Silicone and collagen | Hexagonal structures, 1.52 to 2.02 µm depth, 10–20 µm width | Human mesenchymal stem cells (hMSCs) | Differentiation of hMSCs into corneal endothelial-like cells | Corneal endothelium tissue engineering, potential autologous stem cell therapy | Two-photon lithography | 2019 | [107] |
Tissue culture polystyrene (TCPS) | 1 μm pillars, 1 μm wells, and 250 nm pillars; FNC coating containing fibronectin, collagen I, and albumin | Human corneal endothelial cells (HCECs) | Enhanced proliferation, maintenance of functional markers like ZO-1 and Na+/K+-ATPase | Corneal endothelium tissue engineering, cell therapy, and drug screening | Heat embossing | 2015 | [109] |
PDMS (polydimethylsiloxane) | 1 μm pillars, 1 μm wells, 250 nm pillars, and 250 nm wells | Bovine corneal endothelial cells (BCECs) | Enhanced cell density on pillars, maintenance of functional markers like Na+/K+-ATPase | Corneal endothelium tissue engineering and drug screening | Soft lithography | 2012 | [110] |
PDMS (polydimethylsiloxane) | Nanopillars: 250 nm diameter, 250 nm height; micropillars: 1 µm diameter, 1 µm height; FNC coating containing fibronectin, collagen I, laminin, and chondroitin sulfate | Human corneal endothelial cell line B4G12 (HCEC-B4G12) | Increased cell proliferation; improved Na+/K+-ATPase and ZO-1 expression | Corneal endothelium tissue engineering | Soft lithography | 2014 | [111] |
Gelatin methacrylate (GelMA) | 1 μm pillars with 6 μm spacing (1 × 6 μmpS pillars); 250 nm pillars | Human corneal endothelial cells (HCECs) | Enhanced cell adhesion and mechanical strength, customizable degradation rates, increased amount of ZO-1 expression for 1 × 6 μmpS pillars | Corneal endothelium tissue engineering | -Hybrid crosslinking method (which combines physical crosslinking followed by UV crosslinking to improve the material’s mechanical strength) -PET stamp-based nano-molding for high-resolution patterns | 2017 | [112] |
Silk nanofibrils (SNF) and gelatin methacryloyl (GelMA) | Nanoscale fibrillar structures with 30/70 volume ratio of SNF/GelMA | Human corneal stromal cells | Enhanced transparency, mechanical strength, cell attachment, spreading, and proliferation with customizable degradation rates | Cornea regeneration | UV crosslinking for GelMA; calcium chloride–formic acid dissolution and stirring for nanofibril formation. Casting followed by UV crosslinking for fabrication of SNF/GelMA hybrid films. | 2021 | [75] |
Acrylated star-shaped poly(ethylene oxide-stat-propylene oxide) (Acr-sP(EO-stat-PO)) hydrogels | Micrometer-sized surface patterns (posts and grooves). Groove width: 10 μm, depth: 5 μm (grooves separated by 20 μm space). Wider pattern: 25 μm wide grooves, 10 μm depth (separated by 25 μm spaces) | Mouse fibroblast cell line (L929) and human mesenchymal stem cells (hMSC) | Induced vitronectin (VN) adsorption and strong cell adhesion, alignment, and spreading | Use topographic patterning to promote cell adhesion even on non-adhesive materials without additional surface chemistry modifications | UV-based imprinting | 2011 | [122] |
Star-shaped poly (ethylene glycol) | Posts: 3 µm diameter, 3 µm height; lines: 5–50 µm spacing, 5–50 µm width, 5 µm depth | Mouse fibroblast (L929) | Enhanced cell adhesion and spreading. Posts: cells spread, wrapped around posts. Lines: cells aligned along grooves, best alignment in 5–10 µm grooves. | Use topographic patterning to promote cell adhesion even on non-adhesive materials without additional surface chemistry modifications | Nanoimprinting and replica molding | 2009 | [123] |
Poly(vinyl alcohol) (PVA) hydrogel | Gratings, pillars, convex lens, concave lens (gratings: 250 nm, 10 μm, 2 μm; pillars: 10 μm, 2 μm; convex lens: 10 μm, 2 μm, 1.8 μm; concave lens: 1.8 μm) | Human endothelial cells (EA.hy926) | The 2 μm gratings on PVA hydrogels were found to increase hydrophobicity and were the most effective in promoting endothelial cell adhesion and density. Convex and concave lenses also performed well but were slightly less effective than gratings. Pillars were moderately effective and were the least optimal. | Corneal endothelium tissue engineering | Casting method (for the creation of micro-sized features), nanoimprint lithography (for the creation of nano-sized features), and nitrogen plasma modification | 2016 | [113] |
PHEMA hydrogels | Lotus leaf topography (3 ± 1 µm height, 9 ± 2 µm width) | Human corneal epithelial cells (HCE-T) | Enhanced cell adhesion and proliferation, increased hydrophobicity with static contact angle of 86 ± 2°, and the presence of trapped air pockets. | Tissue engineering, especially in applications requiring enhanced cell adhesion and hydrophobic surfaces | Polymerization in mold-nanoimprint lithography (PIM-NIL), which involves the use of Teflon AF molds to capture the hierarchical structure of the lotus leaf, both at the micro- and nanoscale, and then polymerizing PHEMA within the mold to create a structured hydrogel. | 2016 | [142] |
PHEMA (poly(hydroxyethyl methacrylate)) | Pillar structures (aspect ratio up to 100:1, 30 µm diameter, 1 mm height, 50–500 µm spacing) | Not specified | Microstructured surfaces showed higher contact angles compared to smooth surfaces, indicating increased hydrophobicity | Biomimetic surfaces and hydrophobic surface design | Combination of molding and radical polymerization | 2005 | [143] |
Collagen films | Groove widths of 25 µm, 50 µm, and 100 µm, with a depth of 50 µm and a ridge width of 200 µm | Rabbit corneal epithelial cells (CECs) and keratocytes | Swelling capacity and optical clarity comparable to natural cornea, similar degradation rate to unpatterned films (14 h), significant cell alignment along grooves (alignment index 20% to 60%), normal exponential cell growth (slightly slower on wider grooves), accelerated wound healing with narrower grooves, and inhibition of keratocyte transformation into myofibroblasts (reduced CTGF, aSMA, COL1A1 gene expression). | Design surfaces that promote cell alignment, guide direction migration of cells, accelerate wound healing, and inhibit fibrosis. Epithelialization of corneal epithelial cells. | Combination of soft lithography and solvent casting | 2019 | [114] |
Polydimethylsiloxane (PDMS) | Rose-petal-topography-mimicked surface. Microgroove mean depths of 12.9 µm (red rose) and 6.6 µm (white rose). White rose petal patterned PDMS exhibited hexagonal patterns similar to CEC. | Bovine corneal endothelial cells (BCE C/D-1b) | Collagen IV-functionalized PDMS (PDMS-C4) significantly enhanced CEC proliferation, but white-rose-patterned PDMS-C4 (PDMS-C4-R) provided the highest proliferation rate and cell density. PDMS-C4-R also maintained CEC-specific phenotype. | Corneal endothelium tissue engineering | Soft lithography, followed by functionalization with collagen IV and hyaluronic acid to enhance cell attachment and proliferation. | 2021 | [108] |
Gold with SAMs of oligo(ethylene oxide) | Self-assembled monolayers (SAMs) with variable chain lengths | Proteins (e.g., fibrinogen, lysozyme) | Prevention of nonspecific protein adsorption | Design of non-fouling surfaces for biomedical applications | Adsorption of alkanethiols onto gold surfaces using ethanol solutions, leading to the creation of monolayers with oligo(ethylene oxide) chains | 1993 | [118] |
Glass, silicon, and titanium panes | Ultrathin film (30 +/- 5 nm) of reactive star-shaped poly(ethylene glycol) prepolymers (star PEG). | Human dermal fibroblasts (HDFs), sarcoma osteogenic cells (SaOS-2), human mesenchymal stem cells (hMSCs) | Prevention of unspecific protein adsorption. Promotion of specific cell adhesion and proliferation while preserving normal differentiation process. | Non-fouling implant coatings that promote cell adhesion and proliferation | Not mentioned | 1991 | [119] |
Linear RGD peptide (gRGDsc)-modified star PEG coatings. |