Comparison of the Effect of Sol-Gel and Coprecipitation Routes on the Properties and Behavior of Nanocomposite Chitosan-Bioactive Glass Membranes for Bone Tissue Engineering

Lemos, Elke M. F.; Carvalho, Sandhra M.; Patrício, Patrícia S. O.; Donnici, Claudio L.; Pereira, Marivalda M.

doi:https://doi.org/10.1155/2015/150394

Journal of Nanomaterials

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Abstract Introduction Materials and Methods Results and Discussion Conclusions Acknowledgments References Copyright Related Articles

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Multifunctional Nanomaterials for Biomedical Engineering: Unique Properties, Fabrications, and Diverse Applications

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Research Article | Open Access

Volume 2015 | Article ID 150394 | https://doi.org/10.1155/2015/150394

Comparison of the Effect of Sol-Gel and Coprecipitation Routes on the Properties and Behavior of Nanocomposite Chitosan-Bioactive Glass Membranes for Bone Tissue Engineering

Elke M. F. Lemos,¹Sandhra M. Carvalho,¹Patrícia S. O. Patrício,²Claudio L. Donnici,³and Marivalda M. Pereira¹

Academic Editor: Sharmila M. Mukhopadhyay

Received13 Apr 2014

Revised16 Aug 2014

Accepted25 Sept 2014

Published28 May 2015

Abstract

Recent studies in tissue engineering have highlighted the importance of the development of composite materials based on biodegradable polymers containing bioactive glasses, in particular, composites for high load support and excellent cell viability for potential application in bone regeneration. In this work, hybrid composite films were obtained by combining chitosan with bioactive glass in solution form and in nanoparticle dispersion form obtained by the two different synthesis routes: the sol-gel method and coprecipitation. The bioactive glass served both as a mechanical reinforcing agent and as a triggering agent with high bioactivity. The results of in vitro assays with simulated body fluid demonstrated the formation of a significant layer of fibrils on the surface of the film, with a typical morphology of carbonated hydroxyapatite, reflecting induction of a favorable bioactivity. Maximum tensile stress increased from 42 to 80 MPa to the sample with 5% wt bioactive glass. In addition, samples containing 5% and 10% wt bioactive glass showed a significant increase in cell viability, 18 and 30% increase compared to the control group. The samples showed significant response, indicating that they could be a potential material for use in bone regeneration through tissue engineering.

1. Introduction

Nanoscale systems have generated promising results in bone tissue engineering; a growing consensus of the literature focuses on the development of nanostructured materials based on ceramics or bioactive glasses because of their high capacity for biomineralization [1–4]. The use of nanometer size particles is known to influence the increase in bioactivity of ceramic materials; in addition, the inorganic phase may act as a reinforcing agent for improving the mechanical properties of the material [5, 6]. The production of nanocomposites based on biodegradable polymers and bioactive glasses has been the focus of extensive studies in the literature, which combines the ability of glass to form a strong bond with the bone tissue surface [7, 8]. Bioactive glasses in the system SiO₂-CaO-P₂O₅ have been investigated as biomaterials to be introduced into the organic phase due to their osteoconductivity properties. When a bioactive glass is implanted, a biological response is generated at the interface of the material, leading to a chemical bond between the tissue and the material l [9, 10]. The biomineralization ability of bioactive glasses is related to their composition but is also influenced by their physical properties, such as particle size, porosity, surface area, and morphology [11–13]. The introduction of the bioactive phase in the polymeric composites has generally been produced by the sol-gel method, which is a versatile method that allows the incorporation of inorganic components into polymers at the molecular scale and at low temperatures, resulting in a hybrid material or nanocomposite material [7, 14].

Chitosan is a natural polymer that has shown promising performance in tissue engineering. This polymer has been extensively studied as a biomaterial because it has unique biomedical properties, mainly due to the ability to biodegrade [15, 16], the high biocompatibility [17] with immunogenicity, the ability to act as an antibacterial agent [18], and the antifungal properties [19] in wound healing, in addition to the benefit that the degradation products of chitosan do not generate toxic materials and are not carcinogenic [7, 20]. However, chitosan as a pure material is not ideal for bone regeneration because its osteoconductivity needs to be improved [21]. Because chitosan does not exhibit high bioactivity, it is necessary to combine it with another bioactive material to improve the osteoconductivity [22]. Furthermore, when a cross-linking agent, such as glutaraldehyde, is added to chitosan, it significantly increases its mechanical properties [23]. The mechanical properties are of crucial importance, especially in regard to regeneration of hard tissue such as bone, which requires load support. Therefore, the combination of chitosan and silica-based nanoparticles to form a hybrid nanocomposite is a strategy to address the demands of mechanical loading on bone grafts. There are a few studies demonstrating the interaction at the molecular level of chitosan with silica-based materials [2, 3, 6, 15, 19]. Chitosan has functional groups, such as hydroxyl groups and amines, which have high possibility of rapidly bonding to other functional groups. Hybrids formed from chitosan and silica exhibited an increase of the interfacial interaction with improved mechanical properties [3].

In this work, two strategies were used to produce bioactive nanocomposites: one strategy involves a solution (sol-gel) and the other strategy involves a nanoparticle dispersion obtained by combination of the sol-gel method and the coprecipitation method. These two synthesis routes were used to produce membranes, which were evaluated in terms of their mechanical properties, bioactivity, and biological synthesis for future use in scaffolds of bone tissue engineering.

2. Materials and Methods

Commercial chitosan (high molecular weight and degree of deacetylation 75–85%), tetraethylorthosilicate (TEOS, 98%), and triethyl phosphate (TEP-99%) were supplied by Sigma-Aldrich, and ammonia (NH₃) and Ca(NO₃)₂·4H₂O (99%) were supplied by Synth. The composition of the bioactive glass was 60%:SiO₂, 36%:CaO, and 4%:P₂O₅ (% mol). A solution of glutaraldehyde 2.0% w/v was obtained by dilution of a commercial solution (25% w/v, Sigma-Aldrich).

2.1. Bioactive Glass Solution Preparation

The bioactive glass precursor solution was obtained by acid hydrolysis and polycondensation of tetraethylorthosilicate (TEOS (Si(OC₂H₅)₄)), alkoxide precursor of SiO₂, triethyl phosphate (TEP ((C₂H₅O)₃PO₄)), and alkoxide precursor P₂O₅. The hydrolysis occurred by adding deionized water and was catalyzed by nitric acid. Calcium nitrate (Ca(NO₃)₂·4H₂O) was added as a precursor of CaO.

2.2. Bioactive Glass Nanoparticle Dispersion Preparation

The method of preparation of BGNPs was based on previous work [4, 5] consisting of combining the sol-gel coprecipitation method. In the first step, TEOS and TEP precursors were hydrolyzed under acidic conditions. The precursors were dispersed in methanol and water, and the pH was adjusted to 1-2 by nitric acid. The mixture was kept under magnetic stirring to obtain a transparent sol. In this second step, transparent sol (monodisperse) was condensed separately in alkaline solution. The sol was then dripped in deionized water with ammonium hydroxide under vigorous mechanical agitation. The pH of the solution was adjusted in the range of 10 to 12. After 12 h of mechanical stirring, the suspension was taken to the oven 50°C to evaporate the ammonia (until pH < 8). Calcium nitrate was added and kept under mechanical stirring for 24 h. The dispersion obtained was filtered through Millipore filters of 0.22 μm and 0.11 μm; after passing the dispersion through each of the filters, the dispersion was collected and stored for later use. The final appearance of the dispersion was a colorless liquid.

2.3. Hybrid CS-BG Films Preparation

The hybrid films were obtained by mixing 1% w/v chitosan solution with the precursor solution bioactive glass of the following compositions: 10 wt%, 20 wt%, and 30 wt%; these materials were then cross-linked with glutaraldehyde corresponding to 3% of the total weight of chitosan. Films from pure chitosan were produced. The final solution was poured into polypropylene dishes and kept at room temperature for approximately 60 h. They were then placed in an oven (40 ± 2°C) for 24 h for complete drying.

2.4. Nanocomposites CS-BGNP Films Preparation

The nanocomposite films were obtained by dissolving 1% w/v chitosan commercial powder in the previously prepared dispersion of BGNP (item 2.2), based on previous work under acidic conditions, to obtain the following concentrations of nanoparticles in the films compositions: 1 wt%, 3 wt%, 5 wt%, and 10 wt%. The dissolution procedure consists of the following steps. Deionized water was added to the dispersion BGNP under mechanical stirring; the dispersion was measured to have pH above 7. Nitric acid was added to obtain pH = 2.5. Chitosan powder was added slowly while maintaining the pH below approximately 4. After stabilization, the suspension was kept under mechanical stirring for 24 h. Glutaraldehyde, corresponding to 3 wt% of the total weight of chitosan (the same amount used to synthesize the hybrid films previously described), was added into the suspension, which was subsequently poured into a Petri dish and then kept at room temperature for 60 h. Finally, the suspension was completely dried in an oven (40 ± 2°C) for 24 h.

2.5. In Vitro Bioactivity Tests

The synthesis conditions of the hybrids typically resulted in a product of polymeric character that is sensitive to high temperatures, which prevents the elimination of toxic substances by thermal treatment [24]. When in contact with the culture medium, the dissolution of hybrid products may change the pH of the medium and the cell growth, promoting lower cell viability. This change requires a neutralization step to reduce the acidity of the samples and to make them more biocompatible. Therefore, to assess the bioactivity, a prestudy of variation of pH and hybrid nanocomposites in a solution of SBF (kept at 37°C) was conducted. Samples containing 0 wt%, 10 wt%, 20 wt%, and 30 wt% of BG and samples containing 0 wt%, 1 wt%, 3 wt%, and 5 wt% of BGNP were immersed for zero days, one day, seven days, and 28 days, followed by the measurement of the pH.

The biomineralization tests were performed according to ISO/FDIS 23317:2007 (E) [25–28]. Films with 20 wt% of either BG or BGNP were used in these tests. The samples in triplicate that were cut to a size of 10 mm × 20 mm were immersed in SBF (simulated body fluid) and kept for one day, seven days, and 28 days. The quantity of 40 mL of SBF was used to obey the relationship between the surface area of the sample (Sa) in square millimeters and the volume of SBF solution (Vs) in milliliters given by Vs = Sa/10. The vials containing the samples were placed in a water bath at 37 ± 2°C. After removing the samples from the SBF, they were washed and dried at room temperature. The level of mineralization of the films after immersion was evaluated by scanning electron microscopy (SEM). Fourier transform infrared (FTIR) spectroscopy was also used to confirm the presence of the components of carbonated hydroxyapatite (CHA) (Nicolet 380 of ThermoScientific). Moreover, the standard bioactivity ISO/FDIS 23317: 2007 (E) describes that SEM and FT-IR data must be accompanied by analysis of X-ray diffraction (XRD) data to confirm the formation of the CHA and therefore the formation of the CHA layer was also investigated by XRD [29].

2.6. Mechanical Tests

The selection of samples subjected to tensile tests was defined as the most homogeneous region of the films to obtain more representative results in the mechanical test. The samples of the films were subjected to the tensile test to evaluate the tensile strength and the strain at break. The films were subjected to the test with an initial spacing between the gauge lengths of 50 mm. To ensure accurate results, 6–8 samples of each film were submitted to testing. The tests were conducted on the Machine Model 3000 EMIC DL, using a 200 N load cell, a test speed of 25 mm min⁻¹, and a test temperature of 26 ± 2°C. The tensile tests were performed according to ASTM D882-10 (Standard Test Method for Tensile Properties of Thin Plastic Sheeting) [30].

2.7. In Vitro Cytotoxicity Tests

The films synthesized were submitted to the first stage of in vitro evaluation by the cytotoxicity test following 10993-5:1999 (Biological evaluation of medical devices; Part 5: tests for in vitro cytotoxicity) [25–28]. The Resazurin cell viability assay was used. Human osteosarcoma cells (SAOS), a commercial line of immortalized cells, were kindly provided by Professor Alfredo Miranda Goes, the Department of Biochemistry and Immunology, UFMG. The cells were cultured in DMEM with 10% fetal bovine serum (Gibco BRL, NY), penicillin G sodium (10 IU/mL), streptomycin sulfate (10 mg/L), and 0.25 amphotericin B (Gibco BRL, NY, USA) in an incubator with 5% CO₂ at 37°C. Samples of the films CS-BG and CS-BGNP with 12 mm in diameter were placed in 24-well plates and cells were plated ( cells) on each sample material. Cells with DMEM and 10% FBS were used as reference controls, as positive control PBS (2X), and as negative control chips of sterile polypropylene Eppendorf (0.1 mg/mL) from Eppendorf (Hamburg, Germany). The method of sterilization was ultraviolet radiation for 30 minutes on each side of the samples [31–33]. Tests were performed in triplicate () for each sample type. After 72 h, all of the media were aspirated, and 900 μL of culture medium with serum was placed into each well. One hundred microliters of Resazurin (0.1 mg/mL, Sigma-Aldrich, USA) was added in each well, which was placed in an incubator for a period of 18 h with 5% CO₂ at 37°C. Then, 100 μL was removed from each well and transferred to 96-well flat plates, and the measurement was performed using a spectrophotometer (1.6 Adap, Anthos Labtec Instruments) with two filters of 570 nm and 590 nm.

3. Results and Discussion

3.1. Qualitative Assessment

Homogeneous films were produced by the technique of evaporation of the solvent and visually exhibited a yellowish transparent glossy surface. The films and hybrid nanocomposites containing higher levels of bioactive glass (30 wt% of BG) underwent a change in their physical appearance after drying: the structure retracted and exhibited a loss of flexibility, thereby making the surface appear opaque. This behavior is clearly observed in the films with 30 wt% of bioactive glass.

3.2. Tests of the In Vitro Bioactivity

Table 1 presents the pH values of the medium after immersion of the nanocomposite. The pH values obtained ranged from 7.22 to 7.50; therefore, there was not a significant change of pH in the solution of PBS, indicating that the samples were stable in this aspect and indicating that a neutralization step was not required.

SEM images of the surface of the films with 20 wt% BG immersed in SBF for one day, seven days, or 28 days are shown in Figure 1. Gradual formation of CHA with increasing days of immersion in SBF was observed in the SEM images (Figure 1(A–d)).

On the surface of the hybrid films (20 wt% of BG), a homogeneous morphology was observed due to the dispersion of small crystals with sizes less than 5 μm, which characterizes the formation of the CHA layer. Initially, the apatite grains were more isolated (Figure 1(A-a)) and, after seven days, exhibited a uniform and thicker layer on the surface of the hybrid (Figure 1(B-b)). After 28 days the film surface was completely covered by CHA, exhibiting a more intense biological response, according to the increase of the immersion time (Figure 1(c-D-d)). The identification of the chemical composition of these crystals was performed by EDS, which indicated the presence of Ca (Calcium) and P (phosphorus), as shown in Figure 1(C). Although the analysis by EDS does not represent a quantitative analysis, the Ca and P peaks were very significant in the sample.

The FTIR spectra (Figure 2(a)) for pure chitosan films and for films containing 10, 20, and 30 wt% content of bioactive glass after immersion in SBF immersed for one day to 28 days showed vibration bands at 520 cm⁻¹, 560 cm⁻¹, and 600 cm⁻¹ corresponding to the bending vibration of P-O. These results indicated the formation of a crystalline layer of calcium phosphate. The bands at 600 cm⁻¹ are related to the group, as shown in Figures 2(a) and 2(b). The band at 890 cm⁻¹ that is related to the stretching vibration of the group was more evident in the films with a 10, 20, and 30 wt% content of bioactive glass, as shown in Figure 2(a). The FTIR spectrum of films containing 30 wt% bioactive glass after 28 days of immersion, shown in Figure 2(b), reveals a band at 520 cm⁻¹ related to the bending vibration of P-O. Bands at 1024, 1020, and 1150 cm⁻¹ for films with one-day immersion, as shown in Figures 2(a) and 2(b), are indicative of the shift of the 1100 cm⁻¹ band, which is attributed to the stretching P-O. The intensities of the bands increased after 28 days of immersion, indicating the formation of the CHA layer. Films of pure chitosan did not exhibit bands related to the formation of CHA [14, 34, 35].

(a)

(b)

CHA formation was also recorded by XRD (Figure 3). The XRD patterns of the films revealed a peak with a high intensity at and another peak with a low intensity at , which are associated with the planes (211) and (002), respectively [4, 19, 36, 37]. These peaks are characteristic of the crystalline phase of CHA according to record 19-274 (JCPDS). However, these two peaks only appear in the hybrid with 20 wt% of BG. The XRD patterns of the films containing 0 and 10 wt% glass exhibited broad peaks, indicating that the analyzed area has little or no crystallinity and therefore exhibits low bioactive property. Both the pure chitosan and the film with 10 wt% BG exhibited no diffraction peaks, indicating that these were amorphous materials. The film with 30 wt% BG was not examined by XRD because it was not possible to investigate its surface, due to the irregularities caused by it containing high concentration of BG.

3.3. In Vitro Cytotoxicity Assay

The mitochondrial activity of osteoblasts cultured with and without the presence of materials produced in this work was evaluated by the Resazurin test. This test is used to specifically assess mitochondrial function and cell viability. Figure 4 illustrates the hybrid cell viability of hybrids (CS-BG) and the nanocomposites (CS-BGNP). In the control group, the cells were seeded only by viable osteoblasts (no samples in the middle). In comparative groups, the cells were seeded on each film composition of the hybrid nanocomposites. Comparing the films analyzed with the control group after 72 h, it can be concluded that as the content of the material BGNP increased, the cell viability also increased, and this difference was statistically significant () for films with 5 and 10 wt% BGNP. The results indicated that cells plated on 5% CS-BGNP exhibited an increase of 18 ± 7.5% cell viability and the cells plated on CS-BGNP 10% exhibited an increase of 30 ± 2% cell viability compared to the control group. The cells plated in 10% CS-BG exhibited a 10 ± 1% increase in the cell viability. Studies in the literature identified that the higher cell viability compared to control when using bioactive glasses with 60% silica can be attributed to the ability of the ionic products from these materials to stimulate osteoblast proliferation [38]. Cells plated on CS 1% BGNP and CS 3% BGNP after 72 h exhibited a cell viability similar to that of the control group which was significantly higher compared to the viability of pure chitosan (CS 0% BG). No significant differences in cell viability were found compared to the control group of cells plated on CS 20% BG. A decrease in cell viability was observed compared to the control group for cells plated on pure chitosan and 30 wt% CS-BG. The biological tests conducted with Resazurin in cells grown on the samples after 72 h indicated that samples containing nanoparticles of bioactive glass were more favorably increasing cell viability, but the results obtained by the hybrids CS-BG also induced a significant response from the cells because cell death was not markedly observed.

3.4. Tensile Testing

Figure 5(a) shows the stress-strain behavior relative to pure chitosan and films with 10 and 20 wt% of bioactive glass, each cross-linked with glutaraldehyde. In general, the behavior of the stress-strain curves is typical of a plastic material. It was observed that the films with bioactive glass decrease their percentage of elongation at break while they gradually increase its tensile strength. The bioactive glass behaves as typical reinforcing filler. The chitosan film exhibited a strength value of 42 MPa and elongation at break of 11% (Table 2). The film with 10 wt% of bioactive glass increased its maximum strength to 53 MPa, while its elongation at break decreases to 5%. The film containing 20% glass undergoes a large increase in the maximum tensile strength reaching values of 67 MPa, although its elongation at break decreases to 4%. This behavior occurs due to interactions in the polymer network with the glass; the dispersion of the sol changes the chitosan matrix structure, leaving the hybrid with a less flexible structure, lessening its ductility compared to the films that did not undergo the addition of bioactive glass. Figure 5(b) illustrates the stress-strain curves for films of chitosan with 1, 3, 5, and 10% BGNP, all of which are cross-linked with glutaraldehyde.

(a)

(b)

Tasselli et al. [23] investigated the mechanical properties of chitosan cross-linked with different glutaraldehyde content. For low contents of glutaraldehyde added an increase of the mechanical properties compared to pure chitosan was observed, unlike what was observed with higher contents added, for which the tensile strength decreased dramatically. Similar results were observed in this work. Although cross-linked chitosan produced in this work presented slightly smaller tensile strength than those found by the authors, the mechanical properties were significantly improved after the addition of BGNP.

The behavior in the tensile tests of nanocomposite films with BGNP is fairly similar to the behavior of the hybrid films with BG. The films exhibited a flexible behavior, and their stress-strain curves are typical of a plastic. The nanocomposite films were strongly influenced by the BGNP content and exhibited high performance in comparison with the other hybrid films tested. Films with 3 and 5 wt% BGNP reached maximum strength values of 73 MPa and 80 MPa, respectively. The elongation at break was also very significant, with percentages of 22% and 21% for films with 3 wt% and 5 wt% BGNP, respectively.

4. Conclusions

Hybrid composite films produced by homogeneous chitosan and bioactive glass have been successfully obtained using the two synthetic routes of sol-gel and coprecipitation, achieving adequate performance for the application as a guide to the cell growth of bone tissue. Both systems of CS-BG as CS-BGNP films exhibited high tensile strength and high bioactivity and cell viability. These results indicate that the use of bioactive glass successfully acted as an agent for loading and improved bioactivity, particularly in the form of nanoparticle dispersion (BGNP), whose results are the most promising.

Conflict of Interests

The authors declare that there is no conflict of interests regarding the publication of this paper.

Acknowledgments

The authors thank FAPEMIG, CAPES, and CNPq for the financial support of the work.

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Copyright © 2015 Elke M. F. Lemos 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.

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