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Zhengke Wang, Qiaoling Hu, Lei Cai, "Chitin Fiber and Chitosan 3D Composite Rods", International Journal of Polymer Science, vol. 2010, Article ID 369759, 7 pages, 2010. https://doi.org/10.1155/2010/369759
Chitin Fiber and Chitosan 3D Composite Rods
Chitin fiber (CHF) and chitosan (CS) 3D composite rods with layer-by-layer structure were constructed by in situ precipitation method. CHF could not be dissolved in acetic acid aqueous solution, but CS could be dissolved due to the different deacetylation degree (D.D) between CHF and CS. CHF with undulate surfaces could be observed using SEM to demonstrate that the sufficiently rough surfaces and edges of the fiber could enhance the mechanical combining stress between fiber and matrix. XRD indicated that the crystallinity of CHF/CS composites decreased and CS crystal plane d-spacing of CHF/CS composites became larger than that of pure CS rod. TG analysis showed that mixing a little amount of CHF could enhance thermal stability of CS rod, but when the content of CHF was higher than the optimum amount, its thermal stability decreased. When 0.5% CHF was added into CS matrix, the bending strength and bending modulus of the composite rods arrived at 114.2 MPa and 5.2 GPa, respectively, increased by 23.6% and 26.8% compared with pure CS rods, indicating that CHF/CS composite rods could be a better candidate for bone fracture internal fixation.
Chitin, a natural polymer from marine resources , is found particularly in the shells of crustaceans such as crab and shrimp, the cuticles of insects, and the cell walls of fungi and is one of the most abundant biopolymers next to cellulose . The shells contain 15%–40% chitin and its amount in the whole marine environment has been estimated at 1560 million tons [3, 4]. It has attracted more and more attention nowadays, due to its abundant resources, friendliness to the environment, and potential to substitute some petrochemicals . Commercially, chitin is obtained at a relatively low cost from the wastes of the seafood processing industry. Briefly, the process consists of deproteinization of the raw shell material in a dilute NaOH solution and decalcification in a dilute HCl solution . Chitosan (CS), a fully or partially deacetylated form of chitin, has become important materials in various fields, including medicine, biochemistry, analytical chemistry, and chemical engineering . This derivative product with higher degree of deacetylation (D.D) results from the reaction of chitin with alkali (40%–45% NaOH solution) at elevated temperatures at prolonged exposures [5, 7].
Chitin and CS are polymers consisted of N-acetyl-glucosamine and N-glucosamine units randomly or block distributed throughout the biopolymer chain (Figure 1) [7, 8]. They are characterized by D.D; when D.D is lower than 50%, the biopolymer is named chitin. Conversely, when D.D is higher than 50%, the biopolymer is named CS . The D.D is affected by both the source of the biopolymer and the preparation methods and may range from as low as 30% to almost 100% . It is a key parameter that influences the physicochemical properties of chitin and CS, such as solubility, surface energy, chain conformation, and biological properties [9, 10]. Chitin is not soluble in common solvents because of the strong intermolecular hydrogen bonding, while it is soluble only in special solvents such as hexafluoroacetone and N, N-dimethylacetamide (DMAc) containing 5%–8% LiCl . CS is insoluble in either organic solvents or water; however, it could be readily dissolved in weak acidic solutions, due to the presence of amino groups. The solubilization occurs by protonation of the –N on the C-2 position of the D-glucosamine repeat unit, whereby the polysaccharide is converted to a polyelectrolyte in acidic media . To obtain a soluble product, the D.D of CS should reach 80%–85% or higher .
Both chitin and CS have excellent material properties such as biocompatibility, biodegradability, nontoxicity, as well as chemical and physical stability . Chitin has been generally used in hemostasis and oral dosage excipient. It is also a competent biomaterial in wound healing, anti-inflammation, cholesterol modulation, and enzyme immobilization . CS-based implants, the biocompatible materials with the host tissue, showed little fibrous encapsulation and chronic inflammation and have been tested for tissue engineering in a number of shapes and physical forms, including porous scaffolds and gels. Excellent porous structures, membranes, blocks, tubes, and beads have been obtained by lyophilization [5, 13]. -Chitin whisker-reinforced CS nanocomposite films were prepared using solution-casting technique. The increase in the tensile strength of the nanocomposite films with increasing -chitin whisker content could be attributed to the interaction between CS molecules and -chitin whiskers via hydrogen bonding . However it is difficult to prepare 3-dimensional chitosan rod by Twin Screw Extruder or Single Screw Extruder, because there are stronger intramolecular and intermolecular H-bonds in chitosan, which make the melting temperature of chitosan higher than its decomposing temperature. Novel 3-dimensional CS rod with layer-by-layer structure and its composite rod with multifunctional properties have been constructed via in situ precipitation method by our group (Figure 2) [15–18]. It can be used as bioabsorbable devices for internal fixation, which not only reduce stress shielding to the bone but also avoid a second operation for removal . In this study, CHF/CS composite rods with layer-by-layer structure were prepared by in situ precipitation method. The forming mechanism, microstructure morphology and mechanical properties of CHF/CS composite rods were explored in the following sections.
2. Materials and Experiments
The materials are CS (Biomedical grade, , , Qingdao Haihui Bioengineering Co., Ltd), chitin fiber (CHF, denier: dtex, Weifang Youngdeok Chitosan Co., Ltd), acetic acid (HAc, CP, Yixing Niujia chemical reagent plant), and sodium hydroxide (NaOH, AR, Hangzhou Xiaoshan chemical reagent corporation). These materials are commercially available and used without further purification.
2.2. Preparation of CHF/CS Composite Rods
Different weight (0.05 g, 0.1 g, 0.2 g, and 0.3 g, resp.) of CHFs, which were cut into short fibers (~5 mm in length), were added into 400 ml acetic acid aqueous solution (2%, v/v) and stirred for 0.5 hour. Then 20 g of CS powder were added and stirred for 2 hours. Finally CHFs were suspended in the viscous CS solution. The resulting solution was statically placed for 24 hours to remove the air bubbles trapped in the viscous liquid. The mixture solution was poured into cylindrical mold and then immerged into sodium hydroxide aqueous solution with a concentration of 5(wt/v) for 6 hours to form CHF/CS gel rod. The gel rod was washed with deionized water and air-dried in oven at .
2.3. SEM Observations
HITACHI S-4800 SEM produced by Japan was used to observe the microstructure of the samples which were sputter-coated by gold before observation.
2.4. X-Ray Diffraction Analysis
Crystallinity of the samples was studied with X-ray Diffraction (Rigaku D/max 2550PC) using a monochromatic Cu K radiation generated at 40 kV, 300 mA. The samples were scanned from to at /min.
2.5. Thermal Analysis
The TGA of the samples was studied on Pyris-6 Thermo Analyses (TA) apparatus produced by PerkinElmer and measurements were recorded from to at a heating rate of /minute under flow atmosphere (flow rate: 40 ml/minute).
2.6. Testing of Mechanical Properties
All of the samples were air-dried in oven at for 2 hours to remove the moisture before testing. Bending strength and bending modulus were determined by three-point bending tests (five rods per group), which were performed on the universal materials testing machine made by Shenzhen Reger Company (Shenzhen, China). The span length was 40 mm and loading rate was 2 mm/min.
3. Results and Discussion
3.1. Forming Mechanism of CHF/CS 3D Composite Rods
The forming process of CHF/CS gel rod with layer-by-layer structure was shown in Figure 3. The solubility of CS largely depends on the pH value of environments because of the existence of amino groups. The free amino group of CS was protonated to at [20, 21], but when encountered massive , CS would be precipitated, as shown in what follows:
However CHFs could not be dissolved in acetic acid aqueous solution, so that they dispersed in the viscous CS solution. The mixture solution was charged into semipermeable template which could separate the CHF/CS solution from NaOH solution, so that small molecules and ions such as O, , and could permeate except for CS macromolecules (Figure 3(a)). Due to the concentration gradient of alkali between inside and outside of the semipermeable template, could diffuse from outside into CHF/CS solution and react with . As a result, protonated CS was precipitated in situ to form one layer adhering to semipermeable template closely (Figure 3(b)). As the diffusion process continuing, CS precipitated layer-by-layer to from concentric circle structure (Figures 3(c), 3(d), and 4). At the same time, CHFs were embedded in the CS matrix. Then CHF/CS gel rods were dried and layers became much tighter due to the shrinkage stress.
3.2. Microstructure Morphology of CHF/CS 3D Composites
Microstructure morphology of the CHF, CS rod, CHF/CS (0.25/100, wt/wt), CHF/CS (0.5/100, wt/wt), CHF/CS (1/100, wt/wt), and CHF/CS (1.5/100, wt/wt) was shown in Figure 5. The size of CHF was ~10 m in width. The fiber was not in column form but had several edges. And when it was magnified by 10,000 (Figure 5(b)), undulate surface could be seen, so that the sufficient rough surface and edges of the fiber could potentially enhance the mechanical combining stress between fiber and matrix. Layer-by-layer structure could be clearly seen on the cross-section of pure CS rod in Figure 5(c), which was in accordance with the schematic representation about forming process of CHF/CS gel rod. One fiber with CS adhered on the surface traversed several layers in Figure 5(d). And fiber embedded in CS matrix along with the layer could be seen in Figures 5(e) and 5(h). Fiber was pulled out from CS matrix and chipped facet edge could be observed in Figure 5(f), and holes with fiber fragments remained in CS matrix were very shallow (Figure 5(g)), indicating that interface between fiber and matrix was combined so tightly. CS was the continuous phase that could transfer stress, whereas CHF was randomly dispersed in CS matrix to connect layers of the rod and could endure outside stress.
3.3. Crystallization Property of Samples
XRD patterns of pure CS rod, CHF, and CHF/CS rod (0.5/100, wt/wt) were shown in Figure 6. The peaks at 2 of and are characteristic diffraction peaks of CS (Figure 6(a)). Ratana Rujiravanit reported that -chitin whiskers exhibited two major scattering peaks at 2 of 9° and 19° . At the same time, 2 of CHF shown in Figure 6(b) were and respectively, which were in accordance with previous research. While small amount of CHF was added into CS matrix, two diffraction peaks shifted to and , and intensity of the peaks decreased compared with pure CS rod and pure CHF (Figure 6(c)), indicating strong interactions between CS and CHF, resulting in the reduction of crystallinity of CHF/CS composites. According to the Bragg equation (), CS crystal plane spacing (d) of CHF/CS composites has been become larger than that of pure CS rod.
3.4. Thermal Properties of CHF/CS Composites
The thermal gravimetric (TG) curves of CS rod, CHF, CHF/CS (0.25/100, wt/wt), CHF/CS (0.5/100, wt/wt), and CHF/CS (1/100, wt/wt) were shown in Figure 7, which were tested in the temperature range under atmosphere. The temperatures about different mass residual percentage () of the samples were listed in Table 1. When a little CHF was added into CS matrix (, wt/wt), of CHF/CS composite was higher than that of pure CS rod. Along with increasing content of CHF, of CHF/CS composites decreased. The thermal stability of CHF/CS (0.5/100, wt/wt) rod was weaker than that of CHF/CS (0.25/100, wt/wt) rod but slightly better than that of pure CS rod. When the ratio of CHF/CS arrived at 1/100 (wt/wt), its thermal stability was slightly weaker than that of pure CS rod. In all, thermal stability of CS rod could be enhanced by incorporating little CHF, but decreased at higher content of CHF.
Differential thermogravimetric (DTG) curves of the samples were shown in Figure 8. The temperatures of the fastest weight loss rate () of CHF were and . The of CS rod, CHF/CS (0.25/100, wt/wt), CHF/CS (0.5/100, wt/wt), and CHF/CS (1/100, wt/wt) were , , and respectively. Obviously, the of CHF/CS (0.25/100, wt/wt) and CHF/CS (0.5/100, wt/wt) was higher than pure CS rod, indicating that the thermal stability of CHF/CS is enhanced by adding little CHF. But the of CHF/CS (1/100, wt/wt) was lower than that of pure CS rod, so that the thermal stability of CHF/CS composite decreased.
3.5. Mechanical Properties of CHF/CS Composite Rods
Chitin whiskers were used to reinforce CS nanocomposite films successfully. When there were 2.96% (wt%) chitin whiskers in the composite films, the tensile strength of nanocomposite films could arrive at MPa, while the tensile strength of pure CS films was MPa . The mechanical properties of CHF/CS composite rods were shown in Figure 9. The bending strength of CHF/CS composites was increased first and then reduced along with the increasing of the content of CHF. Bending strength and bending modulus of pure CS rods are 92.4 MPa and 4.1 GPa, respectively. When 0.5% CHF was added into CS matrix, the bending strength and bending modulus of composite rod maximized at 114.2 MPa and 5.2 GPa, respectively, increased by 23.6 and 26.8 compared with pure CS rods. When much more CHF was added into CS matrix, the mechanical properties of composite rods were reduced due to much more fiber tips as stress concentrators.
CHF and CS 3D composite rods with layer-by-layer structure were constructed by in situ precipitation method. CHF could be suspended in the viscous CS solution since CHF could not be dissolved in acetic acid aqueous solution, while CS could be dissolved due to the different D.D between CHF and CS. Undulate surface of CHF seen using SEM demonstrated that sufficient rough surfaces and edges of the fiber could enhance the mechanical combining stress between fiber and matrix. Microstructure morphology also indicated that interface between fiber and matrix was combined tightly. CS was the continuous phase that can transfer stress, whereas CHF was random dispersed in CS matrix to connect layers of the rod and could endure outside stress. While small amount of CHF was added into CS matrix, intensity of the peaks decreased compared with pure CS rod and pure CHF, showing that crystallinity of CHF/CS composites decreased. CS crystal plane spacing (d) of CHF/CS composites has become larger than that of pure CS rod. Mixed little CHF could enhance thermal stability of CS rod to an optimum and higher content of CHF would decrease its thermal stability. When 0.5% CHF was added into CS matrix, the bending strength and bending modulus of composite rods maximized at 114.2 MPa and 5.2 GPa, respectively, increased by 23.6% and 26.8% compared with pure CS rods. Thus, CHF/CS composite rods could be a novel biomedical device used for bone fracture internal fixation.
This work was funded by the National Natural Science Foundation of China (Grant No. 50773070), the Key Basic Research Development Plan (Project 973) of China (Grant No. 2005CB623902) and Grand Science and Technology Special Project of Zhejiang Province (Grant No. 2008C11087).
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