Open Journal of Regenerative Medicine
Vol.05 No.01(2016), Article ID:64640,10 pages

Development of Chitosan/Poly(L-Lactide)/Multiwalled Carbon Nanotubes Scaffolds for Bone Tissue Engineering

A. De la Paz Orozco1, F. Jiménez Vega1, S. A. Martel-Estrada2, A. Hernández Aguilar3, M. E. Mendoza-Duarte4, M. C. Chavarría-Gaytán3, C. A. Rodríguez-González3, I. Olivas-Armendáriz3*

1Instituto de Ciencias Biomédicas, Universidad Autónoma de Ciudad Juárez, Chihuahua, México

2Instituto de Arquitectura Diseño y Arte, Universidad Autónoma de Ciudad Juárez, Chih, México

3Instituto de Ingeniería y Tecnología, Universidad Autónoma de Cd. Juárez, Chihuahua, México

4Centro de Investigación en Materiales Avanzados, Chihuahua, México

Copyright © 2016 by authors and Scientific Research Publishing Inc.

This work is licensed under the Creative Commons Attribution International License (CC BY).

Received 9 February 2016; accepted 14 March 2016; published 17 March 2016


This work focuses to improve the mechanical properties and investigates the growth of osteoblasts on a degradable chitosan/poly(L-lactide)/carbon nanotubes composite for tissue engineering. The morphological and mechanical properties characterizations were performed using scanning electronic microscopy (SEM) and rheometrics analysis system (RSA). Osteoblasts differentiation was determined by alkaline phosphatase activity, total number cells by an Alamar Blue assay, cell attachment and proliferation were visualized qualitatively using SEM, mineralization was characterized by transformed infrared spectroscopy, energy dispersive spectroscopy, and X-ray diffraction. The results suggest that the chitosan/poly(L-lactide)/multiwalled carbon nanotubes composites exhibit the ability to promote cell adhesion, proliferation, and differentiation on their surface.


Chitosan, Poly(L-Lactide), Multiwalled Carbon Nanotubes, Mechanical Properties, Biocompatibility

1. Introduction

Bone structural damage is the major cause of chronic pain, disability, and loss of function, resulting in a high cost in health; subjects with bone loss, whose regeneration is poor, requiring a graft to complete the repair, and restore normal function of the bone [1] . In some cases, placing a graft is not feasible, so it is necessary to search for new options. Tissue engineering presents the use of biomaterials like biological substitutes to regenerate, maintain or improve tissue function lost, requiring artificial scaffolding, degradable, capable of initiating osteoinduction, with resorption rate that equals bone regeneration, so that the material is degraded when the lesion is completely regenerated [2] .

Actually porous matrices manufactured by various techniques, have allowed the processing of natural polymer such as chitosan (Ch), or synthetic including polyhydroxy acids, such as poly(L-lactide) (PLLA) [3] . Chitosan and PLLA are biocompatible, biodegradable and bioabsorbable materials [4] - [7] which serve as a structure for the undifferentiated cells and osteogenic potential as growth factors, inducing the differentiation of osteoblasts [8] . Chitosan has a hydrophilic surface which makes it biocompatible [9] - [11] . However, it is mechanically weak, unstable and it is unable to maintain a predefined shape. As a result of swelling, it has little flexibility to adjust its mechanical properties; while the additional methyl group in PLLA makes it more hydrophobic, reducing its molecular affinity to water, leading to a slower hydrolysis [12] . Meanwhile carbon nanotubes (CNT) are among the strongest and harder materials, they have excellent mechanical, electrical [13] [14] , optical, thermal and chemical properties [15] , making them an excellent choice as filler in biomaterials to improve their properties [16] ; since they can be customized to mimic the extracellular matrix in terms of structure, chemical composition and mechanical properties, as well as support cell growth and differentiation of osteoblasts [17] . In tissue engineering, a material with a single component cannot help mimic all the properties of bone, therefore, the development of composite materials is imperative as an alternative to bone repair.

In this work, we combined chitosan, PLLA, and Multiwalled carbon nanotubes (MWCNT) for preparing composites with good mechanical and physicochemical properties for tissue engineering applications. The objective was to evaluate the in vitro response of rat calvaria osteoblasts growth, by means of culturing them on scaffolds made of Ch/PLLA reinforced with different amount of MWCNT (0%, 1%, 2%, 5% and 10% w/w), at 3, 7 and 14 days of cell culture. Morphology and cell viability of the composites were evaluated by scanning electron microscopy (SEM) and Alamar Blue assay respectively, osteoblast phenotype was analyzed by the activity of alkaline phosphatase (ALP); the formation of hydroxyapatite (HAp) by Fourier transform infrared spectroscopy (FT-IR) and X-ray diffraction (XRD).

2. Materials and Methods

2.1. Preparation of Composites

The MWCNT (CIMAV, Mexico) was added to the solution of 2% acetic acid and dispersed by sonication. Chitosan (Sigma-Aldrich, St. Louis, MO) and PLLA (DURECT Corporation, Cupertino CA.) were dissolved in acetic acid solution with MWCNT and chloroform. Afterwards, PLLA solution was added slowly to the chitosan solution and the mixture was stirred until a homogeneous mixture was obtained. Then, the mixture was frozen at −78˚C and later the solvent was extracted by a freeze-drying system for 48 h. The composites were neutralized in an aqueous solution of NaOH-CH3CH2OH (0.5 wt% NaOH was dissolved in 80% ethanol aqueous solution) at −20˚C for 12 h. Then it was immersed in pure ethanol for 12 h at −20˚C. After that, it was washed with distilled water and dried in a freeze dryer respectively obtaining composites with percentages of 49.5/49.5/1, 49/49/2, 47.5/47.5/5, and 45/45/10 of chitosan, PLLA, and MWCNT.

2.2. Mechanical Properties

RSA III (Rheometrics Analyzes System) TA was used in static mode at a frequency of 6.2832 rad/s and at 37˚C for all samples. Disks of approximately 10 mm in thickness and 25 mm in diameter were used in all the experiments.

2.3. Cell Culture

Osteoblasts calvaria cells were obtained from 14 day old Sprague Dawley rats. Osteoblastic cells were counted using an automated cell counter (Countess® automated cell counter, Invitrogen), seeding 5 × 104 cells into composite fragments of 10 mm in diameter and 3 mm in thick, embedded in α-MEM medium (Sigma-Aldrich, St. Louis, MO), (supplemented with 10% of fetal bovine serum, 3% of gentamicin-penicillin, 3 mM of b-gly-cerol- phosfate and 10 mg/mL of ascorbic acid). The culture medium was renewed every two days. The cultures were maintained in an incubator at 37˚C with 5% of CO2 and 95% of relative humidity. The composite prior to seeding were washed with distilled water to remove residual solvents, lyophilized to −80˚C (Labconco Free-zone) and sterilized by UV for 2 hours, remaining composites were immersed in solution α-MEM at 37˚C in incubator (Shel Lab model 1012) the night before planting osteoblasts.

2.4. Cell Proliferation

To quantify cell proliferation of the composites, a spectrophotometric method was realized using Alamar Blue® reagent following the manufacturer’s instructions (Biosource, Invitrogen), mixing 100 mL of Alamar Blue indicator with 900 mL of α-MEM containing 10% FBS. For reading proliferation the biomaterial was removed from culture medium and washed by stirring in PBS 1×. All samples were immediately immersed in the mixture solution of α-MEM, FBS and Alamar Blue, leaving them to incubate for 4 hours at 37˚C. Spectrophotometric reading was measured at 570 nm (Benchmark Plus, BioRad microplate spectrophotometer). It was used as a calibration curve generated previously with a number of cells known.

2.5. Alkaline Phosphatase Activity

Alkaline Phosphatase Activity (ALP) of the osteoblasts was measured as an early marker of maintaining their phenotype, using a kit ALP substrate (Pierce Biotechnology). This colorimetric test used as a substrate p-nitro- phenyl phosphate (P-NNP) and is based on the P-NNP conversion to p-nitrophenol (p-NP) in the presence of ALP. 10 mg of PNPP were dissolved in 10 ml of diethanolamine buffer, cells were lysed with Triton X-100 1% DEPC-treated water and with three cycles of thermal shock. 100 mL were taken from the sample and 100 mL of PNPP solution was added and incubated at 37˚C for 30 minutes. Once the incubation period stopped the reaction, 50 mL of 2N NaOH solution was added to each sample. The production of P-NP was determined by the absorbance at 405 nm by spectrophotometry (Benchmark Plus Microplate spectrophotometer). Plus Microplate spectrophotometer.

2.6. SEM Analysis

Scaffolds with osteoblasts cultured at 3, 7 and 14 days were removed from the culture medium, rinsed with PBS, placed in a new plate and immersed in a solution of 3% glutaraldehyde for 3 hours to fix the cells. The samples were dehydrated through a series of ethanol solutions (70%, 85%, 90%, 95% and 100%) with an interval of 10 minutes between each set. The dry samples were mounted on aluminum stubs and characterize the morphology and cell proliferation in a field scanning electron microscopy (Jeol JSM7000F).

2.7. Mineralization

FT-IR analysis was performed using a transmission mode in an IR spectrometer (Nicolet 6700, Thermo Scientific, USA), which has a 2 mm diameter diamond window. All spectra were recorded between 4000 and 650 cm−1, for each spectrum 100 scans were performed at 16 cm−1. The X-ray diffraction patterns of the samples were analyzed between 2˚ = 5˚ and 2˚ = 80˚ with a step size of 2˚ = 0.02˚ in an X-ray diffraction instrument in continuous mode (PANanalytical X’Pert PRO). All spectra were recorded using 100 scans and 16 cm−1 resolutions.

2.8. Statistical Analysis

All assays were performed in triplicate and the data analyzed in the statistical package Minitab 16 for Windows XP. The data obtained were evaluated for statistical significance using the Student’s t-test. The results of the analyzed variables were expressed as mean ± standard deviation and the statistical differences between the study groups and the control were considered significant when p < 0.05.

3. Results and Discussion

3.1. Microstructural and Mechanical Properties

Figure 1 shows the images of chitosan/PLLA, chitosan/PLLA-2%MWCNT, and chitosan/PLLA-5%MWCNT.

Figure 1. SEM images of chitosan/PLLA ((a), (b), and (c)), chitosan/PLLA-2%MWCNT ((d), (e), and (f)), and chitosan/ PLLA-5%MWCNT ((g), (h), and (i)) composites.

A similar morphology of the composites matrix with and without multiwall carbon nanotubes can be observed. Figure 1(a), Figure 1(d), and Figure 1(g) show organized morphology in sheets and/or elongated plates through the entire matrix. At higher magnifications, it is possible to observe a highly interconnected porous structure (˂30 µm). The morphology on the scaffolds was dominated by heat transfer and the porosity shows dependency on the route in which the phase separation between the solvents and polymers takes place, as was demonstrated in a previous work [5] . Then in Figure 1(a), Figure 1(d), and Figure 1(g) sheets forming various elongated layers in the gradient direction can be observed. The interconnected porosity could be reached inside the layers, as it is showed clearly in Figure 1(c). Furthermore, Table 1 shows a varied pore size, the average pore size of chitosan/PLLA, chitosan/PLLA-1% MWCNT, chitosan/PLLA-2%MWCNT, chitosan/PLLA-5% MWCNT, and chitosan/PLLA-10%MWCNT composite varied from 96.48 mm to 51.58 mm as measured by SEM. The increase in the concentration of MWCNT in the polymeric matrix, resulted in the decrease of average pore size, this trend can be attributed to carbon nanotubes that filled the space available in the pores and thus decreased the porosity of materials [17] . The pores generated in each composite have a range size from 40 mm to 100 mm and 100 mm to 350 mm (mostly), This highly porous and interconnected structure facilitates uniform distribution of the cells, optimizes biological environment, and provides an adequate nutrient flow [5] [17] [18] .

The mechanical properties of composites were evaluated by means of dynamical-mechanical analysis and the results are shown in Figure 2. The incorporation of MWCNT increases the module of Ch/PLLA-1%MWCNT composite in comparison to the Ch/PLLA composite by 26.48%. Similar trends were observed between Ch/ PLLA-1%MWCNT and Ch/PLLA-2%MWCNT composites, showing an increase of 31.20%. The greatest in- crease between a module and another was between the composites Ch/PLLA-2%MWCNT and Ch/PLLA-5% MWCNT (43.39%). However, the Young´s modulus of the composite containing 5% of MWCNT and the composite containing 10% of MWCNT was similar, being the increment between modules of 9.15%. This result can be due to the agglomeration of MWCNT in the composite [20] , so this result confirms that lower amounts of MWCNT in the composites can significantly improve the mechanical properties [21] and offers a topography that mimics the natural tissue nanostructure, such that, add MWCNT in polymeric biomaterials induce a porous surface, favorable for cell adhesion and proliferation [22] .

Figure 2. Variation of the Young’s modulus of (1) Ch/PLLA, (2) Ch/PLLA-1%MWCNT, (3) Ch/PLLA-2%MWCNT, (4) Ch/PLLA-5%MWCNT and (5) Ch/PLLA-10% composites.

Table 1. Distribution of pore size. Average pore size (mm) and porosity distribution (%) of the chitosan/ PLLA, chitosan/PLLA-1%MWCNT, chitosan/PLLA-2%MWCNT, chitosan/PLLA-5%MWCNT, and chitosan/PLLA-10%MWCNT.

3.2. Cell Proliferation

Cell proliferation of the composites after in vitro culture for 14 days was evaluated by Alamar Blue analysis. Figure 3 shows that the proliferation at 3 days of cell culture that Ch/PLLA-5% MWCNT and Ch/PLLA-10% MWCNT composites had a significantly higher number of cells, maintaining this tendency to day 7; at 14 days of the assay, showed a significant decrease in the rate of proliferation in Ch/PLLA-10%MWCNT and Ch/PLLA- 5%MWCNT. This is coincident when the osteoblast differentiation ends and becomes osteocyte, which is unable to continue proliferating [23] . Ch/PLLA-5%MWCNT and Ch/PLLA-10%MWCNT composites facilitated the adhesion and cell proliferation, and mineralized nodule formation, suggesting that these scaffolds have stimulant effects to promote proliferation rate and cell calcification, due to the surface roughness and porosity of the scaffold [24] [25] . Previous studies have reported that polymer matrices reinforced with concentrations greater than 2% by weight of MWCNT have a negative influence on cell growth, suggesting a maximum amount of MWCNT in which the surface roughness affects cell growth [26] . With the above results it is concluded that up to 10 wt% can be the maximum concentration of MWCNT, without negative implications on osteoblasts.

3.3. Alkaline Phosphatase Activity

In the other hand, osteoblasts reached an aging step, since the ALP activity was increased in the early stages of cell culture and at the end of the assay decreased, by the onset of calcification (Figure 4). Comparing Ch/PLLA and Ch/PLLA-MWCNT, greater activity was significantly observed at day 3 and 14 of cell culture of Ch/PLLA- 2% MWCNT, Ch/PLLA-5%MWCNT and Ch/PLLA-10%MWCNT. These results suggest that the ALP activity of the cells increases proportionally with the percentage of MWCNT composites, this being indicative of osteoblast differentiation [25] [26] .

3.4. SEM Analysis and Mineralization

Figure 5 shows the images on the 14 days of culture, observing the similar structure before culture once hy-

Figure 3. Cell proliferation at 3, 7 and 14 days of cell culture: *p < 0.05 vs. control group #p < 0.05 vs. Ch/PLLA ap < 0.05 vs. Ch/PLLA-1%MWCTN bp < 0.05 vs. Ch/PLLA-2% MWCTN cp < 0.05 vs. Ch/PLLA-5%MWCTN dp < 0.05 vs. Ch/PLLA-10%MWCTN.

Figure 4. Alkaline phosphatase activity. *p < 0.05 vs. Control group #p < 0.05 vs. Ch/PLLA ap < 0.05 vs. Ch/PLLA-1% MWCTN bp < 0.05 vs. Ch/PLLA-2%MWCTN cp < 0.05 vs. Ch/PLLA-5%MWCTN dp < 0.05 vs. Ch/PLLA-10%MWCTN.

drated with cell culture medium. The images reveal the presence of adherent cells on the substrate and spread uniformly, with a greater number of cells in Ch/PLLA-2%MWCNT,Ch/PLLA-5%MWCNT and Ch/PLLA-10% MWCNT (Figure 5(d), Figure 5(g), Figure 5(j)), and evidence of a migration between the pores of the composite. MWCNT nanometer size is close to filopodium osteoblastic, therefore, the distal end of filopodium interacts with MWCNT, giving a high capacity of adherence [21] . At higher magnification (Figure 5(d), Figure 5(e), Figure 5(h), and Figure 5(k)), the preserved morphology of osteoblasts can be observed, tending to extend small filopoidales projections indicative of cell adhesion to the composite. In Figure 5(c), Figure 5(f), Figure 5(i), and Figure 5(l) can be observed incipient formation of HAp crystals, hexagonal morphology as reported in the literature [27] , in Ch/PLLA-2% MWCNT (Figure 5(f)), Ch/PLLA-5%MWCNT (Figure 5(i)) and Ch/PLLA- z10%MWCNT (Figure 5(l)). The image shows that the scaffold containing MWCNT have a positive influence on osteoblasts, promoting cell adhesion and spreading. Figure 6 and Figure 7 correspond to the FT-IR analysis of composites at 14 days of cell culture, showing absorption bands corresponding to PO4 (1089 cm−1, 960 cm−1) and CO3 (1458 cm−1 and 1462 cm−1), [28] [29] .

Figure 8 shows the diffraction pattern of the composite Ch/PLLA/MWCNT in different percentages on the 14 day of cell culture. The shift of the peaks corresponding to HAp were 22˚, 26˚, 40˚, 45˚ and 50˚, in the scale of 2q, the broadening of the RX diffraction peaks indicates the small size of the crystals of HAp formed in situ [30] . XRD patterns show the presence of HAp, these results are consistent with the images obtained by SEM.

4. Conclusion

Within the reinforced composite, proliferation of osteoblast cells was demonstrated and significantly higher ALP content with the addition of 5% and 10%-MWCNT, further facilitating adhesion and mineralized nodule

Figure 5. Scanning electron micrographs of cell-seeded on composite after 14 days of culture. (a), (b), and (c) Ch/PLLA-1%MWCNT; (d), (e), and (f) Ch/PLLA-2%MWCNT; (g), (h), and (i) Ch/ PLLA-5%MWCNT; (j), (k), and (l) Ch/PLLA-10% MWCNT.

Figure 6. FTIR spectra of the Ch/PLLA, Ch/PLLA-1%MWCNT, Ch/PLLA-2%MWCNT, Ch/ PLLA-5%MWCNT and Ch/PLLA-10% composites seeded with osteoblasts at day 14. The spectra observed the characteristic peaks of calcium carbonate (1462 cm−1, 1458 cm−1).

Figure 7. FTIR spectra of the Ch/PLLA, Ch/PLLA-1%MWCNT, Ch/PLLA-2%MWCNT, Ch/PLLA-5%MWCNT and Ch/PLLA-10% composites seeded with osteoblasts at day 14. The spectra observed the characteristic peaks of calcium phosphate (1089 cm−1 y 960 cm−1).

Figure 8. X-ray diffraction of the composites Ch/PLLA with different percentages of MWCNT at 14 days of culture. The characteristic peaks of HAp (•), MWCNT (˚), and chitosan (•) are observed.

formation. Osteoblasts cultured in the composite could migrate to the depth of pores, forming crystals of HAp on the composite surface. The fabrication and characterization of composites reinforced with MWCNT, still represented a challenge for materials engineering, since, CNT was a promising material for developing the next generation of scaffolds in tissue engineering.


The financial support of the Mexican Public Education Secretary (PROMEP) and the Mexican National Council for science and Technology and Chihuahua state Government (FOMIX) through project PROMEP 103.5/10/ 4995 and CHIH-2010-C01-148041.

Cite this paper

A.De la Paz Orozco,F. JiménezVega,S. A.Martel-Estrada,A. HernándezAguilar,M. E.Mendoza-Duarte,M. C.Chavarría-Gaytán,C. A.Rodríguez-González,I.Olivas-Armendáriz, (2016) Development of Chitosan/Poly(L-Lactide)/Multiwalled Carbon Nanotubes Scaffolds for Bone Tissue Engineering. Open Journal of Regenerative Medicine,05,14-23. doi: 10.4236/ojrm.2016.51002


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*Corresponding author.