Cryopreservation requires transformation of a biological material into a solid state for long-term stability. As a sample solidifies during cooling, mechanical stress accumulates due to changing temperature gradients and differential thermal contraction of heterogeneous sample components. If stress becomes larger than the material strength of the sample, fracturing will occur. The extraordinary low critical cooling rate of M22 vitrification solution (0.1 °C/min) has allowed our laboratory to study fracture avoidance during vitrification of multi-liter volumes of solution. A few general observations are notable. Rapid cooling through high sub-zero temperatures ( > 80 °C) is permissible and desirable to reduce risk of ice growth and cryoprotectant toxicity, but cooling should slow as the glass transition temperature (−123 °C) is approached to allow more time for stress relaxation. Glass containers facilitate fracturing by differential thermal contraction stress because vitrification solutions adhere to hydrophilic glass surfaces. Containers made from polyethylene or similar hydrophobic materials can eliminate this source of stress by allowing samples to contract away from container surfaces as they cool. Tissue permeated with cryoprotectant is generally more resistant to fracturing than the same volume of pure vitrification solution, making fracture-free vitrification of a pure solution a conservative test for suitability of a cooling protocol for fracture avoidance. Following these principles, our laboratory has routinely cooled M22-perfused rabbit kidneys to −135 °C without fracturing. Although not believed necessary for long-term storage, a vitrified kidney was also successfully recovered from liquid nitrogen immersion storage without fracturing using the following protocol: Standard perfusion and cooling to −135 °C, 75 min @ −130 °C, 60 min @ −160 °C, 120 min @ −188 °C, 13 days @ −196 °C (under liquid nitrogen), 90 min @ −185 °C, 90 min @ −155 °C, 18 h @ 135 °C, followed by standard warming, cryoprotectant removal, and transplantation with no hemorrhaging or other indication of fractures. For further exploration, a 200 mL bottle (greater than the mass of a human kidney) of 105% M22 was successfully cooled from ∼ 0 °C to liquid nitrogen temperature without fracturing using a simple convection cooling protocol: Placement in 110 °C vapor for 90 min, 170 °C vapor for 4 h, −186 °C vapor for 19 h, then immersion in liquid nitrogen (−196 °C) for 90 min prior to removal and observation that the solution had no fractures. Liquid nitrogen is far colder than necessary for long-term storage; −135 °C to −140 °C is likely satisfactory to arrest ice nucleation over time periods of clinical interest. These experiences suggest that fracture avoidance may be one of the easier problems of human tissue and organ banking. Rather than gross fractures, thermomechanical stress is a suspected cause of more subtle, but still-significant lesions that have sometimes been observed after transplantation of vitrified rabbit kidneys. Developing protocols for cooling as quickly as possible to minimize ice nucleation, while avoiding damaging thermal strain within tissue, is vital to the future success of organ banking. Finite element analysis computer models will be invaluable for this purpose.
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