The physico-chemical properties of collagenous matrices may determine the tissue response after insertion into full-thickness articular cartilage defects. In this study, cross-linked type I and type II collagen matrices, with and without attached chondroitin sulfate, were implanted into full-thickness defects in the femoral trochlea of adolescent rabbits. The tissue response was evaluated 4 and 12 weeks after implantation by general histology and two semi-quantitative histological grading systems. Four weeks after implantation, type I collagenous matrices were completely filled with cartilage-like tissue. By contrast, type II collagenous matrices revealed predominantly cartilaginous tissue only at the superficial zone and at the interface of the matrix with the subchondral bone, leaving large areas of the matrix devoid of tissue. Attachment of chondroitin sulfate appeared to promote cellular ingrowth and cartilaginous tissue formation in both types of collagen matrices. Twelve weeks after implantation, the differences between the matrices were less pronounced. The deep parts of the subchondral defects were largely replaced by new bone with a concomitant degradation of the matrices. The original cartilage contours in defects with type I collagen-based matrices were repaired with fibro-cartilaginous tissue. Defects containing type II matrices showed an increase in the amount of superficial cartilage-like tissue. The original contour, however, was not completely restored in all animals, occasionally leaving a central depression or fissure. It is concluded that different types of collagen matrices induce different tissue responses in full-thickness articular cartilage defects. Type I collagen-based matrices are superior to guide progenitor cells from a subchondral origin into the defect. In type II collagen-based matrices cell migration is less, but invading cells are directed into a chondrocyte phenotype. Based on these observations it is suggested that a composite matrix consisting of a deep layer of type I collagen and a more superficial layer of type II collagen may be the matrix of choice for cartilage regeneration.

The limited intrinsic repair capacity of articular cartilage has stimulated continuing efforts to develop tissue engineered analogues. Matrices composed of type II collagen and chondroitin sulfate (CS), the major constituents of hyaline cartilage, may create an appropriate environment for the generation of cartilage-like tissue. In this study, we prepared, characterized, and evaluated type 11 collagen matrices with and without CS. Type II collagen matrices were prepared using purified, pepsin-treated, type II collagen. Techniques applied to prepare type I collagen matrices were found unsuitable for type II collagen. Crosslinking of collagen and covalent attachment of CS was performed using 1-ethyl-3-(3-dimethyl aminopropyl)carbodiimide. Porous matrices were prepared by freezing and lyophilization, and their physico-chemical characteristics (degree of crosslinking, denaturing temperature, collagenase-resistance, amount of CS incorporated) established. Matrices were evaluated for their capacity to sustain chondrocyte proliferation and differentiation in vitro. After 7 d of culture, chondrocytes were mainly located at the periphery of the matrices. In contrast to type I collagen, type II collagen supported the distribution of cells throughout the matrix. After 14 d of culture, matrices were surfaced with a cartilagenous-like layer, and occasionally clusters of chondrocytes were present inside the matrix. Chondrocytes proliferated and differentiated as indicated by biochemical analyses, ultrastructural observations, and reverse transcriptase PCR for collagen types I, II and X. No major differences were observed with respect to the presence or absence of CS in the matrices.

Articular cartilage lesions resulting from trauma or degenerative diseases are commonly encountered clinical problems. It is well-established that adult articular cartilage has limited regenerative capacity, and, although numerous treatment protocols are currently employed clinically, few approaches exist that are capable of consistently restoring long-term function to damaged articular cartilage. Tissue engineering strategies that focus on the use of three-dimensional scaffolds for repairing articular cartilage lesions offer many advantages over current treatment strategies. Appropriate design of biodegradable scaffold conduits (either preformed or injectable) allow for the delivery of reparative cells, bioactive factors, or gene factors to the defect site in an organized manner. This review seeks to highlight pertinent design considerations and limitations related to the development, material selection, and processing of scaffolds for articular cartilage tissue engineering, evidenced over the last decade. In particular, considerations for novel repair strategies that use scaffolds in combination with controlled release of bioactive factors or gene therapy are discussed, as are scaffold criteria related to mechanical stimulation of cell-seeded constructs. Furthermore, the subsequent impact of current and future aspects of these multidisciplinary scaffold-based approaches related to in vitro and in vivo cartilage tissue engineering are reported herein.

The loading of biocompatible matrices with growth factors offers the opportunity to induce specific cell behavior. The attachment of heparan sulfate (HS) to these matrices may promote the binding, modulation, and sustained release of signaling molecules. In this study, basic fibroblast growth factor (bFGF) was bound to crosslinked collagenous matrices with and without covalently attached HS. The tissue response to these matrices was evaluated after subcutaneous implantation in rats. Attachment of HS to collagen matrices increased the bFGF binding capacity threefold and resulted in a more gradual and sustained release of the growth factor in vitro. bFGF primarily was located at the matrix margins. In vivo, the presence of HS without bFGF resulted in a transient vascularization, predominantly at the matrix periphery. Angiogenesis was further enhanced by combining HS with bFGF. In contrast to collagen-HS and collagen/bFGF matrices, collagen-HS/bFGF matrices remained highly vascularized throughout the matrix during the 10-week implantation period. In addition, these latter matrices revealed an intense and prolonged tissue response and considerably promoted the generation of new tissue. Foreign body reactions were only observed sporadically at this time interval. It is concluded that bFGF loading of collagen-HS matrices has additional value for those tissue-engineering applications that require enhanced angiogenesis and generation of new tissue.

Endothelial cell seeding is a promising method to improve the performance of small-diameter vascular grafts. Growth of endothelial cells seeded on the luminal surface of synthetic vascular grafts, coated with a matrix suitable for cell seeding (e.g. collagen), can be accelerated by local, sustained release of basic fibroblast growth factor (bFGF). In this study two potential matrices for in vivo endothelial cell seeding were studied with respect to bFGF binding and release: collagen crosslinked using N-(3-dimethylaminopropyl)-N'-ethylcarbodiimide (EDC) and N-hydroxysuccinimide (NHS), as well as heparinized EDC/NHS-crosslinked collagen. bFGF binding was determined after incubation of circular samples (10 mm diameter) with 0.25 ml bFGF solution for 90 min. Immobilization of increasing amounts of heparin, also using EDC and NHS, to crosslinked collagen containing 14 free primary amino groups per 1000 amino acid residues (E/N14C) resulted in binding of increasing amounts of bFGF. A plateau in bFGF binding was observed for heparinized E/N14C containing approximately 2.0-3.0 wt% of immobilized heparin which was obtained using a molar ratio of EDC to heparin-carboxylic acid groups of 0.4 during heparin immobilization (E/N14C-H(0.4)). At concentrations up to 840 ng bFGF/ml, 10% of the added bFGF bound to E/N14C, while binding of bFGF to E/N14C-H(0.4) amounted to 22%. Both E/N14C and E/N14C-H(0.4) pre-loaded with bFGF showed sustained bFGF release. A burst release of 30% in endothelial cell culture medium (CM) was observed for E/N14C during the first 6 h, compared to 2% release from E/N14C-H(0.4). After 28 days, the bFGF release from E/N14C and E/N14C-H(0.4) in CM amounted to 100 and 65%, respectively. Combined results of binding and release of bFGF indicate that compared to E/N14C, E/N14C-H(0.4) is the substrate of choice for bFGF pre-loading and subsequent endothelial cell seeding.

The many biocharacteristics of glycosaminoglycans (GAGs) make them valuable molecules to be incorporated in collagenous biomaterials. To prepare tailor-made collagen-GAG matrices with a well-defined biodegradability and (bioavailable) GAG content, the crosslinking conditions have to be controlled. Additionally, the ultrastructural location of GAGs in engineered substrates should resemble that of the application site. Using chondroitin sulfate (CS) as a model GAG, these aspects were evaluated. The methodology was then applied for other GAGs.CS was covalently attached to collagen using 1-ethyl-3-(3-dimethyl aminopropyl) carbodiimide (EDC) and N-hydroxysuccinimide (NHS. A maximum of about 155 mg CS/g matrix could be immobilized. CS incorporation and bioavailability, as evaluated by interaction with specific antibodies and glycosidases, was dependent on the molar ratio EDC:carboxylic groups of CS. The denaturation temperature could be modulated from 61 to 85 degrees C. The general applicability of EDC/NHS for immobilizing GAGs was demonstrated with dermatan sulfate, heparin, and heparan sulfate. These matrices revealed comparable physico-chemical characteristics, biodegradabilities, and preserved bioavailable GAG moieties.At the ultrastructural level, GAGs appeared as discrete, electron-dense filaments, each filament representing a single GAG molecule. Distribution was independent of GAG type. They were observed throughout the matrix fibers and at the outer sites, and located, either parallel or orthogonally, at the periphery of individual collagen fibrils. Compositional and ultrastructural similarity between matrices and tissue structures like cartilage and basement membranes can be realized after attachment of specific GAG types.It is concluded that EDC/NHS is generally applicable for attachment of GAGs to collagen. Modulation of crosslinking conditions provides matrices with well-defined GAG contents, and biodegradabilities. Ultrastructural similarities between artificially engineered scaffolds and their possible application site may favor the use of specific collagen-GAG matrices in tissue engineering. (C) 2000 Elsevier Science Ltd. All rights reserved.

Biocompatibility and tissue regenerating capacity are essential characteristics in the design of collagenous biomaterials for tissue engineering. Attachment of glycosaminoglycans (GAGs) to collagen may add to these characteristics by creating an appropriate micro-environment. In this study, porous type I collagen matrices were crosslinked using 1-ethyl-3-(3-dimethyl aminopropyl)carbodiimide, in the presence and absence of chondroitin sulfate and heparan sulfate. The tissue response to these matrices was evaluated after subcutaneous implantation in rats. Biocompatibility of the matrices was established by the induction of a transitional inflammatory response, and the generation of new host tissue. Non-crosslinked collagen was gradually resorbed and replaced by collagenous connective tissue. By contrast, crosslinked matrices, with and without GAGs, retained their scaffold integrity during implantation, and supported the interstitial deposition and organization of extracellular matrix. In addition, crosslinking decreased tissue reactions at late time intervals. No calcification in any of the implants was observed. The presence of GAGs preserved porous lamellar matrix structures. Heparan sulfate in particular promoted angiogenesis at weeks 2 and 4, predominantly at the matrix periphery. The almost complete absence of macrophages and giant cells associated with collagen-GAG matrices, after 10 weeks implantation, indicated a reduced foreign body reaction. It is concluded that attachment of GAGs to collagen matrices modulates the tissue response. The potential of these biocompatible scaffolds for tissue engineering is increased by preserving porous matrix integrity, promoting angiogenesis and reducing foreign body reactions.

Porous collagen matrices with defined physical, chemical and biological characteristics are interesting materials for tissue engineering. Attachment of glycosaminoglycans (GAGs) may add to these characteristics and valorize collagen. In this study, porous type I collagen matrices were crosslinked using dehydrothermal (DHT) treatment and/or 1-ethyl-3-(3-dimethyl aminopropyl)carbodiimide (EDC), in the presence and absence of chondroitin sulphate (CS). EDC covalently attaches CS to collagen. DHT crosslinking preserved a porous matrix structure. However, attachment of CS to DHT-treated matrices using EDC, resulted in collapsed surfaces, CS located only at the matrix exterior. EDC crosslinking resulted in a partial matrix collapse. This could be prevented if crosslinking was carried out in the presence of ethanol. Matrix porosity was then preserved. The presence of CS during EDC crosslinking resulted in covalent immobilization of CS throughout the matrix. The amount of CS incorporated was increased if crosslinking was performed in the presence of ethanol. EDC-crosslinked matrices, with and without CS, had increased denaturation temperatures and decreased free amine group contents. The susceptibility of these matrices towards degradation by proteolytic enzymes was diminished. Immobilized CS increased the water-binding capacity and decreased the denaturation temperature and tensile strength. Immobilized CS bound anti-CS antibodies and was susceptible to chondroitinase ABC digestion, demonstrating its bioavailability. The modified matrices were not cytotoxic as was established using human myoblast and fibroblast culture systems. It is concluded that the use of ethanol during EDC crosslinking, offers an elegant means for the preparation of defined porous collagenous matrices containing bioavailable, covalently attached CS.