Electrophoretic deposition and characterization of thin hydroxyapatite coatings formed on the surface of NiTi shape memory alloy
Introduction
NiTi alloys with chemical composition close to that of equiatomic ones display unique mechanical properties, such as shape memory effects (SME) and superelasticity, which are used in the preparation of numerous biomedical devices and implants [1], [2], [3], [4], [5], [6], [7]. However, application of NiTi shape memory alloys (SMA), especially in long-term implants, is limited due to alloy corrosion and potential migration of toxic nickel ions into human organism. In order to improve the corrosion resistance and ensure protection against the harmful influence of Ni ions, the surface ought to be modified by forming different layers based on diamond-like phases, titanium oxides, titanium carbides and nitrides, polymers, apatites or composites [8], [9], [10], [11], [12], [13], [14], [15], [16], [17], [18], [19], [20]. It is widely known that modifying the surface with bioactive calcium phosphate (CaPs) coatings, such as hydroxyapatite (HAp), enhances the material's biocompatibility and osteoconductivity [21], [22], [23], [24].
Most of the deposition techniques require using high -temperature conditions, which may lead to the decomposition of the B2 parent NiTi phase to equilibrium ones, such as Ni3Ti and/or NiTi2, limiting at the same time the shape memory effect. SME is related to reversible martensitic transformation occurring between the B2 parent phase (cubic structure) and the B19′ martensite (monoclinic structure) [1], [2], [3], [4], [5], [6], [7]. The martensitic transformation (B2→B19′) is induced by reducing the temperature, whereas the reverse martensitic transformation (B19′→B2) occurs due to alloy heating.
Surface modifications methods, such as electrophoretic deposition (EPD), have to be repeatable, inexpensive and ensure rapidity of the process. These techniques additionally enable controlling the coating thickness, its uniformity and deposition rate. EPD is also particularly recommended for the formation of coatings on substrates with complicated shapes and morphology. It may also be used without the need to ensure elevated temperatures [25], [26], [27], [28], [29]. The desirable thickness of manufactured coatings can be easily obtained by altering the deposition parameters (time or voltage) as well as the concentration of ceramic particles in colloidal suspension. The crucial thing in the process of manufacturing thin and crack-free coatings is to use submicron or nano-sized ceramic particles and to make sure that the prepared colloidal suspension is well stabilized and unagglomerated. It is worth mentioning that according to Derjaguin-Landau-Verwey-Overbeek (DLVO) theory, colloidal stability is closely related to Zeta potential of colloidal particles and pH value. Hence, higher pH values indicate a better dispersion of ceramic particles in the suspension and determine the possibility of applying anodic or cathodic deposition [25], [26], [27], [28].
EPD is one of the most commonly used technique for producing thick hydroxyapatite coatings [30], [31], [32], [33], [34]. It is worth noting that the unique shape memory effect may be limited or completely blocked by too thick and/or too rigid coatings. According to literature, HAp coatings electrophoretically deposited on NiTi alloy had a thickness of about 120 µm but the influence of such thick coatings on the outstanding shape memory effect and its behavior under deformation have not yet been considered [32].
In the present work a new way of improving biocompatibility has been proposed. The surface of NiTi SMA was first modified by autoclaving, which allowed preparing a thin TiO2 film [14], [35], and, next, electrophoretically covered with hydroxyapatite coatings. Passivation in an autoclave leads to the formation of a thin amorphous TiO2 layer, which improves the corrosion resistance [35] and strength of adhesion of ceramic particles to the metallic substrate [36]. This morphology and topography, structural characteristics and the strength of hydroxyapatite coatings’ adhesion to the NiTi substrate as well as the ability to deform and the influence of the technology on martensitic transformation related to the shape memory effect have been analyzed in detail.
Section snippets
Substrate treatment
A NiTi alloy with the following chemical composition: 50.6 at% Ni and 49.4 at% Ti (Memry GmbH) was used as a substrate for multilayers deposition. Quenching from 850 °C to ice water preserves the β-phase (B2) of a NiTi alloy at room temperature [14]. Afterwards, the samples were polished with 2000-grit SiC paper, a 1 µm diamond suspension and, finally, a 0.1 μm colloidal silica suspension to achieve a mirror finish. Before deposition, the substrate was passivated under the same conditions which are
As-prepared materials
Fig. 1a presents X-ray diffraction patterns of HAp powder measured before its deposition. All diffraction lines were identified as belonging to Ca5(PO4)3OH with a hexagonal crystal system (P63/m) (ICDD-PDF 04–016-2958). A NiTi alloy having the B2 type (Pm-3 m) structure was used as a substrate (ICDD-PDF 01–078-4618) (Fig. 1b). The alloy underwent a reversible martensitic transition (Fig. 2) with characteristic temperatures of martensitic transformation below room temperature. The temperatures of
Conclusions
In the present work, the surface of a NiTi shape memory alloy was modified by forming multifunctional layers made up of TiO2 and hydroxyapatite. The submicron HAp powder was used and optimal parameters of the colloidal suspension as well as deposition parameters were determined. It was found that a well-dispersed and stable suspension, with an average particle size of 230.9 nm, was obtained at 5 pH. The deposition process carried out at 40 V and deposition time of 2 min resulted in the forming of a
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2021, Applied Surface ScienceEffects of electrophoretic deposition times and nanotubular oxide surfaces on properties of the nanohydroxyapatite/nanocopper coating on the Ti13Zr13Nb alloy
2019, Ceramics InternationalCitation Excerpt :The presence of the crystalline HAp and the absence of the amorphous form is desired as the last form is unstable in a human body [104]. The diffraction angles found here are slightly dependent on deposition times and the presence of a nanotubular surface, close to previous values, about 26, 32 and 39° [102,105–107]. Tables 2 and 3 show the nanoindentation and nanomechanical properties for tested coatings.