# Nanomechanical Behavior, Adhesion and Corrosion Resistance of Hydroxyapatite Coatings for Orthopedic Implant Applications

Kaouther Khlifi, Hafedh Dhiflaoui, Amir Ben Rhouma, Joël Faure, Hicham

Benhayoune, Ahmed Ben Cheikh Laarbi

► To cite this version:

Kaouther Khlifi, Hafedh Dhiflaoui, Amir Ben Rhouma, Joël Faure, Hicham Benhayoune, et al. Nanomechanical Behavior, Adhesion and Corrosion Resistance of Hydroxyapatite Coatings for Orthopedic Implant Applications. Coatings, 2021, 11 (4), pp.477. 10.3390/coatings11040477. hal-03563453

HAL Id: hal-03563453

https://hal.science/hal-03563453v1

Submitted on 21 Sep 2024

HAL is a multi-disciplinary open access
archive for the deposit and dissemination of sci-
entific research documents, whether they are pub-
lished or not. The documents may come from
teaching and research institutions in France or
abroad, or from public or private research centers.

L'archive ouverte pluridisciplinaire HAL, est
destinée au dépôt et à la diffusion de documents
scientifiques de niveau recherche, publiés ou non,
émanant des établissements d'enseignement et de
recherche français ou étrangers, des laboratoires
publics ou privés.

<figure><img src="image_1.png" /></figure>

Distributed under a Creative Commons Attribution 4.0 International License
Article

# Nanomechanical Behavior, Adhesion and Corrosion Resistance of Hydroxyapatite Coatings for Orthopedic Implant Applications

Kaouther Khlifi <fnref n="1" />*, Hafedh Dhiflaoui ¹D, Amir Ben Rhouma <fnref n="1" />, Joël Faure ²D, Hicham Benhayoune <fnref n="2" /> and Ahmed Ben Cheikh Laarbi <fnref n="1" />

<figure><img src="image_2.png" /></figure>

check for
updates

**Citation:** Khlifi, K.; Dhiflaoui, H.; Ben Rhouma, A.; Faure, J.; Benhayoune, H.; Ben Cheikh Laarbi, A. Nanomechanical Behavior, Adhesion and Corrosion Resistance of Hydroxyapatite Coatings for Orthopedic Implant Applications. *Coatings* **2021**, *11*, 477. https://doi.org/10.3390/coatings11040477

Academic Editor: Mohammad Uddin

Received: 31 March 2021

Accepted: 14 April 2021

Published: 19 April 2021

**Publisher's Note:** MDPI stays neutral with regard to jurisdictional claims in published maps and institutional affiliations.

<figure><img src="image_3.png" /></figure>

**Copyright:** © 2021 by the authors. Licensee MDPI, Basel, Switzerland. This article is an open access article distributed under the terms and conditions of the Creative Commons Attribution (CC BY) license (https://creativecommons.org/licenses/by/4.0/).

**Abstract:** The aim of this work was to investigate the nanomechanical, adhesion and corrosion resistance of hydroxyapatite (HAP) coatings. The electrodeposition process was used to elaborate the HAP coatings on Ti₆Al₄V alloy. The effect of hydrogen peroxide concentration H₂O₂ on the electrolyte and the heat treatment was studied. Surface morphology of HAP coatings was assessed, before and after heat treatment, by scanning electron microscopy associated with X-ray microanalysis (SEM-EDXS). Moreover, X-ray diffraction (XRD) was performed to identify the coatings' phases and composition. Nanoindentation and scratch tests were performed for nanomechanical and adhesion behavior analysis. The corrosion resistance of the uncoated, the as-deposited, and the heat-treated coatings was investigated by electrochemical test. The obtained results revealed that, with 9% of H₂O₂ and after heat treatment, the HAP film exhibited a compact and homogeneous microstructure. The film also showed a crystal growth: stoichiometric hydroxyapatite (HAP) and β-tricalcium phosphate (β-TCP). After heat treatment, the nanomechanical properties (H, E) were increased from 117 ± 7 MPa and 24 ± 1 GPa to 171 ± 10 MPa and 38 ± 1.5 GPa respectively. Critical loads (Lc1, Lc2, and Lc3) were increased from 0.78 ± 0.04, 1.6 ± 0.01, and 4 ± 0.23 N to 1.45 ± 0.08, 2.46 ± 0.14, and 4.35 ± 0.25 N (respectively). Furthermore, the adhesion strength increased from 8 to 13 MPa after heat treatment. The HAP heat-treated samples showed higher corrosion resistance (Rp = 65.85 kΩ/cm<fnref n="2" />; Icorr = 0.63 μA/cm<fnref n="2" />; Ecorr = -167 mV/ECS) compared to as-deposited and uncoated samples.

**Keywords:** hydroxyapatite coating; heat treatment; nanoindentation; scratch test; corrosion

## 1. Introduction

Biomaterials have been successfully developed and used to improve the quality of human life, not just for an aging population but also for younger people with heart problems. The success of such an implant largely depends on the selection of materials for their manufacture. Titanium and its alloys, such as Ti₆Al₄V, are the most used metal implants because of their corrosion resistance and biocompatibility. These alloys also have a good yield strength and low elastic modulus, which is similar to that of bone [1,2]. However, in recent years, it has been noticed that most metallic materials, including Ti alloy, can undergo degradation in the long term [3]. Many studies [2,4] proved that Ti₆Al₄V implant could cause health problems because of the release of aluminum (Al) and vanadium (V) ions into the human body's fluid system [4]. According to Tlotleng et al. [2], both V and Al ions are associated with long-term health problems, such as Alzheimer's, neuropathy, and Osteomalacia. In addition, Ti₆Al₄V alloy, as a bioinert material, exhibits

<footnote n="1">¹ Laboratoire de Mécanique, Matériaux et Procèdes (LR99ES05), Ecole Nationale Supérieure d'Ingénieurs de Tunis, Université de Tunis, 5 Avenue Taha Hussein Montfleury, Tunis 1008, Tunisia; dhafedh@gmail.com (H.D.); amir.benrhouma@enstt.rnu.tn (A.B.R.); Ahmed.cheikhlarbi@gmail.com (A.B.C.L.)</footnote>

<footnote n="2">² Institut de Thermique, Mécanique et Matériaux (ITheMM), Université de Reims Champagne-Ardenne (URCA), 51100 Reims, France; joel.faure@univ-reims.fr (J.F.); hicham.benhayoune@univ-reims.fr (H.B.)</footnote>

<footnote>* Correspondence: kaouther.khlifi@ipeiem.utm.tn</footnote>
poor osteoinductive properties. It cannot form effective bone-bonding between the implant and the human tissue [5]. Currently, these limitations have prompted many researchers to focus on solutions, leading to implant surface modification. Hydroxyapatite has a similar structure to the natural bone component. This similarity makes it the preferred candidate for orthopedic and dental implants [6]. Hence, HAP coating allows for new surface properties such as osteointegration and biocompatibility [6–8], which lead to an improvement in implant functionality. Several techniques have been developed for coating metal implants, including plasma spraying sputtering [2], sol–gel [5], electrophoretic deposition [9], magnetron sputtering [10], LVOF (Low-Velocity Oxyfuel) sprayed [11], and electrodeposition [12,13]. Among the various deposition processes, electrodeposition is widely used in the coating industry, and it is considered to be a simple, quick and low-cost technique. Moreover, this method allows for the coating of substrates that have a complex shape or porous structure [14]. Many studies focus on the various methods used to obtain reliable HAP coatings [15,16], other active research investigate bioactivity [2,11], cytocompatibility, and antibacterial properties [17]. Although the HAP coating should be compatible with the tissue surrounding the implant, it also should possess good mechanical properties, high bonding strength and corrosion resistance. To the best of our knowledge, few works have been done investigating the mechanical properties (the hardness and the elastic modulus) and adhesion behavior of HAP coating obtained by electrodeposition technique [18–20]. Hence, a detailed mechanical and corrosion resistance analysis is indispensable to evaluate the reliability of the HAP deposited thin film. The aim of this work is to study the nanomechanical properties, adhesion behavior and corrosion resistance of HAP coating deposited on Ti₆Al₄V. This work investigates, in detail, the high correlation of the nanomechanical, the adhesion, and the corrosion performances, with the coating morphology, the hydrogen peroxide amount, and the heat treatment.

**2. Materials and Methods**

**2.1. Coating Deposition**

Cylindrical rods of 12 mm in diameter and 4 mm in thickness of Ti₆Al₄V alloy were used as substrates. Then, a polishing procedure with alumina particles was applied. Substrates were etched with hydrofluoric acid until a smooth metallic surface was exposed with an average roughness of about 2 µm. Before the deposition, surfaces were ultrasonically cleaned into acetone and then into ultra-pure water. The electrodeposition of HAP coatings was carried out in an electrolyte solution prepared by mixing 0.042 M of Ca(NO₃)₂·4H₂O and 0.025 M NH₄(H₂PO₄) with varying amounts (0%, 6%, and 9%) of hydrogen peroxide (H₂O₂). The pH value was adjusted to 4.4 by adding 0.1 M NaOH solution and the temperature fixed at 60 °C. The electrodeposition was performed using a potentiostat/galvanostat instrument (Voltalab PGP 201 Radiometer Analytical (Lyon, France)-VOLTAMASTER software (version 4)). This process was carried out with a typical three-electrode configuration: the cathode (Ti₆Al₄V substrate), the counter electrode in platinum (Pt), and the reference electrode SCE (saturated calomel electrode). Pulsed current electrodeposition with a peak pulse current density *j* = 8 mA/cm⁻² and a deposition time *t*<sub>ON</sub> = 1 mn and *t*<sub>OFF</sub> = 2 mn (*j* = 0 mA/cm⁻²) was implemented. The electrodeposition process was detailed in previous work [20,21]. Figure 1 shows the schematic representation of the electrodeposition process.
<figure><img src="image_4.png" /><figcaption>**Figure 1.** Schematic representation of electrodeposition process.</figcaption></figure>

## 2.2. Heat Treatment

The HAP coating was thermally treated inside a tubular furnace (Nabertherm RS 80/500/11). Initially, a secondary vacuum of about $10^{-5}$ mbar was achieved into the working tube with the pumping system. Then, a continuous flow of argon maintained at $100 \text{ L} \cdot \text{h}^{-1}$ was injected, leading to an increase in the pressure to about $10^{-2}$ mbar. Finally, the temperature was applied in two steps according to the protocol previously developed in our laboratory [20]: a first plateau at 120 °C during 1 h for water evaporation followed by a second plateau at 500 °C during 1 h. The flow of argon was maintained during the whole heat treatment until complete cooling to room temperature.

## 2.3. Coating Characterization

The HAP coatings' morphology and the chemical analysis were evaluated using scanning electron microscopy (JEOL JSM-5400LV, JEOL, Tokyo, Japan), associated with X-ray microanalysis (SEM-EDXS) (Éloïse, Tremblay en France, France). To measure the HAP coating thickness, commercial software (ENESIS, Eloïse SARL, Tremblay en France, France) associated with an original procedure for coating analysis developed by Benhayoune H. et al. [22,23] was used. Moreover, X-ray diffraction (XRD) (Bourevestnik, Saint Petersburg, Russia) was performed to identify the coatings phases and composition. Nanomechanical behavior was studied using the nano-indentation technique developed by CSM Switzerland Instruments (Anton Paar, Buchs, Switzerland). Tests were conducted using a nano-indent er equipped with a diamond Berkovich tip under a maximum applied load of 100 mN. The film adhesion was investigated using a conventional progressive scratch test with a loading range between 0 and 5 N. The scratch distance and the loading rate were 3 mm and 0.5 N/s, respectively. An electrochemical corrosion test was carried out at room temperature in 3.5 wt.% NaCl solution using Voltalab system. Measurement was performed using the conventional three-electrode cell: reference electrode, platinum auxiliary electrode, and test sample as a working electrode.

# 3. Results and Discussion

## 3.1. Morphological and Microstructural Properties

### 3.1.1. Effect of Hydrogen Peroxide ($H_2O_2$)

To investigate the effect of hydrogen peroxide, three concentrations (0%, 6% and 9%) were tested. Results of SEM-EDXS and XRD analysis are shown in Figures 2 and 3.
<figure><img src="image_5.png" /><figcaption>**Figure 2.** SEM-EDXS analysis of HAP coatings with various amount of H₂O₂: (a,b) 0%, (c,d) 6% and (e,f) 9%.</figcaption></figure>

<figure><img src="image_6.png" /><figcaption>**Figure 3.** X-ray diffraction (XRD) pattern of HAP coating deposited with 0% and 9% of H₂O₂.</figcaption></figure>

SEM micrograph indicates that the HAP coating, with a thickness of 15 µm, was composed of small needles and crystallites. The increase of H₂O₂ concentration influences the HAP morphology, with 0% of H₂O₂. The obtained coating was non-uniform, and certain uncovered substrate zones are observed (Figure 2a,b). When the amounts of H₂O₂ were 6%, the obtained coating (Figure 2c,d) showed that the needles were agglomerated in crystallite spheres, and some porosity was observed. Figure 2e,f shows that the HAP coating morphology, obtained with 9% of H₂O₂, seems to be similar to that obtained with 6% H₂O₂ but with less porosity. Such a result was found in previous works [21]. The amount of H₂O₂
effect was confirmed by XRD analysis. The increase in H₂O₂ concentration, from 0% to 9%, leads to the appearance of more crystalline phases: hydroxyapatite (HAP) as majority phase and β-tricalcium phosphate (β-TCP) as minority phase. Consequently, the sample with 9% H₂O₂ is retained to analyze the nanomechanical, adhesion, and corrosion behavior.

### 3.1.2. Heat Treatment Effect

Figure 4 shows the heat treatment protocol as well as the SEM micrograph of HAP coatings with various H₂O₂ concentrations before (Figure 4a) and after heat treatment (Figure 4c).

<figure><img src="image_7.png" /><figcaption>**Figure 4.** SEM micrograph of HAP coatings with various H₂O₂ concentrations: (a) before heat treatment, (b) heat treatment protocol and (c) after heat treatment.</figcaption></figure>

SEM micrographs show that the heat treatment profoundly influenced the coating morphology (Figure 4a,c). This effect was more noticeable for the coating deposited with 9% H₂O₂. Figure 5 shows the top-view SEM images of the as-deposited (Figure 5a,b) and heat-treated (Figure 5c,d) HAP coating obtained with 9% H₂O₂. The coating morphology was dominated by the agglomeration of particles having a spheroid shape. The size of these spheroids increased under the heat treatment, suggesting an improvement in the coating compactness and a decrease of its porosity. Such a result was confirmed in other recent works [6,11]. On the other hand, this morphology is required in biomedical applications to ensure osseointegration and stability of the implant [24]. XRD diffractograms of the heat-treated HAP coating (0% and 9% of H₂O₂) are shown in Figure 6.

<figure><img src="image_8.png" /><figcaption>**Figure 5.** SEM micrographs surface of (a,b) as-deposited and (c,d) heat-treated HAP coating deposited with 9% H₂O₂.</figcaption></figure>
<figure><img src="image_9.png" /><figcaption>Figure 6. XRD diffractograms of the heat-treated HAP coating obtained with 0% and 9% of H₂O₂.</figcaption></figure>

Compared to the result given in Figure 3, XRD analysis showed a change in the width and intensities of the peaks for the two concentrations of H₂O₂. The XRD diffractogram of the untreated sample (Figure 3) presented a broader peak and a small crystallinity. After the heat treatment, the XRD pattern showed peaks of Ti with a clearer biphasic phase structure consisting of HAP and β-tricalcium phosphate (β-TCP). The XRD patterns also exhibited a thinner peak, revealing an improvement in the coating crystallinity with the heat treatment. The results confirm those of other market research studies [12,25], Motofumi et al. [25] indicated that the crystallinity of the HAP coating increased after heat treatment over 350 °C. Saman et al. [12] showed a direct relationship between the heat-treatment temperature and crystallinity level.

## 3.2. Nanomechanical Behavior

The nano-indentation test resulted in a graph showing the relation between the normal applied load and the corresponding penetration depth at two distinct phases: loading and unloading. Figure 7 shows the typical load–penetration depth curve. During the nano-indentation test, the penetration depth increased as a function of the applied load. Moreover, a plastic deformation occurred until the maximum load (Pmax) corresponded to the maximum penetration depth (hmax). A residual penetration depth (hr) was obtained after the complete removal of the indenter. The area covered under A–B–D–A presents plastic deformation energy (Wp), and the area covered under D–B–C–D presents the elastic-recovering energy (We) during the indentation process.

Analysis of the load–Penetration depth (P–h) curves, based on the Oliver–Pharr approach [26], allows the extraction of nanomechanical properties (Hardness H and Young modulus E) of the HAP coating. This method uses power law to fit the unloading curve and takes the tangent at peak load (Pmax) as the maximum contact stiffness S (Figure 7). According to this method, the hardness is estimated from

$$H = \frac{P}{A} \qquad (1)$$
<figure><img src="image_10.png" /><figcaption>Figure 7. Typical Load vs. Penetration depth curve.</figcaption></figure>

The film elastic modulus can be estimated from the well-known relation between the real projected contact area $A_c$, the initial unloading slope $S$ (unloading stiffness), and the reduced elastic modulus $E_r$

$$E_r = \frac{\sqrt{\pi} S}{2\beta \sqrt{A_c}} \qquad (2)$$

where $\beta$ is a constant that depends on the geometry of the indenter tip. The film elastic modulus $E$ is calculated using the relation

$$\frac{1}{E_r} = \frac{(1 - \vartheta^2)}{E} + \frac{(1 - \vartheta_i^2)}{E_i} \qquad (3)$$

where $\vartheta$ is the Poisson's ratio of the film, $E_i$ and $\vartheta_i$ were the indenter's elastic modulus and Poisson's ratio, respectively.

Figure 8a shows the load-penetration depth curves of HAP coating before and after heat treatment and the obtained nanomechanical properties ($H$ and $E$) as well as the maximum penetration depth $H_{max}$ and the residual penetration depth $h_r$. The $H/E$ and $H^3/E^2$ ratios are important to predict the HAP coating performance [27]. The $H/E$ ratio, called elastic strain to failure, was used to assess the film resistance to elastic deformation. The $H^3/E^2$ index predicts the resistance to plastic deformation and the wear resistance of the coating. The obtained values of the $H/E$ and $H^3/E^2$ index are given in Figure 8b.

As a general interpretation of the results, for both as-deposited and heat-treated HAP coating, the plastic energy (area covered under A–B–D–A) is much higher than the elastic energy (area covered under D–B–C–D) which reveals the plastic behavior of the HAP coating. Moreover, with the heat treatment, the maximum ($H_{max}$) and the residual ($h_r$) penetration depth are reduced from 8.7 ± 0.34 and 7.95 ± 0.3 µm to 6.2 ± 0.2 and 5.88 ± 0.15 µm, respectively. This result indicated that HAP coating has better resistance to the penetration, which was related to the increase in the hardness and Young's modulus. The enhancement of HAP coating's nanomechanical properties after heat treatment was explained by the increase in coating compactness and a decrease in its porosity, as confirmed by SEM-EDXS analysis (Figures 4–6). The improvement in Young's modulus is necessary for orthopedic implants because it reduces the stress concentration in the bone. The implants with a modulus closer to that of the bone would yield a more homogeneous stress distribution and less micro-motion at the interface [28,29].
<figure><img src="image_11.png" /><figcaption>**Figure 8.** Nanoindentation results: (a) Load-Penetration depth curves and (b) the values of H/E and H³/E² indexes for as-deposited and heat-treated coating.</figcaption></figure>

### 3.3. Adhesion Behavior

To investigate the adhesion behavior of HAP coating, a conventional scratch test was applied. Both quantitative and qualitative analyses were carried out. The graphs, representing the variation in the friction force and penetration depth as a function of the normal load, were superposed to the corresponding optic microscope images of the scratch tracks of the HAP coatings (Figures 9 and 10).

Critical loads were determined by combining the observations of the scratch tracks and the measurements of normal and tangential loads, as well as the penetration depth. As demonstrated in Figures 9 and 10, the friction force and the penetration depth increase linearly by augmenting the normal load. The first sudden slope change indicated the appearance of the first cracks corresponding to $L_{C1}$, representing a cohesive failure (Figures 9a and 10a). At a second slope change corresponding to $L_{C2}$, a first spallation and interfacial delamination were observed, revealing an adhesive failure (Figures 9b and 10b). When the normally applied load increases, the track showed a propagation of micro-cracks caused by the high compressive stress developed in front of the indenter and tensile stress behind the indenter. Then, the highest critical load value $L_{C3}$ was obtained when 50% damage of the film occurred (Figures 9c and 10c). It is also noticeable that the heat-treated HAP coating showed less scratch damage than the as-deposited one. Critical loads obtained before and after heat treatment are given in Table 1.
<figure><img src="image_12.png" /><figcaption>**Figure 9.** Friction load and penetration depth as a function of the applied load and the corresponding optical micrographs of scratch tracks of as-deposited HAP coating: (a) scratch track; (b) first cracking; (c) first delamination; (d) total delamination.</figcaption></figure>

<figure><img src="image_13.png" /><figcaption>**Figure 10.** Variation in the friction load and penetration depth as a function of the applied load and the corresponding optical micrographs of scratch tracks of the heat coated HAP coating: (a) scratch track; (b) first cracking; (c) first delamination; (d) total delamination.</figcaption></figure>
<table><caption>**Table 1.** Critical loads and adhesion strength of the as-deposited and heat-treated HAP coatings.</caption><thead><tr><th>Coatings</th><th>L<sub>C1</sub> (N)</th><th>L<sub>C2</sub> (N)</th><th>L<sub>C3</sub> (N)</th><th>σ<sub>c</sub> (MPa)</th></tr></thead><tbody><tr><td>As deposited</td><td>0.78 ± 0.04</td><td>1.6 ± 0.08</td><td>4 ± 0.23</td><td>8</td></tr><tr><td>Heat treated</td><td>1.45 ± 0.08</td><td>2.46 ± 0.14</td><td>4.35 ± 0.25</td><td>13</td></tr></tbody></table>

During the scratch test, when the interfacial shear stresses were accumulated and sufficiently higher than adhesion forces, the delamination of the film occurred [30]. The adhesion strength obtained with the scratch test was calculated using the following equation

$$ \sigma_c = \left( \frac{2P_c}{\pi d_c^2} \right) \left[ \frac{(4 + \theta_f)3\pi\mu}{8} - (1 - 2\theta_f) \right] \quad (4) $$

where $P_c$ is the critical load of spalling, $d_c$ is the critical width of the scratch, $\mu$ is the friction coefficient, $\theta_f$ is the Poisson's ratio of the film.

The obtained values of the adhesion strength of as-deposited and heat-treated HAP coatings are given in Table 1.

Barnes et al. [31] have used scratch testing to measure the adhesion strength of HAP coatings, and they found strength adhesion values with the same order of magnitude. Furthermore, such a result was found by Sopcak et al. [32] using the standard tensile adhesion test ISO 13779-4. On the other hand, the critical loads and adhesion strength increase with the heat treatment. According to Rocha et al. [33], the heat treatment leads to high crystallinity and the formation of chemical bonding between coating and substrate, which explained the strong coating adhesion. In addition, a high temperature promotes the formation of chemical bonds in a large atomic zone mixed at the interface between the coating and the substrate [33]. Tiwari et al. [11] noticed a slight deformation in the interface film/substrate, which was probably related to the mismatch in the coefficient of thermal expansion between the substrate and HAP coating. This phenomenon contributed to an imperfect interface. Hence, the heat treatment leads to an improvement in interface adhesion. In our previous work [34], we also found that the heat treatment of Bioglass coating deposited on Ti₆Al₄V improved the adhesion behavior.

### 3.4. Corrosion Resistance

The electrochemical corrosion tests of Ti₆Al₄V, as-deposited and heat-treated HAP coatings were carried out in a 3.5 wt.% NaCl solution. Tafel polarization curves are given in Figure 11. Tafel extrapolation method allowed the determination of corrosion parameters such as corrosion potential ($E_{corr}$), corrosion current density ($I_{corr}$), cathodic Tafel slopes ($\beta_a$ and $\beta_c$), and the polarization resistance ($R_p$). These parameters are important data to investigate the kinetics of corrosion resistance.

The polarization resistance ($R_p$) was calculated with Stern–Geary Equation (5) [35].

$$ R_p = \left( \frac{\beta_a \beta_c}{2.303 \times (\beta_a + \beta_c) i_{corr}} \right) \quad (5) $$

The results of the polarization test are presented in Table 2.

<table><caption>**Table 2.** Polarization parameters obtained from Tafel curves.</caption><thead><tr><th>Samples</th><th>E<sub>corr</sub> (mV/ECS)</th><th>I<sub>corr</sub> (µA/cm<sup>2</sup>)</th><th>β<sub>a</sub> (mV)</th><th>β<sub>c</sub> (mV)</th><th>R<sub>p</sub> (Ω/cm<sup>2</sup>)</th></tr></thead><tbody><tr><td>Substrate</td><td>-237</td><td>3.78</td><td>113.1</td><td>271.8</td><td>9.17</td></tr><tr><td>As deposited</td><td>-211</td><td>1.98</td><td>196.3</td><td>241.2</td><td>23.73</td></tr><tr><td>Heat treated</td><td>-167</td><td>0.63</td><td>233.6</td><td>161.7</td><td>65.85</td></tr></tbody></table>
<figure><img src="image_14.png" /><figcaption>**Figure 11.** Tafel polarization curves.</figcaption></figure>

Figure 11 shows that the HAP-coated sample exhibits a more significant shift towards the nobler direction compared to the untreated sample and Ti alloy substrate. In addition, the heat-treated HAP coating was characterized by the lower $I_{corr}$ and $E_{corr}$ and the higher polarization resistance $R_p$ compared to as-deposited and uncoated sample (see Table 2). Results were confirmed by optical micrographs of the corroded coating surfaces obtained after four days of immersion in NaCl solution (Figure 12).

<figure><img src="image_15.png" /><figcaption>**Figure 12.** Optical micrograph of corroded samples: (a,b) as-deposited and heat-treated (c,d) HAP coatings.</figcaption></figure>

The optical micrographs of the corroded coating surface morphologies reveal the elimination of the films due to the diffusion of corrosive elements. Results showed that the heat-treated sample had better corrosion resistance compared to the untreated coating. After heat treatment, the coating was compact and well crystallized, and the particles were distributed densely and homogeneously, which presents a barrier against the corrosion mechanism. In addition, the HAP heat-treated coating morphology had a minimal number of pores and cracks, which favors the corrosion protecting ability.
## 4. Conclusions

The objective of this work was the investigation of nanomechanical properties, adhesion, and corrosion resistance of HAP coating deposited by electrodeposition method on Ti₆Al₄V. The effect of the amount of H₂O₂ and the heat treatment on the coating microstructure and morphology was studied. SEM-EDXS and XRD results showed that the heat-treated HAP coatings deposited with 9% of H₂O₂ exhibited a compact and homogeneous microstructure. The heat-treated coating revealed a crystal growth which is stoichiometric hydroxyapatite (HAP) and β-tricalcium phosphate (β-TCP). An improvement of the nanomechanical and adhesion properties of HAP coatings was found after the heat treatment. The corrosion results indicate that the coatings act as a protective layer and improve the corrosion resistance of the substrate. The corrosion behavior of HAP coatings was also improved by heat treatment.

**Author Contributions:** Investigation, K.K., H.D., A.B.R., J.F., H.B., and A.B.C.L.; Methodology, K.K., A.B.R., H.B., and J.F. All authors have read and agreed to the published version of the manuscript.

**Funding:** This research was funded by the Tunisian Ministry of Research and by the PHC UTIQUE project No 44054ZE.

**Institutional Review Board Statement:** Not applicable.

**Informed Consent Statement:** Not applicable.

**Data Availability Statement:** Not applicable.

**Acknowledgments:** The authors would like to thank Brian Ralph for proof reading, Andy Wallwork, and John Charnock for the experimental assistance. The authors would also like to acknowledge David Rickerby from Rolls-Royce for the supply of the TBC sample.

**Conflicts of Interest:** The authors declare no conflict of interest.

## References

1. De Viteri, V.S.; Fuentes, E. Titanium and Titanium Alloys as Biomaterials. In *Tribology: Fundamentals and Advancements*; IntechOpen: London, UK, 2013; pp. 155–181.

2. Tlotleng, M.; Akinlabi, E.; Shukla, M.; Pityana, S. Microstructures, hardness and bioactivity of hydroxyapatite coatings deposited by direct laser melting process. *Mater. Sci. Eng. C* **2014**, *43*, 189–198. [CrossRef]

3. Tranquillo, E.; Bollino, F. Surface modifications for implants lifetime extension: An overview of sol-gel coatings. *Coatings* **2020**, *10*, 589. [CrossRef]

4. W Nicholson, J. Titanium alloys for dental implants: A review. *Prosthesis* **2020**, *2*, 100–116. [CrossRef]

5. Priyadarshini, B.; Vijayalakshmi, U. Structural, morphological and biological evaluations of cerium incorporated hydroxyapatite sol-gel coatings on Ti-6Al-4V for orthopaedic applications. *J. Mater. Res. Technol.* **2021**, *12*, 1319–1338. [CrossRef]

6. Yu, H.N.; Hsu, H.C.; Wu, S.C.; Hsu, C.W.; Hsu, S.K.; Ho, W.F. Characterization of nano-scale hydroxyapatite coating synthesized from eggshells through hydrothermal reaction on commercially pure titanium. *Coatings* **2020**, *10*, 112. [CrossRef]

7. Beig, B.; Liaqat, U.; Niazi, M.F.K.; Douna, I.; Zahoor, M.; Niazi, M.B.K. Current challenges and innovative developments in hydroxyapatite-based coatings on metallic materials for bone implantation: A review. *Coatings* **2020**, *10*, 1249. [CrossRef]

8. Jiang, J.; Han, G.; Zheng, X.; Chen, G.; Zhu, P. Characterization and biocompatibility study of hydroxyapatite coating on the surface of titanium alloy. *Surf. Coat. Technol.* **2019**, *375*, 645–651. [CrossRef]

9. Sorkhi, L.; Farrokhi-Rad, M.; Shahrabi, T. Electrophoretic deposition of hydroxyapatite–chitosan–titania on stainless steel 316 L. *Surfaces* **2019**, *2*, 458–467. [CrossRef]

10. Surmenev, R.A.; Surmeneva, M.A.; Grubova, I.Y.; Chernozem, R.V.; Krause, B.; Baumbach, T.; Epple, M. RF magnetron sputtering of a hydroxyapatite target: A comparison study on polytetrafluorethylene and titanium substrates. *Appl. Surf. Sci.* **2017**, *414*, 335–344. [CrossRef]

11. Tiwari, S.; Mishra, S.B. Post annealing effect on corrosion behavior, bacterial adhesion, and bioactivity of LVOF sprayed hydroxyapatite coating. *Surf. Coat. Technol.* **2021**, *405*, 126500. [CrossRef]

12. Safavi, M.S.; Walsh, F.C.; Surmeneva, M.A.; Surmenev, R.A.; Khalil-Allafi, J. Electrodeposited hydroxyapatite-based biocoatings: Recent progress and future challenges. *Coatings* **2021**, *11*, 110. [CrossRef]

13. García, E.; Louvier-Hernández, J.F.; Mendoza-Leal, G.; Flores-Martínez, M.; Hernández-Navarro, C. Tribological study of HA/CTS coatings produced by electrodeposition process on 316L stainless steel. *Mater. Lett.* **2020**, *277*, 128–336. [CrossRef]

14. Zhang, H.; Liu, Y.; Yuan, J.; Zhu, M.; Chen, J.; Wang, Z. The influence of substrate surface treatment on the electrodeposition of (Co, Mn)3O4 spinel precursor coatings. *Mater. Res. Express* **2020**, *7*, 076405. [CrossRef]
15. Harun, W.S.W.; Asri, R.I.M.; Sulong, A.B.; Ghani, S.A.C.; Ghazalli, Z. Hydroxyapatite-based Coating on Biomedical Implant. In *Hydroxyapatite: Advances in Composite Nanomaterials, Biomedical Applications and Its Technological Facets*; IntechOpen: Rijeka, Croatia, 2018; pp. 69–88.

16. Pu'ad, N.M.; Haq, R.A.; Noh, H.M.; Abdullah, H.Z.; Idris, M.I.; Lee, T.C. Synthesis method of hydroxyapatite: A review. *Mater. Today Proc.* **2020**, *29*, 233–239. [CrossRef]

17. Sasireka, A.; Rajendran, R.; Raj, V. In vitro corrosion resistance and cytocompatibility of minerals substituted apatite/biopolymers duplex coatings on anodized Ti for orthopedic implant applications. *Arab. J. Chem.* **2020**, *13*, 6312–6326. [CrossRef]

18. Fornell, J.; Feng, Y.P.; Pellicer, E.; Suriñach, S.; Baró, M.D.; Sort, J. Mechanical behaviour of brushite and hydroxyapatite coatings electrodeposited on newly developed FeMnSiPd alloys. *J. Alloys Compd.* **2017**, *9*, 187. [CrossRef]

19. Arres, M.; Salama, M.; Rechena, D.; Paradiso, P.; Reis, L.; Alves, M.M.; Santos, C. Surface and mechanical properties of a nanostructured citrate hydroxyapatite coating on pure titanium. *J. Mech. Behav. Biomed. Mater.* **2020**, *108*, 103794. [CrossRef]

20. Ben Jaber, N.; Drevet, R.; Fauré, J.; Demangel, C.; Potiron, S.; Tara, A.; Benhayoune, H. A new process for the thermal treatment of calcium phosphate coatings electrodeposited on Ti6Al4V substrate. *Adv. Eng. Mater.* **2015**, *17*, 1608–1615. [CrossRef]

21. Drevet, R.; Benhayoune, H.; Wortham, L.; Potiron, S.; Douglade, J.; Laurent-Maquin, D. Effects of pulsed current and H₂O₂ amount on the composition of electrodeposited calcium phosphate coatings. *Mater. Charact.* **2010**, *61*, 786–795. [CrossRef]

22. Benhayoune, H. X-ray microanalysis of multi-elements coatings using Auger formalism: Application to biomaterials. *J. Phys. D Appl. Phys.* **2002**, *35*, 1526–1531. [CrossRef]

23. Benhayoune, H.; Dumelie, N.; Balossier, G. Substrate effects correction in Auger spectroscopy and electron probe microanalysis of thin films. *Thin Solid Film.* **2005**, *493*, 113–123. [CrossRef]

24. Rosa, M.B.; Albrektsson, T.; Francischone, C.E.; Schwartz Filho, H.O.; Wennerberg, A. The influence of surface treatment on the implant roughness pattern. *J. Appl. Oral Sci.* **2012**, *20*, 550–555. [CrossRef] [PubMed]

25. Ohki, M.; Jinnal, R.; Hoshina, T.; Kitadai, S.; Yumoto, K.; Saitoh, H. Influence of substrate surface roughness and post heat treatment on interfacial strength of plasma-sprayed hydroxyapatite coatings. *J. Jpn. Therm. Spray Soc* **2020**, *57*, 1–10.

26. Oliver, W.C.; Pharr, G.M. An improved technique for determining hardness and elastic modulus using load and displacement sensing indentation experiments. *J. Mater. Res.* **1992**, *7*, 1564–1582. [CrossRef]

27. Hong, S.; Wu, Y.P.; Wang, B.; Zhang, J.F.; Zheng, Y.; Qiao, L. Nanomechanical properties and dry sliding wear behavior of conventional and nanostructured WC-CoCr coatings prepared by HVOF spraying. *Dig. J. Nanomater. Biostruct.* **2016**, *11*, 1135–1143.

28. Hedia, H.S. Stress and strain distribution behavior in the bone due to the effect of cancellous bone, dental implant material and the bone height. *Bio-Med. Mater. Eng.* **2002**, *12*, 111–119.

29. Simon, U.; Augat, P.; Ignatius, A.; Claes, L. Influence of the stiffness of bone defect implants on the mechanical conditions at the interface—A finite element analysis with contact. *J. Biomech.* **2003**, *36*, 1079–1086. [CrossRef]

30. Huang, Y.C.; Chang, S.Y.; Chang, C.H. Effect of residual stresses on mechanical properties and interface adhesion strength of SiN thin films. *Thin. Solid Film.* **2009**, *517*, 4857–4861. [CrossRef]

31. Barnes, D.; Johnson, S.; Snell, R.; Best, S. Using scratch testing to measure the adhesion strength of calcium phosphate coatings applied to poly (carbonate urethane) substrates. *J. Mech. Behav. Biomed. Mater.* **2012**, *6*, 128–138. [CrossRef]

32. Sopcak, T.; Medvecky, L.; Zagyva, T.; Dzupon, M.; Balko, J.; Balázsi, K.; Balázsi, C. Characterization and adhesion strength of porous electrosprayed polymer–hydroxyapatite composite coatings. *Resolut. Discov.* **2018**, *3*, 17–23. [CrossRef]

33. Rocha, R.C.; Galdino, A.G.D.S.; Silva, S.N.D.; Machado, M.L.P. Surface, microstructural, and adhesion strength investigations of a bioactive hydroxyapatite-titanium oxide ceramic coating applied to Ti-6Al-4V alloys by plasma thermal spraying. *Mater. Res.* **2018**, *21*. [CrossRef]

34. Azzouz, I.; Faure, J.; Khlifi, K.; Cheikh Larbi, A.; Benhayoune, H. Electrophoretic deposition of 45S5 bioglass® coatings on the Ti6Al4V prosthetic alloy with improved mechanical properties. *Coatings* **2020**, *10*, 1192. [CrossRef]

35. G-Berasategui, E.; Zubizarreta, C.; Bayón, R.; Barriga, J.; Barros, R.; Martins, R.; Fortunato, E. Study of the optical, electrical and corrosion resistance properties of AZO layers deposited by DC pulsed magnetron sputtering. *Surf. Coat. Technol.* **2015**, *271*, 141–147. [CrossRef]