Synthesis and In vitro Evaluation of Electrodeposited Barium Titanate Coating on Ti6Al4V.

Osseointegration has been the concern of implantology for many years. Researchers have used various ceramic coatings for this purpose; however, piezoelectric ceramics (e.g., barium titanate [BTO]) are a novel field of interest. In this regard, BTO (BaTiO3) coating was fabricated by electrophoretic deposition on Ti6Al4V medical alloy, using sol-gel-synthesized nanometer BTO powder. Structure and morphologies were studied using X-ray diffraction and scanning electron microscopy (SEM), respectively. Bioactivity response of coated samples was evaluated by SEM and inductively coupled plasma (ICP) analysis after immersion in simulated body fluid (SBF). Cell compatibility was also studied via MTT assay and SEM imaging. Results showed homogenous coating with cubic structure and crystallite size of about 41 nm. SEM images indicated apatite formation on the coating after 7 days of SBF immersion, and ICP analysis approved ions concentration decrement in SBF. Cells showed flattened morphology in intimate contact with coating after 7 days of culture. Altogether, coated samples demonstrated appropriate bioactivity and biocompatibility.

INTRODUCTION

Healing process in the implants is based on osseointegration that was defined as direct contact between bone and implant without microscopic defection by Berglundh et al.[1] Minimum trauma in surgery, initial stability, and prevention of infection and micromotion are fundamental requirements for osseointegration.[1] Osseointegration and bone response in the case of formation rate, quantity, and quality of the new bone depend on implant properties.[2] Studies have shown that faster bone modeling can fix implant tightly and prevent fibrous layer formation on the surface of implant.[3] Various techniques have been used to improve bone and implant surface connection with the goal of faster integration, bone remodeling, and more implant stability during healing time so that earlier loading could be applied.[2]

Implant properties such as surface chemistry, electrical charge, surface topography, and porosity could affect bone response at in vivo conditions.[4] Titanium and its alloys are the most commercial alloys used for implants due to their mechanical properties, corrosion resistance, and biocompatibility.[56] Different methods have been used to improve implant properties and its integration, such as different coatings like titania, calcium phosphate, or hydroxyapatite, as well as surface roughening or chemical modifications on the implant surface.[6789] However, another concept in this case are piezoelectric materials. They could be useful because of bone intrinsic piezoelectricity.[1011]

Barium titanate (BTO), due to its well-known piezoelectric properties, is one of the electroactive ceramics that has the capability of being used as a bioceramic.[1213] Among various coating methods, electrophoretic deposition (EPD) is a simple and inexpensive method that has interested many researchers in recent years for coating of diverse bioceramics such as hydroxyapatite,[14] bioglass,[15] and forsterite.[16] EPD is an easy, fast, and inexpensive method that provides homogeneous high purity coatings. Furthermore, this method allows coating thickness modification via its various processing parameters.[17] Many researchers have studied EPD process for BTO[181920] but no biomedical evaluation has been reported.

In this study, BTO was introduced as a novel bioceramic coating. BTO electrophoretically was coated on Ti6Al4V medical alloy and its bioactivity and cell compatibility were studied.

MATERIALS AND METHODS

Barium Titanate Powder Synthesis

BTO was synthesized via sol-gel method based on Kuwabara and Miki experiences.[21] Equimolar amounts of barium diethoxide (Ba(OC2H5) 2, Alfa Aesar, USA), and titanium tetraisopropoxide (Ti(OC3H7) 4, Alfa Aesar, USA) were dissolved in ethylene glycol monomethyl ether (EGMME: CH3OC2H4OH, Merck, Germany) to prepare precursor solution with the concentration of 0.25 M under dry argon atmosphere. The solution was hydrolyzed by adding water and EGMME (with a volume ratio of 1:1) at −17°C for 20 min. After aging for 24 h, the obtained gel was dried at 90°C and heat-treated at 800°C for 1 h.

Electrophoretic Deposition

A mixture of EGMME and acetylacetone (Acac: CH3COCH2COCH3, Merck, Germany), with a volume ratio of 9:1, was used as electrophoretic medium. BTO particles were added to the solution with a concentration of 0.2 M and agitated ultrasonically to achieve a stable suspension. Two Ti6Al4V (ASTM grade 5, Galimplant S.L., Spain) plates of 1 cm × 1 cm were used as electrodes with a distance of 2 cm. The specimens were prepared by grinding with silicon carbide abrasive paper up to 600 grits. A DC voltage of 60 V was applied for 3 min. Coatings were dried in the air at 90°C and sintered at 800°C for 1 h.

Structural Characterization

X-ray diffraction (XRD, Philips X’Pert-MPD System, The Netherlands) with CuKα beam (λ = 0.1543 nm) was used for structure analysis in according to Joint Committee on Powder Diffraction Standards (JCPDS) standard cards. The crystallite size of synthesized powder and coating was determined using the Scherrer equation (Eq. 1):

Where β is the width of peak in the middle of its height, λ is the wavelength (0.154 nm), θ is the Bragg angle, k is a constant (0.9), and t is the apparent crystallite size.

Size and Morphologies

The powder particle size distribution was evaluated by dynamic light scattering (DLS, Malvern ZEN3600, UK). The morphology of coatings was investigated by scanning electron microscopy (SEM, Philips XL30, The Netherlands) after gold coating (about several nanometers thick) using a sputter coater (Bal-Tec, SCD 005, USA) to create surface conductivity.

Bioactivity Evaluation

Bioactivity of BTO coatings was evaluated by immersing in simulated body fluid (SBF) prepared using Kokubo method.[22] After immersion for 28 days, specimens’ surface morphology and element analysis was studied using an SEM equipped with energy dispersive X-ray spectroscopy (EDS, SeronAIS-2100, Korea) system. Ions concentration changes also evaluated by means of inductively coupled plasma (ICP, Optima 7300DV, USA) analysis for days of 3, 7, 14, and 28.

Cell Culture

MG-63 cell line cells were cultured in a Dulbecco's modified Eagle's medium (DMEM, Bio-Idea, Iran) containing 10% fetal bovine serum (FBS, Bio-Idea, Iran) and 1% Penicillin/streptomycin (Pen/strep, Bio-Idea, Iran) for several passages to reach a stable phenotype. About 10,000 cells were seeded on each sample and were incubated in 37°C and 5% CO2 atmosphere. After 1 and 7 days, samples were washed with phosphate-buffered saline (PBS, Bio-Idea, Iran) to eliminate unattached cells and fixed in 2% glutaraldehyde for 30 min at room temperature. After several dehydrations in ethanol (30 min in 50%, 70%, 80%, 90%, and 100% ethanol, subsequently), SEM (Philips XL30, The Netherlands) was used to study cells morphology on the surface.

MTT Assay

For 3-(4,5-dimethylthiazol-2-yl)-2,5-diphenyltetrazolium (MTT) assay about 1 × 104 cells were seeded on 1 cm × 1 cm coated samples and were incubated for 1, 4, and 7 days in a 24 well plate (three samples for each day). Polystyrene plate (Biofil, China) was also used as control. At specific intervals after the removal of culture medium, 700 μl DMEM and 70 μl (MTT, 5 mg/ml in PBS) were added to each well, and they were incubated for 3 h. Afterward, the medium was removed, and 700 μl dimethyl sulfoxide (DMSO, Sigma, UK) was added to each well. The samples were incubated for 1 h. DMSO was removed and added to three wells of a 96 well-plate, and the absorbance was read using an automated plate reader (Microplate Reader Model 1680, Bio-Rad, USA) at 540 nm, subsequently. The average value and standard deviation of optical density were calculated and reported. P < 0.05 was considered statistically significant in statistical analyses using ANOVA.

RESULTS AND DISCUSSIONS

Phase Structure Analysis

Figure 1 shows XRD patterns of the synthesized powder and coating. According to the standard card of BTO (JCPDS#01-075-0212), both of them have cubic perovskite structure. Patterns have no lack of peaks and no additional peaks in comparison to standard. Coating shows sharper and higher peaks especially in high angles that reveals higher crystallinity. Calculated crystallite size of the powder was about 25 nm while it was 41 nm for the coating. Furthermore, small peak transition to lower angles could be seen in almost all peaks that show more interplanar distance. All are results of coating further sintering process that eased diffusion and made structure more crystalline.

Figure 1

X-ray diffraction patterns of barium titanate synthesized powder (a) and coating (b). Red bars are JCPDS #01-075-0212 standard

Particle Size Evaluation

DLS analysis of particles size is shown in Figure 2. As it can be seen, particles are in the range of 40–110 nm with one peak around 70 nm. In comparison to XRD results, it seems that each particle consists of a few numbers crystallites. Li et al.[23] reached to an average size of ~10 nm via a similar synthesis method for both crystallite and particle sizes. This difference may relate to better powder dispersion and their colder hydrolyzing temperature (−20°C) that provided higher activation free energy for nucleation.

Figure 2

Particle size distribution of synthesized nanoparticles

Coating Morphology

Figure 3 demonstrates SEM images of the samples after sintering. Particles agglomeration is obvious with signs of substrate roughness. Micro-holes that are the cause of electrolyte evaporation during drying and some micro-cracks were inevitable. Notwithstanding the presence of these defects, coatings have had sufficient qualitative strength and adhesion to substrate.

Figure 3

Scanning electron microscopy micrographs of barium titanate coating deposited by electrophoretic deposition under 60 V/3 min. (a) 125X, (b) 8000X

In vitro biomineralization of the coated samples after 4 weeks of immersion in SBF is shown in Figure 4. Apatite nuclei are appearing on the surface. Globular precipitates growth and conjugation occurred, and new nuclei are obvious on the surface of older ones after 28 days. According to scale bar, size of each globe is about 10 μm.

Figure 4

Scanning electron microscopy micrograph of barium titanate surface immersed in simulated body fluid after 28 days

Lin et al.[24] have reported ball-like calcium phosphate film on the surface of BTO/TiO2 after 21 days immersion in SBF, but with the size of about 3 μm. This size was less than 1 μm in Zarkoob et al.[25] study on BTO/hydroxyapatite. Also in those studies precipitates have covered the surface completely. It seems that there is no appropriate compatibility between BTO and formed apatites, so newer precipitates prefer to form on the surface of older ones instead of BTO surface. This leads to bigger apatite globes versus BTO regions that not covered with precipitates.

EDS result on the sample [Figure 5] qualified precipitates apatite chemistry while it is well known that using standard less EDS analysis do not have sufficient quantitative accuracy to determine the formula of a compound.[26]

Figure 5

Energy dispersive X-ray spectroscopy spectra of apatite nuclei after 28 days of immersion in simulated body fluid

SBF ions concentration during 4 weeks of bioactivity test is shown in Figure 6. Calcium and phosphate ions decreased with an increasing rate, because of growing apatites are more suitable substrates for new apatite nucleation and make precipitation faster. The difference in Ca2+ and PO4 3− losing amount is related to apatite stoichiometry (Ca10(PO4)6(OH)2) that needs Ca2+ about 2 times more than PO4 3−. On the other hand, it could be seen that Ba2+ leached from coating to the solution, as also have seen previously in nanometric BTO.[27] Nevertheless, apatite precipitates slow down the releasing rate of Ba2+ ions by covering the surface along with time.

Figure 6

Simulated body fluid ions concentration changing in the presence of barium titanate coated samples during 4 weeks

The morphology of MG-63 cells cultured on BTO-coated samples was examined using SEM. Some of the images obtained of cells cultured after 1 and 7 days are shown in Figure 7. After 24 h, the appearance of lamellipodia demonstrates cells migration on the surface[28] to reach to an appropriate distribution. On the 7th day, cells completely covered the surface (even over micro-cracks) and showed good attachment to each other and BTO surface.

Figure 7

MG-63 cells morphology after 1 (a) and 7 (b) days of culture on the surface of barium titanate coating

Figure 8 shows MTT assay results comparing the samples and control. BTO had no statistically significant changes during 7 days while control showed cell proliferation. However, this difference could not simply consider as a sign of cytotoxicity since cells were seen in SEM images flattened and attached to the surface.

Figure 8

MTT assay results for barium titanate coating and control in 1, 4, and 7 days after culture

One probable reason may be Ba2+ ions leaching from ceramic as we have discussed in section “Bioactivity Evaluation.” Studies that have investigated composites involving BTO particles, with adequate MTT results[2829] have had micrometer size BTO particles. According to few studies, heat treatment in higher temperatures could decrease Ba2+ ions leaching by means of two parameters. High temperatures increase particle sizes and consequently decrease surface/volume ratio that leads to lower ion leaching.[30] However, by increasing particle size, BTO curie temperature increases and make tetragonal BTO as the stable phase in room temperature.[31] Cubic BTO has exhibited Ba2+ leaching about 3.6 times more than tetragonal BTO because of their differences in crystal structures and the amount of lattice defects contained.[30] Hence, it seems that further sintering processes could be useful to make micrometer size particles and eliminate ions leaching.

Furthermore, in some special circumstances, cultured fibroblasts on the piezoelectric scaffolds have shown that prefer to migrate, adhere, and secrete extracellular matrix,[32] means may be bioactivity of BTO leads to lower cell number and higher protein deposition, that needs a series of protein analyses for approval.

CONCLUSION

Ti6Al4V coated samples with BTO were fabricated by EPD using synthesized nanometer BTO powders followed by sintering at 800°C. Morphological studies showed homogenous coating with signs of EPD medium evaporation. Bioactivity of the coated specimens was studied in SBF at 37°C endorsed apatite formation on the surface. Cell seeding also showed good attachment to the surface but MTT assay resulting in lack of proliferation that may be a result of ion leaching. Hence the results show capability of BTO coating to use as implant coating for in vivo applications.

Financial Support and Sponsorship

Iran National Science Foundation (INSF) (Grant No. 91002863).

Conflicts of Interest

There are no conflicts of interest.