Improved vitrification solutions based on the predictability of vitrification solution toxicity

Long-term preservation of complex engineered tissues and organs at cryogenic temperatures in the absence of ice has been prevented to date by the difficulty of discovering combinations of cryoprotectants that are both sufficiently non-toxic and sufficiently stable to allow viability to be maintained and ice formation to be avoided during slow cooling to the glass transition temperature and subsequent slow rewarming. A new theory of the origin of non-specific cryoprotectant toxicity was shown to account, in a rabbit renal cortical slice model, for the toxicities of 20 vitrification solutions and to permit the design of new solutions that are dramatically less toxic than previously known solutions for diverse biological systems. Unfertilized mouse ova vitrified with one of the new solutions were successfully fertilized and regained 80% of the absolute control (untreated) rate of development to blastocysts, whereas ova vitrified in VSDP, the best previous solution, developed to blastocysts at a rate only 30% of that of controls. Whole rabbit kidneys perfused at -3 degrees C with another new solution at a concentration of cryoprotectant (8.4M) that was previously 100% lethal at this temperature exhibited no damage after transplantation and immediate contralateral nephrectomy. It appears that cryoprotectant solutions that are composed to be at the minimum concentrations needed for vitrification at moderate cooling rates are toxic in direct proportion to the average strength of water hydrogen bonding by the polar groups on the permeating cryoprotectants in the solution. Vitrification solutions that are based on minimal perturbation of intracellular water appear to be superior and provide new hope that the successful vitrification of natural organs as well as tissue engineered or clonally produced organ and tissue replacements can be achieved.     

Cryo-responses of two types of large unilamellar vesicles in the presence of non-permeable or permeable cryoprotecting agents

Cryo-responses of two types of large unilamellar vesicles (LUV) that were made from either egg yolk l-α-phosphatidylcholine (EPC) or 1,2-dipalmitoyl-rac-glycero-3-phosphocholine (DPPC), in the presence of non-permeable or permeable cryoprotective agents (CPA) was investigated. Partial ternary phase diagrams of CPA–salt–water with specific CPA to salt ratio (R), were constructed to estimate the phase volume of ice and unfrozen matrix of the LUV dispersion, which could aid in understanding the mechanistic actions of CPA. Leakage of both EPC and DPPC LUV was reduced if the sugar concentrations are above 10% (w/w) for disaccharides and 5% (w/w) for monosaccharides. Above these sugar concentrations, non-permeable CPA were more effective in preventing leakage of DPPC LUV than in EPC LUV. Below these sugar concentrations, EPC and DPPC LUV with limited mobility in the remaining unfrozen matrix were more likely to approach and interact with one and another, which were not anticipated when the LUV were completely embedded in the ice matrix. In the presence of Me₂SO or EG, EPC LUV that had been subjected to freezing and thawing processes were protected from leakage. At room temperature, Me₂SO and EG were detrimental to the DPPC LUV. This study suggests that the choice of CPA for cell cryopreservation depends on the type of phospholipids in plasma membranes, which vary in their acyl chain length and gel–liquid crystal phase transition temperature.     

Cryopreservation of organs by vitrification: perspectives and recent advances

The cryopreservation of organs became an active area of research in the 1950s as a result of the rediscovery of the cryoprotective properties of glycerol by Polge, Smith, and Parkes in 1949. Over the ensuing four decades of research in this area, the advantages of vitrification, or ice-free cryopreservation, have become apparent. To date, experimental attempts to apply vitrification methods to vascularized whole organs have been confined almost entirely to the rabbit kidney. Using techniques available as of 1997, it was possible to vitrify blood vessels and smaller systems with reasonable success, but not whole organs. Beginning in 1998, a series of novel advances involving the control of cryoprotectant toxicity, nucleation, crystal growth, and chilling injury began to provide the tools needed to achieve success. Based on these new findings, we were first able to show that an 8.4M solution (VMP) designed to prevent chilling injury at -22 degrees C was entirely non-toxic to rabbit kidneys when perfused at -3 degrees C and permitted perfusion-cooling to -22 degrees C with only mild additional damage. We next investigated the ability of the kidney to tolerate a 9.3M solution known as M22, which does not devitrify when warmed from below -150 degrees C at 1 degrees C/min. When M22 was added and removed at -22 degrees C, it was sometimes [corrected] fatal, but when it was perfused for 25min at -22 degrees C and washed out simultaneously with warming, postoperative renal function recovered fully. When kidneys loaded with M22 at -22 degrees C were further cooled to an average intrarenal temperature of about -45 degrees C (about halfway through the putative temperature zone of increasing vulnerability to chilling injury), all kidneys supported life after transplantation and returned creatinine values to baseline, though after a higher transient creatinine peak. However, medullary, papillary, and pelvic biopsies taken from kidneys perfused with M22 for 25min at -22 degrees C were found to devitrify when vitrified and rewarmed at 20 degrees C/min in a differential scanning calorimeter. It remains to be determined whether this devitrification is seriously damaging and whether it can be suppressed by improving cryoprotectant distribution to more weakly perfused regions of the kidney or by rewarming at higher rates. In conclusion, although the goal of organ vitrification remains elusive, the prospects for success have never been more promising.