Fabrication and characterization of aligned nanofibrous PLGA/Collagen blends as bone tissue scaffolds
Graphical abstract
Introduction
Bone is a complex tissue that serves multiple functions, including supporting the body, protecting organs, and storing nutrients. It has a highly anistropic morphology, which results in a range of mechanical properties. When considering engineering bone tissue, particularly for musculoskeletal tissues, matching the anisotropy and properties of the tissue scaffold is a key [1], [2]. In addition, aligning the scaffolds can assist in guided growth for the cells as well as increased cell proliferation [3] and higher natural extracellular matrix (ECM) production [4], compared to random fibers. Recently, electrospinning has emerged as a solution for fabricating scaffolds with nanofibrous features which can mimic the ECM. The inherent nonwoven nature of the electrospun nanofibers results in interconnected pores sufficient for cell attachment and nutrient transfer [5]. Orientation in electrospun nanofibers can be achieved by adapting various collector designs [6].
In addition to the morphology, another important criterion for any scaffold is the choice of materials, and for bone tissue engineering, an obvious choice is type I collagen. Collagen is a major ECM component of bone (30%) and it possesses natural binding sites for the adhesion of osteoblasts and fibroblasts [2]. However, the use of collagen alone as a scaffold material is limited due to its poor mechanical properties and rapid degradation behavior [7], [8]. Blending a bioabsorbable polymer with collagen is expected to modulate its degradation rate, while the collagen should improve the bioactivity of the synthetic polymers. Significant increases in cell adhesion and proliferation has been reported in blends of collagen with polymers [9], [10]. Meng et al. [9] studied electrospun blends of poly(3-hydroxybutyrate-co-3-hydroxyvalerate) (PHBV) and collagen and found that the blending (30% collagen) resulted in significant increase in cell adhesion and growth compared to PHBV nanofibers. Zhang et al. [11] found that the addition of gelatin (denatured collagen) to poly(ɛ-caprolactone) (PCL) resulted in not only better hydrophilicity but a threefold increase in cell infiltration into the depth of the scaffolds. Similarly higher hydrophilicity and an 82% increase in cell proliferation were observed by Venugopal et al. also upon addition of collagen to PCL [12]. Chiu et al. [13] showed the incorporation of type I collagen (<1.0 wt %) in electrospun poly(l-lactide) (PLLA) scaffolds increased both cell attachment and migration tremendously. After 1 week, cells migrated through 85% of the blend scaffold whereas only 32% was observed in the PLLA scaffold. In addition to blending with slowly degradable synthetic polymers, the rapid hydrolysis of a collagenous matrix can be prevented via crosslinking. Several different physical as well as chemical crosslinking methods have been reported for collagen-crosslinking [14], [15], [16], [17], [18]. Recently, use of 1-ethyl-3-(3-dimethylaminopropyl) carbodiimide hydrochloride (EDC) in ethanol has been studied by various researchers [17], [19], [20], [21], [22]. Powell et al. [21] have used EDC crosslinking to stabilize collagen-chondroitin-6-sulfate (GAG) scaffolds with different concentrations of EDC. The characterization of scaffolds revealed no difference in scaffold morphology between control and crosslinked scaffolds, almost no degradation for 30 days at high concentration (50 mM), increase in mechanical properties and cell density at low EDC concentration (5 mM) and a decrease in mechanical properties at higher concentration. Also, Barnes et al. [17] successfully used EDC in ethanol medium for crosslinking type II collagen and showed enhanced structural stability, greater degree of crosslinking and mechanical properties compared to glutaraldehyde crosslinking.
In this study, we prepared aligned nanofibrous scaffolds based on blends of poly (d,l-lactide-co-glycolide) (PLGA) and type I collagen with different blend compositions (PLGA/Collagen: 80/20, 65/35, 50/50). These collagen blended scaffolds were crosslinked using 1-ethyl-3-(3-dimethylaminopropyl) carbodiimide hydrochloride (EDC) in ethanol and the mechano-morphological properties were compared with those of non-crosslinked scaffolds. We report, for the first time, aligned collagen–polymer nanofiber blends in which the morphology was preserved by crosslinking with EDC.
Section snippets
Materials
Poly (d, l-lactide-co-glycolide) (PLGA) copolymer with lactide to glycolide ratio of 85/15 was obtained from Lactel® Absorbable Polymers (AL, USA). Type I collagen from calf skin was purchased from Elastin Products CO., Inc. (MO, USA). 1,1,1,3,3,3-hexafluoro-2-propanol (HFP), 1-ethyl-3-(3-dimethylaminopropyl) carbodiimide hydrochloride (EDC) and phosphate buffered saline (PBS) pellets were purchased from Sigma Aldrich. Other chemicals, 2,4,6-trinitro-benzensulfonic acid (TNBS) were purchased
Morphology of electrospun PLGA/Collagen fibers
The SEM micrographs (Fig. 1) show a smooth nanofibrous bead-free morphology. This suggests the solution concentrations for the neat polymers as well as the blends, the choice of solvent, distance from needle tip to collector and the pumping rate were optimum. It should be noted that varying the relative amounts of the polymers yielded blends with different compositions, while the overall solution concentration was fixed (10 wt/vol%) for the blend systems. The diameter distribution as well as
Conclusion
The spinnablility and characterization of collagen blended electrospun PLGA scaffolds were investigated. Varying the collagen concentration while keeping all other parameters constant, resulted in a reduction in the average nanofiber diameter from 386 nm (neat PLGA) to 240 nm (65/35) with a narrow distribution of fiber diameters. The average diameter decreased by 30% by adding 20% collagen to PLGA. TGA data indicated that the addition of collagen resulted in increased absorbed-water in the
Acknowledgements
The authors would like to thank Xing Zhang of Biomedical Engineering Department and Ting Feng of the Department of microbiology for their help in the crosslinking studies. This work is supported in part by NSF-HRD-0734232 and NSF-CMMI-0728258.
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