Porosity and biological properties of polyethylene glycol-conjugated collagen materials

Doillon, Charles J.; Côté, Marie‐France; Pietrucha, Krystyna; Laroche, Gaétan; C.‐Gaudreault, René

doi:10.1163/156856295x00102

Cited by 38 publications

(18 citation statements)

References 27 publications

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“…On and in scaffolds in which cells are recruited in vivo or inoculated in vitro, tissue architecture is expected to be completed in three dimensions at an early stage of implantation. [16][17][18][19][20][21] There has been active research on creating porous structures from synthetic polymers [28][29][30][31][32][33][34] and biologically derivatized macromolecules such as collagen 35,36 and gelatin 37 to serve as scaffolding. For example, fibrous nonwoven fabrics made of synthetic polymers such as poly(L-lactic acid) 28,38,39 and SPU, [40][41][42] and open-cell structured porous foams, which are fabricated by a particle-leaching technique, 25,43,44 phase inversion technique, 33,45,46 or freeze-drying technique, [47][48][49][50] have been used as microporous scaffolds.…”

Section: Discussionmentioning

confidence: 99%

Surface microarchitectural design in biomedical applications:In vivo analysis of tissue ingrowth in excimer laser-directed micropored scaffold for cardiovascular tissue engineering

Nakayama

Nishi

Ishibashi‐Ueda

et al. 2000

J. Biomed. Mater. Res.

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A micropatterned microporous segmented polyurethane film (20 x 12 mm in size, 30 micrometer thick) with four regions was prepared by excimer laser microprocessing to provide an in vivo model of transmural tissue ingrowth in an open cell-structured scaffold specially designed for cardiovascular tissue engineering. Three microporous regions had the same circular micropores (30 micrometer diameter) but different pore density arrangements (percentage of total pore area against unit area was 0.3%, 1.1%, and 4.5%), and the other region remained nonporous. The covered stent, prepared by wrapping the regionally different density-microporous film on an expandable metallic stent (approximately 3.1 mm in diameter), was delivered to the luminal surface of canine common carotid arteries and placed after expansion of the stent to a diameter of approximately 8 mm using a balloon catheter. At 4 weeks of implantation, all the covered stents (n = 10) were patent. The luminal surfaces of the covered stents were almost confluently endothelialized both in nonporous and microporous regions. Histological examination showed that the neointimal wall was formed by tissue ingrowth from host through micropores (transmural) and anastomotic sites. Thrombus formation occurred frequently in the lowest density porous region and nonporous region. With an increase in pore density, the thickness of the neointimal wall decreased. This study demonstrated how the micropore density of implanted devices influences tissue ingrowth in arterial implantation.

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Section: Discussionmentioning

confidence: 99%

Surface microarchitectural design in biomedical applications:In vivo analysis of tissue ingrowth in excimer laser-directed micropored scaffold for cardiovascular tissue engineering

Nakayama

Nishi

Ishibashi‐Ueda

et al. 2000

J. Biomed. Mater. Res.

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“…It has been reported that PEG could stabilize the porous structure inside collagen sponges, the latter phenomenon facilitating cell infiltration and tissue ingrowth. 24 Furthermore, PEG-modified collagen sponges have demonstrated a significant increase in the resistance to collagenase targeting. 24 It also has been suggested that, in contrast to the nonmodified sponges, PEGmodified tissues do not collapse 60 days after implantation.…”

Section: Discussionmentioning

confidence: 99%

“…24 Furthermore, PEG-modified collagen sponges have demonstrated a significant increase in the resistance to collagenase targeting. 24 It also has been suggested that, in contrast to the nonmodified sponges, PEGmodified tissues do not collapse 60 days after implantation. Hence, it seems the stability of PEG-modified collagen tissues may be linked to the resistant properties of PEG to enzymatic attack after their binding with the tissues.…”

Section: Discussionmentioning

confidence: 99%

Effect of alternative crosslinking techniques on the enzymatic degradation of bovine pericardia and their calcification

Vasudev

Chandy

1997

J. Biomed. Mater. Res.

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The in vitro calcification and enzymatic degradation of bovine pericardia (BP) after a series of surface treatments were studied as a function of exposure time. The degradation of these treated surfaces was monitored by scanning electron micrography and tensile strength measurements. Polyethylene glycol-(PEG) grafted BP and glutaraldehyde-(GA) treated BPs retained maximum stability in collagenase digestion compared with SDS-treated BP. The ability of alpha chymotrypsin, bromelain, esterase, trypsin, and collagenase to modulate the degradation of SDS-, GA-, PEG-, Carbodiimide-, and glycidylether-treated BPs also was investigated. Incubation of various enzymes to these crosslinked pericardia variably reduced the tensile strength of these tissues. It is conceivable that chemical treatments of pericardial tissues might have altered their physical and chemical configuration and the subsequent degradation properties. In vitro calcification studies showed a substantial reduction in the calcification profile of PEG-grafted bovine pericardia compared to other treated tissues. Furthermore, the biocompatibility aspects of pericardial tissues were established by platelet adhesion and octane contact angle. In conclusion, it seems that the surface modification of bovine pericardia via GA-PEG grafting may provide new ways of controlling biodegradation and calcification.

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“…The modification of proteins by attachment of one or more PEG chains (PEGylation) has been applied very successfully to increase the plasma half-life of therapeutic peptides or protein drugs [16]. Based on a similar rationale, PEGylation could be a good strategy for protein-based biomaterial design in as much as the PEG chains can slow down the enzymatic biodegradation of the PEGylated protein scaffold [17][18][19]. At the same time, the PEG chains are nontoxic, non-immunogenic, highly water soluble, and are already approved by the FDA in a number of different clinical indications [20].…”

Section: Introductionmentioning

confidence: 99%

Protein–polymer conjugates for forming photopolymerizable biomimetic hydrogels for tissue engineering

2007

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Porosity and biological properties of polyethylene glycol-conjugated collagen materials

Cited by 38 publications

References 27 publications

Surface microarchitectural design in biomedical applications:In vivo analysis of tissue ingrowth in excimer laser-directed micropored scaffold for cardiovascular tissue engineering

Surface microarchitectural design in biomedical applications:In vivo analysis of tissue ingrowth in excimer laser-directed micropored scaffold for cardiovascular tissue engineering

Effect of alternative crosslinking techniques on the enzymatic degradation of bovine pericardia and their calcification

Protein–polymer conjugates for forming photopolymerizable biomimetic hydrogels for tissue engineering

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