Surface modifications of vascular grafts
| Material | Fabrication | Surface modification | Time of effect | Target effect | Additional notes | Reference |
|---|---|---|---|---|---|---|
| Segments of the vasculature of porcine and rabbit | Glutaraldehyde-cross-linked | Heparin | 5 months | Calcification | Effective in porcine thoracic aorta (AO), pulmonary artery (PA), and ineffective in jugular vein (JV) and rabbit aorta (RA) | [25] |
| Porous polyurethane (PU) vascular graft | Dip-coated | Sulfonated poly(ethylene oxide) (PEO-SO3)-grafted PU copolymer (PU-PEO-SO3) | 14–39 days | Calcification, platelet adhesion, and thrombosis | PU-PEO-SO3 provided additional structural support.Calcium deposits resurfaced over time. | [4] |
| Polycaprolactone (PCL) vascular graft | Electrospinning with catechol/gallol surface chemistry | Polyethyleneimine, heparin, and epigallocatechin gallate | 28 days | Platelet adhesion/activation and fibrinogen formation | - | [26] |
| PU vascular grafts | Dip-coated with multiple layers of plasticized polyvinyl chloride | Polymer containing a nitric oxide dono (dialkylhexanediamine diazeniumdiolate) | 21 days | Platelet adhesion and thrombosis | - | [28] |
| Poly(ester urethane)urea graft | Amine-carboxyl chemical immobilization | Methacryloyloxyethyl phosphorylcholine | 24 weeks | Platelet adhesion | - | [31] |
| Tissue-engineered decellularized vascular grafts | Covalent attachment of thiol-functionalized hyaluronan onto the thiol-reactive vessel/graft | Hyaluronic acid hydrogel | 5 weeks | Platelet adhesion/activation and fibrinogen and fibrin formation | Decrease macrophage adhesion | [32] |
| PCL fibers | Electrospinning | Cu-metal organic frameworks | 12 weeks | Platelet adhesion/activation | Promote endothelial monolayer | [33] |
| Hydroxyl-terminated poly(ethylene-co-vinyl alcohol) | Covalent attachment through hydroxylgroups | Vascular endothelial growth factor receptor | Not stated | Increase endothelialization of graft | - | [36] |
| Expanded polytetrafluoroethylene (ePTFE) vascular grafts | Covalent attachment of silanized anti-CD34 antibodies (CD34-APTES) to the hydroxyl-terminated ePTFE surface | Perfluoroperhydrophenanthren lubricant and (3-aminopropyl) triethoxysilane (APTES) silanized anti-CD34 | 4 days | Thrombosis | Capture endothelial cells and prevent nonspecific adhesion | [46] |
| PU and polyethylene terephthalate(PET) | Covalent attachment through hydroxylgroups | Slippery-liquid infused porous surface (SLIPS) | 8 hours | Thrombosis; Icing; Scaling; Fouling; Corrosion | - | [49] |
| Titanium alloy | Covalent attachment through hydroxyl groups | SLIPS | 25 hours | Platelet adhesion | - | [6] |
| ePTFE | Dip-coating | SLIPS (Three lubricants tested perfluoropolyether, and perfluorodecalin | 21 days | S. aureus infection | Decrease macrophage inflammatory cytokine | [53] |
| Glass substrates | Chemical-vapor deposition | Tethered-liquid perfluorocarbons | 40 minutes | Platelet adhesion | Measured optimal thickness (between 100 nm and 2 μm) of lubricant to limit loss due to shear stress | [54] |
| Tissue-engineered decellularized vascular grafts | Dynamic culturing | Human endothelial progenitor cells and umbilical cord-derived mesenchymal stem cells | 2 hours | Thrombosis | - | [5] |
| Tissue-engineered decellularized vascular grafts | Dynamic culturing | Human umbilical vein endothelial cells | 14 days (cell viability) | Thrombosis | - | [55] |
-: no data