Abstract
In this work, carbonated hydroxyapatite (CHA) based on abalone mussel shells (Haliotis asinina) is synthesized using the co-precipitation method. The synthesized CHA was mixed with honeycomb (HCB) 40 wt.% for the scaffold fabrication process. CHA and scaffold CHA/HCB 40 wt.% were used for coating a Titanium (Ti) alloy using the electrophoretic deposition dip coating (EP2D) method with immersion times of 10, 20, and 30 min. The synthesized B-type CHA with a stirring time of 45 min could have lower transmittance values and smaller crystallite size. Energy dispersive X-ray spectroscopy (EDS) showed that the Ca/P molar ratio was 1.79. The scaffold CHA/HCB 40 wt.% had macropore size, micropore size, and porosity of 102.02 ± 9.88 μm, 1.08 ± 0.086 μm, and 66.36%, respectively, and therefore it can also be applied in the coating process for bone implant applications due to the potential scaffold for bone growth. Thus, it has the potential for coating on Ti alloy applications. In this study, the compressive strength for all immersion time variations was about 54–83 MPa. The average compression strengths of human cancellous bone were about 0.2–80 MPa. The thickness obtained was in accordance with the thickness parameters required for a coating of 50–200 μm.
Highlights
For several years, there has been an increased demand for bone replacement or hard tissue damaged from various factors such as osteoarthritis, osteoporosis, dentistry, war-related injuries, and traffic accidents [1]
The morphology results were supported by particle size distribution analysis (Table 1)
This work presents a successful fabrication of carbonated hydroxyapatite (CHA) based on abalone mussel shells with stirring times of 15, 30, and 45 min and the scaffold CHA/HCB 40 wt.%
Summary
There has been an increased demand for bone replacement or hard tissue damaged from various factors such as osteoarthritis, osteoporosis, dentistry, war-related injuries, and traffic accidents [1]. This treatment creates problems due to the low level of biocompatibility of the metal, which causes pain and bruising in the surrounding tissue [4]. The 316L SS devices can result in problems from galvanic corrosion, crevices, and the release of dangerous Cl and Fe ions into tissues. Because these surfaces are not bioactive, they must be modified using osteoconductive materials such as bioceramics, including hydroxyapatite (HA). These new alternatives are used because they can effectively reconstruct human bone tissue [5,6,7]
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