of an organ transport container  980 . The organ transport container is configured to receive the organ preservation apparatus, which includes either an active lid assembly  810  or a static lid assembly  910 . 
       FIG. 38  shows the organ transport container  980  with the top portion  982  and bottom portion  984  connected. The container is a sterile carrier similar to the carrier  880  described in  FIG. 33 . The container  980  includes a top portion  982 , a bottom portion  984 , and one or more latches  886  configured to couple the top portion  982  to the bottom portion  984 . The container  980  is configured to receive an organ preservation apparatus (i.e., a lid assembly  810  or  910  described above, coupled to a canister) in an interior compartment defined by the top and bottom portions  982 ,  984 . The container  980  is configured to protect the apparatus contained therein, including ensuring that the sterility of the apparatus is not compromised when the apparatus is removed from a sterile field. In this manner, the container  980  facilitates transportability of the apparatus. Additionally, the top portion  982  includes a handle  987  for easily carrying the container and placing it in a transporter described below. 
       FIG. 39  shows a view of the bottom portion  984  of the container  980 , with the top portion  982  removed. The bottom portion  984  defines an inner volume  971  sized and configured to receive an organ preservation apparatus, such as those described above. The bottom portion  984  includes mechanical connectors  806 B and  804 B, which are configured to slide axially into and be received by corresponding mechanical connectors  806 A and  804 A of the lid assembly  910  or  810 . Disposed between the mechanical connectors  806 B and  804 B is an electrical connector  819 B, which is a male counterpart to electrical connector  819 A, and is configured to slide axially into and be received by connector  819 A. As previously described, the mechanical connectors help with aligning the smaller electrical connectors. The inner volume  971  is configured to receive the organ preservation apparatus in a particular orientation that aligns the female connectors  804 A,  806 A, and  819 A with their corresponding male connectors  804 B,  806 B, and  819 B. Therefore when a user places the apparatus inside the bottom portion  984  of the container  980 , the connectors are correctly aligned and all of the connections are made without requiring a second step of manually connecting them. 
       FIG. 40  shows an inferior view of the bottom portion  984  of the container  980 . The bottom portion  984  includes female connectors  804 C,  806 C, and  819 C which are visible from the inferior view. Connectors  804 C,  806 C, and  819 C are disposed generally beneath where connectors  804 B,  806 B, and  819 B are located (not shown, but visible from the superior view in  FIG. 39 ). Mechanical connectors  804 C and  806 C are substantially similar to mechanical connectors  804 A and  806 A on lid  910  or  810 . They are configured to receive corresponding male connectors located on a transporter unit described below. Mechanical connectors  804 C and  806 C may comprise pneumatic passageways that are in fluid communication with connectors  804 B and  806 B, and therefore also in fluid communication with the lid assembly  810  when connectors  804 B and  806 B are connected to connectors  804 A and  806 A. Likewise, electrical connector  819 C is in electrical communication with electrical connector  819 B. The bottom portion  984  of container  980  is sized and configured to be received by an opening in a transporter apparatus. 
       FIGS. 41-43  show multiple views of a transporter unit  650 . The transporter  650  is generally configured to receive and enclose the sterile container  980 . 
       FIG. 41  shows a portion  670  of a transporter  650 . Transporters for use with the present invention can be any similar transporter described in U.S. Patent Publication 2014/0041403, filed Aug. 10, 2012, the contents of which are incorporated by reference in their entirety. For purposes of illustration, the transporter  650  shown in  FIG. 41  generally comprises a transporter body  670  and a transporter lid  680  (shown in  FIG. 43 ). The transporter body  670  defines an opening  675  that is sized and configured to receive the container  980 . When a container  980  is inserted into the opening  675 , tabs  661  and  663  are pushed open and secure the container  980  in place. The tabs  661  and  663  can be released by squeezing them together, allowing the container  980  to be lifted out. 
     The transporter  650  also defines a tank cavity  627  for holding a fluid container such as an oxygen tank  629 . During operation the oxygen tank  629  is connected to and in fluid communication with a pneumatic connector (shown in  FIG. 42 ) for providing fluid 
     The fluid such as oxygen can serve a dual purpose of oxygenating the preservation solution contained in the apparatus, and also providing pressure to circulate the preservation solution around or through the tissue being preserved. The transporter also includes a power source (not shown) in electrical communication with electrical connector  819 D (shown in  FIG. 42 ). 
     The transporter may have one or more clasps  641  for securing the body  670  and lid  680  together. One or more wheels  633  mounted on the transporter body  670  allow the transporter  650  to be rolled, and a retractable handle  623  allows a user to manually move the transporter  650  by rolling it on the wheels  633 . Other handles, straps, or mechanisms known in the art to aid in transportation of objects can be included on the transporter  650 . 
     Controls (not shown) on the transporter allow a user to easily control temperature, fluid pressure, and other variables while the transporter is closed. The transporter can include a display screen (not shown) for showing temperature conditions within the transporter, or other relevant information including pressure, time since harvest, oxygen consumption rate, and the like. 
       FIG. 42  shows a superior view of the transporter body  670  with the lid  680  removed. The inside of the opening  675  is visible, including mechanical connectors  806 D and  804 D. Mechanical connectors  806 D and  804 D are substantially similar to mechanical connectors  806 B and  804 B in that they are male connectors which may comprise pneumatic passageways to establish a fluid connection with counterpart female connectors. In other embodiments that do not require introduction of fluid into the apparatus, the mechanical connectors are plugged and do not allow passage of fluid therethrough. Like the other connectors described above, an electrical connector  819 D is disposed between the mechanical connectors. The mechanical connectors  806 D and  804 D aid in aligning the electrical connector  819 D with a corresponding female electrical connector  819 C on the container  980 . 
     The container  980  and the opening  675  are configured so that when the container  980  is inserted into the opening  675 , it is oriented in the correct position to make the connections described above. 
       FIG. 43  shows the transporter  650  in its fully assembled configuration. The transporter lid  680  is connected to the transporter body  670  by a plurality of clasps  641 . 
     Although various embodiments have been described as having particular features and/or combinations of components, other embodiments are possible having any combination or sub-combination of any features 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 than the embodiments shown, while still providing the functions as described herein. Thus, the breadth and scope of the invention should not be limited by any of the above-described embodiments. The previous description of the embodiments is provided to enable any person skilled in the art to make or use the invention. While the invention has been particularly shown and described with reference to embodiments thereof, it will be understood by those skilled in the art that various changes in form and details may be made therein without departing from the spirit and scope of the invention.