Nanohybrid structure analysis and biomolecule release behavior of polysaccharide-CDHA drug carriers
© Huang et al.; licensee Springer. 2013
Received: 19 July 2013
Accepted: 13 September 2013
Published: 8 October 2013
Nanoscaled polymer composites were prepared from polysaccharide chitosan (CS) and Ca-deficient hydroxyapatite (CDHA). CS-CDHA nanocomposites were synthesized by in situ precipitation at pH 9, and the CS-CDHA carriers were then fabricated by ionic cross-linking methods using tripolyphosphate and chemical cross-linking methods by glutaraldehyde and genipin. Certain biomolecules such as vitamin B12, cytochrome c, and bovine serum albumin were loaded into the CS-CDHA carriers, and their release behaviors were investigated. Furthermore, these CS-CDHA carriers were examined by transmission electron microscopy, electron spectroscopy for chemical analysis, and X-ray diffraction. The release behavior of the biomolecules was controlled by the CS/CDHA ratios and cross-linked agents. By increasing the concentration of CS and the concentration of the cross-linking agents, cross-linking within carriers increases, and the release rate of the biomolecules is decreased. Moreover, the release rate of the biomolecules from the CS-CDHA carriers at pH 4 was higher than that at pH 10, displaying a pH-sensitive behavior. Therefore, these CS-CDHA hydrogel beads may be useful for intelligent drug release and accelerate bone reconstruction.
KeywordsChitosan Ca-deficient hydroxyapatite (CDHA) Drug release Nanohybrids
Recently, much attention has been focused on chitosan (CS)-based hydrogel for cartilage tissue engineering and bone substitute with controlled release function due to its structure similar to that of natural glycosaminoglycan [1–3]. CS is a cationic polysaccharide with an isoelectric point of 6.2 , thus is pH sensitive and has been proposed for electrically modulated drug delivery . Furthermore, CS has been identified as hydrophilic, non-toxic, biodegradable, antibacterial, and biocompatible. In our previous study , we demonstrated that the addition of clay to the CS matrix could strongly affect the cross-linking density as well as the mechanical properties, swelling-deswelling behavior, and fatigue property of the nanohybrids. Hence, the incorporation of negatively charged delaminated (exfoliated) montmorillonite is expected to electrostatically interact with the positively charged -NH3+ group of CS to generate a strong cross-linking structure in the nanohydrogel , thus strongly affect the macroscopic property of the nanohydrogel and the drug diffusion through the bulk entity.
There have been some reports in the preparation of CS nanoparticles by ionic and chemical cross-linking methods, for example, the use of an ionic gelation method to prepare CS NPs as reported by Calvo et al. . Cationic CS nanoparticles were formed through the inter- and intra-cross-linking of the amino groups of CS with the negatively charged phosphate groups of tripolyposphate (TPP). TPP is a non-toxic polyanion which can interact with CS via electrostatic forces to induce ionic cross-linked networks , which could be used for the preparation of CS hydrogel beads owing to its immediate gelling ability. Furthermore, Mi et al.  reported the preparation of chitosan gel using a natural chemical cross-linker, i.e., genipin (GP), which is obtained from its parent compound traditionally used as a component of Chinese medicine, geniposide, which was separated from Gardenia jasminoides Ellis. GP cross-linked networks in the biopolymers display significantly less cytotoxicity than those chemical cross-linked by glutaraldehyde (GA) and thus recently was widely used for various biomedical applications [11–14].
The purpose in this study is to modulate the release rate of biomolecules from highly swollen hydrogel beads and its loose structure  in order to extend the drug release period of the CS hydrogel. The drug release permeability of CS can be further regulated by the incorporation of Ca-deficient hydroxyapatite (Ca10-x(PO4)6-x (HPO4) x (OH)2-x, 0 ≤ x ≤ 1, CDHA, Ca/P = 1.5) nanorods, because it has long been employed to improve the mechanical strength and osteoconductivity of chitosan [16–18]. The influence of the nanofiller (CDHA nanorods) in the CS hydrogel for the drug release behavior might be critical and can be explored further.
Therefore, the major research objective of this study is to explore the role of CDHA nanorods in the release behavior of biomolecules (vitamin B12, cytochrome c, and bovine serum albumin (BSA)) from CS hydrogel beads. In addition, the degree and methods (ionic or chemical) of cross-linking in the CS hydrogel beads were also investigated. This study is expected to provide a fundamental understanding of the CS-CDHA nanocomposite drug carrier used for medical applications and also of the drug (growth factor) delivery to enhance bone repair.
Synthesis of CS-CDHA nanocomposites
CS-CDHA nanocomposites with various CDHA contents were prepared via in situ processes to characterize the influence of nanofiller and polymer-filler interaction on the behavior of this drug delivery system. Chitosan (molecular weight 215 kDa, 80% degree of deacetylation) was purchased from Sigma-Aldrich (St. Louis, MI, USA). CS solution (1% (w/v)) was first prepared by dissolving the CS powder in 10% (v/v) acetic acid solution. For the in situ process (PO43-→CS→Ca2+), H3PO4 aqueous solution (0.167 M) was first added into the CS solution, and Ca(CH3COO)2 aqueous solution (0.25 M) was then added into this mixture solution under stirring for 12 h. The pH value was kept at 9 by adding NaOH solution (1 M). The nanocomposites with different volume ratios of CS/CDHA were modulated at 0/100, 10/90, 30/70, 50/50, 70/30, and 100/0, abbreviated as CDHA, CS19, CS37, CS55, CS73, and CS, respectively. Subsequently, these CS-CDHA nanocomposites were dried at 65°C for 24 h.
Preparation of CS-CDHA hydrogel beads
Various ratios of CS/CDHA nanocomposites and biomolecules (vitamin B12, 1,355 Da; cytochrome c, 12,327 Da; or BSA, 65,000 Da) were dissolved in the 10% (v/v) acetic acid solution and then the mixing solution was dropped into the different concentrations of TPP (1, 5, 10 wt.%) for ionic cross-linking or further chemical cross-linking by GA or GP under stirring. The morphology of the CS-CDHA carriers (diameter 500 to 1,000 μm) was evaluated using an optical microscope (OM).
The crystallographic phase of the CDHA/CS nanocomposites was identified by X-ray diffraction (XRD, M18XHF, Mac Science, Tokyo, Japan). The morphology of the CDHA nanocrystals and various CS-CDHA nanocomposites were observed by transmission electron microscopy (TEM, JEOL-2000FX, Tokyo, Japan). The chemical structure change was evaluated by electron spectroscopy for chemical analysis (ESCA), equipped with MgKα at 1,253.6 eV and 150 W power at the anode. A survey scan of the varying electron volts for N1s, Ca2p, and P2p was taken.
Drug release test
These nanocomposite hydrogel beads were put into phosphate-buffered solution (pH 7.4) to test for drug release. The release medium was withdrawn for each juncture and replaced with equivalent volume of fresh buffer. UV-visible spectroscopy (Agilent 8453, Agilent Technologies Inc., Santa Clara, CA, USA) was used for the characterization of absorption peak to determine the amount of vitamin B12 (361 nm), cytochrome c (410 nm), or BSA (562 nm, using BCA kits) released via the use of predetermined standard concentration-intensity calibration curve.
where L and Rt represent the initial amount of drug loaded and the cumulative amount of drug released at time t, respectively.
Results and discussion
Figure 1 shows the XRD patterns of the CDHA, CS, and CS-CDHA nanocomposites. One major peak at 26° and 32°, and four minor peaks at 40°, 46°, 50°, and 53° were observed (peak of pure CS appeared at 21°). According to the ICDD No. 39–1894 and No. 46–0905, these peaks could be identified as semi-crystalline of CS (2θ approximately 21°) and crystalline of CDHA, respectively. Using CS73 nanocomposite as an example, both CS and CDHA characteristic peaks (seven peaks) were observed. This indicated that the CDHA/CS nanocomposites could be synthesized via in situ precipitated processes. Furthermore, it was observed that the crystallinity of CS decreased with increasing CDHA content, because the homogenously dispersive CDHA nanorods would induce defects in the CS network. Moreover, it is also demonstrated that strong polymer-filler interaction could modify the molecular configuration of the polymer chains in the vicinity of the filler to the formation of localized amorphous regions. This would inhibit and retard the crystalline development of the CS chains. It became more pronounced when the CDHA content exceeds 30 wt.%. However, the crystallinity of CDHA seems to be enhanced by the addition of CS. The full-width at half maximum of the XRD peak of the CS-CDHA nanocomposites was observed to be lower than that of the pristine CDHA, thereby displaying sharper peak (better crystallinity). Thus, we suggest that the CS chains might induce the crystallinity of CDHA.
Figure 2 shows the TEM images of the pristine CDHA (a), CS37 (b), CS55 (c), and CS73 (d) nanocomposites. The pristine CDHA exhibited needle-like structure of nanorods (5 to 20 nm in diameter and 50 to 100 nm in length). The CS-CDHA nanocomposites exhibited homogenously dispersed nanorods in the CS networks, especially in the CS73, as illustrated in Figure 2b,c,d. The reason is that the electrostatic attraction between the NH3+ group (positive charge of the CS chains) and the PO43- group (negative charge of the CDHA nanorods) served as the stable force for the colloid suspension, favoring the dispersion of CDHA. Moreover, the structure of the CS-CDHA nanocomposites (CS73) became denser with the increase of the CS content due to the better compatibility and stable network of high molecular weight of CS. In contrast, CS55 and CS37 exhibited less dense morphologies.
A comparison of the chemical binding energy change of the pristine CDHA, pristine CS, and CS37 nanocomposites was shown in the ESCA spectra. The ESCA analysis shows that the surface was mainly composed of N, Ca, and P atoms, which could represent the chemical structure and interaction of CS (N atom) and CDHA (Ca and P atoms). Figure 3a shows the ESCA data of N1s scan spectra in CS, CDHA, and CS37. The N1s peak in the pristine CS was found at 402.3 eV, implying the amino group of CS (no peak existing in the pristine CDHA). However, the NH2 peak was shifted from 402.3 to 400.0 eV in the CS37, implying the complex formation of CS and CDHA. Two Ca2p peaks of the pristine CDHA were observed with the binding energy of 347.8 eV (2p3/2) and 351.4 (2p1/2), as indicated in Figure 3b. Two peaks (2p3/2 348.0 eV and 2 p3/2 351.6 eV) were exhibited in CS37 and displayed 0.2 eV chemical shift compared to the pristine CDHA, suggesting the formation of CDHA in the CS37 and some chemical interaction between CS and CDHA (no additional peak in the pristine CS). Similar with the ESCA spectrum of Ca2p, 0.8 eV (133.1-eV shift to 133.9 eV) chemical shifts were found between the pristine CDHA and CS37 in the P2p spectrum. These results indicate that the CDHA nanorods were grown in the CS matrix through in situ precipitated process.
LYH is a postdoctoral fellow at the National Taiwan University of Science and Technology. TYuL holds an assistant professor position at Ming Chi University of Technology. AH and AM are PhD students at the National Taiwan University of Science and Technology. TYiL holds an assistant professor position at the National Yang-Ming University. HCL and CCL are researcher and manager at Industrial Technology Research Institute (ITRI) of Taiwan, respectively. MCY holds a professor position at the National Taiwan University of Science and Technology.
This work was financially supported by the National Science Council of Taiwan (NSC 101-2221-E-011-058 and NSC 101-2321-B-002-026). Technical supports from the Industrial Technology Research Institute (ITRI) of Taiwan are acknowledged.
- Suh JK, Matthew HW: Application of chitosan-based polysaccharide biomaterials in cartilage tissue engineering: a review. Biomaterials 2000, 21: 2589–2598.View ArticleGoogle Scholar
- Lee JY, Nam SH, Im SY, Park YJ, Lee YM, Seol YJ, Chung CP, Lee SJ: Enhanced bone formation by controlled growth factor delivery from chitosan-based biomaterials. J Control Release 2002, 78: 187–197.View ArticleGoogle Scholar
- Kim S, Park JH, Cho YW, Chung H, Jeong SY, Lee EB, Kwon IC: Porous chitosan scaffold containing microspheres loaded with transforming growth factor-β1: implications for cartilage tissue engineering. J Control Release 2003, 91: 365–374.View ArticleGoogle Scholar
- Liu TY, Liu TY, Chen SY, Chen SC, Liu DM: Effect of hydroxyapatite nanoparticles on ibuprofen release from carboxymethyl-hexanoyl chitosan/O-hexanoyl chitosan hydrogel. J Nanosci Nanotechno 2006, 6: 2929–2935.View ArticleGoogle Scholar
- Ramanathan S, Block H: The use of chitosan gels as matrices for electrically-modulated drug delivery. J Control Release 2001, 70: 109–123.View ArticleGoogle Scholar
- Liu KH, Liu TY, Chen SY, Liu DM: Effect of clay content on electrostimulus deformation and volume recovery behavior of a clay–chitosan hybrid composite. Acta Biomater 2007, 3: 919–926.View ArticleGoogle Scholar
- Haraguchi K, Farnworth R, Ohbayashi A, Takehisa T: Compositional effects on mechanical properties of nanocomposite hydrogels composed of poly(N, N-dimethylacrylamide) and clay. Macromolecules 2003, 36: 5732–5741.View ArticleGoogle Scholar
- Calvo P, Remuñán-López C, Vila-Jato JL, Alonso MJ: Novel hydrophilic chitosan-polyethylene oxide nanoparticles as protein carriers. J Appl Polym Sci 1997, 63: 125–132.View ArticleGoogle Scholar
- Mi FL, Shyu SS, Lee ST, Wong TB: Kinetic study of chitosan-tripolyphosphate complex reaction and acid-resistive properties of the chitosan-tripolyphosphate gel beads prepared by in-liquid curing method. J Polym Sci Pol Phys 1999, 37: 1551–1564.View ArticleGoogle Scholar
- Mi FL, Sung HW, Shyu SS, Su CC, Peng CK: Synthesis and characterization of biodegradable TPP/genipin co-crosslinked chitosan gel beads. Polymer 2003, 44: 6521–6530.View ArticleGoogle Scholar
- Tsai CC, Huang RN, Sung HW, Liang HC: In vitro evaluation of the genotoxicity of a naturally occurring crosslinking agent (genipin) for biologic tissue fixation. J Biomed Mater Res 2000, 52: 58–65.View ArticleGoogle Scholar
- Sung HW, Chang Y, Chiu CT, Chen CN, Liang HC: Crosslinking characteristics and mechanical properties of a bovine pericardium fixed with a naturally occurring crosslinking agent. J Biomed Mater Res 1999, 47: 116–126.View ArticleGoogle Scholar
- Sung HW, Liang IL, Chen CN, Huang RN, Liang HF: Stability of a biological tissue fixed with a naturally occurring crosslinking agent (genipin). J Biomed Mater Res 2001, 55: 538–546.View ArticleGoogle Scholar
- Sung HW, Chang Y, Liang IL, Chang WH, Chen YC: Fixation of biological tissues with a naturally occurring crosslinking agent: fixation rate and effects of pH, temperature, and initial fixative concentration. J Biomed Mater Res 2000, 52: 77–87.View ArticleGoogle Scholar
- Royce SM, Askari M, Marra KG: Incorporation of polymer microspheres within fibrin scaffolds for the controlled delivery of FGF-1. J Biomater Sci-Polym Ed 2004, 15: 1327–1336.View ArticleGoogle Scholar
- Ito M, Hidaka Y, Nakajima M, Yagasaki H, Kafrawy AH: Effect of hydroxyapatite content on physical properties and connective tissue reactions to a chitosan–hydroxyapatite composite membrane. J Biomed Mater Res 1999, 45: 204–208.View ArticleGoogle Scholar
- Zhao F, Yin Y, Lu WW, Leong JC, Zhang W, Zhang J, Zhang M, Yao K: Preparation and histological evaluation of biomimetic three-dimensional hydroxyapatite/chitosan-gelatin network composite scaffolds. Biomaterials 2002, 23: 3227–3234.View ArticleGoogle Scholar
- Sivakumar M, Rao KP: Preparation, characterization, and in vitro release of gentamicin from coralline hydroxyapatite-alginate composite microspheres. J Biomed Mater Res Part A 2003, 65: 222–228.View ArticleGoogle Scholar
- Khare AR, Peppas NA: Swelling/deswelling of anionic copolymer gels. Biomaterials 1995, 16: 559–567.View ArticleGoogle Scholar
This article is published under license to BioMed Central Ltd. This is an open access article distributed under the terms of the Creative Commons Attribution License (http://creativecommons.org/licenses/by/2.0), which permits unrestricted use, distribution, and reproduction in any medium, provided the original work is properly cited.