In vitro Bioactivity, Bio-Corrosion Resistance and Antibacterial Property of Laser Cladded HA Coatings with Different Content of ZnO on Ti-6Al-4V Substrate

Abstract

HA/ZnO coatings with varying content of ZnO were fabricated on Ti-6Al-4V substrate to enhance its bioactivity and antibacterial ability. The main phases are identified as CaTiO₃, Ca₃(PO₄)₂, ZnTiO₃ and CaO. The coatings with higher ZnO content presented smaller grain size, resulting in a higher surface free energy and better wettability. Consequently, the mineralization of the ZnO/HA coatings, especially for the higher ZnO content samples were improved, indicating better enhanced in vitro bioactivity. The ZnO-HA coated Ti-6Al-4V presented better corrosion resistance than bare Ti-6Al-4V substrate. Furthermore, better corrosion resistance was obtained by increasing ZnO content in the precursor. The antimicrobial ratio of all coatings was approximately 100%, indicating the ZnO doped HA coatings presented excellent antibacterial ability.

Keywords:
ZnO/HA coating; wettability; in vitro bioactivity; bio-corrosion resistance; antibacterial ability

1. Introduction

In recent years, titanium and its alloys are widely used for load bearing implants to heal skeletal defects caused due to old age, trauma, and injury. The advantages of titanium and its alloys include high strength to weight ratio, low modulus, and high biocompatibility ^1,2. However, as a potential scaffold biomaterial, providing excellent mechanical support for bone tissue growth is very important, meanwhile, it is also expected to provide enhanced bioactivity, bio-corrosion resistance, and antibacterial property on the surface ^3-5. Hydroxyapatite (HAp) owns excellent properties such as similarity to the inorganic components of human hard tissue, and good affinity for biological tissue ⁶. In light of this, several researchers have synthesized HAp coatings on Ti-6Al-4V substrates to enhance its in vitro bioactivity and in vitro biocompatibility ^7,8. However, pure HAp coatings have relative low corrosion resistance in the biological environment and poor antibacterial property, which affects its long-term stability ⁹.

For the purpose of improving biocompatibility, several researchers have synthesized HAp coating doped with trace amounts of useful metal ions such as Zn²⁺, Sr²⁺, Mg²⁺, Na⁺ and F^-. These ions exist in human bones, and have been found to be beneficial in regeneration of bone ^10-14. Among them, Zinc is found to be not only beneficial for bone regeneration, but also anti-inflammatory after implantation ^15,16. Corrosion resistance and biocompatibility of SrHAp/ZnO coating fabricated by CED method has been investigated by Huang and his coauthors ¹⁷, and the results showed that ZnO doped SrHAp coated Ti had a lower corrosion rate than the pure HAp-coated sample. Different techniques, including Cathodic electro deposition (CED) ¹⁷, sol-gel ¹⁸, plasma-spraying ¹⁹, and laser deposition ²⁰ procedures have been developed. Of these methods, laser cladding (LC) has gained extensive use due to its ability to achieve appropriate surface textures and surface chemistry and thereby improve the biocompatibility of metallic surfaces at the tissue-implant interface ^21-23. So far, the influences of different content of ZnO addition on the in vitro bioactivity, bio-corrosion resistance, and antibacterial property have not been extensively investigated.

In the current study, ZnO/HA coatings were fabricated by laser cladding technology. The influence of ZnO content on the wettability, in vitro bioactivity, bio-corrosion resistance, and antibacterial ability of ZnO containing HA coating were investigated.

2. Materials and Methods

2.1 Preparation of ZnO/HA composite coating

Commercially Ti-6Al-4V substrate coupons of 100 × 100 × 3 mm³ size were finished gradually with SiC papers of different grits (600, 800, 1000, and 1200), and sequentially rinsed with ethanol, acetone and distilled water in an ultrasonic cleaner to get a clean surface.

Commercially hydroxyapatite with chemical formula Ca₁₀(PO₄)₆(OH)₂ and ZnO powder, obtained from Sinopharm Group Shenyang Co. LTD, were used as the precursor materials. The HA and ZnO powder had a spherical morphology with a unimodal distribution in the range of 10 - 30 μm. The precursors (pure HA andx wt.% ZnO-HA, x = 5, 10, and 15) were mixed in a water based organic solvent polyvinyl alcohol. The mixed slurry was then sprayed onto the clean substrate coupons using an air pressurized spray gun. The sprayed coupons were then dried in an oven in which the temperature was kept at 100°C to remove the moisture. The thickness of 100 μm of the precursor was maintained for all samples.

A JHM-1GY-700 pulsed Nd:YAG laser with a wavelength of 1064 nm was used to carry out laser cladding process. The maximum power of the laser is 700 W. The laser parameters used in present work are listed in Table 1. A metallurgical bonding between the precursor and the substrate is achieved.

Table 1.
Laser parameters used in present study

Pulse width/ms	1.5
Pulse repetition rate/Hz	30
Laser scan speed/mm.s-1	17
Defocus distance/mm	20
Single pulse energy/J	2.5
Average power/W	75

2.2 Wetting and in vitro studies in SBF

Before in vitro assays, wetting activity of the coatings was studied. Contact angle measurements were conducted by a static sessile drop technique using a CAM-Plus contact angle goniometer (Experimental Instrument Factory of HARKE, Beijing, China) equipped with video camera for imaging. With the aim of calculating surface energy, an apolar liquid (diiodomethane) and two polar liquids (distilled water and formamide) were used. In order to correlate the surface energy calculations to the mineralization behaviors of the samples, contact angles of the samples against a similar ionic composition to that of the human plasma, known as simulated body fluid (SBF) were measured. SBF solution as listed in Table 2 was prepared according to Ref. ²⁴. Six independent sets contact angles were measured for each sample to get the average value.

Table 2.
Components and amount needed to prepare 1000 ml of SBF

Salt	Amount	Salt	Amount
NaCl	8.026 g	CaCl2	0.293 g
NaHCO3	0.352 g	Na2SO4	0.072 g
KCl	0.225 g	1M HCl	40 ml
K2HPO4.3H2O	0.230 g	(CH2OH)3CNH2	6.063 g
MgCl2.6H2O	0.311 g	(Tris)

In vitro studies were performed using the SBF solution. To study the bioactivity, the in vitro assays were carried out for a set of three samples from each processing condition. The samples were soaked in 10 ml of SBF solution in plastic containers. The solution was refreshed every 24 h to maintain a pH value of 7.4, and the temperature was maintained at 37 °C during the soaking course. After soaking 14 days, the samples were removed from the fluid and rinsed with distilled water, and then air dried for characterizing the sample surfaces by XRD and SEM-EDS.

2.3 Coating characterization techniques

A Rigaku-D/MAX-A X-ray diffractometer system was employed to analyze the phase structure of the coatings before and after SBF immersion. The radiation source was Cu Ka radiation (wavelength, 0.15406 nm), which was operated at 30 kV and 20 mA in a 2θ range of 20-90° using a step size of 0.02°. Addition of ZnO in the precursor was expected to produce refined grain structure. Hence, the grain size of the coated samples was calculated using the Scherrer formula ²⁵:

(1) $t=\frac{0.9\lambda }{B\cos {\theta }_B}$

Here, t is the grain size of a particular phase, B is the broadening of diffraction line measured at half its maximum intensity (radians) at Bragg angle θ_B, and λ is the wavelength of Cu Kα radiation (0.15406 nm). The peaks used for calculating grain size were chosen to avoid too much overlapping from different phases. In the above equation, the instrumental broadening is not taken into account as our interest was only to see the effect of ZnO content on the relative grain size.

After immersed in SBF, surface morphology and elements distribution of the samples was observed by means of scanning electronic microscope (SEM, SSX-550, Japan) instrument, which was operated at a volt of 15 kV.

2.4 Potentiodynamic polarization test

To evaluate the bio-corrosion resistance of the coatings, SBF solution prepared as listed in Table 2 was used. The corrosion behavior of the ZnO/HA coatings in SBF solution at 37.0 ± 0.5 °C was investigated by means of potentiodynamic polarization test (electrochemical workstation, CHI660D, China). The platinum sheet was designed as auxiliary electrode, a saturated calomel electrode (SCE) as reference electrode and the samples as working electrode with an exposed surface area of 150 mm². The polarization curves of the samples in SBF were obtained at a scan rate of 0.01 V/s. For the purpose of getting stable open circuit potential, the specimens were soaked in SBF solution for 1000 s.

2.5 Antibacterial activity tests

The antibacterial activity of the ZnO/HA coatings against the Gram-negative Staphylococcus aureus (S. aureus) was studied. The antibacterial activity determined using plate-counting method. Before the test, all samples and plates were sterilized using moist heat sterilization method in an autoclave at 120 °C for 30 min. After that, the samples were put into the Petri dishes, and 0.2 ml bacteria culture with a concentration of 5.0 ~ 10.0×10⁵ CFU/ml was dripped onto the surfaces of each sample, and incubated for 24 h at 37°C ± 1°C. The blank plastic plate was used as a reference. The surviving bacterial colonies were counted after the incubation. The antibacterial rate (R) were calculated according to Eq.(2) to evaluate the bacterial effect:

(2) $R=\left(1-\frac{N}{N_0}\right)\times 100\%$

Where N₀ and N are the number of viable bacteria on a reference sample and ZnO/HA coatings after antibacterial tests, respectively.

3. Results and Discussions

3.1 Phase evolution

Surface characterization of ZnO/HA precursor-coated samples was carried out for several aspects, including phase analysis, crystallite size, and microstructure prior to wettability assays. The X-ray diffraction patterns corresponding to pure HA, 5 wt.% ZnO-HA, 10 wt.% ZnO-HA, and 15 wt.% ZnO-HA precursor samples are illustrated in Fig. 1 (a) - (d), respectively. No major change in the types of phases was observed in the coatings with varying ZnO content. Besides Ti phase from the substrate, the new phases are identified as CaTiO₃, Ca₃(PO₄)₂, ZnTiO₃ and CaO after laser cladding process. It is noted that typical diffraction peaks for HA and ZnO from the original precursor were not found. This can be attributed the following possible primary and intermediate reactions between the material systems during laser processing. With the purpose of determining the possibility of the following reactions, the change of Gibbs free energy (ΔG) for each reaction was calculated according to thermodynamic theory and indicated in each equation.

(3) ${\mathrm{Ca}}_{10}{\left({\mathrm{PO}}_4\right)}_6{\left(\mathrm{OH}\right)}_2=3{\mathrm{Ca}}_3{\left({\mathrm{PO}}_4\right)}_2+\mathrm{CaO}+H_{2}O\uparrow \left(∆G={}_{-}1333.75\mathrm{kJ}/\mathrm{mol}\right)$

(4) $\mathrm{Ti}+O_2={\mathrm{TiO}}_2\left(∆G={}_{-}864.09\mathrm{kJ}/\mathrm{mol}\right)$

(5) ${\mathrm{TiO}}_2+\mathrm{CaO}={\mathrm{CaTiO}}_3\left(∆G={}_{-}80.90\mathrm{kJ}/\mathrm{mol}\right)$

(6) ${\mathrm{TiO}}_2+\mathrm{ZnO}={\mathrm{ZnTiO}}_3\left(∆G{=}_{-}516.84\mathrm{kJ}/\mathrm{mol}\right)$

Figure 1
XRD patterns of (a) pure HA coating, (b) 5 wt.% ZnO-HA coating, (c) 10 wt.% ZnO-HA coating, (d) 15 wt.% ZnO-HA coating after laser cladding procedure, and (e) grain size as a function of percentage of ZnO in the precursor

The results of ΔG of the above equations revealed that the primary reaction is the decomposition reaction of HA, which results in the generation of Ca₃(PO₄)₂ and CaO as indicated in XRD results. The reaction process between Ti from the substrate and O₂ gas from the air results in the generation of TiO₂ (Eq.(4)). Accordingly, part of the CaO generated by decomposition of HA reacted with the TiO₂ and led to the formation of CaTiO₃(Eq.(5)). These reaction processes as shown in Eqs.(4) and (5) are likely to accelerate the resolving process of HA. That is the reason that no typical peaks for HA was detected by XRD in the coatings. As shown in Eq. (6), the reaction between TiO₂ and ZnO results in the formation of ZnTiO₃ as illustrated in Fig. 1.

The average grain size of the coatings was calculated using Scherrer formula as stated in Eq. 1. To avoid too much overlapping from different phases, the peaks for Ca₃(PO₄)₂ are used for calculating grain size. The results are presented in Fig. 1e. It is obvious that the grain size decreased with increasing of ZnO content in the coating. The grain size in 15 wt.% ZnO-HA coating is the smallest. It was reported that dopant was found to restrict possible grain growth consequently producing nanoscaled grains ²⁶. And it has been proven that the addition of ZnO facilitated the densification of forsterite ceramics ²⁷. In the recrystallization process, the porosities between grains were gradually removed due to the presence of zinc, and it was easier to form conglomerated grains, thus improved the degree of densification of hydroxyapatite coating. The result reveals the effect of ZnO addition on grain refinement.

3.2 Wettability investigation

For the purpose of studying wettability and in turn investigating in vitro bioactivity of ZnO/HA covered samples, the surface energy components were calculated using the equations as stated in detail in our previous work ²⁸. The surface energy (γ_S) and contact angles against different solid are listed in Table 3. The variation of surface energy components (Lewis acid component γ_s⁺, Lewis base component γ_s^-, apolar component γ_S^LW and surface energy γ_S) as function of ZnO content in the precursors of laser cladded ZnO/HA coatings are illustrated in Fig.2. Evidently, the dispersive component (γ_S^LW) of pure HA coating is 44 mJ/m² and it varies slightly in the range of 37 - 40 mJ/m² with increasing weight percentage of ZnO in the precursor. The basic polar component γ_s^- of pure HA coating is 2.2 mJ/m² and the acid polar component γ_s⁺ is 0.2 mJ/m². With the addition of ZnO, the basic polar component γ_s^- decreased to 1.6 mJ/m² and then increased to 8.2 mJ/m² showing a law of decreasing first and then increasing, while the acid polar component γ_s⁺ increased to 1.4 mJ/m² and then decreased to 0.2 mJ/m² showing a law of increasing first and then decreasing with increasing ZnO content from 5 wt. % to 15 wt. %. The surface free energy of pure HA coating is 45 mJ/m² and the 5 wt.% ZnO/HA coating and 10 wt.% ZnO/HA coating have similar value of surface free energy γ_S which is around 40 mJ/m², however, that of the 15 wt.% ZnO/HA coating increases to 50.2 mJ/m². As evidenced in Table 3, the laser processed ZnO substituted HA coatings result in higher surface energy compared to Ti-6Al-4V control. The possible reason for the variation in surface energy for these samples may be due to the grain size. As described above (Fig. 1e), the average grain size of 15 wt.% ZnO-HA sample is smaller than that of the pure HA coating, the 5 wt.% ZnO-HA and the 10 wt.% ZnO-HA samples. It is well known that grain size strongly influences the grain boundary segregation. Therefore, more grain boundary grooves were formed with more content of ZnO addition leading to formation of more pinning of tripple lines. These pinned tripple lines act as open capillaries to reinforce wetting ²⁹.

Table 3.
Surface energy and contact angles against SBF solution of samples

	Contact angle in different fluids			Surface Energy γs (mJ.m-2)	Contact angle against SBF (°)
Coatings	Distilled water	Formamide	Dioiodomethane
Pure HA	86.4±4.2	56.5±3.3	30.2±5.0	44.9±1.8	64.4±2.1
5 wt. % ZnO/HA	101.8±3.0	82.6±3.1	44.0±6.5	40.7±3.9	51.6±2.1
10 wt. % ZnO/HA	89.5±3.2	74.8±5.6	46.0±2.5	40.4±3.1	51.3±1.8
15 wt. % ZnO/HA	81.0±3.0	64.5±4.4	38.6±3.1	50.2±2.4	46.0±2.2
Ti control	82.6±0.1	57.4±0.1	53.0±0.4	34.2±2.1	63.7±0.3

Figure 2
Surface energy as function of ZnO content in coating precursor

After a biomaterial being implanted into the biological system, the first and the foremost event is wetting. A material used in clinical practice must have appropriate wettability ³⁰. Wettability is perhaps one of the most important factors determining the quantity and quality of adsorbed proteins and the biocompatibility ^31,32. Hence, it is very essential to understand the wettability with SBF solution and wetting behavior of ZnO/HA coated samples on the basis of surface free energy calculation. The static contact angle against SBF solution reflects directly the wettability of a material, therefore, the static contact angles of laser cladded ZnO/HA coatings against SBF solution were performed and presented in Table 3 together with the corresponding light optical images of the liquid droplet shadow. As a reference, that of the Ti-6Al-4V control was also presented. The smaller the contact angle of a material against SBF solution, the better the wettability of the material is. In present work, the static contact angles of the x wt. % ZnO/HA coatings against SBF solution are 51.6 ± 2.1°, 51.3 ± 1.8°, and 46.0 ± 2.2° corresponding to x = 5, 10, 15, respectively, which are relatively smaller than that of the Ti-6Al-4V control (63.7 ± 0.3°) and the pure HA coating (64.4 ± 2.1°). The contact angle was lower to some extend by adding more ZnO in the coatings. This means that laser cladded ZnO/HA coatings are more hydrophilic (higher surface free energy, and smaller contact angle), indicating the improved wettability. The static contact angle has been proven to be the most significant determinant of adhesion strength of cell and protein ³³. A higher surface energy results in a smaller static contact angle against SBF solution. This, in turn, will accelerate the adhesion and growth rate of the cells and protein. In the work by Zhang Li et al. ³⁴, it was postulated that the osteoblasts will preferentially adhere onto hydrophobic surfaces of biomaterials. Hence, it is expected that the enhanced hydrophilicity by presence of ZnO/HA coatings will be favorable to the protein adsorption and osteoblast adhesion.

3.3 In vitro behavior

Studying the precipitation behavior of bone-like apatites in the SBF is one important way to investigate the in vitro bioactivity of the biomaterials. Fig.3a shows the XRD patterns of ZnO-HA coatings after being soaked in SBF for 14 days. Typical apatite peaks were identified in three patterns. With increasing of ZnO content in the coating, the peaks for apatite became more and more clear, indicating that a higher weight percentage of ZnO in the precursor can accelerate apatite nucleation and growth after soaking in SBF. SEM images (Fig.3b-3e) presented the similar morphologies for all samples after being soaked in SBF for 14 days. The chemical compositions were analyzed using EDS and presented the figures as insets. The atom ratio of Ca to P was calculated from the EDS results. It is evident that the ratio of Ca/P is 0.39, 1.23, 1.35, and 1.75, respectively, corresponding to pure HA, 5 wt.% ZnO-HA, 10 wt.% ZnO-HA, and 15 wt. % ZnO-HA coated samples. The results indicated that the ZnO-HA coating can successfully induce apatite nucleation and growth on Ti-6Al-4V surface. The atom ratio of Ca to P of the deposited layer on 15 wt.% ZnO-HA coating is close to that of HCAP (Ca/P=1.67), which is similar to the mineral composition of human bone, indicating that higher ZnO content in the precursor is more benefit for improving the mineralization after being soaked in SBF solution. This improvement in mineralization for the higher ZnO content samples can be attributed to the refining of the grain size and the improvement in wetting behavior as evidenced in Fig.1e and table 3. It is generally accepted that SBF assays may be useful to assess the capability to facilitate mineral composition of human bone ³⁵. The influence of ZnO dopant is more pronounced in stabilizing the HAp and inhibiting the decomposition of Hap. The presence of Zn²⁺ makes hydroxyapatite more aggregated and then easier to precipitate.

Figure 3
XRD patterns of the pure HA coating and ZnO-HA coatings (a), SEM image of (b) pure HA coating, (c) 5 wt.% ZnO-HA coating, (d) 10 wt.% ZnO-HA coating, and (e) 15 wt.% ZnO-HA coating after immersion in SBF for 14d . (The insets are SEM views with higher magnification and EDS analysis results)

3.4 Electrochemical corrosion results

After being implanted in the human body, corrosion resistance of the material is one of the most important factors to influence the stability and lifetime of the implants. Hence, good corrosion resistance is very important for the implant devices besides wettability and bioactivity. The corrosion properties of Ti-6Al-4V control and ZnO/HA coatings were investigated in a SBF environment.

The potentiodynamic scan of Ti-6Al-4V control and pure HA coating, x wt.% ZnO/HA (x = 5, 10, and 15) coatings in SBF solution at 37 °C are illustrated in Fig. 4. Correspondingly, the corrosion potential (E _corr) and corrosion current density (I _corr) were calculated from the potentiodynamic curves based on the Tafel extrapolation method. The results of these corrosion parameters are listed in the inset of Fig. 4. Compared to Ti-6Al-4V control, the curves of x wt.% ZnO/HA coatings shifted toward nobler E_corr and lower I_corr with increasing of ZnO content in the precursor. This shift reveals that the ZnO-HA coatings increased the corrosion resistance of Ti-6Al-4V control. Meanwhile, better corrosion resistance was obtained by increasing ZnO content in precursor. The shift in E_corr was also identified by the decrease in I_corr as indicated in the inset in Fig. 4. The corrosion rate is proportional to the I_corr at a given potential, and materials with higher value of I_corr will be more prone to corrosion ³⁶.

Figure 4
Polarization curves of Ti-6Al-4V and coating-covered samples in SBF

The results of Tafel slope values revealed that I_corr of Ti-6Al-4V control in SBF (approximately 93.2 μA) is higher than that of the x wt.% ZnO-HA coatings (90.9μA, 90.1μA, 49.3μA, and 19.3 μA corresponding to x = 0, 5, 10, and 15, respectively). Hence, the results demonstrated that the 15 wt.% ZnO/HA coated sample is more corrosion resistant than uncoated Ti-6Al-4V and pure HA, 5 wt.% ZnO/HA and 10 wt.% ZnO/HA coated sample in SBF solution. The coatings with higher ZnO content improved the protection ability of the Ti-6Al-4V substrate, and served as barrier layers against ionic diffusion. The study by H. Farnoush ³⁷ and Li ³⁸ showed the same kind of results. The ZnO/HA coatings, especially that with higher content of ZnO in the coating decreased the grain size as proven by the calculation results in Fig.1e. ZnO addition has a function of reducing crystallite size. The reduced grain size, in turn, had a significant function in promoting the activity of electrons at the grain boundaries ³⁹. The promotion of electrons’ activity decreased i_corr and thus improved corrosion protection. These results illustrated that the ZnO/HA coatings, especially 15 wt.% ZnO-HA coating acted as a protective barrier layer to avoid ion diffusion and offer corrosion protection for the Ti-6Al-4V substrate.

3.5 Antibacterial properties evaluation

After 24-h incubation periods, the photographs of bacterial colonies were taken and antibacterial ratio was counted from the number of colonies. The results were shown in Fig. 5. It can be seen from the results that the pure HA coating sample shows an antibacterial ratio of about 20.83% ，however, the antibacterial ratio for all ZnO/HA coatings is approximately 100%. All x-wt. % ZnO/HA (x = 5, 10, 15) coatings presented more excellent bactericidal ability against S. aureus compared to the reference sample and pure HA coating. As discussed earlier, the wettability and bio-corrosion resistance of the coatings with lower content of ZnO (5 wt.% and 10 wt.%) was not ideal compared to 15 wt.% ZnO/HA coating, however, regarding the antibacterial activity, the coating with lower content of ZnO is as better as the coating with higher content of ZnO, indicating that lower content of ZnO can also present excellent antibacterial ability compared with the pure HA coating. The precipitated Zn²⁺ cause the dissolution of the cell contents by destroying the bacterial cell membrane, hindering the synthesis of the metabolic enzymes of the bacteria, destroying the genetic factors, thereby causing the bacteria to lose their biological activities. The experimental results show that the addition of ZnO greatly improved the antibacterial properties of the samples.

Figure 5
Antibacterial experiment photograph of the reference sample, pure HA and ZnO/HA coatings

4. Conclusions

HA coatings substituted with different content of ZnO were fabricated on the surface of Ti-6Al-4V. The influence of ZnO content on the wettability, in vitro bioactivity and bio-corrosion resistance was investigated. Studies of the coatings by XRD demonstrated that there is no major change in the types of phases with varying ZnO content in the precursor. Apart from the original phase from the substrate (Ti), the various other phases are identified as CaTiO₃, Ca₃(PO₄)₂, ZnTiO₃ and CaO due to the decomposition reaction of HA and reactions between the new phases in laser melt pooling.

The grain size decreased with increasing of ZnO content in the coating. The results reveal that the addition of ZnO play an important role in grain refinement. The grain refinement, in turn, results in the increasing of surface free energy and decreasing of contact angle of coatings against SBF solution. The contact angle of the coating with higher content of ZnO against SBF solution was lower than the coatings with lower content of ZnO. Laser cladded ZnO/HA coatings are more hydrophilic (higher surface free energy, and smaller contact angle), indicating the more excellent wettability. As a result of refining of the grain size and the improvement in wetting behavior, the mineralization and in turn the in vitro bioactivity of the ZnO/HA coatings, especially for the higher ZnO content samples was enhanced.

The Tafel curves of the coatings shifted toward nobler E_corr and lower I_corr with increasing of ZnO content in the precursor, revealing that the ZnO-HA coatings increased the corrosion resistance of Ti-6Al-4V control. Better corrosion resistance was obtained by increasing ZnO content in precursor. The antimicrobial ratio of all ZnO/HA coatings was approximately 100%, indicating the ZnO doped HA coatings presented excellent antibacterial ability.

5. Acknowledgements

The work described in this paper is financially supported by the Natural Science Foundation of Liaoning province (No. 201602264), the 12^th University Student’s Innovation Training Project (No. 180027), and the Fundamental Research Funds for the Central Universities (N180705002).

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Publication Dates

• Publication in this collection
  05 Sept 2019
• Date of issue
  2019

History

• Received
  20 Nov 2018
• Reviewed
  24 June 2019
• Accepted
  02 July 2019