Abstract
The alumina and zirconia surfaces were pretreated with chemical etching using alkaline mixtures of ammonia, hydrogen peroxide and sodium hydroxide, and followed with application of the powder layer of Ca-deficient hydroxyapatite (CDH). The influence of etching bath conditions time and concentration on surface development, chemical composition and morphology of medicinal ceramic powders were studied. The following analyses were performed: morphology (scanning electron microscopy), phase composition (X-ray diffraction analysis), changes in binding interactions and chemical composition (FT-Infrared and Energy dispersive spectroscopies). Both types of etchants did not expose the original phase composition changes or newly created phases for both types of ceramics. Subsequent decoration of the surface with hydroxyapatite revealed differences in the morphological appearance of the layer on both ceramic surfaces. The treated zirconia surface accepted CDH as a flowing layer on the surface, while the alumina was decorated with individual CDH aggregates. The goal of this study was to focus further on the ceramic fillers for polymer-ceramic composites used as a biomaterial in dental prosthetics.
Highlights
Bioceramic materials, such as zirconia, alumina or groups of hydroxyapatites (HAp) are widely used in medical applications, especially in orthopedics and dental prosthetics [1,2,3].The bioceramics used in medicine may be nonporous and almost bioinert, bioactive, resorbable and porous for tissue ingrowth [4,5].For medical applications, it is critical to obtain a correct connection between the bioceramics and the polymers or coated metals
Comparing the size and morphology of agglomerates, the particles are similar in nature
The two ceramic powders, alumina and zirconia, showed very slight changes when treated with the two etchant mixtures
Summary
Bioceramic materials, such as zirconia, alumina or groups of hydroxyapatites (HAp) are widely used in medical applications, especially in orthopedics and dental prosthetics [1,2,3].The bioceramics used in medicine (e.g., for hips, knees and teeth replacements) may be nonporous and almost bioinert (e.g., zirconia or alumina), bioactive (e.g., dense HAp or glass–ceramic), resorbable (e.g., tricalcium phosphate) and porous for tissue ingrowth (e.g., porous Hap or HAp-coated porous metals) [4,5].For medical applications, it is critical to obtain a correct connection between the bioceramics and the polymers or coated metals. Using alumina or zirconia ceramics as a component of the composites may be problematic due to the adhesion of its ceramic grains to the polymer resin This is a consistent problem in cases, for example, in dental prosthetics and dentistry, where it is important to connect the patient’s enamel and prosthetic restoration with adequate abrasion [6,7]. Improvements to the adhesion are crucial for obtaining appropriate physicochemical properties, i.e., low abrasion, fatigue strength or resistance and thermal shocks [7,8]. For these reasons, surface modification to the zirconia and alumina remains a serious challenge to overcome. Several types of surface treatment—such as sandblasting, acid etching, sintering particles onto the surface, nanotechnological applications, laser irradiation, biofunctionalization and self-assembly—
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