Collagen/chitosan porous scaffolds with improved biostability for skin tissue engineering
Introduction
The skin loss is one of the oldest and still not totally resolved problems in surgical field. Due to the spontaneous healing of the dermal defects would not occur, the scar formation for the full thickness skin loss would be inevitable unless some skin substitutes are used. In the past decades, many skin substitutes such as xenografts, allografts and autografts have been employed for wound healing. However, because of the antigenicity or the limitation of donor sites, the skin substitutes mentioned above cannot accomplish the purpose of the skin recovery and yet not be used widely [1], [2], [3], [4], [5]. Therefore, many studies are turning toward the tissue engineering approach, which utilizes both engineering and life science discipline to promote organ or tissue regeneration and to sustain, recover their functions [6], [7], [8], [9]. One crucial factor in skin tissue engineering is the construction of a scaffold. A three-dimensional scaffold provides an extra cellular matrix analog which functions as a necessary template for host infiltration and a physical support to guide the differentiation and proliferation of cells into the targeted functional tissue or organ [10], [11]. An ideal scaffold used for skin tissue engineering should possess the characteristics of excellent biocompatibility, suitable microstructure such as 100–200 μm mean pore size and porosity above 90%, controllable biodegradability and suitable mechanical property [12], [13], [14], [15]. Collagen is known to be the most promising materials and have been found diverse applications in tissue engineering for their excellent biocompatibility and biodegradability. However, the fast biodegrading rate and the low mechanical strength of the untreated collagen scaffold are the crucial problems that limit the further use of this material. Cross-linking of the collagen-based scaffolds is an effective method to modify the biodegrading rate and to optimize the mechanical property.
For this reason, the cross-linking treatment to collagen has become one of the most important issues for the collagen-based scaffolds. Currently, there are two different kinds of cross-linking methods employed in improving the properties of the collagen-based scaffolds: chemical methods and physical methods. The latter include the use of photooxidation, dehydrothermal treatments (DHT) and ultraviolet irradiation, which could avoid introducing potential cytotoxic chemical residuals and sustain the excellent biocompatibility of the collagen materials [16]. However, most of the physical treatments cannot yield high enough cross-linking degree to satisfy the demand of skin tissue engineering. Therefore, the treatments by chemical methods are still necessary in almost all cases. The reagents used in the cross-linking treatment recently involve traditional glutaraldehyde (GA), 1-ethyl-3-(3-dimethylaminopropyl)-carbodiimide (EDAC), polyglycidyl ether and polyepoxidic resins, etc. [17], [18], [19], [20], [21]. GA is a kind of bifunctional cross-linking reagents that can bridge amino groups between two adjacent polypeptide chains and has become the predominant choice in skin tissue engineering because of its water solubility, high cross-linking efficiency and low cost [22].
Chitosan is another biomaterials used in a variety of biomedical fields such as drug delivery carriers, surgical thread, and wound healing materials [23]. Due to its many advantages for wound healing such as hemostasis, accelerating the tissue regeneration and the fibroblast synthesis of collagen, many applications of chitosan in skin tissue engineering have been reported [24], [25], [26], [27]. In addition, chitosan can function as a bridge to increase the cross-linking efficiency of GA in the collagen-based scaffolds owing to the large number of amino groups in its molecular chain (Fig. 1). Hence, one can expect that less GA could be used in the presence of chitosan and the potential cytotoxicity of GA might be decreased.
Herein we describe the fabrication of collagen porous scaffold in the presence of 10 wt% chitosan, which functions as a cross-linking bridge in the further treatment of GA cross-linkage. The microstructure, the swelling capacity, as well as the degradability both in vivo and in vitro of the collagen/chitosan scaffold were investigated. In vitro culture of human dermal fibroblasts and in vivo animal tests demonstrated that the scaffolds showed good cytocompatibility and could effectively guide the infiltration and growth of fibroblasts.
Section snippets
Materials
Chitosan (viscosity average molecular weight Mη: 1.0×105–1.7×105, 75–85% deacetylation degree), collagenase I (278 U/mg), rhodamine B isothiocyanate, fluorescein isothiocyanate (FITC) and fluorescein diacetate (FDA) were purchased from Sigma. Trypsin (250 U/mg) was a commercial product from Amresco. Glutaraldehyde (GA), 25% water solution, was purchased from Shanghai Pharm. Co. (China). All other reagents and solvents are of analytical grade and used as received.
Collagen type I was isolated from
Distribution of collagen and chitosan
One of the important purposes adding chitosan is providing additional amino groups which function as binding cites to increase the GA cross-linking efficiency. Therefore, the interpenetration of collagen and chitosan in the scaffold is crucial. Exploiting the sequential scanning mode of CLSM, the distribution of FITC-Chi (Fig. 2a) and Rd-Col (Fig. 2b) in their complex scaffold was separately measured at wet state. A merged image is shown in Fig. 2c. The CLSM observations indicate that the
Conclusion
Herein we have described the fabrication of porous collagen/chitosan scaffold by freeze-drying their mixture and the further cross-linking with GA. Collagen and chitosan were evenly distributed in the scaffold. The GA treatment had an influence on the morphology and the swelling property of the scaffold, while no significant differences were observed among the scaffolds treated with different concentration GA. After addition of chitosan, the ability to resist the collagenase degradation was
Acknowledgments
The authors thank Prof. Yiyong Chen for his valuable discussion. This work was supported by the Natural Science Foundation of China (50173024) and the Major State Basic Research Program of China (G1999054305).
References (33)
Design principles of composition and performance of cultured skin substitutes
Burns
(2001)- et al.
Tissue engineering scaffolds using superstructures
Biomaterials
(1996) - et al.
Fabrication of biodegradable polymer scaffolds
- et al.
Cellular materials as porous scaffolds for tissue engineering
Progr Mater Sci
(2001) - et al.
Cellular proliferation on desamidated collagen matrices
Comparative Biochem Physiol Part C
(1999) Methods for the treatment of collagenous tissues for bioprostheses
Biomaterials
(1997)- et al.
Investigation into the biological stability of collagen/chondroitin-6-sulphate gels and their contraction by fibroblasts and keratinocytesthe effect of crosslinking agents and diamines
Biomaterials
(1999) - et al.
Influence of different chemical cross-linking treatments on the properties of bovine pericardium and collagen
Biomaterials
(1999) - et al.
Collagen and its interaction with chitosan II. Influence of the physicochemical characteristics of collagen
Biomaterials
(1995) - et al.
Collagen and its interaction with chitosan III. Some biological and mechanical properties
Biomaterials
(1996)