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An Introduction to Bio-Implants and Biodegradable Materials
Published in Atul Babbar, Ranvijay Kumar, Vikas Dhawan, Nishant Ranjan, Ankit Sharma, Additive Manufacturing of Polymers for Tissue Engineering, 2023
Tapinderjit Singh, Sandeep Singh, Gurpreet Singh
The most frequently used metals for fracture fixation, angioplasty, and bone remodeling are surgical stainless steel (316L), cobalt-chromium (CoCr) alloys, and titanium (Ti), which are also categorized as bioinert metals. These metals have low corrosion, wear, and friction rate as well as long-term stability under highly reactive in vivo conditions. The osteolysis might destabilize the fixation and eventually the loading and force shift of the implant, leading to implant failure, corrective surgeries, or post-surgery complications (Yu et al., 1993). Figure 3.4 shows the permanent hip replacement implant in pelvis bone (Lawry et al., 2010).
Ti/β-TCP composite porous scaffolds fabricated by direct ink writing
Published in Virtual and Physical Prototyping, 2023
Guangbin Zhao, Qingxian Zhang, Xiaoli Qu, Yanlong Wu, Xu Chen, Yaning Wang, Hang Tian, Yaxiong Liu, Zhikang Li, Bingheng Lu
Titanium (alloy), with great mechanical strength and biocompatibility, is a common material for metal implants in clinical use. However, because it is biologically inert, titanium has a poor capability of bone conduction after implantation and is difficult to form synostosis with the surrounding bone tissues. Its long-term implantation is likely to lead to osteolysis and implant loosening and failure. The bioactivity of titanium (alloy) implants can be improved by depositing a layer of bioactive ceramic coating (e.g. β-tricalcium phosphate and hydroxyapatite) through plasma spraying (Hung et al. 2013; Xia et al. 2018), hydrometallurgy sedimentation (Shin et al. 2015) and laser deposition (Eraković et al. 2014) because of the excellent biocompatibility and osteoconductivity of the coating due to the similarity of its composition to that of the inorganic mineral phase of bones (Zhang et al. 2007; Montazerian et al. 2022). However, due to the poor bonding strength between the titanium (alloy) matrix and the ceramic coating and the brittleness of the coating itself, the coating may peel off after long-term implantation, resulting in the loosening of the implant (Surmenev, Surmeneva, and Ivanova 2014). Therefore, noncoated titanium (alloy)/bioceramic composite materials are becoming a hot research topic.
Diagnosis and management of implant debris-associated inflammation
Published in Expert Review of Medical Devices, 2020
Stuart B. Goodman, Jiri Gallo, Emmanuel Gibon, Michiaki Takagi
Current methods for determining implant wear and osteolysis rely primarily on simple imaging (radiographs, MRI, etc.) and blood tests (e.g. metal ions in the blood) [186]. Future implants might incorporate sensors that could be queried non-invasively to report on the important functions of implants including the degree of wear. More sophisticated biomarkers of wear and wear byproducts must also be developed, paralleling our current tests for implant infection.
Magnetorheological finishing of UHMWPE acetabular cup surface and its performance analysis
Published in Materials and Manufacturing Processes, 2020
Kunal Arora, Anant Kumar Singh
In the modern medical implant industry, ultra-high molecular weight polyethylene (UHMWPE) is most commonly used in the joint replacement prosthesis.[1] Properties such as good mechanical strength, high hardness, good chemical resistance, excellent biocompatibility, and low-cost increase its importance even more in the medical field for making sockets in the hip, knee, and spline implants.[2,3] In hip implants, the acetabular cup component consists of the UHMWPE liner in an alloy shell (mostly titanium alloy). During the stiffness measurement of the UHMWPE cup by the rim compression, it was found that the UHMWPE liner is less stiffened as compared to the metals and ceramics.[4] Further, Small et al.[5] suggested that the lower stiffness leads to the balanced load distribution owing to which there is a low surface strain. This further adds up to the advantage of using UHMWPE cup liner. However, in the joint replacement prosthesis, the limiting factor is the functionality and longer life span of the implant which is due to the wear and creep deformation.[4] One of the main reasons for the failure of the hip implant is the osteolysis which is due to the polyethylene particles resultant from the wear, friction, and creep rate degradation.[6] The osteolysis is polyethylene wear which leads to the loss of bone stock and implant fixation. Kumakura et al.[7] highlighted that the main reasons for the failure of the UHMWPE acetabular cup are oxidative degradation, creep deformation, and the pressure on the surface due to creep penetration. Choudhury et al.[4] highlighted that the main issue for the wear in the acetabular component is creep penetration. This results in the wear debris formation and bone stock loss which lead to osteolysis. Cubillos et al.[8] have discussed that osteolysis may lead to implant failure which is induced by wear from the UHMWPE particles.