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Int J Med Sci 2013; 10(12):1608-1614. doi:10.7150/ijms.6496 This issue Cite

Research Paper

A Comparative Study on Morphochemical Properties and Osteogenic Cell Differentiation within Bone Graft and Coral Graft Culture Systems

Subramaniam Puvaneswary, Hanumantha Rao Balaji Raghavendran, Nurul Syuhada Ibrahim, Malliga Raman Murali, Azhar Mahmood Merican, T. Kamarul

Tissue Engineering Group (TEG), Department of Orthopaedic Surgery, NOCERAL, Faculty of Medicine, University of Malaya, Kuala Lumpur-50603, Malaysia.

✉ Corresponding author: Dr. T. Kamarul, Deputy Dean (Research), Tissue Engineering Group, NOCERAL, Faculty of Medicine University of Malaya. 03-79492061 or 03-79494642 tkzreaedu.my.

Abstract

The objective of this study was to compare the morphological and chemical composition of bone graft (BG) and coral graft (CG) as well as their osteogenic differentiation potential using rabbit mesenchymal stem cells (rMSCs) in vitro. SEM analysis of BG and CG revealed that the pores in these grafts were interconnected, and their micro-CT confirmed pore sizes in the range of 107-315 µm and 103-514 µm with a total porosity of 92% and 94%, respectively. EDS analysis indicated that the level of calcium in CG was relatively higher than that in BG. FTIR of BG and CG confirmed the presence of functional groups corresponding to carbonyl, aromatic, alkyl, and alkane groups. XRD results revealed that the phase content of the inorganic layer comprised highly crystalline form of calcium carbonate and carbon. Atomic force microscopy analysis showed CG had better surface roughness compared to BG. In addition, significantly higher levels of osteogenic differentiation markers, namely, alkaline phosphatase (ALP), Osteocalcin (OC) levels, and Osteonectin and Runx2, Integrin gene expression were detected in the CG cultures, when compared with those in the BG cultures. In conclusion, our results demonstrate that the osteogenic differentiation of rMSCs is relatively superior in coral graft than in bone graft culture system.

Keywords: Osteogenic, Porous materials, Tissue engineering, Biomaterial, Coral graft, Microstructure.

Introduction

Three-dimensional (3D) scaffolds such as bone graft and coral graft have received much attention in tissue engineering field due to its promising properties. The 3D architecture of these scaffolds in which cells interact with other cells and the extracellular matrix (ECM) offers supportive roles in addition to its enhanced cellular responses [1]. In stem cell therapies and tissue engineering, various types of scaffolds are prepared using natural polymer, synthetic polymer, and bioceramic material by employing emulsion freeze-drying method, porogen leaching method, and phototyping [2].

The exoskeleton of these high-content calcium carbonate scaffolds has been shown to be biocompatible and biodegradable at variable rates depending on their porosity, implantation site, and species [3]. Coral grafts act as an adequate carrier for growth factors and allow cell attachment, cell growth, cell differentiation. Coral graft has been reported to be non-genotoxic and biologically inert. Bone grafts have been used as a gold standard for tissue engineering applications, although several studies have reported limitations such as pain at the donor site and limited donors [4]. A previous study has reported the upregulation of gene expression in CG seeded with human osteoblast cell line CRL 1543 in vitro [5]. However, to our knowledge, a comparative study on morphochemical properties and osteogenic cell differentiation potential of BG and CG using rMSCs has not yet been carried out.

Materials and Methods

Scaffold preparation

Briefly, Dead Sea coral of Porites species processed using lab standardized protocol. Coral skeleton material were cleaned from debris and washed with distilled water several times. Coral was cut and processed into granules and blocks with different dimension according to the requirements of the study, which had a mean cubic diameter 4.0-5.0 mm X 4.0- 5.0 mm X 4.0-5.0 mm. For bone graft, fat and tissue free bone were cut into desired size and shape. After several washing using sterile water samples were centrifuged several times with vigorous shaking. These cubical were treated chemically followed by freeze drying. The samples were triple packed and radiosterilized at Malaysian Nuclear Agency using gamma irradiation under permissible limits. The integrity of the scaffold before and after was also confirmed using analytical techniques. Quality control test was performed to ensure the consistency of the scaffold.

Rabbit bone marrow isolation and seeding

Bone marrow derived mesenchymal stem cells (rMSCs) were harvested from 3-month-old New Zealand White rabbits using lab standardized protocol. Aliquots of 40-60 µl of cell suspension were seeded (2×10⁴ cells/cm²) onto the top of each scaffold (n=5) placed in 48 multi-well plates. A volume of 100 µl of the medium was added to each well. The scaffolds were incubated for 12 h to allow the cells to attach to its surface, and were cultured using commercial Stempro Osteogenesis Differentiation Kit (Invitrogen Cell Culture, USA).

Scanning electron microscopy (SEM) & Energy dispersive spectroscopy (EDS)

The specimens were fixed overnight in 4% glutaraldehyde in 0.1M calcodylate buffer and post-fixed for 1 h in 1% aqueous osmium tetraoxide. The processed specimens were examined using a digital SEM (JSM 6400; JEOL, Tokyo, Japan). EDS (10-30-kV INCA Energy 200, Oxford Inst.) spectrum was plotted using X-rays emitted from the specimens using Microanalysis Suite software version 4.05 (Oxford Inst.).

X-Ray diffraction (XRD) & Atomic force microscopy (AFM)

XRD patterns were recorded on a D8 Advance X-Ray diffractometer (D8 Bruker-AXS, USA) using Ni-filtered CuK_α monochromatized radiation at 40kV, 40mA, and 25°C. The 2θ range from 20 to 40° was covered at a scan speed of 0.1/min. The mass fractions were calculated and diffractograms were generated using DIFFRACplus-EVA software. Following critical point drying of samples, atomic force microscopy (NT-MDT Slover Next, Russia) with a feedback gain below 1 with 1.00Hz probe frequency was used. The surface topography, 3D image were read using Nova Px 3.2.5 software.

Fourier Transform Infrared Spectroscopy (FTIR)

The scaffolds were crushed and pressed to obtain thin circular wafer using KBr. FTIR (IFS 66v/s Bruker, USA) spectra were recorded at a range of 4000-400 cm^-1.

Microtomography

The samples were scanned at 20 µm voxel resolution with an integration time of 120 microseconds using micro-CT system (SkyScan 1076, Belgium). Porosity and pore sizes were measured from the constructed 3D model of the coral and bone grafts.

Confocal Microscopy

Scaffold seeded with mesenchymal stromal cells were stained with Hoechst dye and analysed using confocal microscopy (Leica TCS-SP5 II, Leica Microsystem, Mannheim, Germany) after 20 min incubation at room temperature. The 3D image obtained from incorporation of multiple series of images collected by confocal laser further assisted the investigation of cell infiltration up to 300 µm into scaffolds.

Alkaline Phosphatase Assay (ALP) and Osteocalcin Assay (OC)

ALP activity was assessed based on the hydrolysis process of p-nitrophenyl phosphate to p-nitrophenol using an assay kit (Abcam, USA) and OC using a commercial ELISA kit (IBL International, Germany).

Gene expression

The total RNA was isolated from BG and CG for one week after culturing in osteogenic medium to monitor early trends of gene expression. The samples were washed with 1X PBS and incubated for 4 min in Versene solution (Invitrogen), and then vortexed gently. The supernatants of all the sample groups were collected and the RNA from the collected supernatants was isolated using an RNeasy Mini Kit, according to the manufacturer's instructions. Subsequently, 1 μg of RNA was used to generate cDNA using the Superscript III First Strand Synthesis Kit, according to the manufacturer's instructions. Primers for beta catenin, bone morphogenic protein 2 (BMP-2), integrin, osteonectin (OC), Runx2 were designed using NCBI database (USA) prior to q-PCR (Table 2). After an initial denaturation step at 95ºC for 3 min, the cDNA products were amplified with 40 PCR cycles, consisting of a denaturation step at 95ºC for 30 s, annealing temperature ranging from 50 to 60ºC, and an extension step at 72ºC for 5 min. The relative quantification values were analyzed using the Bio-Rad CFX manager 2.0. The level of expression of each target gene, normalized to housekeeping gene where E_t is the amplification efficiency of the target sequence.

Statistical analysis

The results were expressed as mean ± SDs and concentrations were analysed by SPSS v.16.0 (SPSS Inc., Chicago, IL) using one-way ANOVA followed by post-hoc LSD, with a significant level set at p < 0.01.

Results and Discussion

The use of BG and CG scaffold in tissue engineering applications has gained considerable interest due to its biocompatibility and absorbability properties [6]. In this study, we tested coral graft to determine its potential in enhancing osteogenic differentiation of rMSCs under in vitro conditions. To prove the properties of 3D scaffolds, first, the characterization criteria such as morphology (e.g. porosity, pore size, and surface area) as well as mechanical and surface properties were examined. SEM analysis revealed that the pores in the CG were interconnected and their size ranged from 107 to 315 µm (Fig. 1A & Fig. 1C). On the other hand, the pore diameters for the bone graft were found to be 103-514 µm, indicating that the scaffold environment was sufficiently large to accommodate stromal cells. Cell attachment on the scaffold was observed to be randomly distributed within the pore, which had roughened blebs and protrusions on the scaffold surface (Fig. 1E & Fig. 1G).This observation is in agreement with the findings reported in previous studies, demonstrating that osteoid cells can colonize in pores of 40-100 μm diameter. It has been previously reported that osteoblast-like behavior such as cell attachment efficiency, spreading, fiber formation, and cell migration is dependent on the surface chemistry of any material, which, in the present study, appears to be positive [7].

Micro-CT results confirmed large interconnecting paths in CG, especially, the nature of pore arrangement that appears to be similar to that of cancellous bone (Table 1). EDS analysis indicated the presence peaks for calcium in both CG and BG scaffolds. The level of calcium in CG was relatively higher than that in bone graft, which appears to be correlated with the enhanced osteogenic differentiation observed in the coral graft (Fig. 1B, Fig. 1D, Fig. 1F & Fig. 1H). FTIR bands demonstrated a range of 1476 cmˉ¹, corresponding to the carbonyl group which contributes to surface polarity, while the spectra of BG showed peaks corresponding to respective functional groups, as shown in Fig. 2A & Fig. 2B. The XRD results confirmed that the phase content of the inorganic layer of BG and CG comprised highly crystalline form of aragonite (calcium carbonate) and carbon (Fig. 3A & Fig. 3B). It must be noted that the mineral composition of bone is mainly HA and amorphous calcium phosphate associated with calcium carbonate, while that of coral is essentially calcium carbonate [8]. AFM confirmed that the average roughness of CG was higher than that of BG (Fig. 4A & Fig. 4B). The average roughness of the surface of BG was 10.228 nm, whereas that of CG was 19.541 nm. In addition to SEM analysis, the infiltration of cells into the scaffold material was confirmed using confocal microscopy. Confocal microscopy results demonstrated cell attachment and its random distribution on the surface of the scaffolds (blue spots). The 3D image obtained from the incorporation of multiple series of images collected by confocal laser further assisted the investigation of cell infiltration up to 300 µm into the scaffolds (Fig. 4C & Fig. 4D).

 Fig 1 

SEM and EDX analysis of BG (A & C) and CG (B & D) without cells respectively. Cell attachment representative photographs of BG (E & G) and CG (F & H) respectively, arrows indicate osteogenic like cells, (60x and 2000x).

 Fig 2 

The functional groups of BG and CG using FTIR (A & B). Scaffolds crushed and pressed with Kbr were analysed using FTIR.

 Fig 3 

XRD pattern of BG and CG (A & B). XRD patterns were recorded on a D8 Advance X-Ray diffractometer (D8 Bruker-AXS, USA) using Ni-filtered CuK_α monochromatized radiation at 40 kV, 40 mA,and 25° C. The 2θ range from 20 to 40° was covered at a scan speed of 0.1/min.

 Fig 4 

Atomic force microscopy of BG (A) and CG (B) without cells. The materials were subjected to critical point drying (CPD) and viewed using atomic force microscopy. The average surface roughness of the BG and CG were 10.10 nm and 19.54 nm respectively. (C & D) Confocal miscroscopy examination of BG and CG at early time point. Positive staining (Blue spots) of indicates the penetration of cells inside the bone and coral graft.

Previous reports have shown that osteoblasts migrate faster into the larger pore of microcellular scaffolds, which provide the extra cellular matrix environment. However, pore size has not been observed to affect the depth of cell penetration or extent of mineralization. It has been reported that cell-scaffold binding can block pores of inadequate size and geometry. In addition, high interconnectivity of pores has also been found to be essential for the supply of nutrients and oxygen exchange in the inner regions of a scaffold to maintain cell viability, especially for complex tissue engineering of organs. In the present study, with regard to reproducibility, the number of samples used was six for in vitro culture assay, and four samples of each scaffold were used for the characterization study using FTIR, XRD, SEM, and Micro-CT. Overall, the results appeared to be statistically more or less similar for all samples examined. The statistical mean comparative analyses demonstrated no significant differences. Previous studies have reported that osteoblasts exhibited higher proliferation and elevated marker activity as well as OC expression on the rough surface than on the smooth one, which is correlated with the findings of the present study in which CG presented better expression of osteogenic marker and gene expression [9]. Depending on the scale of irregularities of the material surface, surface roughness can be divided into macro, micro, and nano roughness, each with its unique influence. The response of cells to roughness is different depending on the cell type. For larger cells, such as osteoblasts and neurons, macroscopic descriptions of the surface roughness could be reasonable [10, 11]. Nevertheless, the underlying mechanism, i.e., the role of pore size or surface of the scaffold structure and cell behavior, needs to be examined in detail in future studies.

ALP, an early-stage marker of osteogenic differentiation, was found to gradually increase and become two fold in cells cultured in the CG scaffold by day 18 (P<0.01). Though a gradual increase in ALP was noted in cells cultured in BG, the increase was not as high. In CG culture, ALP production was significantly higher (P<0.01) on day 27 (Fig. 5A). Studies have shown that SaOS-2cells grown for 25 days usually get detached from the culture, thereby limiting the assessment of ALP activity beyond 25-day time point [6]. In the present study, the production of OC, a late-stage marker of osteogenesis, was significantly enhanced (P<0.01) in the CG culture approximately two fold increase in OC was observed in the supernatant of cells grown on CG on day 9,when compared with that noted in earlier time points. In contrast, it took 18 days for OC to reach high levels in the BG (Fig. 5B). A quantitative RT-PCR method was used to assess the gene expression (Fig. 5C) of osteoblasts at early time point (day 7). To determine whether early osteoblast differentiation was affected by BG or CG, we selected beta-catenin, BMP-2, integrin, osteonectin, and Runx-2 as markers for osteoblastic differentiation. Osteonectin is exclusively secreted by osteoblasts, is believed to play a role in metabolic regulation, and is pro-osteoblastic. It is also known as SPARC, a glycoprotein abundantly found in bone undergoing active remodeling process. In the present study, osteogenic differentiation was evidenced by the expression of osteonectin in CG induced with osteogenic differentiation medium. The genes encoding osteonectin are related to bone ECM formation. Osteonectin is synthesized by cells of the osteoblastic lineage, which binds to hydroxyapatite, calcium, and BG, and has been observed to assist inactive osteogenic differentiation of rabbit mesenchymal cells. Runx-2 gene is a member of the Runx-2 family of transcription factors and encodes a nuclear protein with a Runt DNA-binding domain. The protein can bind to DNA both as a monomer and, with more affinity, as a subunit of a heterodimeric complex. This protein has been implicated as a key transcription factor associated with osteoblast differentiation. As shown in Figure 5C, significant differences could be observed in the gene expression between BG and CG on day 7. The osteonectin expression was 5.5-fold higher on day 7.

 Fig 5 

(A) ALP production in BG and CG and (B) osteocalcin production in BG and CG. Condition media collected at different time were subjected to ALP and OC assay using commercial kit p<0.01, a* CG Vs BG. Gene expression on early time point (Day 7) in bone graft and coral graft (C). cDNA products were amplified with 40 PCR cycles, consisting of a denaturation step at 95ºC for 30s, annealing temperature ranging from 50 to 60ºC, and an extension step at 72ºC for 5 min. The relative quantification values were analyzed using the Bio-Rad CFX manager 2.0

Furthermore, the Runx-2 expression was significantly higher day 7 in CG when compared to BG where as the expressions of other genes were relatively the same between BG and CG [12-14].In addition, the results obtained in the present study confirmed upregulation of integrin in early time point. It has been reported that integrin-mediated cell adhesion is involved in different cellular responses to the same environmental stimuli. Moreover, integrins also modulate cellular physiology by transmitting external mechanical stimuli into the cells. It has been observed that integrin could bind to its cognate ligand in the ECM molecules only after being activated by the G-protein-coupled receptors on the cell membrane. As integrins are considered to have diverse activities and densities in 300 different types of cells, various time periods have been noted for the cells to get attached and spread in the same micro environment [15].

In conclusion, the osteogenic differentiation potential of CG was found to be superior to that of BG. This suggests that coral graft may be a suitable material for future tissue engineering application when used with MSCs.

Acknowledgements

The authors are grateful to the Fundamental Research Grant Scheme FRGS (FP016) and HIRG-MOHE, University Malaya for supporting this study.

Competing Interests

The authors have declared that no competing interest exists.

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Author contact

Corresponding author: Dr. T. Kamarul, Deputy Dean (Research), Tissue Engineering Group, NOCERAL, Faculty of Medicine University of Malaya. 03-79492061 or 03-79494642 tkzreaedu.my.

Received 2013-4-17
Accepted 2013-8-30
Published 2013-9-14

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