Nanocomposite scaffolds of bioactive glass ceramic nanoparticles disseminated chitosan matrix for tissue engineering applications
Introduction
Bone tissue engineering is gaining popularity as alternative method for treatment of osseous defects. A number of biodegradable polymers have been explored for tissue engineering purposes. These include synthetic polymers like poly(caprolactone), poly(lactic-co-glycolic acid), poly(ethylene glycol), poly(vinyl alcohol) and natural polymers like alginate, collagen, gelatin, chitin, chitosan etc. (Hirano et al., 1990). Chitosan is a biopolymer derived from partial deacetylation of chitin. Chitosan is considered as an appropriate functional material for biomedical applications because of its high biocompatibility, biodegradability, non-antigenicity and protein adsorption properties (Gupta et al., 2006, Jayakumar et al., 2007, Jayakumar et al., 2005, Jayakumar et al., 2006, Jayakumar et al., 2008, Muzzarelli et al., 1988, Muzzarelli, 2009). CS favour cell adhesion due to its chemical backbone, which resembles glycosaminoglycans, a major component of bone and cartilage. However, continuous efforts are being made to improve the bioactivity & compatibility of chitosan along with better mechanical properties. Many inorganic materials are in the literature, like hydroxyapatite (Jayakumar and Tamura, 2006, Jiang et al., 2006, Kong et al., 2005, Zhang et al., 2008, Zhao et al., 2006), β-TCP (Takahashi et al., 2005, Yin et al., 2003) and montmorillonite (Zheng et al., 2007), which are added to improve the properties of chitosan.
Bioactive glass ceramic is a group of osteoconductive biomaterial used as bone repair materials. They are silicate glasses containing SiO2–CaO–P2O5 networks. This ceramic is known to bond to hard and soft tissues by the formation of surface hydroxy carbonate apatite (HCA) layer (Cao & Hench, 1996). Reports also suggest that bioactive glass ceramic influences the cell adhesion, proliferation, differentiation and colonization on surface of implants (Bosetti and Cannas, 2005, Verrier et al., 2004, Xynos et al., 2000). Bioactive glass also allows the expression of peculiar osteoblast differentiation marker, namely osteocalcin (Foppiano et al., 2007, Oliva et al., 1998).
Nanosurface and nanoparticles are known to influence cell behaviour including attachment & spreading (Dalby et al., 2006, Lauer et al., 2001, Linez-Bataillon et al., 2002). Significantly enhanced cell–material interactions are reported on nanophase ceramics compared to microphase ceramics (Webster, Ergun, Doremus, Siegel, & Bizios, 2000). Therefore, continuous efforts are being made to engineer biomaterials/particles in nanoscale topography/size. Recently, bioactive glass ceramic has been synthesized as nanoparticles (nBGC) by sol–gel process (Xia & Chang, 2007). Hence it is interesting to investigate the possibility of preparing a scaffold using chitosan matrix disseminated with nBGC to evaluate the influence of nBGC addition in scaffold properties for tissue engineering applications. Therefore in this paper, we address the preparation of chitosan/nBGC composite scaffolds and its properties relevant to tissue engineering applications.
Section snippets
Materials
Chitosan (Degree of deacetylation – 85%) was purchased from Koyo Chemical Co Ltd (Japan). Tetraethyl orthosilicate (TEOS), calcium nitrate (Ca(NO3)2·4H2O), citric acid, ammonium dibasic phosphate, sodium borohydride, acetic acid, sodium hydroxide, Alpha minimum essential medium (α-MEM), and 3-(4,5-dimethylthiazol-2-yl)-2,5-diphenyltetrazolium bromide MTT, were purchased from Sigma Aldrich Company. Glutaraldehyde and hen lysozyme was purchased from Fluka. Trypsin–EDTA and fetal bovine serum
FT-IR studies
FT-IR spectra of CS/nBGC (Fig. 1A) showed a peak at 1649 cm−1, which corresponds to the primary amine groups of chitosan. The peak at 1030 cm−1, which is attributed to phosphate groups, was also present in CS/nBGC scaffolds. In comparison to CS, CS/nBGC scaffolds were characterized by three absorption bands at 602 and 564 cm−1, corresponding to the stretching vibration bands of P–O from and 467 cm−1 assigned to Si–O–Si bending mode.
XRD studies
The XRD analysis of the composite scaffolds (Fig. 1B) showed
Conclusions
Nanocomposite scaffolds were prepared using nBGC disseminated chitosan matrix by lyophilization technique. The prepared composite scaffolds were characterized using FT-IR, SEM, XRD and EDS studies. In addition, swelling, density, degradation, bioactivity, cytotoxicity and cell attachment studies of the composite scaffolds were also performed. The macro porous scaffolds showed interconnected pores (150–300 μm) in the nanoparticles dispersed chitosan matrix. The developed composite scaffolds
Acknowledgements
The Department of Science and Technology, Government of India supported this work, under a centre grant of the Nanoscience and Nanotechnology Initiative program monitored by Dr. C.N.R. Rao. The authors are thankful to Prof. Greta R. Patzke, Institute of Inorganic Chemistry, University of Zurich for helping in TEM studies. The authors are also thankful to Mr. Sajin. P. Ravi for his help in SEM studies. One of the authors N. S. Binulal gratefully acknowledged to Council of Scientific and
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