Development of polymer based cryogel matrix for transportation and storage of mammalian cells

We studied the potential of polymeric cryogel matrices such as 2-hydroxyethyl methacrylate (HEMA)-agarose (HA) and gelatin matrix as a transporting and storage material for mammalian cells. Both the HA and gelatin matrices were found to possess a homogenous distribution of pores as shown by scanning electron microscopic (SEM) images and flow rate of 8 and 5 mL/min, respectively. In the case of HA cryogel, after 5 days of simulated transportation, C2C12 cells kept in cryogel matrix showed higher percentage viability (89%) as compared to 64.5% viability of cells kept in suspension culture. The cells recovered from the HA cryogel were able to proliferate as revealed by the microscopic analysis. In the case of gelatin cryogel, it was shown that C2C12 cells seeded on the cryogel under simulated transportation condition were found to proliferate over the period of 5 days. It was also observed that the cells after simulation can be cryopreserved and the duration of cryopreservation does not affect their viability. Furthermore, gelatin cryogel was used for cryopreservation of HepG2 and HUVEC cells to extend the system for other cell types. These results show the potential of cryogels as efficient, low-cost transporting matrix at room temperature and in cryo-conditions.

of thawing 9 . To overcome these limitations, gel-based methods are used for cryopreservation through cells encapsulation 8 . This method has an advantage as it protect cells against any kind of mechanical damage and reduce the chance of cell disruption via immobilization of cells within the hydrogel. However, this method cannot be used for every cell-type, because for each cell-type a gel of specific mechanical property is required 10 . Recently, matrices synthesized at subzero temperature using cryogelation technology known as cryogel have been reported for cryopreservation 10,11 . These polymeric cryogels possess three-dimensional (3D) structure and have already been used as a scaffold for tissue engineering applications 12 . Cell-scaffold construct for regenerative medicine was cultured in vitro which was then transplanted in in vivo 11,13,14 . Pausing or storing of the developed tissue engineered construct is not allowed during this entire process. Therefore, cryopreservation of cell-scaffold construct having viable and functional cells is a preferable approach to meet the demand. Due to their ready-to-use nature, they could be immediately utilized. These cryogel-based methods for cryopreservation have advantages over the gel-based method because in the former cell encapsulation and gel formation do not occur simultaneously 10 .
In this study, we have examined the possibility of using cryogels for cell transportation so that it could be integrated with the methodology of using cryogel for cryopreservation. Our findings suggest that the cells recovered from the cryogel were viable after simulated transportation using 2-hydroxyethyl methacrylate (HEMA)-agarose (HA) cryogel. Further, we have also shown that the cells stored in the gelatin cryogel remain fit for cryopreservation even after the simulated transportation for up to five days. The results show that cryogels not only overcome the above-mentioned problems of transportation of cells but also provide a ready-to-use scaffold for further engineering of adherent cells, including cryopreservation. Using cryogels for transportation and storage one also have an added advantage of cell proliferation during transportation. Cryogels could, therefore, be seen as a better solution for tissue engineering, involving cell-transportation and cell-cryopreservation.

Results and Discussion
Synthesis of HA and gelatin cryogels. Both HA and gelatin cryogels were synthesized via cryogelation process. HA cryogel (Fig. 1Aa) formation involves free radical polymerization of HEMA into polyHEMA 15 and physical gelation of agarose 16 . Gelatin cryogel (Fig. 1Ab) synthesis involves crosslinking between aldehyde group of glutaraldehyde and the amino group of gelatin molecules 17 . All the three polymers agarose, HEMA and gelatin in different compositions have already been used as cell culture matrix for various tissue engineering purpose such as: chitosan-agarose-gelatin cryogel has been used for cartilage tissue engineering 18 , polyHEMA-gelatin cryogel was used for culturing myoblast cell line (C2C12) 19 and PEG-alginate-gelatin cryogel has been used for liver tissue formation 20 . In this study, synthesized HA and gelatin cryogels were used for simulated transportation of cells at room temperature. Further, gelatin cryogel was used for cryopreservation of cells for a given time period at − 80 °C after simulated transportation.
Rational behind using HEMA and agarose is that since both are hydrophilic polymers 15,21 they do not allow cells to get adhered on their surface, instead they provide support to the cells while transportation. The hydrophilic surface resists protein absorption thus it also resist cell adhesion 21 . Agarose has already been used for encapsulating the cells as a hydrophilic agarose microbeads. Thus in this study, we chose these two given polymers to encapsulate the cells during transportation. Encapsulation provides a 3D environment to the cells and cryogel matrix act as a cushion for cells. The cells recovered from HA cryogel can be further used for various tissue engineering or bioprocess application. Agarose also provided strength to the HA cryogel. On the other hand, gelatin possess amino acid sequence arginine-glycine-aspartic acid (RGD) on its surface and hence provides the adherent surface for cell 19,22 . Gelatin had already been used as a matrix for various cells example: neural cells 23 , cartilage 18 and liver 20 cells thus gelatin can be used as a common matrix for cryopreservation of various cells. The gelatin used in the study was derived from cold water fish skin. It has been studied that gelatin derived from cold-water fish, has higher amounts of hydrophobic amino acids and low water vapour permeability than warm-water fish gelatin or mammalian gelatin 24 . The hydrophobic surfaces have a strong tendency to absorb protein and thereby bind with cells. Thus, the type of gelatin has additional adherent property to be used as a cell culture matrix.
Flow rate and swelling kinetics analysis. Flow rate measures the volume of solvent that passes through the cryogel monolith in one min. Flow rate of HA and gelatin cryogels were found to be around 8 mL/min and 5 mL/min, respectively indicating that the pores in the synthesized cryogel were interconnected. In the case of HA cryogel, the high flow rate enable easy recovery of the cells after transportation. On the other hand, in the case of gelatin cryogel good flow rate helps easy passage of nutrient and oxygen during simulated transportation and also makes dimethyl sulfoxide (DMSO) available for all the cells in case of cryopreservation. DMSO is needed for the cells present inside the cryogel as these cells may experience cryoinjury in absence of cryoprotectant.
Swelling kinetics determine the solvent uptake capacity of the cryogels. In the first cycle of swelling-de-swelling, HA cryogels swelled up to 86 ± 2.3% (Fig. 1Ba) while, gelatin cryogel swelled up to 89 ± 8% (Fig. 1Bb) in 30 sec and both the cryogels reached their equilibrium state in 90 sec. During the second cycle, in the case of HA cryogels, there was a slight decrease in initial water uptake capacity rate. However, it reached its equilibrium state in 90 sec. This shows that the behavior of HA cryogels does not change with cyclic swelling and de-swelling process. From the result, we can also infer that the behavior of the HA cryogel in terms of solvent uptake capacity will remain same during cell transportation. The high swelling capacity of the HA cryogel helps in easy recovery of cells without damaging the cryogel matrix. On the other hand, in the case of gelatin cryogels equilibrium was reached in 120 sec in the second cycle. The soft nature of gelatin cryogels might be the reason for this increase in equilibrium time.
Scanning electron microscope (SEM) analysis. The surface morphological analysis was done using SEM and it showed homogenous pore distribution on both the cryogels. Pore diameter was found in the range of 10-100 μ m in the case of HA (Fig. 1Ca) and 20-90 μ m in the case of gelatin (Fig. 1Cb) presence of pores helps in easy recovery of cells. On the other hand, in the case of gelatin cryogel pore wall provides an adherent surface to the cells and helps in cell proliferation.
Pore interconnectivity and Diffusion analysis. The solute permeability was analyzed by studying the diffusion of BSA through the cryogel. The effective diffusion coefficient (Deff) of BSA in the case of HA and gelatin cryogel were found to be 3.4 × 10 −7 and 3.8 × 10 −7 cm 2 /s, respectively, which are slightly lower than diffusion coefficient in water (Do), i.e. 5.9 × 10 −7 cm 2 /s 25 . As the matrices have high porosity and pore-interconnectivity, the diffusion property of cryogel matrices lies in the range of Do in water 14 . This close resemblance of the diffusion coefficient indicates easy passage of BSA through the cryogel matrix. This unhindered movement is advantageous in passing nutrient and oxygen during cell transportation.
Rheology and compression analysis. Flow and deformation of a materials in response to applied force can be studied by rheology, which includes elasticity, viscosity, and visco-elasticity behavior. Elastic modulus and elastic nature of the material is defined as storage modulus (G′ ). The dissipation (viscous) of the flow is represented by loss modulus (G″ ). The visco-elasticity behavior or phase angle is the difference between the storage and loss modulus.
Rheology analysis of HA cryogel showed that storage modulus of cryogel increased from 2.37 × 10 5 Pa to 2.59 × 10 5 Pa in the dry state (Fig. 2Aa) and 2.4 × 10 3 to 2.7 × 10 3 Pa, in the wet state (Fig. 2Ba). Similarly, in the case of gelatin cryogel the storage modulus decreased from 3.35 × 10 5 Pa to 3.19 × 10 5 Pa in the dry state ( Fig. 2Ab) whereas, there were an increase in the storage modulus from 3.5 × 10 3 to 4.1 × 10 3 Pa in the wet state ( Fig. 2Bb). Increase in storage modulus in the case of wet HA and gelatin cryogel indicate that the elastic property of the cryogel increased with time. The wet state has low storage modulus than the dry state indicating that in the wet form the elasticity of the cryogel decreases, mechanical stability increases and also cryogels respond quickly to the applied stress in wet condition. Reduction in phase angle indicates that the both HA and gelatin cryogel are more elastic and less viscous. The viscoelastic nature of the synthesized cryogel supports its use for in vitro cell culture.
Mechanical properties of cryogels were analyzed by its microstructure network. Both HA and gelatin cryogels can bear compression strain of 80% without permanent deformation or mechanical destruction. The mechanical strength of both HA and gelatin cryogels is a very important parameter in cells storage and transportation. Young's modulus of HA and gelatin cryogels were found to be 6.1 ± 0.46 kPa (Fig. 2Ca) and 4.6 ± 0.44 kPa (Fig. 2Cb). Such low value of Young's modulus demonstrates the elastic nature of the scaffold and thereby supports the culture of mouse myoblast cell line or hepatic cells proliferation. This result also shows the soft nature of the cryogel. The soft and elastic nature of the synthesized cryogel provides it with appropriate physical property for soft tissue engineering.
Simulated transportation of cells using HA cryogel. HA cryogel was used to understand the effect of simulated transportation on the C2C12 cells. For this, cell viability of the cells stored in HA cryogels (test) was compared with the cells viability of cells stored in cryovial as cell suspension (control). Cells were recovered from the HA cryogel matrix using Trypsin EDTA (TE) because the presence of TE helps in disaggregating the cluster of the cells 26 and also to detach cells from the scaffold surface (if any). It was reported that after five days of simulated transportation, the percentage viability of cells stored in HA cryogels was around 89 ± 2.6% while cells stored in cryovial as suspension showed 64.5 ± 2%. This difference in percentage viability was statistically significant P < 0.05 (Fig. 3A). Cell viability was maintained in case of cells stored in HA cryogels during five days of simulated transportation at room temperature. This enhancement in viability may be due to the reason that the cryogel possibly prevent the shear force and damage produced during simulation and thereby maintained the viability of the cells. Further, recovered C2C12 cells from HA cryogel when cultured on a 24 well plate in a CO 2 incubator, were growing normally and became confluent in 5 days as revealed by phase contrast microscopy images (Fig. 3B). Therefore it can be concluded that transportation of cells using HA cryogel has an advantage that the cells can be recovered from the cryogel. The recovered cells can be further used for any cell culture application and can be cryopreserved for future use.
In the case of both test and control groups 4-(2-hydroxyethyl)-1-piperazineethanesulfonic acid (HEPES) buffer was added to maintain the change in pH, which may occur due to change in CO 2 concentration via cellular respiration. HEPES is a better buffering agent than sodium bicarbonate in maintaining pH in cell culture medium. It is known for an effective buffering action even at low temperature 27 . This property of HEPES gives an additional benefit when cells seeded cryogels were stored at room temperature.

Simulated transportation of cells using gelatin cryogels. Simulated transportation of C2C12 cells
was performed using gelatin cryogel in order to develop a ready-to-use scaffold. Effects of simulated transportation on cell viability and proliferation of cells were studied by storing cell-laden cryogels at room temperature for one, three and five days. Gelatin cryogel seeded with 1 × 10 5 cells after one day simulated transportation showed the presence of 2.2 ± 0.07 × 10 5 viable cells. Comparing this with the positive control, cell seeded gelatin scaffold incubated directly in CO 2 incubator, show no significant difference in number of cells ( Fig. 4Ab and Bb). However, by the 3 rd and 5 th day of room temperature incubation, the number of cells on the scaffold was found to be around 3.5 ± 0.117 × 10 5 and 3.9 ± 0.136 × 10 5 , respectively ( Fig. 4Cb and Db). This indicates that cell number increased over five days and thereby, showing cells proliferation during simulated transportation.
Further, in order to check the proliferation capability of the cells-laden cryogel after simulated transportation, they were cultured in a CO 2 incubator for 7 days. As HEPES lowered the pH of the medium in a CO 2 incubator, scaffolds were washed to remove HEPES buffer before transferring it into a CO 2 incubator 27 . After seven days of incubation, there was a 4-fold increase in cell number for the positive control (without simulation) and for one day simulated transportation experiment ( Fig. 4Ab and Bb). However, in the case of three and five days of simulated transportation experiment, cell number increased by 3.5-fold and 3.4-fold after 7 days of incubation, respectively ( Fig. 4Cb and Db). This difference may be due to the stress condition experienced by the cells during simulated transportation. Fluorescent image of day 1 showed the presence of cells after simulated transportation (Fig. 4Aa,Ba,Ca and Da). Increase in cell number from day 1 to day 7 showed that the cells were proliferating. (Fig. 4Ac,Bc,Cc and Dc). The microscopy results further confirmed that simulated transportation cells were viable and able to proliferate when cultured in a CO 2 incubator. Integrated system of cell transportation and cryopreservation. From the above experiments we found that after five days of simulated transportation using HA and gelatin cryogel, cells retain their viability. Further, we also tried to understand whether the viable cells recovered after simulated transportation can be cryopreserved or not. For this, after five days of simulated transportation of cell-laden gelatin cryogels, was cryopreserved for 1 day and 30 days. The viable cells recovered after cryopreservation were compared with the initial number of cells prior to five days of simulated transportation. It was found that after five days of simulated transportation followed by 1 day and 30 days of cryopreservation 78 ± 1.7% and 81 ± 7.4% of viable cells were recovered, respectively ( Fig. 5Ab and Bb). Cell viability was maintained prior to cryopreservation, as the 3D porous structure of cryogel helps in inhibiting the stress developed at the time of freezing and thawing. This also shows that duration of cryopreservation does not have any significant effect on the viability of post-thawed recovered cells.
Further, we have also checked the proliferation behavior of the viable cells recovered after five days of simulated transportation followed by cryopreservation for 1 day and 30 days. For this, after thawing cells seeded cryogels were kept in a CO 2 incubator for a period of 7 days. After seven days of incubation, there was 2.9-and 3.3-fold increase in cell number, in the case of 1 day and 30 day cryopreservation, respectively ( Fig. 5Ab and Bb). However, in the case of control (5 days simulated transportation and without cryopreservation), there was a 3.4-fold increase in cell number (Fig. 4Db). Increase in value of absorbance in a CO 2 incubator from day one to day seven shows that cells seeded on the cryogel were functional and proliferating well. This was further substantiated by fluorescent imaging using a nuclear stain, DAPI (Fig. 5Aa,Ac,Ba and Bc). This shows that cryopreservation does not affect morphology and proliferation behavior of cells seeded gelatin cryogel. Here in our system, cells were adhered on the surface of cryogel matrix while simulated transportation and cryopreservation. As the porous structure of cryogel lessen the stress produced while freezing and thawing, the viability of cells was maintained. Transportation and cryopreservation of cells using cryogel matrix have an added advantage, as in this case detachment of the cells from the matrix is not needed. Therefore one can directly use the cells seeded scaffold after 5 days of transportation and can also freeze the scaffold for later use.

Effect of cryopreservation on HepG2 and HUVECs cells.
In order to understand how the developed system behave with other cell types, we have checked the effect of cryopreservation on the viability of HepG2 and HUVECs cells using gelatin cryogel. Proliferation behavior of HepG2 cells seeded on gelatin cryogel was monitored for 1 day and 30 days duration of cryopreservation. There was no significant difference observed in viability and proliferation behavior of cells stored at cryo condition for 1 day and 30 days (P > 0.05) (Fig. 6Ab,Bb and Cb). Similarly, fluorescent image result showed a similar type of proliferation profile in case of 1 day (Fig. 6Aa,Ba and Ca) and 30 days cryopreservation (Fig. 6Ac,Bc and Cc). Cryopreservation for a longer duration, that is 30 days, does not have any adverse effect on cells proliferation. This denotes that these cryogels can be used as an alternate method of cell cryopreservation, having the advantage that the cell can be used as in vitro and in vivo 3D cell culture applications even after 30 days of cryopreservation.
In the case of HUVECs-seeded gelatin cryogel, after 1-day cryopreservation followed by 1-day incubation in a CO 2 incubator, the absorbance value showed a significant difference as compared to positive control (without cryopreservation) (P < 0.05) ( Fig. 7Aa and Ab). However, upon 4 and 7 days CO 2 incubation there was no significant difference as compared to positive control (without cryopreservation) (P > 0.05) (Fig. 7Aa and Ab). On the other hand, in case of 30 day cryopreservation, after 1, 4 and 7 day CO 2 incubation there was no significant difference found as compared to positive control and 1 day cryopreservation. Fluorescent microscopic results showed an increase in cell number from day 1 to day 7 CO 2 incubation. This further substantiate that proliferation behavior of post-thawed recovered cells did not alter with the duration of cryopreservation and was able to grow and proliferate.
Cell viability and proliferation assay. Cell viability was measured using two different approach based on surface property of the cryogel matrices. In case of HA cryogel, cells can be eluted after transportation thus, cell viability of eluted cells were measured using trypan blue. However, in case of gelatin cryogel it is difficult to isolate the cells as cells were adhered on the polymer surface thus we have used MTT assay to measure viable cells.
Here we are not comparing the % viability results among the two cryogel systems as both the cryogel were meant for different application. In both the cryogel we observed cells were viable and able to proliferate after simulated transportation. Further in case of gelatin cryogel we have also observed that cells were able to proliferate after cryopreservation.
In summary, we have explored the potential of HA and gelatin cryogel to transport and store adherent-cells. As both the cryogel have different surface properties, they can be used for various application. We have synthesized HA cryogel for cell's transportation in which cells can be eluted after transportation. On the other hand, gelatin cryogel can be used for both cell transportation as well as for cryopreservation. In both the cryogels we observed cells were viable and able to proliferate after simulated transportation. Using HA cryogels and C2C12 cells, we have demonstrated that the adherent-cells kept in cryogels remain up to 25% more viable as compared to the adherent-cells kept in cryovial as suspension culture under the same simulation conditions for transportation. We have also shown that by using gelatin cryogels and C2C12 cells, the adherent-cells can be stored in cryogels for up to five days at room temperature while retaining up to 80% viability. It has further shown that these adherent-cells indeed remain fit for cryopreservation even after the simulated transportation in cryogels for up to five days. This suggests that cryogels can minimize the effect of shear force, which is the main cause for the reduction of viability in transporting cells in suspension. Above results clearly show the potential of cryogels as an efficient, low-cost storing and transporting matrix at room temperature and at cryo-conditions, and therefore may have important implications for ready-to-use transplantation, in vitro drug testing, and regenerative medicines. These results thus pave the way for establishing cryogels as a better solution for tissue engineering, involving cell-storage, cell-transportation, and cell-cryopreservation.  Post thawing cells were cultured in a CO 2 incubator for 7 days (37 °C, 5% CO 2 ). Cell proliferation assay of cells seeded gelatin cryogel (Ab) without cryopreservation (control), (Bb) 1 day and (Cb) 1 month cryopreservation. Nuclei staining at day 1 (Aa,Ba,Ca) and at day 7 (Ac,Bc,Cc) in case of control, after 1-day, and 1-month cryopreservation, respectively. Nuclei were stained with DAPI (blue). Scale bar: 200 μ m; magnification: 100× . of 10% w/v) and TEMED (10 μ L). For gelatin cryogel, gelatin (5% w/v) was dissolved in 9.9 mL of deionized water and pre-cooled at 4 °C for 15 min. Crosslinking agent glutaraldehyde [1% (v/v)] was added to solution. Both the solutions were then poured into a syringe and were placed in a cryostat (Julabo, Seelbach, Germany) at − 12 °C for incubation of 16 h. After incubation, polymerized matrices were thawed using de-ioinized water at room temperature and then vacuum-dried for storage.

Flow rate analysis.
A cryogel monolith of 12 mm height and 8 mm diameter was used to determine the flow rate using a peristaltic pump. Deionized water was allowed to pass through cryogel monolith at varying flow rate ranging from 1 to 8 mL/min until there was no back-pressure generated in the cryogels. In a separate experiment as control, the flow rate was determined without connecting a cryogel in between the flow path 28 .
Cyclic swelling kinetics and morphological analysis. Swelling kinetics was determined using a conventional gravimetric procedure, as described earlier 29,30 . Three cryogel discs of equal size (2 mm thickness and 8 mm diameter) and weight were dipped in 0.1 M PBS and weighed at regular time interval. Swelled cryogels were then dried for 24 h and de-swelling were done up to three consecutive days with the same cryogel sample. The percentage of water uptake capacity (W u, %) was calculated using the formula where, W t , W d and W eq is the weight of disc at regular time interval, dry disc and swollen disc at swelling equilibrium respectively. The morphology and pore size of the synthesized cryogel was determined using scanning electron microscope (SEM) (FEI Quanta 200). For this wet cryogel samples were dehydrated using gradient ethanol (20-100%) and then dried under vacuum. Samples were then coated with gold using sputter gold coater machine (Vacuum Tech, Bangalore, India) and observed under SEM.
Pore interconnectivity and diffusion analysis. Diffusion of bovine serum albumin (BSA, Mw: 67,000 kDa) was used to analyze the pore interconnectivity of HA and gelatin cryogel by comparing the D eff of BSA in the scaffolds to their diffusion coefficient in free water (D 0 ). The cryogel disc was cut into 5 mm height (8 mm diameter) and dipped in 5 mg/mL BSA solution prepared in 10 mM PBS (pH 7.2, 0.02% sodium azide). The scaffolds were incubated at 37 °C for 96 h and were allowed protein solution to equilibrate throughout the scaffolds. The externally adsorbed proteins were washed away with PBS and the scaffolds were then immersed in 10 ml of PBS at 37 °C. Periodically, aliquots of 1 ml were collected and replaced with fresh PBS 31 . The protein concentration of the aliquots was measured using a Pierce ® BCA protein assay kit according to the manufacturer's instructions. Based on free volume theory, Deff was estimated using the following formula valid for monolithic devices 32 .
Where, Mt is the cumulative amount of protein released at time t, M∞ is the amount of protein originally present in the scaffold and r is the radius of the scaffold.
Rheology and compression analysis. The rheological analysis of both the cryogel samples was done using Anton-Paar MCR 102 rheometer. Cryogel samples were cut into the size of 2 mm thickness (8 mm diameter) and placed under load cell of rheometer set at 37 °C. Analysis of samples was carried out at a load of 1 N and frequency of 1 Hz in both dry and wet state. The readings were recorded at an interval of 15 s for a total of 15 min. The compression analysis of swollen HA and gelatin cryogels were performed using uniaxial compression test by the mechanical tester (NI DAQ card USB 6009 with labview software and load cell from Eltek). The analysis was done using scaffolds with dimension 1 cm height and 8 mm diameter by placing the scaffolds in between the two arms of load frame. The scaffolds were then compressed up to 80% of the total length with a speed of 1 mm/min. The applied force and change in column length due to compression was measured. The Young's modulus was calculated using the equation where E is the Young's modulus, F is the applied force, A is the cross-sectional area, l is the initial length of the test sample and Δ l is the change in length under the compressive force. Prior to cell seeding, monoliths of cryogels were cut into discs of size 2 mm in thickness and 8 mm in diameter. They were then sterilized by gradient ethanol (20%, 40%, 60%, 80%, 100%) followed by three times phosphate buffered saline (PBS) wash of 15 min each. After PBS wash, cryogels discs were incubated in complete medium overnight at 37 °C in a CO 2 incubator.

HA cryogel: a non adherent matrix for transportation of cells. Simulated transportation of C2C12
cells were performed using HA cryogel in a cryovial. Cells needed for simulated transportation were suspended in complete DMEM containing 10 mM HEPES buffer. Cell suspension (100 μ L) with a total of 1 × 10 5 viable cells were seeded on the HA cryogel matrix kept in a cryovial (test) and were suspended directly in a cryovial (control). These cryovials were locked using parafilm, wrapped in an aluminum foil, sealed in a zip-lock bag and then transferred into a styrofoam box to prevent any kind of contamination. In order to simulate transportation condition, cryovials were placed on a seesaw rocker for five days at room temperature. Cryovials from both the test and control group were taken out after first, second and fifth day of simulation. The cells from the cryogel were recovered, and the percentage cell-viability of both the groups were compared.
For recovery, in the case of test group cell-laden cryogels from a cryovial were transferred into a syringe and were washed with PBS. TE was then added to the cryogels. After 2 min incubation with TE, complete DMEM was passed through the cryogel and flow through was collected. The recovered cells were then centrifuged and the pellet was dissolved in the medium. In the case of control group, cells in suspension were resuspended in the medium after centrifugation. In both the groups, the percentage viability of the cells was then determined directly by counting live and dead cells using trypan blue.
Gelatin cryogel: an adherent matrix for cell transportation and cryopreservation. Potential of gelatin cryogel scaffold for cell storage and transportation was evaluated under different conditions. In the first condition, each gelatin scaffold kept in a multiwell plate was seeded with 1 × 10 5 C2C12 cells and cultured in an incubator for 4 h. After incubation, complete DMEM (200 μ L) containing 10 mM HEPES buffer was added on to it. The plates were locked and simulated transportation condition was maintained for one, three and five days, as mentioned above in the case of cryovial. In the case of first condition, at each day point, a plate was taken out and kept in a CO 2 incubator after washing with PBS. As a positive control, a plate containing cell-seeded cryogels without room temperature incubation was also kept in a CO 2 incubator. Cell viability and proliferation analysis were done up-to seven days prior to simulated transportation.
In the second condition, after five days of room temperature storage, the cells seeded scaffolds were cryopreserved for 1 and 30 days, after washing with PBS. For cryopreservation, freezing medium (ratio 7:2:1, DMEM:FBS:DMSO) was added on to the scaffolds and plates were sealed using parafilm. After sealing, plates were kept at 4 °C for 10 min and then stored in a styrofoam box at − 80 °C. Plates were removed from the styrofoam box and thawed at 37 °C in an incubator. Cryogel scaffolds were washed with PBS twice to remove DMSO followed by the addition of complete medium. For both the conditions cell viability, proliferation and fluorescent image analysis were done up-to seven days.

Cryopreservation of HepG2 and HUVEC cells on gelatin cryogel. In this experiment gelatin cryogels
were seeded with HepG2 cells, kept in a multiwell plate. Cell seeded cryogels were cryopreserved for 1 day and 30 days. The procedure of cryopreservation of cell seeded cryogels was same as mentioned above. After cryopreservation, the proliferation analysis and the imaging were done. A similar set of experiments was also conducted using HUVEC cells.
Cell viability, proliferation and microscopic assay. Two different test methods were used for analysing the % viability in case of HA and gelatin cryogel based on different application. In the case of HA cryogel, cells were recovered from the cryogel and percentage viability was calculated using trypan blue, a vital stain. The recovered cells were mixed with trypan blue in (1:1) ratio and were counted using a hemocytometer. Percent viability was evaluated using the following formula = + ×

Percentage viability Number of live cells Total number of cells live dead
On the other hand, in the case of gelatin cryogel, number of viable cells was determined using MTT assay. MTT assay was performed as reported earlier 33 . Briefly, the medium was aspirated from the well plate containing scaffolds and was washed with PBS. MTT (0.5 mg/mL dissolved in DMEM) solution of 500 μ L was added to the scaffolds in the well plate. The plate was then incubated for 4 h at 37 °C. After incubation, MTT was removed and formed formazan crystal was dissolved in 1.5 mL of DMSO. The plate was again incubated for 20 min and sample was collected, and centrifuged at 370 rcf for 2 min. Spectrophotometer (Thermo scientific-Helios Alpha) was used to take a reading of the sample at two wavelengths 570 nm and 630 nm. As the MTT absorbance value directly indicates the cell number, a standard plot was plotted using a known cell number corresponding to the MTT absorbance value. Then using this standard graph MTT absorbance value was converted into cell number 20 .
Cell distribution on the cryogel was analyzed using fluorescent imaging. For staining, cells seeded cryogel were washed with PBS and then fixed with 4% paraformaldehyde for 30 min followed by permeabilization using Triton-X. Sections were then stained using a nuclear stain DAPI and analyzed under a fluorescent microscope. Statistical analysis. Data were expressed as mean value ± standard deviation (S.D). P value ≤ 0.05 was considered to be significant. The mean values of the two groups were compared using unpaired t-test.