Method of preparing organs for cryopreservation

This invention relates to the field of organ perfusion. More particularly, it relates to a method for perfusing isolated animal, including human, organs. Still more particularly, this invention relates to methods for introducing vitrifiable concentrations of cryoprotective agents into isolated organs or tissues in preparation for their cryopreservation.

Cryopreservation (that is, preservation at very low temperatures) of organs would allow organ banks to be established for use by transplant surgeons in much the same way that blood banks are used by the medical community today. At the present time, cryopreservation can be approached by freezing an organ or by vitrifying the organ. If an organ is frozen, ice crystals form within the organ which mechanically disrupt its structure and hence damage its ability to function correctly when it is transplanted into a recipient. Vitrification, by contrast, means solidification, as in a glass, without ice crystal formation.

The main difficulty with cryopreservation is that it requires the perfusion of organs with high concentrations of cryoprotective agents (water soluble organic molecules that minimize or prevent freezing injury during cooling to very low temperatures). No fully suitable equipment or method(s) has been developed to date for carrying out this perfusion process. This has prevented the establishment of viable organ banks that could potentially save lives.

Devices and methods for perfusing organs with cryoprotectant have been described in the literature since the early 1970's. See, Pegg, D.E., in <i>Current Trends in Cryobiology</i> (A.U. Smith, editor) Plenum Press, New York, N.Y., 1970, pp. 153-180, but particularly pages 175-177; and Pegg, D.E., <i>Cryobiology</i> 9:411-419 (1972).

In the apparatus initially described by Pegg, two perfusion circuits operated simultaneously, one with and one without cryoprotectant. Cryoprotectant was introduced and removed by abruptly switching from the cryoprotectant-free circuit to the cryoprotectant-containing circuit, then back again. The pressure was controlled by undescribed techniques, and data was fed into a data logger which provided a paper tape output which was processed by a programmable desk-top Wang calculator. The experimental results were poor. The equipment and technique described were considered inadequate by Pegg and his colleagues, who later modified them considerably.

In 1973, Sherwood <i>et al.</i> (in <i>Organ Preservation</i>, D.E. Pegg, ed., Churchill Livingstone, London (1973), pp. 152-174), described four potential perfusion systems, none of which are known to have been built. The first system consisted of a family of reservoirs connected directly to the organ via a multiway valve, changes being made in steps simply by switching from one reservoir to another.

The second system created changes in concentration by metering flow from a diluent reservoir and from a cryoprotectant concentrate reservoir into a mixing chamber and then to the kidney. No separate pump for controlling flow to the kidney was included. Total flow was controlled by the output of the metering pumps used for mixing. A heat exchanger was used before rather than after the filter (thus limiting heat exchanger effectiveness), and there was an absence of most arterial sensing. As will become readily apparent below, the only similarity between this system and the present invention was the use of two concentration sensors, one in the arterial line and one in the venous line of the kidney. Organ flow rate was forced to vary in order to minimize arteriovenous (A-V) concentration differences. The sensing of concentration before and after the kidney in the circuit is analogous to but substantially inferior to the use of a refractometer and a differential refractometer in the present invention. The present inventors' experience has shown that the use of a differential refractometer is necessary for its greater sensitivity. The concept of controlling organ A-V gradient by controlling organ flow is distinctly inferior to the system of the present invention.

The third system described by Sherwood <i>et al.</i> also lacked a kidney perfusion pump, relying on a "backpressure control valve" to recirculate perfusate from the filter in such a way as to maintain the desired perfusion pressure to the kidney. As with the second Sherwood system, the heat exchanger is proximal to the filter and no bubble trap is present. The perfusate reservoir's concentration is controlled by metered addition of cryoprotectant or diluent as in the second Sherwood system, and if flow from the organ is not recirculated, major problems arise in maintaining and controlling perfusate volume and concentration. None of these features is desirable.

The fourth system was noted by Pegg in an appendix to the main paper. In this system, perfusate is drained by gravity directly from the mixing reservoir to the kidney through a heat exchanger, re-entering the reservoir after passing through the kidney. Concentration is sensed also by directly and separately pumping liquid from the reservoir to the refractometer and back.

Modifications and additional details were reported by Pegg <i>et al.</i> (<i>Cryobiology 14</i>:168-178 (1977)). The apparatus used one mixing reservoir and one reservoir for adding glycerol concentrate or glycerol-free perfusate to the mixing reservoir to control concentration. The volume of the mixing reservoir was held constant during perfusion, necessitating an exponentially increasing rate of diluent addition during cryoprotectant washout to maintain a linear rate of concentration change. The constant mixing reservoir volume and the presence of only a single delivery reservoir also made it impossible to abruptly change perfusate concentration. All components of the circuit other than the kidney and a pre-kidney heat exchanger were located on a lab bench at ambient temperature, with the reservoir being thermostated at a constant 30°C. The kidney and the heat exchanger were located in a styrofoam box whose internal temperature was not controlled. Despite this lack of control of the air temperature surrounding the kidney, only the arterial temperature but not the venous temperature or even the kidney surface temperature was measured. The use of a styrofoam box also did not allow for perfusion under sterile conditions. The only possible way of measuring organ flow rate was by switching off the effluent recirculation pump and manually recording the time required for a given volume of fluid to accumulate in the effluent reservoir, since there was no perfusion pump which specifically supplied the organ, unlike the present invention. Pressure was controlled, not on the basis of kidney resistance, but on the basis of the combined resistance of the kidney and a manually adjustable bypass valve used to allow rapid circulation of perfusate through the heat exchanger and back to the mixing reservoir. The pressure sensor was located at the arterial cannula, creating a fluid dead space requiring manual cleaning and potentially introducing undesired addition of unmixed dead space fluid into the arterial cannula. Pressure control was achieved by means of a specially-fabricated pressure control unit whose electrical circuit was described in an earlier paper (Pegg <i>et al., Cryobiology 10</i>:56-66 (1973)). Arterial concentration but not venous concentration was measured. No computer control or monitoring was used. Concentration was controlled by feeding the output of the recording refractometer into a "process controller" for comparison to the output of a linear voltage ramp generator and appropriate adjustment of concentrate or diluent flow rate. Glycerol concentrations were measured manually at 5 minute intervals at both the mixing reservoir and the arterial sample port: evidently, the refractometer was not used to send a measurable signal to a recording device. Temperature and flow were recorded manually at 5 minute intervals. Arterial pressure and kidney weight were recorded as pen traces on a strip chart recorder. None of these features is desirable.

Further refinements were reported by Jacobsen <i>et al.</i> (<i>Cryobiology 15</i>:18-26 (1978)). A bubble trap was added, the sample port on the kidney bypass was eliminated (concentration was measured at the distal end of the bypass line instead), and temperature was recorded as a trace on a strip chart recorder rather than manually every 5 minutes. Additionally, these authors reported that bypass concentration lagged reservoir concentration by 5 min (v. 3 min or less for arterial concentration in the present invention) and that terminal cryoprotectant concentration could not be brought to less than 70 mM after adding 5 liters of diluent to the mixing reservoir (v. near-zero terminal concentrations in the present invention using less than 3 liters of diluent and using peak cryoprotectant concentrations approximately twice those of Jacobsen <i>et al., supra</i>).

A variation on the system was also reported the same year by I.A. Jacobsen <i>(Cryobiology 15</i>:302-311 (1978)). Jacobsen measured but did not report air temperatures surrounding the kidney during perfusion. He reduced the mixing reservoir volume to 70 ml, which was a small fraction of the 400 ml total volume of the circuit. No electronic-output refractometer appears to have been used to directly sense glycerol concentration and control addition and washout. Instead, the calculated values of concentrate or diluent flow rate were drawn on paper with India ink and read by a Leeds and Northrup Trendtrak Programmer which then controlled the concentrate/diluent pump. Despite the low circuit volume, the minimum concentration of cryoprotectant which could be achieved was about 100 mM.

Additional alterations of the same system were reported by Armitage <i>et al. (Cryobiology 18</i>:370-377 (1981)). Essentially, the entire perfusion circuit previously used was placed into a refrigerated cabinet. Instead of a voltage ramp controller, a cam-follower was used. Again, however, it was necessary to calculate the required rates of addition of glycerol or diluent using theoretical equations in order to cut the cam properly, an approach which may introduce errors in the actual achievement of the desired concentration-time histories. Finally, a modification was made in which an additional reservoir was added to the circuit. This reservoir was apparently accessed by manual stopcocks (the mode of switching to and from this reservoir was not clearly explained), and use of the new reservoir was at the expense of being able to filter the perfusate or send it through a bubble trap. The new reservoir was not used to change cryoprotectant concentration; rather, it was used to change the ionic composition of the medium after the cryoprotectant had been added. The volume of the mixing reservoir was set at 500 ml, allowing a final cryoprotectant concentration of 40 mM to be achieved.

An approach to organ preservation at cryogenic temperatures previously described by one of the Applicants involved vitrifying rather than freezing organs during cooling (see, for example, Fahy <i>et al., Cryobiology</i><i>21</i>:407-426 (1984); and U.S. Patent 4,559,298). "Vitrification" means solidification without freezing and is a form of cryopreservation. Vitrification can be brought about in living systems, such as isolated human or other animal organs, by replacing large fractions of the water in these systems with cryoprotective agents (also known as cryoprotectants) whose presence inhibits crystallization of water (i.e., ice formation) when the system or organ is cooled. Vitrification typically requires concentrations greater than 6 molar (M) cryoprotectant. However, using known techniques, it has not been possible to use sufficiently high cryoprotectant concentrations to vitrify an organ without killing it. The limiting concentration for organ survival was typically just over 4 M.

One type of damage caused by cryoprotectants is osmotic damage. Cryobiologists learned of the osmotic effects of cryoprotectants in the 1950's and of the necessity of controlling these effects so as to prevent unnecessary damage during the addition and removal of cryoprotectants to isolated cells and tissues. Similar lessons were learned when cryobiologists moved on to studies of whole organ perfusion with cryoprotectants. Attention to the principles of osmosis were essential to induce tolerance to cryoprotectant addition to organs. Despite efforts to control the deleterious osmotic effects of cryoprotectants, limits of tolerance to cryoprotectants are still observed. There appear to be genuine, inherent toxic effects of cryoprotectants that are independent of the transient osmotic effects of these chemical agents.

WO 87/01940 discloses a new composition for the preservation of organs prior to implantation. The composition comprises hydroxyethyl starch substantially free of ethylene glycol, ethylene chlorhydrin and acetone in a pharmaceutically acceptable organ perfusate.

Studies by the present inventors and others have examined methods of controlling the non-osmotic, inherent toxicity of cryoprotective agents. The results indicate that several techniques can be effective alone and in combination. These include (a) exposure to the highest concentrations at reduced temperatures; (b) the use of specific combinations of cryoprotectants whose effects cancel out each other's toxicities; (c) exposure to cryoprotectants in vehicle solutions that are optimized for those particular cryoprotectants; (d) the use of non-penetrating agents that can substitute for a portion of the penetrating agent otherwise needed, thus sparing the cellular interior from exposure to additional intracellular agent; and (e) minimization of the time spent within the concentration range of rapid time-dependent toxicity. Means by which these principles could be applied to whole organs so as to permit them to be treated with vitrifiable solutions without perishing, however, have not been clear or available.

Some of these techniques are in potential conflict with the need to control osmotic forces. For example, reduced temperatures also reduce the influx and efflux rate of cryoprotectants, thereby prolonging and intensifying their osmotic effects. Similarly, minimizing exposure time to cryoprotectants maximizes their potential osmotic effects. Thus, there must be a balance reached between the control of osmotic damage and the control of toxicity. Adequate means for obtaining this balance have not been described in the literature. In some cases, intensifying the osmotic effects of cryoprotectants by minimizing exposure times to these agents can be beneficial and complementary to the reduced toxicity that results, but safe means for achieving this in whole organs have not been described.

Organ preservation at cryogenic temperatures would permit the reduction of the wastage of valuable human organs and would facilitate better matching of donor and recipient, a factor which continues to be important despite the many recent advances in controlling rejection (see, Takiff <i>et al., Transplantation 47</i>:102-105 (1989); Gilks <i>et al., Transplantation 43</i>:669-674 (1987)).

One major limitation in organ cryopreservation studies has been the lack of suitable equipment for controlling perfusion parameters such as cryoprotectant concentration-time history, pressure, and temperature. Previously described standard perfusion machines are not designed for this application and are unable to meet the requirements addressed here. Patented techniques heretofore known are described in: <ul id="ul0001" list-style="none" compact="compact"><li>U.S. Patent No. 3,753,865 to Belzer <i>et al.</i>;</li><li>U.S. Patent No. 3,772,153 to De Roissart <i>et al.</i>;</li><li>U.S. Patent No. 3,843,455 to Bier, M.</li><li>U.S. Patent No. 3,892,628 to Thorne <i>et al.</i>;</li><li>U.S. Patent No. 3,914,954 to Doerig, R.K.;</li><li>U.S. Patent No. 3,995,444 to Clark <i>et al.</i>;</li><li>U.S. Patent No. 4,629,686 to Gruenberg, M.L.; and</li><li>U.S. Patent No. 4,837,390 to Reneau, R.P.</li></ul>

Equipment described for cryopreservation applications in the past has permitted only relatively simple experimental protocols to be carried out, and has often been awkward to use. Only Adem <i>et al.</i> have reported using a computer for organ perfusion with cryoprotectant (see, for example, <i>J. Biomed. Engineering 3</i>:134-139 (1981)). However, their specific design has several major flaws that limit its utility.

WO 93/00808 describes a computer-controlled apparatus and and a method for perfusing a biological organ. In the method, following an initial baseline perfusion, the cryoprotectant concentration is elevated at a constant rate until a first plateau of concentration is established. During concentration elevation, the temperature is simultaneously lowered. Thereafter, a step change in concentration is executed from said first concentration plateau to a concentration sufficient for vitrification. However, there still remains the need for a process to reduce possible cryoprotectant toxicity and cooling injury, in particular with very large organs such as the kidney and the liver, that reveal realtively low tolerances to high pressures and high cryoprotectant concentrations on the one hand, but require relatively low vitrification temperatures and high cryoprotectant concentrations at ambient pressures to ensure vitrifiability on the other hand.

The present invention overcomes substantially all of the deficiencies of known methods.

<i>Summary of the Invention</i>

This invention is directed to a method which is used to prepare the organ for cryopreservation, by vitrification.

This invention is directed to a method of preparing a biological organ or tissue for cryopreservation, comprising the phases of: <ul id="ul0002" list-style="none"><li>(a) perfusing or superfusing said organ or tissue with a solution under conditions in which the concentration of the cryoprotectant in the solution is gradually increased to a first predetermined non-vitrifiable concentration while concurrently reducing the temperature of said organ or tissue;</li><li>(b) maintaining the concentration of said cryoprotectant for a sufficient time to permit the approximate osmotic equilibration of said organ or tissue to occur;</li><li>(c) increasing the cryoprotectant concentration of said solution to a higher second predetermined non-vitrifiable concentration;</li><li>(d) maintaining the cryoprotectant concentration of said solution at said second concentration for a time sufficient to permit the approximate osmotic equilibration of said organ or tissue to occur;</li><li>(e) reducing the temperature of the organ or tissue to a temperature below that of phase (a);</li><li>(f) increasing the cryoprotectant concentration of said solution to a level sufficient for vitrification; and</li><li>(g) reducing the temperature of the organ or tissue to a cryogenic temperature.</li></ul>

The organ is then removed from the perfusion apparatus and is cryopreserved using an appropriate method or is further prepared for cryopreservation.

Exemplifications include the rabbit kidney, the rat liver, and the human kidney.

The apparatus which is used to execute the process and, however, is no part of the invention comprises a computer operated perfusion circuit containing a plurality of fluid reservoirs, a means for raising and lowering concentrations and an organ container. A first fluid flow path is defined as a loop from the plurality of reservoirs to necessary sensors and temperature conditioning means and back to the plurality of reservoirs. The reservoirs are selectively connectable to the first fluid flow path. Pump means are interposed in a second fluid flow path for pumping fluid from the first fluid flow path to a second fluid flow path. The organ container is located in this second fluid flow path. Pump means may also be included in the second fluid flow path for pumping fluid from the organ container to one or more of the reservoirs or to waste. One or more sensors are interposed in the fluid flow paths for sensing at least one of the concentration, concentration differential, temperature, pressure, and pH of the fluid flowing in the first and/or second fluid flow paths. Measuring means are interposed in the first and second fluid flow paths for measuring concentration and temperature differences between the upstream and downstream sides, in the fluid flow direction, of the organ container. The sensor(s) and the measuring means are connected to a programmable computer for providing a continuous information stream from the sensor(s) to the computer. Finally, the computer is coupled to the selection means and the pump means to continuously selectively control (a) the flow of fluid from each of the reservoirs individually to the fluid flow paths, (b) the flow of fluid from each of the fluid flow paths individually to each of the reservoirs, and (c) at least one of the concentration, temperature, pressure and pH of the fluid flowing in the first and/or second fluid flow path, in accordance with a predetermined computer program without substantial operator intervention.

Additional features of the apparatus may include a heat exchanger interposed in the first fluid flow path for conditioning the temperature of fluid flowing in this fluid flow path. A second heat exchanger may be interposed in the second fluid flow path for conditioning the temperature of fluid flowing in the second fluid flow path.

<i>Brief Descriptions of the Figures</i>

Note: Figures 1 to 4 show subject matter being no part of the invention which, however, is deemed to contribute to a better understanding how to execute the process of the invention.

<b><i>Figure 1</i></b> (comprising <b>Figures 1A</b> and <b>1B</b>). <b>Figure 1A</b> shows the overall fluidic circuit diagram of an apparatus for the execution of this invention. Figure <b>1B</b> shows the construction of the Effluent Distribution Block (EDB) and the means by which the effluent flow is divided to allow sampling by the Δ R.I. pump <b>126</b> in <b>Figure 1A.</b>

<b><i>Figures 2A-C</i></b> show side, top and bottom views, respectively of a two-chamber gradient former employed as reservoir <b>R1</b> in the apparatus of Fig. 1A.

<b><i>Figures 3A-C</i></b> show side, top and bottom views, respectively, of a three-chamber gradient former used as reservoir <b>R3</b> in the apparatus of Fig. 1A.

<b><i>Figures 4A-C</i></b> show left, front, and right side views, respectively, of the Heat Exchanger/Bubble Trap/Mixer <b>(HBM)</b> used in the apparatus of Fig. 1A; <b>Figure 4D</b> shows the basic mixing unit area of the <b>HBM;</b> and Figure <b>4E</b> shows a top view of the base of the <b>HBM.</b>

<b><i>Figure 5</i></b> shows the part of the protocol for the two-step introduction of fully concentrated vitrification solution that was carried out inside the standard perfusion machine.

The following abbreviations have the following meaning: <ul id="ul0003" list-style="none" compact="compact"><li>M means the target molar concentration</li><li>M̂ means the measured molar cocentration</li><li>F means flow in ml/min</li><li>P/10 means pressure divided by 10</li><li>V55 means cryoprotectant agent</li></ul>

<b><i>Figures 6A-6C</i></b> comprise a flow chart of activities for organ cryoprotectant perfusion.

<b><i>Figure 7</i></b> is a schematic diagram of the details of the two-step cooling technique for introducing high concentrations of cryoprotectants. The minuscules in parethesis designate the phases referred to later; by comparison, the upper graph including C1, T1 represents the one-step process which is no part of the invention.

<b><i>Figure 8</i></b> shows an apparatus to perfuse kidneys with vitrification solutions outside of the standard perfusion machine and at temperatures in the vicinity of -20 to -30°C.

<b><i>Figure 9</i></b> shows the effect of cooling to -30°C on rabbit kidneys previously perfused with 7.5 M or 8 M cyroprotective agents, in comparison to the results for the non-cooled kidneys exposed to -3°C.

<b><i>Figure 10</i></b> shows the results of exposing rabbit kidney slices to high concentrations of cryoprotectant after rather than prior to cooling to -23°C, demonstrating that both the cooling injury and the toxicity associated with high concentrations are prevented by cooling initially in a low (6.1 M) concentration.

<b><i>Figure 11</i></b> shows that cooling injury is also successfully avoided in the intact kidney at 6.1 M croprotectant (100% survival, excellent final creatinine levels), proving the hypothesis that cooling injury is abolished at low concentrations.

<b><i>Figure 12</i></b> shows the feasibility of the two-step approach for introducing 8 M cryoprotectant at -22°C; the survival rate was 7/8 and the creatinine levels after two weeks were excellent and identical to those for kidneys exposed only to 6.1 M cryoprotectant.

<b><i>Figure 13</i></b> shows the feasibility of using the two-step approach to avoid cooling injury down to -32°C with 8 M cryoprotectant (survival rate = 100%, final creatinine levels identical to those for kidneys exposed only to 6.1 M cryoprotectant).

<b><i>Figure 14</i></b> shows that kidney slices treated with V55 and cooled to -46°C experience maximum cooling injury, no further injury being apparent when slices were cooled all the way to the glass transition temperature.

<b><i>Figure 15</i></b> shows the postoperative serum creatinine levels in an intact kidney that was treated with V55 and cooled to -46°C with subsequent life support funtion (survival rate: 1/1 kidneys so treated; final creatinine levels: acceptable.)

<b><i>Figure 16</i></b> (comprising <b>Figures 16A</b> and <b>16B</b>) show data from the perfusion of a human kidney with the vitrifiable solution known as V55 by the method of this invention. Specifically, <b>Figure 16A</b> shows successful control of cryoprotectant concentration. <b>Figure 16B</b> shows resistance and flow data. The data are all from the same 232 gram human kidney. In <b>Figure 16A,</b> P means pressure in mm Hg. In <b>Figure 16B,</b> resistance is expressed as weight times pressure divided by flow rate<maths id="math0001"><img file="EP0777413B1_D0001.tif" /></maths>

<b><i>Figure 17</i></b> shows cooling data from the same kidney as <b>Figure 16.</b> The kidney was cooled after immersion in a 60% w/v mixture of dimethyl sulfoxide and acetamide. These data gave a continuous recording of organ core temperature from 0°C, which was reached in about 15 minutes, to about the glass transition temperature. The data revealed no evidence of ice formation within the kidney.

<b><i>Figure 18</i></b> shows loading (ascending portion) and unloading (descending portion) of a human pediatric kidney with V55 using the method of this invention. The solid line was the target V55 concentration while the dotted line was the actual measured V55 concentration in the circuit. Since the cryoprotectant was unloaded from this kidney a cooling curve was not generated.

<b><i>Figure 19</i></b> (comprising <b>Figures 19A-19C</b>) shows viability data for rabbit kidney slices (<b>Figure 19A</b>), human kidney slices (<b>Figure 19B</b>) and comparative rabbit:human data (<b>Figure 19C</b>). The human kidney slices showed identical responses to V49 as the rabbit slices but showed slightly lower recovery after cooling to -30°C.

<i>Definitions</i>

In order to provide a clear and consistent understanding of the specification and claims, including the scope to be given such terms, the following definitions are provided. Any terms which are not specifically defined in this or other sections of this patent application have the ordinary meaning they would have when used by one of skill in the art to which this invention applies at the time of the invention.

As used herein, "cryopreservation" means the maintaining of the viability of excised tissues or organs by storing them at very low temperatures. Cryopreservation is meant to include freezing and vitrification.

As used herein, "vitrification" means solidification of an organ or tissue without freezing it.

As used herein, "cryoprotectant" means a chemical which inhibits ice crystal formation in a tissue or organ when the organ is cooled to subzero temperatures and results in an increase in viability after warming, in comparison to the effect of cooling without the cryoprotectant.

As used herein, all temperatures are in °C unless otherwise specified.

As used herein, "non-penetrating" means that the great majority of molecules of the chemical do not penetrate into the cells of the tissue or organ but instead remain in the extracellular fluid of the tissue or organ.

As used herein, "approximate osmotic equilibration" means that the difference between the arterial and venous concentrations is less than about 50 to 200 mM. (A difference of 200 mM at an arterial concentration of 4 M means that the venous concentration is 95 % of the arterial concentration. A 153 mM difference is equivalent to a 1 % w/v concentration difference for our preferred cryoprotectant formula described below.)

As used herein, "animal" means a mammal including, but not limited to, human beings.

<i>Detailed Description of the Preferred Embodiment and Best Mode</i>

<i>I. Description of the Perfusion Apparatus</i> (no part of the invention)

The apparatus for the execution of the method of this invention is contained in a refrigerated cabinet <b>100</b> (shown by double dashed lines in <b>Figure 1A</b>). The refrigerated cabinet contains two sides, the reservoir/solenoid side and the organ/refractometer side. The cabinet is faced with double paned transparent doors each containing approximately 1 inch of insulating air (which can be reduced in pressure and/or humidity if necessary) between the panes to avoid condensation of moisture on the doors and to minimize heat leak into the cabinet. The organ-side door is split to form a "Dutch door". This allows the upper portion of the organ-side door to be opened and closed to place the organ in the system and to remove the organ without changing the temperature below the upper portion of the door, where the organ container and most other equipment are located. The cabinet may also employ a "Dutch door" on the reservoir side of the cabinet to enable the operator to make any needed adjustments (e.g., fluid addition to the reservoirs, transfer of upper fluid lines, etc.) without disturbing the cabinet's temperature to an unnecessary degree.

The primary features of the invention and its mode of operation are shown in the fluidic logic schematic of Figure 1A. All fluid available for circulation through the system is drawn into the main circuit by a circuit pump <b>102</b> through fluid uptake lines <b>U1, U2, U3,</b> or <b>U4</b> depending upon the computer-controlled actuation pattern of three-way solenoid valves <b>S1, S2,</b> and <b>S3.</b> Uptake lines <b>U1-U4</b> connect either to fluid delivery lines <b>D1-D4</b> leading from reservoirs <b>R1-R4,</b> respectively, or to cleaning ports <b>C1-C4,</b> through standard tubing quick disconnects. By clamping <b>D1-D4</b> and unplugging them from uptake lines <b>U1-U4,</b> lines <b>U1-U4</b> can be plugged into cleaning ports <b>C1-C4,</b> as indicated by the curved arrows. While this is presently done manually, it will be appreciated by those skilled in the relevant arts that appropriate valves, tubing and controls could be added to handle most of these tasks automatically.

In the apparatus for the execution of the present invention, the reservoirs <b>R1-R4</b> are supported on a thick transparent plastic shelf from which four magnetic stir tables hang which stir the four reservoirs (not shown in Fig. 1). Thorough stirring of <b>R1, R3,</b> and <b>R4</b> is necessary for proper generation of the desired concentration-time histories. The on/off states and stir rates of the stir tables are independently controlled by instrumentation located outside the refrigerated cabinet.

Ports <b>C1-C4</b> lead to sources of sterile (distilled) water, air, and disinfectant. Solenoid valves <b>S0</b> and <b>S00</b> are interposed in the delivery lines for these sources and are arranged to ensure that traces of disinfectant do not enter the perfusion system by accident. Solenoid <b>S0</b> controls whether air or fluid will enter the perfusion circuit for cleaning, while solenoid <b>S00</b> determines whether the fluid selected will be water or disinfectant. The breakup of the main cleaning line into four independent channels outside of the cabinet rather than just before reaching <b>C1-C4</b> (not so indicated in Fig. 1) ensures that each channel is independent of the others, i.e., not subject to any meaningful cross-contamination resulting from diffusion of unpurged solution backwards from the fluid uptake lines <b>U1-U4</b> into the cleaning lines leading to cleaning ports <b>C1-C4.</b>

Distilled water and disinfectant are drawn into the system through a sterilizing filter <b>F4</b>, while air is drawn into the system through an air filter <b>F5</b>. The disinfectant of choice at present is a clinically accepted dialysis machine cold sterilant such as Actril™ (Minntech, Minneapolis, Minnesota). The cleaning procedure is to wash the perfusate out of the system with water and then to displace the water with sterilant. Prior to the next perfusion, the sterilant is washed out of the system with water and the water is then washed out of the system with air. The system is then primed by displacing the air with appropriate perfusate. The air flush is used to avoid the persistence of any lingering traces of sterilant dissolved in the rinse water, and to avoid any possible dilution of the priming fluid with water (i.e., to reduce the amount of priming fluid needed for displacing water from the system), to allow a visual check of the completeness of priming, and to reduce spillage of water in the cabinet when the reservoirs, filters, and organ cassette are placed into the system after cleaning but before priming. The air purge can, however, be omitted if desired. The air filter is used to prevent contamination from pathogens in the air, if necessary.

Solenoid valves <b>S9-S12</b> normally direct fluid to reservoirs <b>R1-R4</b> or to the waste line (LW). Reservoirs <b>R1-R4</b> can also be detached from the system by removing recirculation lines <b>RL5-RL8</b> from reservoirs <b>R1-R4</b> and plugging them into waste ports <b>W1-W4,</b> respectively (as indicated by curved arrows), allowing reservoirs <b>R1-R4</b> to be removed from the system for cleaning, sterilizing, and refilling. When reservoirs <b>R1-R4</b> are removed, valves <b>S9-S12</b> direct fluid to waste ports <b>W1-W4.</b> The four waste lines corresponding to waste ports <b>W1-W4</b> converge to a single common waste line <b>LW</b>. A two-way solenoid valve <b>S16</b> is located on the common waste line. When the waste ports are not in use, the common waste drainage line is blocked by closing valve <b>S16</b> to prevent any possible backflow of waste or pathogens into the sterile cabinet.

The use of this system of uptake lines <b>U1-U4,</b> which are plugged alternately into reservoir delivery lines <b>D1-D4</b> or cleaning ports <b>C1-C4,</b> in combination with recirculation lines <b>RL5-RL8,</b> which are plugged alternately into the reservoir internal return lines (not shown in the figure) or into waste ports <b>W1-W4,</b> allows complete sterilization of the perfusion circuit. The blunt ends of the uptake lines <b>U1-U4,</b> delivery lines <b>D1-D4,</b> cleaning ports <b>C1-C4</b> and waste ports <b>W1-W4</b> may be sterilized by swabbing with disinfectant when the tubing is being transferred from one alternative position to the other. The tubing transfer is accomplished while applying digital pressure to the tubing so as to occlude it while making the transfer to prevent fluid leaks and further reduce the risk of contamination.

The fluid withdrawn from reservoirs <b>R1-R4</b> or from ports <b>C1-C4</b> is delivered through one of several filters <b>F1, F2,</b> and <b>F3,</b> depending upon the state of actuation of solenoid valves <b>S4</b> through <b>S7.</b> These actuation patterns will be described in more detail below. Experience has shown, however, that a single filter <b>F1</b> or two filters <b>F1, F1'</b> in parallel will be adequate for most studies (rendering valves <b>S4-S7</b> optional, as indicated by broken lines) since virtual step changes in concentration can be imposed even when only one or two filters in parallel are present in the circuit.

It is desirable to minimize the distance between the circuit pump <b>102</b> head and the solenoids <b>S1-S7</b> to minimize circuit dead space and dead time and to minimize the effects of perfusate viscosity. Short distances and adequate tubing inner diameters are particularly critical for <b>S1-S3</b> to assure adequate fluid withdrawal from <b>R1-R4.</b>

Standard Millipore filters appear (Bedford, MA) compatible with our cryoprotectants. The filters are capable of sterilizing the perfusate and are autoclavable. All filter holders can be removed from the system for cleaning and sterilization by means of the quick disconnects shown in Figure 1A. Vent lines <b>V1-V3</b> lead to solenoid valves <b>S13-S15,</b> located outside of the refrigerated portion of the cabinet <b>100</b>. These vent lines are opened and closed under computer control during priming and cleaning of the system to permit air to escape and thereby prevent the filters from becoming blocked by air or damaged. A manual bypass (shown only for the <b>S13</b> bypass) is provided for <b>V1-V3</b> for emergency purging of air from the circuit. Obviously, air purges of the system beyond filters <b>F1-F3</b> are not possible if filters <b>F1-F3</b> are present in the circuit; hence filters <b>F1-F3</b> must be removed before beginning the washout of sterilant if an air purge is to be included in that procedure.

In an apparatus for the execution of the invention, a 90 mm diameter filter of 0.22 micron pore size is located in each filter holder. This size filter is able to pass enough vitrification solution at -6°C to permit the successful perfusion of a rabbit kidney, with an overlying 1.2 micron filter and a coarse prefilter to prevent clogging. The standard configuration for the operative version employs two identical filters in parallel. This is necessary to accommodate the flows required for human organs and provides a safety factor for any air which may be inadvertently introduced into the arterial fluid, as well as minimizing pressure build-up proximal to the filter. This continuous filter sterilization and resterilization of the perfusate during the perfusion can serve as a back up for pre-sterilized solutions in case of contamination for any reason during the perfusion. (The incidence of renal infections has been 0% after literally several hundred perfusions.)

Once the fluid from the selected reservoir has passed through the appropriate filter, it goes through some preliminary temperature conditioning in a heat exchanger <b>104</b> and then travels to a position as close to the organ as possible, at which point it encounters a "T" type tubing connector <b>T1.</b> The bulk of the flow passively takes the path <b>L1</b> ("refractometer loop") that leads to a flow-through process control refractometer <b>106</b> that measures the index of refraction of the liquid and hence the cryoprotectant concentration. The remainder of the flow is directed through an organ loop <b>L2</b> by means of an organ pump <b>108</b>. The organ pump speed is controlled by the computer so as to maintain the desired organ perfusion pressure despite wide variations in the organ's vascular resistance. By changing the organ pump head and the diameter of the tubing going through it, a wide range of flows can be generated sufficient to perfuse organs of a wide range of sizes: organs as small as rat hearts to organs as large as human kidneys have been successfully perfused.

The flow rate delivered by the circuit pump <b>102</b>, which supplies both the refractometer loop <b>L1</b> and the organ loop <b>L2,</b> must be high enough to both exceed the flow rate through the organ at all times and to ensure that sufficient flow is available for the refractometer <b>106</b> and other in-line sensors, generally designated <b>110</b>, for measuring temperature, pH, and other desired parameters of the perfusate, to permit accurate measurements. The flow must also be high enough to minimize the "dead time" between changes in reservoir concentration and changes in the sensed concentration and other sensed parameters in the refractometer loop as well as to minimize the "dead time" between the reservoir and the organ. The circuit pump flow is limited by the need to prevent fluid from being delivered to the filters at a rate in excess of what these filters or the tubing leading to them can pass without failing, as well as by constraints of heat output and wear and tear on the circuit pump tubing. The speed of the circuit pump is usually not varied during an experiment and does not therefore usually require computer control, though computer control is available as an option.

After passing through the organ pump <b>108,</b> the perfusate passes through a second heat exchanger <b>112</b> that finalizes perfusate temperature conditioning. This is done by adjusting the flow of both cold and warm liquid from cold and warm baths <b>114, 116,</b> respectively, using computer-controlled pumps (not shown) between heat exchanger <b>112</b> and baths <b>114</b> and <b>116.</b>

The computer is able to vary flow through both the cold path and the warm path so as to adjust perfusate temperature in the arterial line and therefore also in the effluent of the organ. The arterial and effluent temperatures provide an indication of the actual organ temperature. By controlling the flow rate of cold and warm bath fluid, organ temperature can be adjusted independently of organ flow, provided flow is not close to zero. Experience has shown that arterial and venous temperatures at least as cold as -6°C and at least as high as 25°C can be achieved with this invention. Generalized cabinet cooling is not an alternative to the heat exchange system shown for subzero perfusions because cooling of the cabinets to subzero temperatures will cause freezing of the more dilute solutions in the tubing lines. Specific jacketing and cooling of the organ container is of particular theoretical value, however, and may optionally be included.

The temperature-conditioned perfusate is then debubbled and mixed in a bubble trap/mixer <b>120</b> just before entering an organ container <b>122.</b> Arterial and venous temperature probes, generally designated "T" in Figure 1A, penetrate the wall of organ container <b>122</b> through simple holes. Pressure and, optionally, temperature is sensed in the bubble trap. Although shown separately in the drawing for ease of understanding, the bubble trap and mixer <b>120</b> are in fact an integral part of the heat exchanger <b>112,</b> so heat exchange continues to be controlled while debubbling and mixing are accomplished. Experience has shown that mixing was important due to the tendency for layering of dilute solutions on more concentrated, denser solutions. Details as to the specific construction of the heat exchanger/bubble trap/mixer <b>(HBM)</b> are described below.

Under normal circumstances, the cooling fluid effluent from this second heat exchanger <b>112</b> is used to cool the perfusate passing through the preliminary heat exchanger <b>104.</b> This cooling fluid then travels to a solenoid holding block <b>118</b> physically containing solenoids <b>S1-S12,</b> so as to draw off waste heat from these solenoids before returning to the cold bath.

The holding block <b>118</b> currently consists of a large aluminum block (but may be either metal or plastic) perforated with cylindrical holes of sufficient diameter to closely match the outside diameters of the held solenoids. The solenoids are inserted such that the base, containing the fluid inlets and outlets, faces the operator and the head, from which the electrical leads penetrate into or through the holding block. The solenoid holding block is equipped with an internal fluid path for drawing off waste heat from the solenoids. Feet are provided to position the holding block, prevent it from moving, and protect the fluid inlet and outlet ports when the holding block is removed from the cabinet. The block is positioned behind and above the reservoirs in the refrigerated cabinet so that the solenoid inlets and outlets and their connections to the reservoirs are always readily visible.

The solenoids are preferably 3-7 watt (or less) piston type 3-way solenoids of minimal internal fluid volume having orifices on the order of 0.156 inches or more and Cv values ≥ 0.16 (e.g., Model 648T033 solenoids from Neptune Research, Maplewood, NJ) while resisting pressures of up to 500 mm Hg or so. The inventors presently prefer Neptune Research (<i>supra</i>), 3-watt solenoids fitted with RC dropping circuits to reduce heat generation after activation. Solenoids having 1/16 inch orifices and Cv values of 0.01 to 0.03, e.g., Valcor's Model 20-2-3 (Valcor Scientific, Springfield, NJ) are not fully satisfactory due to the high viscosity of the solutions used for cryopreservation (causing difficulty aspirating viscous fluid through <b>S1-S3</b>), the high flows desired for controlling dead times and for perfusing larger organs, the possibility of clogging, and the buildup of pressure between the circuit pump and <b>S8-S12.</b> The detailed actuation pattern of the solenoids is described below. The solenoids inside the refrigerated cabinet that are not held in the solenoid block, <b>SR1, SR31</b> and <b>SR32,</b> are described in more detail below.

An effluent distribution block (EDB) <b>124</b> (Figure 1A) is connected to the output side of the organ container <b>122</b>. The EDB is designed so that a small amount of effluent is always present at the bottom of the block. This residual fluid is withdrawn by the two-channel "delta R.I. pump" <b>126</b> and sent to the differential refractometer ("delta R.I. meter") <b>130</b> where its refractive index (a measure of concentration) is compared to that of the perfusate from refractometer loop <b>L1</b> (pumped at the same rate as the venous effluent sample) and a difference signal generated and sent to the computer. Since the fluid in the refractometer loop <b>L1</b> will approximate the concentration of the fluid entering the artery of the organ, the delta R.I. output provides an estimate of the arterio-venous concentration gradient across the organ. When this gradient is large (in either the positive or negative direction), the organ is far from equilibrium. When the gradient is zero, the organ is at least largely in osmotic equilibrium with the perfusate. The nonlinear baseline resulting from this unorthodox use of the differential refractometer is accounted for in the software for running the perfusion program.

All effluent from the organ (together with the arterial fluid sampled by the delta R.I. pump) is ultimately collected by the recirculation pump <b>128</b> and sent to solenoid <b>S8,</b> which controls whether the effluent is recirculated to the reservoirs or discarded. Effluent to be returned to a reservoir is combined with the fluid flowing through the refractometer loop <b>L1</b> at a T connection <b>T2.</b> As noted above, return to the correct reservoir is then controlled by the actuation of solenoids <b>S9</b> through <b>S12.</b>

The recirculation pump <b>128,</b> like the circuit pump <b>102,</b> need not require flow adjustment. It is normally set to a rate sufficient to exceed the maximum flow through the organ pump <b>108.</b> Since the output of the recirculation pump exceeds that of the organ pump, air is continually introduced into the tubing leading to solenoid <b>S8</b> and usually to the reservoirs <b>R1-R4.</b> Provisions to prevent excessive bubbling of the reservoirs as a result of this are described below.

Although the delta R.I. pump speed can be changed, it is usually kept constant throughout an experiment. In the presently operative version, it has not been under computer control, but computer control would be a desirable option in some cases. The delta R.I. pump employs very small diameter polyethylene tubing to reduce delays in fluid transit time. This small tubing is particularly important because the flow rate through the delta R.I. circuit is limited by the lowest flow rate through the organ, which may be small, and by the limited size of the fluid paths in commercially available differential refractometers.

The return of the differential refractometer output to the organ effluent line is proximal to the effluent recirculation pump. This placement rather than placement distal to the pump ensures a steady flow through the differential refractometer, whereas distal placement may prevent or alter differential refractometer flow by virtue of a higher exit pressure.

An important element of the fluidic circuit is the gradient pump <b>132</b> connected to the circuit by a line <b>P1</b> (Figure 1A). The function of the gradient pump is to allow for gradual changes in concentration within the appropriate reservoirs within the cabinet. The method by which this is accomplished will be described below. The placement of the line <b>P1</b> to the gradient pump at <b>T3A,</b> just after the point of joining of the refractometer loop <b>L1</b> and the organ loop <b>L2,</b> presents one option for ensuring the removal of some of the air introduced by the organ effluent recirculation pump <b>128</b> and therefore helps reduce bubbling of the reservoir fluid.

A better option, however, and the one presently used, is to draw no air into line <b>P1.</b> This is accomplished by connecting <b>P1</b> at point <b>T3B</b> and results in fully controlled concentration-time histories. The bubbling problem is then overcome by continuously regulating the speed of the recirculation pump <b>128</b> to be just slightly in excess of the combined flows of the organ pump <b>108</b> and the delta R.I. pump <b>126</b> so as to introduce little air. Attaching the recirculation output of <b>S8</b> directly to <b>P1</b> without regulating the speed of pump <b>128</b> results in degraded concentration control and is not recommended.

The present operative version uses silastic tubing of 1/8 inch diameter throughout the system, which is sufficient to accommodate the needed flows and is preferred. Silastic is compatible with Actril™ (Minntech, Minneapolis, Minnesota) cold sterilant, is translucent (important for visualizing flow to detect problems and for observing any signs of microbial growth), is impervious to common cryoprotective agents such as dimethyl sulfoxide, and is soft enough to be easily manipulated. However, silastic tubing should not be used in circuits coming into contact with silicone cooling fluids, which swell and weaken silastic tubing. In addition, C-Flex® tubing (Cole Palmer Instrument Co., Chicago, IL) should be used in the pump heads due to its greater strength (silastic tubing undergoes spallation) and greater flexibility when cold.

Reservoir <b>R1</b> is constructed as a gradient former (Figure 2). Essentially the gradient former consists of two concentric cylinders, an outer cylinder <b>200</b> and an inner cylinder <b>201.</b> A fluid path <b>205</b> allows fluid to flow from the outer cylinder <b>200</b> to the inner cylinder <b>201</b> under the influence of gravity in response to a reduction of volume in the inner cylinder. The concentric orientation of the fluid compartments is very space efficient. The fluid delivery line <b>204</b> corresponds to the line <b>D1</b> of Figure 1A. The unit shown is a modification of a commercially available gradient former. The necessary modifications for the execution of this invention are as follows. <ul id="ul0004" list-style="none" compact="compact"><li>1) The stopcock normally used to control flow from the outer cylinder to the inner cylinder in the commercial device is replaced by a pinch-type two-way (on/off) solenoid valve <b>202</b> (currently, a Bio-Chem Valve Corp. model 100P2WNC, East Hanover, NJ) (Figure 2C). A pinch-type valve is preferable for this application to a piston-type valve because of the small pressure difference available to drive fluid flow and the consequent need for a large working diameter fluid path <b>202b.</b> It is also preferable for easy removal from its tubing <b>202b</b> when the reservoir is to be removed from the cabinet for cleaning, leaving the solenoid behind. The base of the gradient former has been modified, at <b>203,</b> to make room for the solenoid and to support it on a platform. Platform <b>203</b> is equipped with a vertical metal post <b>203b.</b> Solenoid <b>202</b> is lashed to this post with a rubber band so as to keep the solenoid oriented correctly. The solenoid is located a sufficient distance from the reservoir to avoid excessive heating of the reservoir fluids.</li><li>2) The diameter of the fluid path <b>205</b> from the outer cylinder <b>200</b> to the inner cylinder <b>201</b> has been enlarged to permit flow at an adequate rate of the viscous solutions required for organ cryopreservation. An inner diameter of 1/8 to 3/16 inch is adequate.</li><li>3) A lid <b>206</b> has been provided (Fig. 2B). The lid has an outer overhang <b>207</b> that prevents the lid from moving from side to side after it is placed on the cylinder as well as concentric grooves into which the wells of <b>200</b> and <b>201</b> fit. The lid has built-in outer and inner filling funnels <b>208a</b> and <b>208b</b> with removable lids, and a recirculation port <b>209.</b></li><li>4) Funnels <b>208a</b> and <b>208b</b> extend into respective internal fill tubes <b>210a</b> and <b>210b.</b> The internal fill tubes are preferably rigid hollow rods located next to the wall of the inner and outer cylinders and are perforated at 1-2 cm intervals with holes <b>211a</b> and <b>211b,</b> respectively, which are approximately 3 mm in diameter. The function of the fill tubes is to reduce the creation of bubbles as recirculating fluid impacts the surface of the liquid in the reservoir. The purpose of the perforations is to enable air to escape from the tube through the perforations so as not to force air to the bottom of the reservoir to form bubbles. These functions are particularly important in perfusates containing protein, which tend to stabilize bubbles.</li><li>5) A fill mark has been provided to enable the reservoir to be filled reproducibly to the same, predetermined volume. The operator can establish his/her own fill mark depending upon the details of the application. The gradient formers may have approximate graduations (horizontal lines on both the inner and outer cylinders, aligned so as to permit avoidance of parallax error in reading the liquid level in either cylinder) spaced approximately 0.5 cm apart for a 2 liter gradient former. These graduations are also important for establishing slight, deliberate mismatches in liquid level between inner and outer cylinders, which are necessary to prevent premature mixing of solutions of widely differing densities, such as cryoprotectant-free perfusate and vitrification solution. They also permit a rough quantitative check by the operator on the progress of the gradient as represented on the computer screen.</li><li>6) The plastic composition of commercially available gradient formers may create problems for certain types of cryoprotectant, which could conceivably attack the plastic. It is therefore preferred to use reservoirs made of transparent material (e.g., glass, plexiglass or the like) that is compatible with the cryoprotectant chemicals or use reservoirs whose surfaces have been siliconized or otherwise treated to prevent the attack. In the inventors' experience, acrylic has been found to be an acceptable material.</li><li>7) The reservoir <b>R1</b> contains a stir bar <b>212.</b> The stir bar is housed in a jacket <b>213</b> attached to a freely spinning vertical pin <b>214</b> extending to the stir bar from the lid of the reservoir to prevent the jacket, and hence the stir bar, from moving laterally. This change is necessary to make sure chattering, and therefore poor mixing, does not occur while the perfusion machine is unattended. Support from above rather than below prevents unnecessary perfusate frictional heating and wear and tear to the floor of the reservoir.</li></ul>

Reservoir <b>R3</b> is also constructed as a gradient former. The details of reservoir <b>R3</b> are shown in Figure 3. Reservoir <b>R3</b> contains an outer compartment <b>315</b> (<b>R3</b>_<b>3</b>), an inner compartment <b>318</b> (<b>R3</b>_<b>1</b>), and a third intermediate compartment <b>316</b> (<b>R3</b>_<b>2</b>). Intermediate compartment <b>316</b> is connected to inner compartment <b>318</b> through a fluid conduit <b>320</b> controlled by a solenoid <b>317</b> (<b>SR3</b>_<b>1</b>). Compartment <b>316</b> also connects to outer compartment <b>315</b> by a fluid conduit <b>321</b> controlled by a solenoid <b>319</b> (<b>SR3</b>_<b>2</b>). The use of an outer compartment is necessary when concentration is being reduced to zero or nearly zero, for reasons noted below in the discussion of the function of the gradient pump and the action of the gradient formers. The use of an outer compartment is greatly preferred compared to a middle compartment having a larger volume of fluid (and no outer compartment) because simply increasing the volume of fluid in the middle compartment would cause the concentration profile resulting from a constant gradient pump <b>132</b> flow rate to become non-linear. Control of concentration-time history would then become more complicated. More importantly, an excessive amount of fluid in the middle compartment would be required to approach a zero concentration in the circuit compared to the amount of fluid required in the outer compartment after virtual emptying of the inner and middle compartments.

Automated use of reservoir <b>R3</b> poses some problems which are successfully addressed in part by software and in part by the specific construction of <b>R3.</b> Specifically, actuation of solenoid <b>SR3</b>_<b>2</b> allows fluid in the outer compartment (<b>R3</b>_<b>3</b>) to flow first into the middle compartment (<b>R3</b>_<b>2</b>) and from this compartment to the inner cylinder (<b>R3</b>_<b>1</b>). This is because the pressure head present between <b>R3</b>_<b>3</b> and <b>R3</b>_<b>2</b> is large when <b>R3</b>_<b>1</b> and <b>R3</b>_<b>2</b> are nearly empty, which occurs when <b>SR3</b>_<b>2</b> is activated. At this point, <b>R3</b>_<b>3</b> is still full. This large pressure head causes fluid to flow too rapidly into <b>R3</b>_<b>1</b> if <b>R3</b>_<b>3</b> is connected directly to <b>R3</b>_<b>1</b> rather than using <b>R3</b>_<b>2</b> as a buffer between <b>R3</b>_<b>3</b> and <b>R3</b>_<b>1</b><b>.</b> By adjusting the level of <b>R3</b>_<b>3</b><b>,</b> the flow can also be partially controlled. But even with these two precautions, further control of flow is required by using an appropriate duty cycle for <b>SR3</b>_<b>2</b><b>.</b> The flow to <b>R3</b>_<b>1</b> should be slow at first and more and more rapid as the concentration is brought closer and closer to zero, whereas passive flow under the influence of gravity will always be fastest at first and slowest at the end unless the flow is metered by the sort of tailored duty cycle currently being imposed on <b>SR3</b>_<b>2</b><b>.</b>

The other modifications to <b>R3</b> resemble those of <b>R1.</b>

Reservoir <b>R4</b> is a gradient former constructed in the same manner as <b>R1.</b>

The purpose of the gradient pump <b>132</b> is to remove some of the recirculating fluid from the circuit. This removal of fluid causes the flow rate of fluid back to the reservoir of origin to be less than the flow rate of fluid from this reservoir to the circuit. This causes the level in the inner cylinder of the reservoir (<b>R1, R3</b>, or <b>R4</b>) to go down. This lowering of inner cylinder fluid level in turn causes the fluid in the outer or middle compartments to flow into the inner cylinder to keep the two levels similar. Thus the two dissimilar concentrations in the two cylinders are mixed in the inner cylinder, generating the concentration gradient which is then sent to the rest of the circuit. This is the manner in which the gradient pump effects the desired gradual changes in concentration which reach the organ and the refractometers. Any necessary adjustments to the gradient pump speed are made by the computer.

The principle involved is that of an ordinary linear gradient former in which the portion of the circuit external to the gradient former can be regarded, to a first approximation, as extra volume in the inner cylinder. Withdrawal and discard of fluid from the inner cylinder at a constant rate will result in a linear molar concentration change with time despite the presence of the rest of the circuit and the recirculation of fluid back to the reservoir. However, unlike an ordinary gradient former, the concentration of fluid leaving the gradient former at the moment the volume in the gradient former becomes zero will not be equal to the concentration of fluid in the outer (or middle) cylinder of the gradient former. Therefore, in order to approach a concentration of zero during cryoprotectant washout using an ordinary two-compartment gradient former, it is necessary to add additional fluid to the outer cylinder while continuing to discard fluid from the inner cylinder normally. This is why <b>R3</b> has been modified to have a third compartment. The extra fluid required to continue cryoprotectant washout is added from this third compartment by the computer more accurately than a human operator could accomplish this task manually. During introduction of cryoprotectant, on the other hand, the desired final concentration can always be reached by using a concentration in the outer compartment which significantly exceeds the final concentration desired in the circuit at the end of the gradient. Since the current method involves an upward step change in concentration (see below), it is convenient to fill <b>R1'</b>s outer compartment with the same fluid used in <b>R2.</b>

The <b>HBM</b> heat exchange system is shown in detail in Figures 4A-E.

Perfusate enters the <b>HBM</b> through an entry port <b>403,</b> travels through a central channel <b>400,</b> and leaves the <b>HBM</b> via an outlet port <b>406.</b> On either side of the central perfusate path are separate chambers for regulating temperature. The two innermost temperature control chambers <b>401</b> (one on each side of the perfusate path) are used for the circulation of coolant, while the outer chambers <b>402</b> are a pathway for the flow of room temperature fluid for offsetting the coolant. (For specialized applications involving, for example, normothermic perfusion, these pathways can be reversed.)

The direction of cold fluid flow is optional. Adequate temperature control has been found when all fluids (perfusate, coolant, and warming fluid) flow in the same direction (uphill) despite the lack of countercurrent heat exchange. This mode allows the avoidance of air or carbon dioxide accumulation in the outer chambers.

Perfusate enters the bottom of the <b>HBM</b> unit through inlet <b>403</b> and travels upward in a zig zag pattern. It emerges into a small upper reservoir which has an air space above: this is the bubble trap area <b>404.</b> Perfusate then travels beneath the bubble trap and goes through a perfusate mixing area <b>405</b> before finally traveling onward to the arterial outlet.

The inlets for cold <b>407</b> and warm <b>408</b> fluid are each split into two channels within the base of the unit. The outlets <b>410, 411</b> for warm and cold fluid, respectively, each receive fluid collected from two channels such that each channel of the same kind (i.e., each cold channel or each warm channel) is the same length and nominally experiences the same pressure difference from start to finish, so that flow rate through each like channel should be approximately equal.

All of the cold and warm fluid pathways include a length of flexible tubing <b>412</b> at the rear of the unit. These tubing segments serve two purposes. First, by introducing an air gap between the four channels, heat exchange between them is minimized. This is particularly desirable when all of the cold and warm fluid is flowing in the direction opposite to that of perfusate flow (i.e., in orthograde direction) and has not already undergone heat exchange with the perfusate. Second, each tube can be clamped. In this way, if by chance one cold channel or one warm channel should take all of the cold or warm fluid delivered while the other channel "airlocks", this situation can be corrected by clamping the channel receiving all of the flow and purging the air out of the inactive channel, bringing each channel into full function and equal flow.

Because in the orthograde mode the temperature conditioning fluid enters the heat exchanging portion of the unit at the top and exits at the bottom, it is necessary upon installation to run the cold and hot pumps in retrograde direction in order to purge all air out of the cold and warm channels. This is best accomplished if the cold and warm tubing leading to and from the bath is no more than about 1/8 inch in internal diameter, since at this diameter fluid flow will displace air from the tubing rather than allowing it to flow uphill in a direction opposite to the direction of fluid flow or otherwise to remain unpurged in various parts of the tubing. Thus, when the pump direction is reversed again from retrograde to orthograde, no air will be present in the tubing and none will be trapped in the heat exchange chambers of the unit.

In addition to serving a heat exchange function, the zig zag pattern is also designed to force mixing of previously perfused dense perfusate or, when perfusate density is rising rather than falling, to purge the less dense perfusate from the perfusate path.

As the perfusate emerges from the zig zag heat exchange area, it enters the bubble trap <b>404</b> at trap entry area <b>418.</b> Perfusate exits the bubble trap through exit region <b>419.</b> The zig zag pattern, in fact, is also designed to allow any air bubbles to exit the heat exchange area and to emerge into the bubble trap area. The bubble trap area is designed to have the following features. <ul id="ul0005" list-style="none" compact="compact"><li>1. Its volume is sufficiently large to reduce the pulsatile action of the perfusion pump to a minimum by distributing the shock of each stroke over a relatively large air volume. This simplifies pressure control and measurement and may be less damaging to the organ.</li><li>2. Its volume is sufficiently low to minimize the liquid volume present in the trap and thereby to minimize the dead time and dead volume between the organ pump and the organ itself. A minimal volume is also desirable to minimize layering of more dilute perfusate over more dense perfusate.</li><li>3. A pressure sensing port <b>413</b> is provided. Port <b>413</b> has no fluid connection to the perfusate, thus eliminating a "blind alley" in which fluid cannot be mixed properly or in which disinfectant might fail to penetrate or might be trapped. Both an electronic pressure transducer (to provide a signal to the computer) and a sphygmomanometer gauge (for calibration and visual checking) are used.</li><li>4. The lid <b>414</b> of the trap is removable for cleaning.</li><li>5. A vent port <b>416</b> is provided which is used to adjust fluid level in the trap so as to make it the minimum required to serve the bubble trap function and to maximize pressure wave damping. The tubing from this vent leads to the outside of the cabinet, permitting adjustments to be made without opening the cabinet door.</li><li>6. A third port <b>417</b> is provided through the bubble trap lid to permit the injection of drugs, vascular labeling materials, fixative, etc.</li><li>7. The walls of the bubble trap are angled near the trap entry and exit points <b>418, 419,</b> respectively, to produce a certain amount of mixing of the perfusate both as it enters and as it leaves the trap, and to break up and minimize the volume of layers of dilute perfusate overlying more dense perfusate.</li><li>8. The option exists of introducing probes, such as a temperature probe via one of the ports in the trap lid to make measurements in the perfusate without permanent embedding of the sensor: the port consists of flexible tubing attached to a plastic threaded fitting. A probe can be freely admitted or withdrawn and the tubing clamped with hemostats or an equivalent clamp to effect a pressure-tight seal. This simplifies removal and reinstallation of the <b>HBM</b> when it must be cleaned and allows flexibility in probe selection and the opportunity of using the probe for other measurements elsewhere.</li></ul>

After leaving the bubble trap, the perfusate descends to a mixing area <b>405</b> (see Figure 4D). The basic unit of the 3-unit mixing path is a narrow horizontal entry area <b>HE</b> emerging into a "wide" basal area <b>BA</b> which rises to an area of flow restriction <b>FR</b> and ends in a descent <b>D</b> to the next horizontal entry area. Fluid entering <b>HE</b> is forced through an opening too small to support much layering of low density fluid on top of high density fluid, especially considering the right angle turn required just before <b>HE.</b> Fluid flowing into <b>BA</b> may, if less dense, rise immediately upward toward <b>FR.</b> If more dense, it may be driven into the wall and rise upward along this wall. Upon encountering <b>FR,</b> however, the denser liquid will be accelerated toward the less dense liquid rising directly from <b>HE,</b> creating turbulence and mixing. If <b>BA</b> fills with dense perfusate, again the speed of the fluid flowing directly upwards at <b>FR</b> should cause the dense liquid to mix with any low density fluid layered above <b>FR.</b> Furthermore, the narrow descending path <b>D</b> should draw layered liquid down the angle along with denser liquid, again preventing stagnant layers from persisting. In practice, three such mixing units aligned in series as shown in Figure 4B are sufficient to mix initially very poorly mixed perfusate, which is encountered frequently in the course of abruptly raising or lowering cryoprotectant, concentration. One final function of the mixing units is to serve as a trap for any small bubbles which for any reason are not removed in the bubble trap area. (Bubbles in the mixing area are, however, easily purged by the operator prior to initiation of organ perfusion.)

After leaving the mixing region, the perfusate descends to an outlet port <b>406</b> leading directly to the organ. The path from the final mixing unit to port <b>406</b> is deliberately created at an angle to the horizontal in order to provide one last chance of stopping any bubbles from reaching the organ, since in order to reach the organ a bubble in this pathway would have to flow downhill, contrary to its tendency to flow uphill.

The mixing area and subsequent areas are purged of air by occluding the outlet tubing affixed to port <b>406</b> with the vent open until approximately 1/2 inch of fluid has accumulated in the bubble trap. The vent is then closed until the pressure has reached about 60-120 mmHg. Finally, fluid is once again allowed to flow freely through port <b>406.</b> The jet of fluid through the mixing area and out port <b>406</b> sweeps all air out of the fluid path from the bubble trap to port <b>406</b>. If some air persists, it can be removed by repeating the process. After air has been purged, the vent is opened to allow unnecessary fluid in the bubble trap to exit the trap under the influence of gravity, reaching a final depth of about 1/8 inch. A final depth of 1/8 inch cannot be set before purging the line of air because insufficient volume exists to avoid refilling the mixing area with air from the bubble trap during the purging process.

The <b>HBM</b> is designed to require removal for cleaning only infrequently. Disinfection and removal of disinfectant from the bubble trap area is effected automatically but presently requires some operator attention afterwards to ensure that all uppermost exposed surfaces are disinfected and later washed free of disinfectant without contaminating the outlet tubes. The option exists of arranging the outlet tubes at <b>413, 416,</b> and <b>417</b> in such a way that, with specific solenoids attached to them, they could be individually purged with water, disinfectant, and air under automated control, thus relieving the operator of the need for diligence in cleaning the bubble trap.

After the perfusate exits the <b>HBM</b> unit through port <b>406,</b> it enters the organ in the organ container <b>122</b> (Fig. 1). In the preferred embodiment, the organ container comprises a rectangular box with a hinged lid, lid stop, lid handle, sloped floor, specially sloped feet, arterial and venous thermocouple inlets, perfusate inlet, and effluent outlet in the foot opposite the inlet. The slope of the floor is downward in both the right to left and the back to front directions to ensure that all fluid runs to the foot outlet with very little fluid accumulation anywhere in the container. One needle probe is inserted directly through the wall of the arterial line. A second probe is placed directly in the stream of fluid emerging from the organ. In typical results, the arterial and venous temperatures differ by only tenths of a degree, but both are useful for quality control. The organ container may employ a soft mesh support for the organ similar to that used in the MOX-100 DCM™ organ cassette (Waters Instruments Inc., Rochester, Minnesota) or the organ can be placed directly on the floor of the organ container or on a specially designed independent and removable support. The latter option is preferred and is presently in use.

The organ container <b>122</b> and the organ pump <b>108</b> are placed in maximum proximity to reduce dead times and dead volumes between the two, and the tubing leading from the organ pump to the organ container is chosen to be as small in inner diameter as possible for the same reason.

Most perfusate does not go through the organ loop <b>L2</b> as described above but travels instead from the filters to the in-line analog refractometer <b>106</b>. The presently preferred embodiment of the invention uses a modified commercially available refractometer from Anacon Inc. (Burlington, Mass.). In particular, small diameter tubing inlet and outlets are used rather than the very large standard Anacon pipe fittings.

The modification of the refractometer sensing head appropriate for the execution of the invention could also contain the following additional changes from the ordinarily available Anacon unit. <ul id="ul0006" list-style="none" compact="compact"><li>1. The internal volume of the fluid path could be further minimized.</li><li>2. Presently, it is necessary to purge the air space of the unit with a slow flow of dry nitrogen gas to prevent condensation of moisture due to the low temperatures and high humidities prevailing in the cabinet. In a modified version, the electronics area of the sensing device could be hermetically sealed with some desiccant inside to eliminate the need for a nitrogen purge.</li><li>3. The present unit must be oriented with the fluid flow direction being vertical and upwards. However, the unit is not built to be used in this orientation, and body changes could be made to adapt the unit's shape to this orientation.</li></ul>

The apparatus for the execution of the invention allows the operator to access reservoirs in any sequence and to otherwise custom-design the process which may be of interest. The operator is even free to switch solenoid positions depending on what he may want to do. Nevertheless, the following nominal application illustrates the actuation patterns required to deliver fluid from and to each individual reservoir and filter. It also illustrates the "standard protocols" for organ cryoprotectant perfusion and for cleaning of the system which the system was designed primarily to carry out.

Solenoid <b>S1</b> admits fluid from <b>R1</b> when off, or from <b>R2</b> when activated. Solenoid <b>S2</b> is open to <b>R3</b> when not energized, or to <b>R4</b> when energized. The output of <b>S1</b> and <b>S2</b> is to <b>S3,</b> which accepts fluid from <b>S1</b> (that is, from <b>R1</b> or <b>R2</b>) when in the resting state and which accepts fluid from <b>S2</b> (i.e., from <b>R3</b> or <b>R4</b>) when activated. The common outlet for <b>S3</b> (always open) leads to the circuit pump <b>102,</b> which then withdraws fluid from the solenoid-selected reservoir.

If differential filters are to be included, then the output of the circuit pump <b>102</b> is to <b>S4</b>'s common port (always open). When <b>S4</b> is not energized, its output is directed to filter <b>F1.</b> The return from filter <b>F1</b> returns to the normally open port of <b>S5</b> and exits through the <b>S5</b> common outlet to the refractometer loop <b>L1</b> and the organ loop <b>L2.</b> If, on the other hand, <b>S4</b> is energized, then its output is directed to the common inlet port of <b>S6</b>. When <b>S6</b> is in the resting state, its output is directed to filter <b>F2,</b> and the return from filter <b>F2</b> enters <b>S7</b> through its normally open port. The output from <b>S7</b> travels to the normally closed port of <b>S5,</b> which must be energized to accept this output. Once fluid has entered <b>S5,</b> it flows out the <b>S5</b> common outlet to the refractometer loop and the organ loop. Finally, if <b>S4</b> is energized and <b>S6</b> is also energized, fluid will be directed through both of these valves and will reach filter <b>F3.</b> The return from filter <b>F3</b> occurs via the energized <b>S7</b> and the energized <b>S5</b> solenoids and goes to the two loops <b>L1</b> and <b>L2</b> as above. As noted earlier, the use of filters <b>F2</b> and <b>F3</b> and therefore of solenoids <b>S4, S5, S6,</b> and <b>S7</b> is optional and will be useful primarily when very abrupt changes from one solution to another are required, or when particularly heavy particulate contaminates must be removed.

Effluent from the organ eventually returns to <b>S8.</b> If <b>S8</b> is activated, the fluid is discarded. If <b>S8</b> is not activated, the fluid is directed from <b>S8</b> to combine with fluid from the refractometer loop and is returned to a desired reservoir.

Fluid traveling through the refractometer loop travels successively to solenoids <b>S9, S10, S11,</b> and <b>S12</b> and then to the waste line if none of these solenoids are energized. Energizing <b>S9</b> diverts flow to the <b>R1</b> recirculation line. <b>S10'</b>s activation (in the absence of activation of <b>S9</b>) diverts flow to <b>R2.</b> Similarly, selective activation of <b>S11</b> or <b>S12</b> will, respectively, recirculate fluid to <b>R3</b> or <b>R4.</b>

There are two basic processes of solenoid-actuated fluid control, one for actual perfusions and one for system cleaning and priming. The perfusion process typically proceeds from <b>R1</b> through <b>R4</b> whereas priming must occur in the reverse order to load the fluid uptake and fluid recirculation lines for reservoirs <b>R2-R4,</b> particularly if filters <b>F2</b> and <b>F3</b> and their associated lines are used, leaving the circuit primed with fluid from (typically) <b>R1</b> (or <b>C1</b>) at the end of the priming (or cleaning) process. The typical sequence of solenoid activations required to prime the complete system (or to clean it) is listed in tabular form below.

<i>Solenoid Control Sequence For Standardized Rinsing</i>/<i>Priming</i>

The conditions of the solenoid control processes are set forth in Tables 1 and 2. The uses of these control processes are to: replace perfusate with filter-sterilized H₂O at the end of the process; replace cleaning H₂O with chemical sterilant between perfusions; remove disinfectant using filter-sterilized distilled H₂O; remove water using air; remove air using reservoir fluid, i.e. prime the system.

When only <b>F1</b> (not <b>F2</b> or <b>F3</b>) is present, priming (and cleaning) may proceed in any order of reservoirs, provided, in the case of priming, that the final reservoir corresponds to the first reservoir used for the subsequent perfusion. Applicants now use a procedure involving momentary aspiration from <b>R2,</b> then <b>R3,</b> then <b>R4,</b> then <b>R1,</b> taking just enough time to prime <b>U2, U3, U4,</b> and <b>U1,</b> respectively, followed by computer/user interactive activation of <b>S12, S11, S10,</b> and <b>S9</b> to allow manual filling of <b>RL8, RL7, RL6,</b> and <b>RL5</b> by syringe with retrograde exhaust via <b>P1,</b> because this procedure saves large quantities of perfusate and is fast.

The standard process of solenoid actuation for withdrawing fluid from <b>R1-R4</b> and for creating gradients for a normal perfusion is as follows (assuming (1) use of optional filters <b>F2</b> and <b>F3,</b> (2) straightforward or typical use of the gradient-controlling solenoids, and (3) the existence of a gradient former as <b>R2</b>). The staged completion of a closed circuit upon going from one reservoir to another is to avoid recirculating solution of undesired composition to the new reservoir before its contents have displaced the previous solution from the circuit. If there is no problem with recirculating the previous solution, the precaution of delayed recirculation can be dropped. <tables id="tabl0001" num="0001"><img file="EP0777413B1_D0002.tif" /></tables><tables id="tabl0002" num="0002"><img file="EP0777413B1_D0003.tif" /></tables><tables id="tabl0003" num="0003"><img file="EP0777413B1_D0004.tif" /></tables>

The number of reservoirs could be less than or greater than the number specified here, with corresponding changes in solenoid number. Furthermore, the number of layers of <b>R1-R4</b> need not conform to the descriptions given above. The limits would be one reservoir at the least and perhaps eight reservoirs at the maximum, in which any reservoir could have from one to four compartments. The upper limits are based partly on volume and crowding constraints and partly on the improbability of any procedure complex enough to require more than 8 reservoirs for its control.

Another variation would be to employ different capacity reservoirs at different positions (e.g., instead of the herein preferred embodiment, one might have a 2-liter reservoir followed by a one-liter reservoir followed by a 3-liter reservoir followed by a one-liter reservoir, and so on).

In principle, the use of individual reservoirs could be abandoned in favor of one multicompartment reservoir consisting of perhaps four to twenty concentric cylinders each activated by solenoids or even by manual levers external to the temperature-controlled area, all stirred by a single central stir table. Abrupt or step changes in concentration could still be accommodated if the stepped change is not delivered via the stirred central area. The relative positions of the reservoirs could also change.

Finally, a fluid metering system could be employed rather than a gradient former. In this system, a pump would deliver concentrated cryoprotectant or diluent to a mixing reservoir rather than relying on gravity. This pump would be computer operated to adjust for departures from the programmed concentration. The gradient pump, however, would be retained in order to control overall circuit volume.

The arterial concentration sensor could be located proximal to, rather than distal to, the origin of the organ loop in the circuit, but should not be located proximal to the filters.

A pressure sensor to sense pressure developing on the circuit pump side of the filters could be incorporated as a warning device.

More generally, the device could be separated into two devices, the first for preparing organs for cryopreservation and the second for preparing previously cryopreserved organs for transplantation. The first device would omit R3 and R4 (and associated solenoids) while the second would omit R1 and R2 (and associated solenoids) while otherwise being substantially the same as the unified device. Given that cryopreservation and the recovery from cryopreservation may occur at different locations and under the direction of different individuals, this variation is likely to be of use under practical conditions. Essentially, these two devices would be identical except for the use of different software and the use of different reservoirs for adding and for removing cryoprotectant. Another usage could involve the unorthodox use of only two reservoirs to accomplish both loading and unloading, for example, loading could be done using R1 and R3 if only the inner compartment of R3 were used (R3 standing in for R2), and unloading could be done using R1 and R3 if R1 substituted for R4.

<i>II. Description of the Method</i>

<i>A. Preparing an Organ For Cryopreservation</i>

The complete cryopreservation method using the above-described apparatus comprises several parts. One part consists of the pretreatment of the donor organ prior to its removal from the donor to prepare the organ for its cryopreservation. Which is no part of this invention another part consists of the choice of the cryoprotective agents. Another part is the actual protocol for perfusing the cryoprotectant into the organ prior to its cryopreservation. Another part is the cryopreservation, storage and warming of the organ using appropriate techniques none of which are part of this invention. Another part which is no part of the invention is the protocol for removing the cryoprotectant(s) from the organ after its warming in preparation for transplantation into a recipient. Another part is treatment of the organ and the recipient upon organ transplantation, which, again, is no part of the invention. <tables id="tabl0004" num="0004"><img file="EP0777413B1_D0005.tif" /></tables><tables id="tabl0005" num="0005"><img file="EP0777413B1_D0006.tif" /></tables>

1. <i>Cryoprotective Agents: Formulae of the Vitrification Solutions V49, V52, V55, V49B and V55B</i>

All perfusion experiments were carried out using solutions designated here by V49, V52 and V55 (V49 has sometimes been referred to as VS4. V55 has been referred to as VS41A.). At low cooling rates (5-10°C/min) V49 was found to vitrify at 1,000 atm of applied hydrostatic pressure but not at ordinary ambient pressures. V52 was inferred to vitrify at 500 atmospheres (atm) of applied pressure. V55 was found to vitrify at 1 atm.

V49 was composed of dimethyl sulfoxide (D), formamide (F), and 1,2-propanediol (P) such that the mole ratio of D to F was 1:1, the total mass of D+F+P per liter was 490 grams, and the total mass of P per liter was 150 grams. Thus, per liter, D + F = 340 grams, F = 124.33 grams, and D = 215.67 grams. This mixture of cryoprotectants was preferred based on the results described below. Acceptable variations for the proportions of D, F, and P are: D:F weight ratio can be as low as 1.4 and as high as 3.5; for the former, the proportion of P:(D + F) should be elevated to 18:34 and/or the total concentration raised to 50-51% w/v (grams/deciliter) by the addition of extra P.

The formula for V52 was obtained by multiplying the cryoprotectant content of V49 by 52/49, keeping the vehicle solution the same as for V49. The formula for V55 was obtained by multiplying the cryoprotectant content of V49 by 55/49, keeping the vehicle solution the same as for V49. Thus, the total concetnration of solutes in V55 was 550 grams/liter vs. the 490 grams/liter of V49. V49B was a variation of V49 in which the 1,2-propanediol content was replaced gram for gram by 2,3-butanediol (levorotatory form or racemic mixture with less than 5% w/w meso form present), and V55B was, similarly, a variation of V55 in which 2,3-butanediol replaced the 1,2-propanediol gram for gram. The total cryoprotectant molarities of V49, V52 and V55 were 7.49, 7.95 and 8.41M, respectively. The molarities of V49B and V55B were slightly lower than those of V49 and V55 due to the greater molecular weight of butanediol vs. propanediol.

While not wishing to be bound by any theory, V49 and V55 appear to be particularly beneficial due to the exceptional ability of formamide to penetrate kidney tissue, the ability of dimethyl sulfoxide to block the toxicity of formamide, the beneficial balance between the three ingredients (maximizing vitrification tendency while minimizing both toxicity and total solute concentration), the lack of a colloid (typical colloid concentrations of about 4-7% w/v elevate viscosity), the extraordinarily slow rate of devitrification of these solutions at appropriate pressures (1,000 atm and 1 atm, respectively), and the good stability of V55 at -135°C during at least 6 months of storage.

The cryoprotectants used for organ perfusion were adjusted between the limits represented by V49 and V55, depending upon the pressure to which the organ was to be subjected. Balancing an organ's tolerance to high pressures and its tolerance to high cryoprotectant concentrations allowed optimization of the tradeoff between pressure and concentration required to maintain vitrifiability. For example, an organ that cannot tolerate 1,000 atm but that can tolerate 500 atm may be perfused with V52. Concentrations in excess of 550 grams/liter, to a maximum of about 600 grams/liter, may be used when heterogeneous nucleation on cooling is a significant problem, since the nucleation process and the growth of any nucleated ice crystals will be suppressed at these higher concentrations. One example of a situation in which this problem will arise is the vitrification of very large organs such as the human liver that will cool particularly slowly. At elevated pressures, similar proportional increases in solute concentration will be required as the cooling rate is lowered.

Experiments (see results below) with kidney slices indicated that V49B provided viability identical to the viability obtained with V49. V49B may have greater stability than V49. Variations between V49B and V55B are to be used as per the descriptions above for V49 and V55.

All cryoprotectant solutions must contain, in addition to the cryoprotectants themselves, slowly-penetrating solutes comprising the "carrier" or "vehicle" solution for the cryoprotectants. Typical examples would be modified UW solutions, Euro Collins solution, or Renal Preservation Solution 2 (RPS-2) (see Table 3). The best mode method used Euro Collins as the vehicle solution of choice for kidneys, modified UW solution (as per Table 3) as the vehicle solution of choice for the liver, and commercial UW solution (Viaspan®) (E.I. DuPont and Nemours) as the vehicle solution of choice for hearts.

2. <i>Protocol for Perfusing the Organ with Cryoprotectant</i>

Typical protocols for cryoprotectant introduction that were shown to yield reliable, high-quality survival of rabbit kidneys after cryoprotectant washout, transplantation, and long-term functional and histological follow-up were divided into at least 4 discrete phases. Prior to Phase (a) was an equilibration period during which the organ established stable baseline characteristics prior to the introduction of cryoprotectant. Phase (a) was a gradual increase in cryoprotectant concentration that ended in a concentration plateau known as phase (b). After spending a certain amount of time in phase (b), during which time the A-V cryoprotectant concentration gradient usually became approximately zero, the concentration was stepped in phase (c) to a new plateau, this new plateau phase being phase (d). As described in more detail below phase (d) is not the highest concentration attained. For example, the phase (d) concentration is 6.7 M, but the final concentration in the experiment was actually 8.4 M. <ul id="ul0007" list-style="none" compact="compact"><li><b><i>a) Perfusion pressure:</i></b> The organ was perfused at pressures sufficient to overcome the organ's critical closing pressure but otherwise low enough to avoid needless damage to the vascular tree. For example, the best mode perfusion pressure for the rabbit kidney was 40 mm Hg without significant pulsation. A desirable range of acceptable pressures has been found to be 20-70 mm Hg for different organs and species, including man, except for the liver. The liver normally receives most of its flow through a vein at a pressure typically below 10 mm Hg. Rat livers perfused at 5 mm Hg were able to achieve approximate osmotic equilibration after perfusion with V49 for 20 min when no colloid was present, and half of these livers supported life after transplantation. Consequently, the pressure limits for livers are 5-40 mm Hg through the portal vein, and 5-70 mm Hg through the hepatic artery.</li><li><b><i>b) Initial perfusion</i></b> prior to phase (a): In the best mode protocol, perfusion was first carried out for 15 min to establish baseline values for vascular resistance and calibrations (for pressure and refractive index); to ensure complete blood washout; and to thermally equilibrate the organ, here the rabbit kidney or the rat liver. Clinically, the initial perfusion time is arbitrary, and can be adjusted (from zero minutes to 1-2 days or more) to meet the requirements of the organ procurement and transportation process. In Applicants' laboratory, the perfusate in this period was Euro Collins solution or RPS-2 for kidneys and a modified UW solution for livers. However, this initial perfusate could also be another stabilizing solution in a clinical setting depending upon the needs of the hospital or procurement team.</li><li><b><i>c) Initial temperature:</i></b> The initial perfusion temperature required for the procurement and transportation of an organ, such as, for example, the kidney, need not be identical to the perfusion temperature established prior to phase (a). For example, while most organs may be shipped while surrounded by crushed ice at 0°C, other organs may be shipped while being perfused at normothermia (37°C). When organs are ready for cryoprotectant administration, however, a preselected, standardized perfusion temperature is established. In the best mode, the initial perfusion temperature was 3.5-4°C, and the acceptable limits were 0-15°C. The inventors consider that organs requiring normothermic perfusion for best long-term maintenance can nevertheless be cooled to within this same temperature range and can be treated in a manner similar to that of hypothermically-preserved organs without damage within the relatively short times required for this method.</li><li><b><i>d) Phase (a):</i></b> Following the initial baseline perfusion, cryoprotectant concentration was elevated at a constant rate until a first plateau of concentration was established. When using a V49-type mixture of cryoprotectants, the proportions of different cryoprotectants in the mixture were held constant while the total concentration was allowed to change. The rate of increase in total concentration for V49-type solutions was set to about 51 mM/min (nominally 3 M/hr) in the best mode for the kidney, acceptable variations being 31-150 mM/min. These rates were considerably in excess of the 30 mM/min rates used by known techniques for glycerol and propylene glycol which were considered to be unnecessarily and undesirably slow for most applications of the method. Linear elevation of concentration promoted equilibration without creating unnecessarily large osmotic stresses.</li><li><b><i>e) Temperature reduction during phase (2):</i></b> The temperature was lowered during phase (2) to protect the kidney from the chemical toxicity of the cryoprotectant. In the best mode, the temperature reduction began as the arterial cryoprotectant concentration reached 1.3 M; acceptable limits are 0.5 M to 3.5 M. Temperature descent was terminated as phase (b) was reached. The concentration change during cooling was about 2.5 M in the best mode but may vary from about 1 M to 4.4 M. As noted above, the initial perfusion temperature should be between 0°C and 15°C. The temperature after cooling should fall within the range of -13°C to +5°C and the total temperature drop during cooling should be between 2°C and 25°C. Cooling should not continue to below the freezing point of the organ. In the best mode, the final arterial temperature was -3°C, representing a fall of 6.5°C from the initial temperature and a cooling rate of about 0.33°C/min. The overall cooling rate should not exceed 3°C/min in order to provide adequate opportunity for cryoprotectant diffusion and in order to avoid possible thermal shock to the organ. </li><li><b><i>f) Phase (b):</i></b> The phase (b) plateau was set in the best mode for the kidney at 25% w/v total cryoprotectant (250 grams/liter, or about 3.8 M) when 40-49% w/v cryoprotectant was to follow, or 30% w/v, (4.6 M) when higher concentrations (e.g., V55) were to follow, acceptable variations being 20-40% w/v or w/w. The phase (b) plateau was set to a level that was close to half of the phase (d) concentration. Lower phase (b) levels will increase osmotic stress upon moving through phase (c) to phase (d), whereas substantially higher phase (b) levels will produce increased toxicity due to longer exposure times to concentrated cryoprotectant. The duration of phase (b) was set to about 10 min in the best mode procedure, acceptable variations being 5-30 min, depending on perfusion pressure (and thus organ flow rate), vascular resistance, organ permeability to cryoprotectant, and the rapidity of toxic responses. The duration was long enough to allow the organ to at least approximately osmotically equilibrate with the arterial perfusate, as indicated by an arteriovenous concentration difference no greater than 50-200 M, so as to minimize unnecessary osmotic stress during the subsequent jump to higher concentrations.</li><li><b><i>g) Perfusion with vitrification solution by</i> a <i>two-step or three-step method:</i></b> A change in concentration from phase (b) to phase (d) was necessary in phase (c) to control the exposure time to highly concentrated cryoprotectant. The concentration at the end of phase (c) is insufficient for vitrification (requiring one or two additional steps to achieve vitrifiability). The concept behind the two- (and the three-) step approach is illustrated schematically in Figure 7. In a "one-step" approach, that is no part of the invention, all of the cryoprotectant was added in one continuous process (Cl), and cooling to cryogenic temperatures then occurred in one step (T1) as well. In the "two-step" approach of the invention, part of the cryoprotectant is added in the first step in phase (c), and the rest of the cryoprotectant is added in the second step in phase (f) carried out at temperatures near the freezing point of the solution used in the first step. In this approach, cooling also took place in two steps, the first step in phase (e) having been used to prepare for the second concentration increment in phase (f), and the second step in phase (g) being used to cool the organ to cryogenic temperatures. In practice, the first cooling step was preferably to temperatures somewhat above the nominal freezing points to guarantee the avoidance of crystallization prior to introducing higher concentrations of cryoprotectant. In the best mode, the phase (d) concentration was set to 40% (6.1 M) to 44% (6.7 M) w/v V49 solutes, a concentration that was not sufficient for vitrification (Figure 5). Acceptable variations for sub-vitrifiable concentrations are 30% w/v to 48% w/v V49 solutes or their equivalent. The concentration in phase (d) was held steady for 20 min in the best mode, acceptable variations being 10-60 min. The concentration should be held steady long enough for the organ to closely approach osmotic equilibrium with the perfusate according to the above-described criterion. For the two step approach, the organ was removed from the perfusion machine after the completion of phase (d), and was cooled in phase (e) by being placed into precooled vitrification solution for 5-30 min (5 min in the preferred mode for rabbit kidneys, longer for more massive organs) prior to being perfused with the vitrification solution in phase (f). In the best mode, the organs were cooled toward and subsequently perfused at a temperature of -22±2°C (if previously perfused with 6.1 M cryoprotectant) or -25°±2°C (if previously perfused with 6.7 M cryoprotectant). The temperature chosen at the end of step (e) will be referred to as the "low temperature perfusion temperature." More generally, the low temperature perfusion temperature may range from -5°C to -35°C. The inventors have perfused rabbit kidneys with V52 at -22°C or with V55 at -25°C at a perfusion pressure fluctuating between 20 and 40 mm Hg but usually not exceeding 30 mm Hg, having obtained excellent results after subsequent transplantation. Acceptable method limits for perfusion pressure range from 50% to 150% of the previous pressure in the perfusion apparatus for organs other than the liver, or from 50% to 400% of the previous perfusion pressure in the case of the liver. The time required for equilibration with vitrifiable concentrations at the low-temperature perfusion temperature was determined in the case of the kidney by collecting "urine" produced during the low-temperature perfusion and determining its osmolality after suitable dilution. The kidney was deemed to have been equilibrated when the osmolality of the urine approached the osmolality of the arterial perfusate. For other organs, the extent of equilibration is determined as usual by the arteriovenous concentration difference. Acceptable equilibration times were determined to range from about 20 to about 60 minutes. Another embodiment that will apply to organs which cannot tolerate exposure to fully vitrifiable solutions at the low-temperature perfusion temperature is the three-step introduction method. These organs may be successfully cryopreserved by perfusing a less-than-fully-vitrifiable concentration at the low-temperature perfusion temperature at the end of step (e) which concentration, being higher than the concentration used prior to cooling to the low-temperature perfusion temperature, will depress the freezing point of the organ to substantially (i.e., 3 to 20°C) below the low-temperature perfusion temperature. The organ can then be perfused with fully vitrifiable concentrations near the new organ freezing point temperature (step three), at which temperature the fully vitrifiable concentrations will be sufficiently nontoxic as to be tolerated. This embodiment will apply also to organs that require it for avoiding cooling injury. </li><li><b><i>h) Rationale for the two-step best mode method:</i></b> While not wishing to be bound by any theory, the main rationale for the best mode two-step method was the avoidance of cooling injury. Introducing cryoprotectant at the low-temperature perfusion temperature was hypothesized to reduce cryoprotectant toxicity as well. The inventors discovered that kidneys perfused at -3°C with V49 survived 100% of the time (14 survivors out of 14 perfusions) but when they were cooled to -30°C, warmed and washed out using the best techniques known at the time, the survival rate fell substantially (see Figure 9). Kidneys perfused with V52 at -3°C using the optimal techniques of the time survived 75% of the time, but when these kidneys were cooled to -30°C, the survival rate upon warming and washout was 0%. Thus, cooling caused injury at 49% w/v cryoprotectant and caused complete loss of viability at 52% w/v cryoprotectant. Since, ideally, organs should be preserved in V55 (to avoid the need for high pressures), this trend was unfavorable. However, a positive implication was that cooling injury might become negligible at concentrations lower than 49%, so that cooling to temperatures near -30°C might then be innocuous. This suggested the possibility of cooling at a relatively low concentration so as to avoid cooling injury and then raising the concentration to a vitrifiable level at the lower temperature. This approach would have the additional advantage of exposing the organ to vitrification solution at a temperature at which its toxicity should be reduced. Thus, by avoiding cooling injury, toxicity might also be avoided. A secondary point was that a variety of experiments on the phenomenon of thermal shock in both erythrocytes and kidney slices suggested that cooling injury below -30°C might be minimal even in the presence of V55 if cooling injury above -30°C were first prevented. Therefore, by first cooling to near -30°C in the presence of a concentration that does not cause cooling injury, it was inferred that even V55 might not cause fatal cooling injury when the organ was loaded with V55 at the low-temperature perfusion temperature and was subsequently cooled to below-30°C. As noted in the preceding section, the first hypothesis was verified in that the two-step approach successfully avoided cooling injury and the toxicity of V55 at -25°C. As noted in the results section, the second hypothesis was also verified in that fatal injury did not occur upon further cooling to below -46°C was also avoided. </li></ul>

3. <i>Cryopreservation of the Organ</i>

The next step of any practical cryopreservation procedure, such as vitrification, is to cool the organ to cryogenic temperatures using appropriate protocols, with or without prior pressurization. The cryopreservation step also includes the storage of the organ. The present invention is not concerned with the actual cryopreservation and storage of the organ, but only with the preparation of the organ for cryopreservation.

<b>A</b>

.

<i>Rabbit Kidneys.</i>

<i>1. Suitability of V49B-type Solutions.</i>

Viability data from rabbit kidney slices after treatment with V49 or V49B are shown in Table 4. <tables id="tabl0006" num="0006"><table frame="all"><title>Table 4</title><tgroup cols="2" colsep="1" rowsep="1"><colspec colnum="1" colname="col1" colwidth="78.75mm" /><colspec colnum="2" colname="col2" colwidth="78.75mm" /><thead valign="top"><row><entry namest="col1" nameend="col2" align="center"><b>Viability of Rabbit Kidney Slices Treated With V49 or V49B</b></entry></row><row><entry namest="col1" nameend="col1" align="left">Treatment</entry><entry namest="col2" nameend="col2" align="center">K/Na ratio of tissue* (mean +/- SEM)</entry></row></thead><tbody valign="top"><row><entry namest="col1" nameend="col1" align="left">V49</entry><entry namest="col2" nameend="col2" align="center">3.43 +/- 0.07†</entry></row><row><entry namest="col1" nameend="col1" align="left">V49B</entry><entry namest="col2" nameend="col2" align="center">3.27 +/- 0.12†</entry></row><row rowsep="1"><entry namest="col1" nameend="col1" align="left">   †p &gt; 0.05</entry><entry namest="col2" nameend="col2" /></row></tbody></tgroup><tgroup cols="2" colsep="0" rowsep="0"><colspec colnum="1" colname="col1" colwidth="78.75mm" /><colspec colnum="2" colname="col2" colwidth="78.75mm" /><tbody valign="top"><row><entry namest="col1" nameend="col2" align="justify">*The K/Na ratio was measured after washing out the cryoprotectants and incubating the cortical slices at 25°C for 90 minutes to permit active transport of K⁺ and Na⁺.</entry></row></tbody></tgroup></table></tables>

<i>B. Overcoming Cooling Injury at -46°C and Toxicity at 8.4 M Cryoprotectant</i>

When kidneys were treated with either 7.5 M or 8 M cryoprotectant using 3% HES during washout they were still unable to withstand cooling to -30°C (Figure 9). The 100% survival rate at 49% cryoprotectant fell to just over 50% as a result of cooling, and the 75% survival rate of the 8 M group fell to 0%.

Although some of this injury was due to the greater time required to allow cooling and warming to take place, tissue slice evidence indicated that cooling <i>per se</i> was actively detrimental. As seen in Figure 10, exposure of slices to 8 M cryoprotective agent at 0°C was considerably more damaging than exposing them to 6.1 M cryoprotectant at the same temperature (cf. bars 2 and 4), and cooling these 8 M slices to -23°C caused additional injury (cf. bars 2 and 3). Interestingly, however, cooling 6.1 M slices to -23°C did not cause additional injury (cf. bars 4 and 5). Even more interestingly, when slices loaded with 6.1 M cryoprotectant were transferred to a -23°C solution of 8 M, or even 8.4 M cryoprotectant, there was still no damage associated with cooling, nor was there damage associated with cooling, nor was there damage associated with exposure to these higher concentrations (cf. bars 4 and 5 to bars 6 and 7). In fact, slices exposed to 8.4 M at -23°C according to the two-step approach (first cool, then expose to higher concentrations, bar 7) had more viability than slices simply exposed to the lowest concentration of 8 M at 0°C without cooling (bar 2, p=0.033). These results showed that, at least in slices, both cooling injury and cryoprotectant toxicity were preventable by cooling first in a low concentration and introducing higher concentrations only in a second step at the lower temperature, in this case -23°C.

Re-examination of Figure 9 suggested that the same phenomenon applied to the intact kidney. Recovery was higher at the lower concentration of cryoprotectant, and if one drew a line connecting the 8 M cooled point and the 7.5 M cooled point, it extrapolated to 100% survival at some concentration below 7.5 M. Because the linearity of such an extrapolation was not known, the inventors elected to try an experiment with a concentration comfortably below 7.5 M, i.e., with 6.1 M as in the slice experiment.

The results of this experiment are indicated in Figure 11. 100% of the kidneys loaded with 6.1 M cryoprotectant, cooled to around -22°C, and warmed up (protocol indicated in the insert) supported life, giving excellent mean serum creatinine levels after 14 days (Cr₁₄) and acceptable peak creatinine values (pCr). Figure 12 shows the results of loading 6.1 M cryoprotectant at -3°C, cooling to -23°C, and then perfusing the kidney with 8 M cryoprotectant until equilibrium was achieved. As in the previous experiments, the 8 M cryoprotectant was washed out using 3% HES. In stark contrast to the results of the one-step cryoprotectant addition method followed by cooling to -30°C (Figure 9), the 8 M kidneys of Figure 12 had an excellent survival rate of 7/8, and the kidneys that did survive were not different from the 6.1 M kidneys in terms of their Cr₁₄ and pCr values, in full agreement with the slice results of Figure 10. Furthermore, as shown in Figure 13, when kidneys were perfused with 8 M cryoprotectant at -22°C, they could then be cooled another 10°C to -32°C (colder than in Figure 9), with 100% survival upon warming and with Cr₁₄ values identical to those of slices exposed only to 6.1 M cryoprotectant, again in complete agreement with the predictions of Figure 10.

The inset of Figure 14 shows that the injury associated with cooling increases between -30 and -60°C but does not increase with further cooling to near the glass transition temperature. The main portion of Figure 14 shows an attempt to more precisely determine where between -30° and -60°C, cooling injury stops increasing. Although the magnitude of the drop was somewhat small in this experiment, it appeared that slices cooled to -45° to -50°C experienced a maximum amount of cooling injury.

Using the information of Figure 14 as a guideline two additional experiments were done with intact kidneys. After spending approximately 9 months optimizing the procedure for introducing and removing V55, the following optimum method was identified. The first step of the two-step approach was to perfuse 44% w/v cryoprotectant (6.73 M) at -3°C and then cool to -25°C for perfusion with V55 (55% cryoprotectant, 8.4 M). The kidneys were then warmed back to -3°C and were washed out with 3% w/v HES and 350 mM sucrose as described above, This protocol resulted in a survival thus far of 2 out of 3 kidneys so treated. These kidneys looked excellent after 40 min of blood reflow <i>in vivo</i> and, as shown in Figure 15, they were able to return serum creatinine levels to near or below 2 mg/dl, an excellent result, Furthermore, one kidney perfused with V55 at -25°C by this procedure was cooled to -46°C prior to warming and washed by the same procedure used in the non-cooled V55 kidneys. The result for this kidney, also shown in Figure 15 (dashed line), was similar: the kidney looked excellent upon transplantation and, at the time of submission of the patent application, was restoring serum creatinine to a value near 2 mg/dl. The kidney showed a peculiarly delayed recovery, maintaining creatinine at values near 15 for an unprecedented amount of time, but the peak creatinine and the rate of return of serum creatinine back to baseline after this long delay were not different than what was observed for the other two V55 kidneys.

Taken together, the slice results of Figure 14 and the intact kidney data of Figure 15 indicated that rabbit kidneys can now be cooled to the glass transition temperature without losing viability. Furthermore, since Figure 15 employed a concentration of cryoprotectant that vitrifies without applied pressure, the implication is that high pressures are no longer mandatory for organ vitrification.

<i>C. Pertinence of Animal Data to Human Kidney Cryopreservation</i>

<i>1. First Human Kidney</i>

A 232 gram human kidney was perfused according to the method of this invention and was then vitrified. Digital data from the method was captured using a BASIC program and was edited and plotted using a sigmaPlot 5.0 graphics package (Jandel Scientific, San Rafael, CA) to generate the data in Figures 16A, 16B and 17.

The data in Figure 20A show that the method of the invention produced the expected results in this human kidney. Although the measured molarity was slightly greater than the target molarity and the first step change in concentration slightly overshot the target, the data follow the protocol reasonably well.

The data in Figure 16B from the same human kidney show that resistance (expressed as mm Hg divided by flow) and flow (ml/min/gm of kidney) behaved in a way that was qualitatively similar to their behavior in rabbit kidneys.

The data from the subsequent vitrification of this human kidney demonstrated that this method performed adequately. The data in Figure 17 provide no indication of freezing of the kidney which would have been represented by a temperature plateau followed by a relatively rapid fall in temperature. After an initial thermal lag above 0°C which represented the time for the external temperature front to penetrate through the mass of the kidney to the temperature probe in the middle, the temperature dropped rather smoothly, revealing virtually no evidence for ice formation.

<i>2. Second Human Kidney</i>

This human kidney was a pediatric kidney from a four month old donor. This kidney was stored for about 79 hours after it was collected but before it was perfused with V55 cryoprotectant according to the method of this invention. The data in Figure 18 show the perfusion of this kidney with V55 (ascending portion of the curve), and the removal of V55 cryoprotectant from the kidney (descending portion of the curve). The dotted and solid lines in Figure 18 show the achieved and target V55 concentrations, respectively. The perfusion pressure was set at 35 mmHg in this experiment.

The discrepancy between the measured and target concentrations was merely a matter of calibration rather than a true limitation of the method. The pressure spikes which occurred when a concentration of 8.4 M was quickly approached or retreated from reflected software that was not specifically designed to prevent these spikes and has since been corrected. This was not a limitation of the method. Since this kidney was unloaded, a cooling curve was not generated. Resistance, flow and temperature are not shown in Figure 18.

<i>D. Kidney Slice Viability Data</i>

Viability data from rabbit (Figure 19A) and human (Figure 19B) kidney slices and normalized data for rabbit (R) and human (H) kidney slices (Figure 19C) show nearly identical responses of the human and rabbit kidney slices to V49. Although the data showed a slightly lower recovery of human kidney tissue compared to rabbit tissue after cooling to -30°C, this recovery was within the variability seen with rabbit kidney slices. The human kidney was several days old before the experiment was carried out, whereas the rabbit kidneys were "fresh". The absolute human K/Na ratio was depressed about as much as would be expected for rabbit slices stored for a similar time.

These data in combination with the perfusion data in this section showed that human kidneys can be loaded with cryoprotectant according to the method of this invention and can be essentially vitrified on cooling -- e.g., be cooled below the glass transition temperature with minimal or no ice formation in the organ. These data also showed that the cryoprotectant can be removed from the human kidneys using the method of this invention. Lastly, the similarity of the viability data of the rabbit and human kidney slices combined with the fact that rabbit kidneys actually survived and maintained the lives of rabbits into which they had been transplanted, suggest similar results will be obtained when human kidneys are treated using the methods of this invention.