Journal of NanomaterialsVolume 2011 (2011), Article ID 391596, 5 pagesdoi:10.1155/2011/391596

Research Article

Mechanical Properties of Chitosan-Starch Composite Filled Hydroxyapatite Micro- and Nanopowders

Jafar Ai,¹ Mostafa Rezaei-Tavirani,² Esmaeil Biazar,³ Saeed Heidari K,² and Rahim Jahandideh³

¹School of Advanced Medical Technologies, Tehran University of Medical Sciences, Tehran, Iran²Proteomics Research Center, Faculty of Paramedical Sciences, Shahid Beheshty University of Medical Sciences, Tehran, Iran³Department of Biomaterials Engineering, Tonekabon Branch, Islamic Azad University, Tonekabon, Iran

Received 30 April 2011; Revised 4 July 2011; Accepted 4 July 2011

Academic Editor: Donglu Shi

Copyright © 2011 Jafar Ai et al. This is an open access article distributed under the Creative Commons Attribution License, which permits unrestricted use, distribution, and reproduction in any medium, provided the original work is properly cited.

Abstract.

Hydroxyapatite is a biocompatible ceramic and reinforcing material for bone implantations. In this study, Starch-chitosan hydrogel was produced using the oxidation of starch solution and subsequently cross-linked with chitosan via reductive alkylation method (weight ratio (starch/chitosan): 0.38). The hydroxyapatite micropowders and nanopowders synthesized by sol-gel method (10, 20, 30, 40 %W) were composited to hydrogels and were investigated by mechanical analysis. The results of SEM images and Zetasizer experiments for synthesized nanopowders showed an average size of 100 nm. The nanoparticles distributed as uniform in the chitosan-starch film. The tensile modulus increased for composites containing hydroxyapatite nano-(size particle: 100 nanometer) powders than composites containing micro-(size particle: 100 micrometer) powders. The swelling percentage decreased for samples containing hydroxyapatite nanopowder than the micropowders. These nanocomposites could be applied for hard-tissue engineering.

1. Introduction

Hydroxyapatite (HA; Ca₁₀(PO₄)₆(OH)₂) is a type of calcium phosphate that has extensive application in the healing of bones and teeth, due to its biocompatibility and similar composition to that of natural bone. Biodegradability and nontoxicity, especially mechanical properties, are important factors for scaffolds in hard-tissue engineering [1–5].

Chitosan has been proved and regarded as biodegradable noncytotoxic material which has some interesting biological activities [6–8]. Some of the recent studies, however, indicate that chitosan, with higher than 60% deacetylation degree, shows little amount of degradation and is not absorbed easily in-vivo [8]. Starch, an biodegradable biopolymer, is getting increasingly more attractive because of its renewability, biodegradability, and low cost. Starch-based polymers have recently been proposed as having great potential for applications in biomedical field as implant materials, drug delivery systems, and tissue engineering scaffolds [9, 10]. In order to use it in temporary medical applications, such as temporary hard-tissue replacement, bone fracture fixation, and bone tissue scaffold, blends of starch with different materials such as ethylene-vinyl alcohol copolymer (SEVA) and poly (caprolactone) (SPCL) have been proposed [11–13]. Over the past 30 years, synthetic hydroxyl apatite and glass/ceramics have been developed and used in the medical field [14]. It is well known that when these bioactive ceramics are implanted in the body, spontaneously bond to living bone via an apatite layer deposited on their surface and is expected to confer a bone-bonding behavior and to improve the mechanical properties of these composites [15, 16]. Starch/ethylene vinyl alcohol (SEVA-C) as scaffold showed unsuitable mechanical properties for bone engineering, but starch-based polymers are a potential alternative, especially when reinforced by bioactive bone-like [17, 18]. In most biomedical applications, membranes are in direct contact with living tissues. Therefore, besides the usual mechanical characterization carried out in the dry state, new systems should also be subjected to test routines that allow for the evaluation of their mechanical performance in more realistic conditions [17–22]. In this study, the starch-chitosan composites containing micro- and nanopowders were synthesized and investigated by mechanical analysis.

2. Materials and Methods

2.1. Materials

Chitosan (deacetylation degree 87%), acetic acid, sodium hydroxide, sodium periodate (merk), Ca(NO₃)₂·4H₂O (Acros 99%), P₂O₅ (Acros 99%), HAP (sigma-aldrich; particle size: 60–180 micrometer), ethyl alcohol, PBS Solution, and deionized water.

2.2. Methods

The Hap nanopowder was prepared (Ca/P molar ratio: 1.67) using Ca (NO₃)₂·4H₂O and P₂O₅ by a simple sol-gel approach. A designed amount of phosphoric pentoxide was dissolved in absolute ethanol to form a 0.5 mol/L solution. A designed amount of calcium nitrate tetrahydrate was also dissolved in absolute ethanol to form a 1.67 mol/L solution. The mixture was stirred constantly for 24 h by a mechanical stirrer, allowing the reaction to complete at 800°C. A transparent gel was obtained. The gels were individually heated at a rate of 5°C/min up to 1000°C for 6 h. The sintered powders were ball-milled at 100 rpm to get fine powders.

Commercially obtained Ca(NO₃)₂4H₂O (0.01 mol; Acros 99%) and P₂O₅ (0.03 mol; Acros 99%) were poured into 10 mL of ethyl alcohol with the molar ratio of 10 : 3 (which is desired Ca/P ratio for hydroxyapatite). This solution transformed into a gel after stirring slowly for 1 h. The gel was then dried in an oven at 120°C in air for 15 h followed by subsequent heat-treating in stagnant air at 950°C for 12 h. HAP powders were obtained with particle sizes of 100–150 nanometers by this sol-gel method. Oxidized starch was prepared according to the procedure described by Hermanson [23]. 4.65 mL oxidized starch was mixed with 20 mL (1% w/v) of chitosan (weight ratio of 0.38). Then, the nanoparticles and microparticles in the different ratios were added slowly with vigorous stirring with the help of a mechanical stirrer at 3000 rpm. After addition of entire nanoparticles to the polymer solution, the resulting solution mixture was kept in a vacuum desiccator to remove the bubbles. Then, the mixture was heated in a water bath to evaporate water. The resulting slurry was poured into a glass petri dish and dried to make a film, keeping it in a vacuum oven at 60°C over night. Samples were washed several times with distilled water and then were incubated with aqueous sodium borohydride solution (0.05%) for 1 h to reduce excess noncross-linked aldehyde groups and chitosan. After washing several times with distilled water, samples were allowed to be dried on the petri dishes at room temperature. The morphological characteristics and size of the samples were studied by Zetasizer (3000 HAS; Malvern Instruments Ltd, Malvern, UK), scanning electron microscopy (SEM) (XL30; Philips, Eindhoven, Holland), and transmission electron microscopy (TEM) (CM200FEG; Philips). The tensile test of composite (membrane strips with 5 mm in width) in dry state was carried out with Instron Universal Mechanical Tensile Machine at room temperature using a crosshead speed of 1 mm/min and 40 mm grip distance. The presented results are the mean values of five independent measurements. The swelling percentage of swollen samples was measured after reaching equilibration point (3 h) where no change in weight of samples was observed. This percentage could be calculated according to the following: where %S is the percentage of swelling, and mi and mw are the weight of the samples before immersion and after equilibration period in physiological buffer solution (PBS), respectively.

3. Results and Discussion

3.1. Microscopic Results

SEM images of powders with magnification 10,000X are shown in Figures 1(a) and 1(b). Figure 1(a) shows particle sizes about 100 μm for commercial particles, and spherical particles formed in sol-gel method showed particle sizes to be about 100 nm. Considering the SEM image, it seems that the agglomerates were sufficiently dispersed in the Zetasizer testing conditions. The Zetasizer experiments for the dispersed particles in its own conditions showed particle sizes with an average size of 100 nm (Figure 2). Figure 3 shows SEM micrographs of chitosan-starch/HAp nano- and microcomposite samples (30% W). The figures indicated uniform distribution of nanoparticles in the polymer, but it is not for microparticles.

(a)

(b)

Figure 1: SEM micrographs of HAp nano- and micropowders (a) HAp micropowders (b) HAp nanoparticles (10000X).

Figure 2: Particle size distribution of HAP nanopowder in 10000°C.

(a)

(b)

(c)

Figure 3: SEM micrographs of chitosan-starch/HAp nano- and microcomposite samples (a) chitosan-starch (b) chitosan-starch/HAp micro composite samples 30% (w/w), (c) chitosan-starch/HAp nanocomposite samples 30% (w/w).

3.2. Mechanical Test

Figure 4 illustrates stress-strain curve for chitosan-starch copolymer. This figure shows that strain increases with stress increasing. Table 1 and Figure 5 show tensile modulus of composites containing HAP micro- and nanopowders. It could be observed that tensile modulus of these composites increases from 1.8 to 5.8 Gpa with the increasing HAP micropowders from 0 to 40% and from 1.8 to 6.1 Gpa with increasing of HAP nanopowders from 0 to 40%.

Table 1: Tensile modulus of starch-chitosan composites containing HAP micro and nanopowders. E1% (elasticity modulus in 1% strain).

HAP%
E1% (Gpa) composite containing HAP micropowder
E1% (Gpa) composite containing HAP nanopowder

0
1.8
1.8

10
3.4
3.8

20
4.1
4.7

30
5.1
5.5

40
5.8
6.1

Figure 4: Stress-strain curve obtained for starch-chitosan with weight ratio of 0.38.

Figure 5: Tensile modulus of starch-chitosan composites containing HAP micro- and nanopowders. (The tensile modulus of these composites was increased gradually with increasing filler percentage. Error bars indicate the maximum and minimum values for 4–6 samples measured.)

3.3. Swelling Test

Figure 6 and Table 2 show that swelling percentage of composites containing HAP powders decreases with increasing HAP percentage, and also values obtained from results show that swelling percentage for composites containing HAP nanopowders is less than this percentage for composites containing HAP micropowders.

Table 2: Swelling percentage of starch-chitosan composites containing HAP micropowders.

HAP%
Swelling % composite containing HAP micropowder
Swelling % composite containing HAP nanopowder

0
0.135
0.135

10
0.1
0.09

20
0.08
0.05

30
0.06
0.03

40
0.04
0.02

Figure 6: Swelling Percentage of starch-chitosan composite containing HAP micro- and nanopowders. The swelling percentage of composites with HAP micro and nanopowders was decreased gradually with increasing filler percentage, but swelling percentage of composites with HAP nanopowders is lower than composites with HAP micropowders.

4. Conclusions

In this study, starch-chitosan hydrogel were produced by oxidation of starch solution and subsequently cross-linked with chitosan via reductive alkylation (weight ratio (starch/chitosan): 0.38) and then filled with HAP nanopowders produced by sol-gel method and micropowders (10, 20, 30, 40 %W). The SEM and Zetasizer analysis showed morphology and size average of nanoparticles. The results obtained from SEM images showed uniform distribution of nanoparticles in the chitosan-starch composite. The tensile modulus of composites containing the HAP micro- or nanopowders was increased gradually with increasing filler ratio, but strength of composite with the HAP micropowders was lower than the HAP nanopowders due to more uniform distribution of nanoparticles in the polymeric matrix. The swelling percentage of composites with the HAP micro- or nanopowders was decreased gradually with filler percentage increasing, but swelling percentage of composite with the HAP nanopowders was lower than the composite with the HAP micropowders that could be due to more uniform distribution of nanoparticles in polymeric matrix and barrier for water penetration in membrane. These composite containing nanopowders could be used for hard tissue engineering.

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