A new strategy with bone tissue engineering by mesenchymal stem cell transplantation on titanium implant has been dawn attention. The surface scaffold properties of titanium surface play an important role in bone regenerative potential of cells. The surface topography and chemistry are postulated to be two major factors increasing the scaffold properties of titanium implants. This study aimed to evaluate the osteogenic gene expression of mesenchymal stem cells on titanium processed by wire-type electric discharge machining. Some amount of roughness and distinctive irregular features were observed on titanium processed by wire-type electric discharge machining. The thickness of suboxide layer was concomitantly grown during the processing. Since the thickness of oxide film and micro-topography allowed an improvement of mRNA expression of cells, titanium processed by wire-type electric discharge machining is a promising candidate for mesenchymal stem cell based functional restoration of implants.
The dental implant failure is frequently ascribed to large bone defect or surrounding poor bone quality. Functional restoration of bone following surgical interventions is a crucial step for the success and long term survival of orthopedic and dental implants [1,2]. Although the bone graft is widely accepted as the standard in such surgical site, inherent donor-site limitations with respect to tissue rejection and disease transfer are of particular shortcomings in autografting [2,3]. A new strategy with bone tissue engineering by mesenchymal stem cell (MSC) transplantation has been dawn attention [1,[4][5][6][7]. Titanium is a primary metallic biomaterial used in orthopedic and dental implants [8,9]. The surface scaffold properties of titanium surface, namely osteogenic gene expression of adherent cells play an important role in the bone tissue engineering of implants [4,7,10,11]. A large number of surface modification techniques have already existed, including commercial ones. Rough surfaces such as the sand-blasted, acid-etched titanium implant have generally proven superior to smooth surface in terms of promoting bone-cells and implant contact at the interface [12][13][14]. The authors have reported that the wire-type electric discharge machining (W-EDM) of titanium allowed a microstructured titanium surface with an irregular morphology. W-EDM processes electro-conductive materials by spark discharge generated between a narrow metal wire and the material through running pure distilled water. This computer associated technique enables extremely accurate complex sample shaping. It also yields an optimal micro textured surface during the processing [15]. Various thicknesses of the oxide film the type of crystallinity, and the amount of oxygen incorporated into the surfaces of differently processed titanium samples have been reported [13,[16][17][18]. The thickness of oxide film is another important determinant of osteoblast responses on titanium as the thickness of oxide film may improve the surface free energy that accumulates functional groups and osteogenic biomolecules at the surface. The surface topography and chemistry are postulated to be two major factors increasing the osteoconductivity of titanium implants. Titanium alters the thickness of the surface oxide film even in a simple heated setting. Since the titanium oxide film is sensitively altered by each processing, the authors hypothesized that W-EDM processes the thickness of oxide film and micro topography at the same time. In this study, the chemical characteristics and surface topographies of titanium processed by W-EDM and titanium-coated W-EDM epoxy resin replicas were evaluated. The scaffold property of the samples was evaluated by the mRNA expression of MSC onto the samples.
JIS grade 2 titanium (KS-50, Kobe Steel, Kobe, Japan) was used as the starting material. The smooth surfaces of titanium plates, 10 x 10 x 1.0 mm, were gradually ground with waterproof polishing papers from #500 to #1200 under running water. They were then polished with alumina particles until an average diameter of 0.3 µm. W-EDM samples (W-EDM-Ti) of arXiv:1004.4045 [q-bio.CB] the same dimensions were processed under conditions of 6.5 µsecond τ off (pulse off time) and 0.65 µsecond τ on (pulse on time) at 15 amps I P (peak current) and 90 V (non-load voltage) (LS 350X, Japan). The samples were ultrasonically cleaned in acetone, detergent solution (7X, ICN), and pure distilled water for 15 min of each cleaning process. The specimens were then dried and stored in a desiccator for 24 hrs in 50% humidity and at a temperature of 23°C.
The method for titanium coated replicas was given in the paper written by Burunett DM et al [19,20]. Impressions of polished titanium and W-EDM surfaces were made with vinyl polysiloxane impression material (PROVIL ® novo Light, Heraeus Kulzer, Dormagen, Germany). Vinyl polysiloxane negative replicas were used to cast epoxy-resin (EPO-TEK 302-3, Epoxy Technology, Bellerica, MA) positive replicas of the surfaces. The epoxy replicas of polished titanium (Ti) and W-EDM were cleaned with in a detergent (7X) (ICN Biomedicals, Inc., Costa Mesa, CA), baked at 60°C for 4 days, and sputter-coated (IB-2, Eiko Engineering, Tokyo, Japan) with 50 nm of Ti.
The micro topography of the samples was obtained using a scanning electron microscope (S-2360N, HITACHI, Hitachi, Japan). The average roughness of the samples was evaluated by a surface texture measuring instrument (SURFCOM, 480A, TOKYO SEIMITUS, Tokyo, Japan). The results were expressed as the mean ± SD of 6 specimens (n = 6), and analyzed statistically by analysis of variance (ANOVA).
The crystal phases of the samples were detected by TF-XRD (XRD-6100, SHIMADZU, Kyoto, Japan) with CuKα radiation. XRD was operated at 40 kV, 40 mA with a scanning speed of 0.02°/4 sec and a scanning range of 20-50°.
The surfaces of each specimen were characterized by X-ray photoelectron spectroscopy (XPS) (ESCA-340
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