The emergence of regenerative medicine therapies in ophthalmology has provided potential treatment pathways for conditions which previously were untreatable [1–4]. One of the major challenges faced by those working in the area has been to develop cytocompatible, surgically deliverable scaffolds with good optical properties, which can be consistently produced at low cost. In the case of cell therapies, an additional requirement is that these scaffolds must reproducibly support sensitive populations of therapeutic cells [5,6]. Recent research has focused upon natural polymer proteins due to their similarity to native tissues [7–9].
Gelatin, a protein based material derived from the hydrolysis of collagen, has been well utilised in this area on account of its biodegradable, biocompatible nature and its commercial availability at low cost . It has been shown to have advantages over its parent protein, which include lower immunogenicity [11–14], better solubility in aqueous systems and a sol-gel transition at 30 °C . In addition, gelatin can be crosslinked or modified with the inclusion of other materials to significantly alter its mechanical and biochemical properties.
Research into the use of crosslinked gelatin-based materials in ocular repair has occurred in three distinct areas: bio-adhesives [16,17], structural scaffolds [18,19] and cell-sheet carriers [20,21] with an extensive body of research focused on the latter.
1.1. Gelatin as a Biomaterial
Gelatin exists as a mixture of water soluble protein fragments, comprised of the same amino acid sequences as collagen, from which it is derived . Collagen differs from gelatin in that it contains far more tertiary structure, leading to a lower aqueous solubility . Gelatin can be manufactured from a variety of animal collagens with the most commonly used forms in tissue engineering derived from porcine [24,25], fish  and bovine  tissues. Gelatin output quality can be dependent on the pH, temperature, and extraction time used in collagen processing . Parameters such as molecular weight and isoelectric point (IEP) can be changed depending on the processing conditions [27,29]. Gelatin can be obtained under acidic and alkaline pre-treatment conditions which give rise to type A gelatin (IEP at pH 8–9) and type B gelatin (IEP at pH 4–5) respectively .
The Bloom strength of gelatin is a measure of gelation properties of the material and will largely be dictated by the triple-helix content [30–33]. Specifically the Bloom strength refers to the number of grams required for a 0.5 inch diameter probe to deflect a set gel by 4 mm, typically ranging from 30 to 300 g. It has been proposed that Bloom strength is related to the proline-hydroxyproline content of the resultant gelatin , which in turn will be determined by the composition of collagen being processed . Typically fish gelatins possess lower levels of these important amino acids resulting in gelatin with lower gelling temperatures and lower bloom strength than those derived from mammals . When using gelatin of porcine or gelatin source, religious beliefs (e.g., Islam, Judaism, Jainism and Hinduism) should be acknowledged. However, despite this mammalian gelatin has found wide use as an excipient in pharmaceutical processing , as a stabilizer in vaccines , and as an agent in food processing for many years .
The common use of gelatin in these applications has been shown in a very small number of cases to raise hypersensitivity to the protein [37,38]. However, reports of clinical reactivity to porcine and bovine gelatin have been relatively uncommon [39–41]. Immune reactivity has been reported to vary with molecular weight of gelatin being employed [42,43]. Thus considering the mode of processing and the specification of gelatin used will be important in clinical translation of tissue engineered constructs.
Mammalian gelatin, is rich in domains that bind to cell-surface receptors and to other extracellular matrix (ECM) proteins, such as fibronectin, offering an excellent substrate for attachment of adherent cells . In addition, gelatin matrices can undergo collagenase mediated digestion, which allows biologically driven remodeling of the matrices in vivo . Gelatin-based materials often have good transparency given their high water-content making them ideal for use in repair of ocular tissues in the visual axis .
1.2. Gelatin vs. Collagen
Collagen has been shown to be a suitable material for multiple applications in ophthalmology [7,46–49] however it is not without drawbacks. The main disadvantage of collagen is the potential antigenic and immunogenic response that can be elicited from its in vivo use . Antigenicity of exogenous collagen is attributable both to the helical structures as well as central and terminal amino acid sequences. Gelatin has been reported to reduce the potential of an antigenic response in vivo, relative to its parent protein. Unlike collagen, gelatin is deficient in both tyrosine and tryptophan, and contains only low levels of phenylalanine . Consequently, gelatin has a lower potential for the formation of aromatic radicals which have been linked to increased antigenic responses .
Issues with collagen’s immunogenic response have been circumvented through the use of recombinant human collagens (RHC), although these are costly to produce [53,54]. Chemically crosslinked RHC hydrogels have been used successfully to treat patients suffering corneal thinning . Transplanted RHC constructs remained stable for 24 months post-surgery without the need for systemic immunosuppression .
The benefits of lower immunogenicity, cost and aqueous solubility make gelatin an excellent choice of base biomaterial for ocular tissue engineering applications. This review will take stock of the variety of different ways gelatin has been crosslinked and processed to create biocompatible scaffolds for ocular tissue engineering.
3. Tailoring Gelatin-Based Materials to Ocular Applications
Crosslinked gelatin biomaterials have found application in many ocular tissues: as a bio-adhesive to secure and stabilize retinal tissue [16,17], as a cell-sheet carrier for corneal endothelial cells , and as cellularised scaffolds for repair and regeneration of the corneal stroma (Figure 1) . At the time of writing, only two relevant gelatin products could be identified, both used in bio-surgery: Gelfilm®, an absorbable film marketed for use in thoracic, ophthalmic and neuro- surgery  and Gelfoam®, a compressed gelatin sponge, marketed as a hemostatic device . Current endeavors to develop gelatin-based biomaterials for regenerative medicine applications in ophthalmology are reported herein.
The cornea exists as the multi-layered, transparent window covering the front of the eye . The cornea is made up of six component layers: Epithelium; Bowman’s layer; Stroma; Descemet’s membrane; the newly described Dua’s layer and Endothelium . Only the epithelium, stroma and endothelium are made up of cells, the structures of these three layers are shown in Figure 1. The cornea is responsible for a large proportion of the eyes’ refractive power, and thus its transparency is critical for normal function. A healthy cornea is avascular and immune privileged . However in cases of trauma, burns and infectious disease, often vascularization and inflammation can occur which result in a loss of the transparency and immune privilege of the tissue .
Tissue engineered corneal tissues provide an alternative for patients suffering transplant rejection and also supplements the donor pool of corneal tissues . The technology which has progressed the furthest is arguably that of the acellular recombinant human collagen scaffold which has had some success in clinical treatment of patients with corneal thinning [56,104]. In addition, scaffolds comprised of compressed collagen [8,48,49], amniotic membrane  and even decellularised corneas are currently under investigation .
Research into gelatin-based biomaterials for cornea tissue engineering is still preclinical and has mainly focused on providing substrates for cultivation and delivery of different corneal cell types . These include the growth and delivery of corneal endothelial cells [73,74,107], growth of epithelial or limbal cells for corneal surface delivery [13,108], and investigation into the use of gelatin as a stromal replacement [18,19,69,108].
In addition, studies have examined the application of topical drugs to the ocular surface via gelatin particles [26,109–111] or by contact lenses containing immobilized gelatin particles loaded with hydrophilic protein .
3.1.1. Corneal and Limbal Epithelium
Loss of the limbal epithelial stem cell (LESC) population can occur through trauma, burns, infectious or genetic disease and it is often associated with pain, inflammation and impaired vision . LESC transplantation is often the only option for patients and involves grafting LESCs from a healthy donor eye, usually on an amniotic membrane carrier . Whilst the procedure has shown success, biological variability of the amniotic membrane has produced varied levels of graft survival . The search for new carriers has led to investigation into crosslinked gelatin biomaterials to provide low cost and effective solutions to this clinical problem.
De la Mata and colleagues recently reported the use of a LESC carrier composed of chitosan and gelatin covalently bound through crosslinking with glutaraldehyde and subsequently reduced with sodium borohydride . Introduction of chitosan was an attempt to mimic the glycosaminoglycan composition of the native limbus, thought to be important in maintaining the “stemness” of seeded LESCs. This work demonstrated that at an optimum ratio of chitosan to gelatin (20:80), LESCs maintained a more stem-like phenotype than those cultured on tissue culture plastic (TCP) .
Cationised gelatin films have been used as a therapeutic bandage loaded with epidermal growth factor (EGF) to enhance wound healing in epithelial scars in an in vivo rabbit model . Although cationised gelatin stabilized and controlled the release of epidermal growth factor, the films themselves did not have potential for further translation since they were too weak to be sutured in the rabbit model and required fixation through use of a soft contact lens. Additionally, the combination of a low water content hydrogel and the oxygen impermeable contact lens led to hypoxic conditions on the corneal epithelium and issues with re-epithelialization .
Another approach has been to chemically crosslink gelatin, collagen and hyaluronic acid with EDC and NHS in different ratios . Hyaluronic acid is an important component of the extracellular matrix, which has been found to facilitate the adhesion and proliferation of corneal cells [116,117]. Seeding epithelial cells upon films made of a 3:6:1 ratio of gelatin, collagen and hyaluronic acid respectively increased proliferation compared to TCP. The combination reported represents an interesting example of a complex crosslinked mixture with a high porosity allowing satisfactory diffusion of important small molecules.
3.1.2. Corneal Stroma
The main challenges in tissue engineering the corneal stroma lie in fabricating a fibrous extracellular matrix, sparsely populated with an even distribution of quiescent keratocytes and nerve fibres, into a single, strong, perfectly transparent construct . Such a target would require either encapsulation or surface seeding of keratocytes upon a scaffold which would be supportive of a quiescent phenotype .
Mimura et al. , attempted to circumvent difficulties in handling keratocytes by instead culturing keratocyte precursors. Stromal cells were isolated and cultured as spheroids within a GA crosslinked gelatin matrix (Figure 2A). This work demonstrated a novel method of reconstructing the corneal stroma: the keratocyte precursor spheres not only tolerated the GA crosslinked hydrogels but differentiated into mesenchymal fibroblasts and neural cells. Implantation into a rabbit corneal stromal pocket (Figure 2B–F) showed no immune cell infiltration even after 4 weeks of implantation, with keratocytes presenting desirable surface markers by histological immunostaining (Figure 2G–H) . Although cell spheres required centrifugation after surface seeding to produce an even dispersion of the keratocyte precursors, this study demonstrated both in vitro and in vivo biocompatibility of GA crosslinked gelatin.
Hydrogels formed from covalently linking gelatin with hydroxypropyl chitosan have also been investigated for corneal stromal replacement , with a highly transparent and relatively permeable gel made to include chondroitin sulphate (CS), a linear anionic polysaccharide found in the corneal stroma . It has been reported that introduction of CS improved gelatin hydrogel biocompatibility as seen by cell adhesion and proliferation data . Lai et al. [18,19] have provided convincing evidence that incorporation of CS into gelatin hydrogels can enhance the biocompatibility of stromal replacement scaffolds. Firstly, the group demonstrated that increasing CS in the scaffold increased the total collagen and glycosaminoglycan (GAG) production by cultured rabbit corneal keratocytes without eliciting increased IL-6 expression . However it was noted that the level of keratocan expression, an important biomarker of the keratocyte phenotype, was reduced in cells on scaffolds cultured on high CS content scaffolds. More recent studies have demonstrated that altering the crosslinking concentration (NHS-EDC) of gelatin–CS scaffolds significantly affected the fibronectin absorption, glucose permeability and keratocyte adhesion .
Yan and Gao [108,121] have reported investigations into the biocompatibility of gelatin-based electrospun membranes and the effect of fibre alignment upon keratocytes and epithelial cells. Keratocytes favoured aligned fibre scaffolds compared to random fibre orientations on gelatin-based scaffolds, and showed better proliferation  and keratocyte biomarker expression . This work demonstrated that the use of scaffolds with instructive topographies, such as aligned electrospun scaffolds, could give rise to keratocytes expressing a more quiescent phenotype .
3.1.3. Corneal Endothelium
The corneal endothelium covers the posterior surface of the cornea and plays a critical role in regulating the water content of the stroma. Conditions in which the endothelium is disrupted (e.g., Fuchs dystrophy)  often require surgical intervention to replace the endothelium, normally with a donor endothelium . Given the limitations of donor corneal material, many researchers in this area have attempted to develop cultivated cell-sheet implants which could potentially be used to repair and regenerate the damaged endothelium . For a detailed overview of this field, readers are directed to an excellent review by Mimura et al. .
A large body of work investigating endothelial cell-sheet delivery has focused on delivering cell sheets derived from thermoreversible poly-N-isopropylacrylamide (pNIPAM) culture substrates . Following a small thermal change, polymeric culture surfaces release intact cell sheets ready for implantation at the posterior cornea . One significant challenge faced by groups working in this area is the handling and transport of the cell sheet. To this end gelatin has been thoroughly investigated as a carrier substrate [20,73,74].
Lai et al. [73,107] were one of the first teams or groups to explore in vivo the possibility of an endothelialised gelatin carrier for endothelial sheet delivery to the posterior cornea. Culture of primary human corneal endothelial cells (HCECs) on poly-NIPAM substrates generated an intact endothelial cell sheet, which was transferred to a gelatin carrier. The resultant constructs were delivered to a de-endothelialised rabbit cornea in vivo and monitored for 6 months . A schematic diagram of this process is presented in Figure 3. The use of cast hydrogels which were air-dried without crosslinking resulted in high swelling and dissolution rates of the gelatin discs, which rapidly dispersed in the anterior chamber, leaving no solid constructs in the visual axis. Investigations of intraocular pressure (IOP) and corneal thickness as measures of ocular health demonstrated that gelatin could be used effectively in this application. The transplanted HCEC-gelatin construct effectively restored both the IOP and corneal thickness close to that of the healthy cornea. In contrast, rabbit corneas receiving the gelatin carrier alone presented no reduction in corneal swelling, showing no signs of improved water regulation. This indicates that the cellular component really is important in restoring the function of the corneal endothelium in vivo . In addition Lai et al.  showed that by using different molecular weights and isoelectric points of gelatin the mechanical and biocompatibility properties of air dried gelatin sheets could be changed.
Whilst this study was a good starting point for the use of gelatin hydrogels as a HCEC carrier, the use of the dense air dried gelatin scaffold was associated with reduced flow of aqueous humor which disrupted the flow of nutrients to other tissues and which could result in increased ocular pressure. To increase perfusion of aqueous humor, efforts have been made to increase the porosity of HCEC carrier membranes . Highly porous membranes were achieved using a stirring-freeze drying process followed by chemical crosslinking. These porous gelatin films were seen to degrade in less than one day in physiological conditions; it was hypothesized that this would reduce swelling in the anterior chamber and hence improve nutrient perfusion.
Recently, it was further shown through a series of in vivo experiments that HCEC-gelatin constructs can be delivered to the target region effectively through a cannula. After delivery, corneal swelling occurring from de-endothelialisation was restored. The gelatin carriers dissolved rapidly within 2 weeks of implantation with no signs of biological reactions in the anterior chamber in test or control groups. These developments provide good evidence that this approach may be suitable for endothelial regeneration .
Other researchers have attempted to culture HCEC directly onto gelatin carrier films. Comparing dehydrothermally crosslinked gelatin sheets to atelocollagen, a water soluble form of collagen, the gelatin scaffolds were seen to offer better elasticity, transparency and permeability. However, in assessing the biocompatibility, the gelatin sheets were coated in collagen, making an accurate comparison between the two materials difficult .
Gelatin carrier sheets are able to play an important role in delivering endothelial cell sheets to the diseased corneal endothelium. This method has distinct advantages in ensuring there is no residual carrier material left in the anterior chamber, a challenge often faced when long lasting carriers such as amniotic membrane are employed .
3.2. Retinal Pigment Epithelium
The retinal pigment epithelium (RPE) is a highly specialized tissue, situated between the choroid and the neural retina. The tissue performs both metabolic and transport functions critical to maintaining the health of the neural retina . These processes include transport of nutrients and waste products to and from photoreceptor cells . Each cuboidal pigmented epithelium is estimated to support around 20 photoreceptors .
Dry age-related macular degeneration (AMD) is one of largest cause of blindness in developed nations. Prevalence of the disease continues to rise with the increase in average life expectancy. Loss of vision in dry AMD is the result of degeneration of photoreceptors occurring as RPE cells with which they are associated deteriorate and die. With the exception of macular translocation, there are currently no therapies available for the treatment of dry-AMD .
One strategy currently being explored for the treatment of dry AMD, amongst other macular dystrophies is that of RPE transplantation. Such a therapy would involve the delivery of donor RPE cells, or allogeneic RPE progenitors beneath the neural retina, in order to restore the damaged tissue . Whilst a bolus injection of RPE cells into the sub-retinal space has been demonstrated to be effective , issues with cellular positioning and cell survival after injection have been reported . Strategies to overcome these hurdles have included the use of injectable cell laden hydrogels to prevent death of cells by reflux  or through generating RPE sheets  that can be transplanted either with  or without a carrier system [134,135]. A schematic of the transplantation of RPE-carrier sheets is presented in Figure 4.
There are several literature reports of the use of gelatin as an RPE sheet carrier which have offered signs of success. Hsiue et al.  reported initial success with a gelatin-cell construct in which sheets of confluent RPE cells were sandwiched between two gelatin discs. One study investigated an array of treatments for the sterilization of gelatin membrane carriers including: hydrogen peroxide gas plasma, ethylene oxide gas, and γ-ray irradiation, to assess their cytotoxicity towards RPE cells. Scaffolds sterilized with, low dose γ-ray irradiation (16.6 kGy), were seen to be least cytotoxic in vitro and well tolerated when injected into the sub-retinal space in a rabbit model, with no signs of inflammation. The effects of Bloom strength have also been assessed in the gelatin-RPE-gelatin sandwich. Lower Bloom gelatins were generally easier to deliver through a cannula to the sub-retinal space, and dissolved faster and were cytocompatible relative to higher Bloom gelatin . Lai et al.  examined the cell compatibility of gelatin Bloom strengths and suggested that lower Bloom strengths were associated with lower levels of inflammation as measured by the production of the pro-inflammatory cytokine IL-6.
Both GA and EDC crosslinked gelatin membranes have been investigated for retinal epithelial sheet tissue engineering . A comparison of the biocompatibility of the two crosslinkers demonstrated that EDC was less cytotoxic, as demonstrated by a proliferation assay. In addition ARPE-19 cells expressed higher levels of IL6 when cultured on GA crosslinked gelatin.
An evaluation of the effect of crosslinker concentration of EDC (0–0.4 mmol EDC/mg gelatin) on physical and biocompatibility properties showed that increased crosslinker concentrations decreased water solubility and collagenase digestion times. Higher concentrations of EDC (0.1–0.4 mmol) reduced the biocompatibility of the membranes as measured through an MTT assay. The effect of solvent composition was also investigated showing that the crosslinking density could be controlled using different ethanol to water ratios .
3.3. Bio-Adhesives for Retinal Tears
The investigation of gelatin-based materials as bio-adhesives for the treatment of retinal detachment has been of interest to a number of research groups in this area . Studies have investigated the potential use of microbial transglutaminase (m-TG) crosslinked gelatin as a bio-adhesive [16,17]. Enzymatic crosslinking has been shown to be well suited to this application given the need for in situ gelling. Gelatin solutions 20% (w/v) were made up and mixed for 1 minute with a 20% (V/V) solution of microbial transglutaminase . After injection of the bio-adhesive into the vitreous cavity of a rat model, there were no signs of any inflammatory or antigenic response after 2 weeks, demonstrating the in vivo biocompatibility of the adhesive. With a more concentrated solution of the adhesive, an in vitro lap shear assessment showed that a lap shear moduli of 12–25 kPa could be achieved, similar to other soft tissue adhesives (12–20 kPa) .
Gelatin solutions 15% (w/v) with microbial transglutaminase have been used in vivo in a vitrectomy model (simulating retinal detachment) . The bio-adhesive was seen to successfully cover a retinal tear model 7 days after administration. Optical coherence tomography demonstrated that the gelatin material had completely disappeared by day three. In addition, electroretinograms showed no adverse effects of the gelatin–mTG adhesive on retinal function. A schematic of how the bioadhesive could be used for the repair of retinal tears is shown in Figure 5.
4. Opportunities for Future Work
Gelatin-based materials have been most successful in ocular tissue engineering as cell sheet carriers, with effective delivery of both corneal endothelial sheets to the posterior cornea , and also RPE sheets to the sub-retinal space . In both applications dehydrated gelatin discs were successfully delivered through a cannula and were swiftly resorbed in vivo, with no adverse biological events reported.
In addition to altering the bulk chemistry of gelatin, the process of crosslinking also changes both the matrix compliance and potentially the topography of the constructs . The work described in this review largely attributes changes in biocompatibility to the toxicity and antigenicity of the chemical changes . Future work to evaluate the effect of matrix elasticity of gelatin grafts is an important step to develop a deeper understanding of the biocompatibility of gelatin. Gelatin methacrylamide offers a gel-based system with tunable matrix stiffness, which can be controlled without significantly changing the chemical composition . Generation of gelatin methacrylamide gels of different elastic moduli  has been previously demonstrated. In the authors opinion this material would be an effective tool in determining the optimum material properties for application in ocular tissue engineering.
Photocrosslinkable gelatin scaffolds in recent years have been a popular choice for use in a range of tissue engineering applications including cartilage repair , generating blood vessels  and also cardiac tissue development . However to the authors’ knowledge this highly versatile material has yet to be explored in ocular tissue engineering. The authors hypothesize that the additional spatial control of crosslinking offered through photo- patterning [94,142], molding  and stereolithography  will provide a range of opportunities in both creating candidate scaffolds for stromal tissue engineering and also in exploring the influence of matrix compliance and topography on ocular cell types.
Crosslinked gelatin scaffolds make up a small but important part of the ocular tissue engineering landscape. Gelatin’s similarity to collagen offers an excellent, low cost starting substrate that if crosslinked using appropriate methods could provide lower antigenic and immunogenic risk than its parent material.
Gelatin and its derivatives have been used as potential scaffolds for corneal epithelium , corneal endothelium  and retinal pigment epithelium , as a bioartificial corneal stroma  and as a potential bioadhesive in treatment of retinal detachment . The range of crosslinking options used to strengthen gelatin scaffolds in this field to date is extensive. There is good evidence to suggest that zero-length crosslinkers may be preferable in terms of both cell compatibility and biocompatibility ; the authors’ review of recent literature suggests this is a more popular method than non-zero-length crosslinking. Whilst there may be uses for glutaraldehyde to crosslink matrices, such as fragile electrospun matrices which are short lived in aqueous solutions , the risk of cell toxicity of excipients could be a potential issue.
The utility of dehydrated gelatin discs in ocular tissue engineering has been dominated by application as a cell sheet carrier in the delivery of either endothelial cell sheets to the posterior cornea , or retinal pigment epithelial cells to the sub-retinal space [30,75]. These gelatin carriers have provided effective cell delivery in vivo and have been well-tolerated with few adverse events reported .
Over the last decade the rise in popularity of partial thickness corneal transplants [123,143] has led to an opportunity to supplement the insufficient donor cornea pool with tissue engineered partial thickness grafts. To date there have been few applications of gelatin in this area and studies have examined cell toxicity  rather than creation of functional tissues. One issue that is likely to have limited research in this area is the difficulty in forming even dispersions of corneal stromal cells through gelatin matrices, with the harsh or lengthy crosslinking processes not amenable to producing cell laden constructs. Developments in other areas of tissue engineering have shown that photo crosslinkable gelatin products can be used to good effect to create cell-laden hydrogels [94,95]. The application of photo crosslinkable gelatin in corneal stromal tissue engineering is foreseen by the authors as being an area which must be investigated, particularly if gelatin-based materials are to fulfil their potential in stromal tissue engineering.
The authors would like to acknowledge funding from the Engineering and Physical Sciences Research Council (EPSRC) Doctoral Training Centre in Regenerative Medicine.
All authors contributed to both the planning and preparation of this review article equally.
Conflicts of Interest
The authors declare no conflict of interest.
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|Type of crosslinking||Gel composition||Cell type||Target tissue||Clinical application||Validation of biocompatibility||Reference|
|in vitro experiments||in vivo experiments|
|Chemical: non-zero-length||GA||10% Gelatin||Primary corneal endothelial||Corneal endothelium||Endothelial cell sheet delivery||Proliferation assay; live/dead; PIC expression||IOP; cell morphology corneal thickness;|||
|GA||10% Gelatin||Keratocyte sphere||Corneal stroma||Stromal tissue graft||ICC; gene expression; histology||Biomacroscopy; histology; IHC||[69,70]|
|GA||Gelatin and Chitosan||Limbal epithelial cells||Limbal epithelium||Limbal Epithelial Stem Cell Carrier||Proliferation assay; gene expression; ICC||–|||
|GA||10% Gelatin||ARPE-19 Cells||RPE||RPE Sheet Delivery||Proliferation assay PIC expression||–|||
|Chemical: zero-length||EDC||10% Gelatin||Primary Corneal Endothelial||Corneal Endothelium||–||Proliferation assay; Live/Dead; PIC expression||IOP; Corneal Thickness; Morphology; Biomacroscopy; h-Proline in aq. humor; Histology; IOP;||[12,72]|
|EDC||10% Gelatin||ARPE-19 Cells||RPE||RPE Sheet Delivery||Proliferation; Live/Dead; PIC expression; glutamate uptake;||–|||
|EDC||15% Gelatin||Primary Corneal Endothelial||Corneal Endothelium||Endothelial Cell Sheet Delivery||Proliferation assay; Endothelial Gene Expression||Endothelial Cell Density|||
|EDC/NHS||10% Freeze dried crosslinked with CS||Primary Corneal Stromal Cells||Corneal Stroma||Stromal Tissue Graft||Adhesion assay; Proliferation assay; Collagen and GAG production; gene expression; Cell morphology||–||[18,19]|
|Enzyme||m-TG||22.5% Gelatin + 20mg/mL m-TG||–||Neural Retina||Retinal Reattachment||–||Histology|||
|m-TG||12% Gelatin/10.8 IU/mL m-TG||–||Neural Retina||Retinal Reattachment||–||Fundus Examination; Histology; OCT|||
|Physical||Dehydration||10% Gelatin||Primary Corneal Endothelial||Corneal Endothelium||Endothelial Cell Sheet Delivery||ICC; Live/Dead; Morphology (SEM and TEM); Western Blot||Biomacroscopy; Corneal Thickness, Histology, Localization Studies||[27,29,73,74]|
|Dehydration||10% Gelatin||Primary Rat IPE cells; ARPE19 cell line||RPE||RPE Sheet Delivery||Morphology; Proliferation assay; Live/Dead; Glutamate uptake; PIC expression||Graft survival Histology Post-Implantation||[30,31,75]|
|DHT||Gelatin||Primary Corneal Endothelial||Corneal Endothelium||Endothelial Cell Sheet Delivery||ICC; Cell morphology||–|||
CS, chondroitin sulphate; DHT, dehydrothermal; GA, glutaraldehyde; GAG, glycosaminoglycan; ICC, immunocytochemistry; IHC, immunohistochemistry; IOP, intraocular pressure; IPE, iris pigment epithelial cells; m-TG, microbial transglutaminase; OCT, optical coherence tomography; PIC, pro-inflammatory cytokine; SEM, scanning electron microscopy; RPE, retinal pigment epithelial.
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