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A New Mathematical Model for the Human Ankle Joint
Published in J. Middleton, M. L. Jones, G. N. Pande, Computer Methods in Biomechanics & Biomedical Engineering – 2, 2020
A. Leardini, J.J. O’Connor, F. Catani
The rearfoot plays a fundamental role in human locomotion. A better understanding of normal behaviour of the ankle joint complex still remains a crucial issue in the prevention of joint degeneration, treatment of bone fractures, surgical techniques for ligament reconstruction but above all to improve the disappointing results of total ankle replacement arthroplasty for the surgical treatment of severe joint degeneration [1, 2, 3]. Although the early model of the ankle as a pure hinge joint has been recently questioned [4, 5], no models have been proposed that could explain and predict experimental findings such as the change in both position and orientation of ankle axis of rotation [6, 7, 8] and the shifting contact area on the tibial mortise (tibiotalar articulation) during ankle flexion [9].
Hard Tissue Replacements
Published in Joseph D. Bronzino, Donald R. Peterson, Biomedical Engineering Fundamentals, 2019
Sang-Hyun Park, Adolfo Llinás, and Vijay K. Goel
Total ankle replacements had not met with as much success as total hip and knee replacements, and typically loosened within a few years of service (Claridge et al. 1991; Guyer and Richardson 2008; Durr 2009; Coetzee and Deorio 2010). is was due, presumably, to the high load transfer demand over the relatively small ankle surface area and the need to replace three articulating surfaces (tibial, talar, and bular). e joint congurations that have been used are cylindrical, reverse cylindrical, and spherical. e materials used to construct ankle joints are usually Co-Cr alloy and UHMWPE. Degeneration of the ankle joint is currently treated with fusion of the joint, since prosthesis for total ankle replacement is considered to be in intermediate stages of development. e current outcomes have improved and the trend suggests that they will approach, in the future, those of total hip and knee replacement (Fevang et al. 2007). Figure 37.10a shows ankle and other total joint replacements.
Hard Tissue Replacements
Published in Joyce Y. Wong, Joseph D. Bronzino, Biomaterials, 2007
Sang-Hyun Park, Adolfo Llinás, Vijay K. Goel, J.C. Keller
Total ankle replacements have not met with as much success as total hip and knee replacements, and typically loosen within a few years of service [Claridge et al., 1991]. This is mainly due to the high load transfer demand over the relatively small ankle surface area, and the need to replace three articulating surfaces (tibial, talar, and fibular). The joint configurations that have been used are cylindrical, reverse cylindrical, and spherical. The materials used to construct ankle joints are usually CoCr alloy and UHMWPE. Degeneration of the ankle joint is currently treated with fusion of the joint, since prostheses for total ankle replacement are still considered to be under initial development. Figure 9.10 shows ankle and other total joint replacements.
Simulation of ankle joint kinematics in sagittal plane using passive imaging data – a pilot study
Published in Computer Methods in Biomechanics and Biomedical Engineering: Imaging & Visualization, 2019
Dinesh Gundapaneni, James T. Tsatalis, Richard T. Laughlin, Tarun Goswami
Dinesh Gundapaneni has recently completed his PhD in Medical and Biological Systems at Wright State University. His background is in biomedical engineering, with specific training and expertise in musculoskeletal disorders, biomaterials, biomechanics, failure analysis and orthopedic devices. His primary research involves design and development of novel total ankle replacement devices.
Bone remodelling around the tibia due to total ankle replacement: effects of implant material and implant–bone interfacial conditions
Published in Computer Methods in Biomechanics and Biomedical Engineering, 2019
Scandinavian Total Ankle Replacement (S.T.A.R@TM) prosthesis was used in this study. Prosthetic components were positioned (optimal position) according to surgical guidelines (Small Bone Innovations, Inc.). Tibial, meniscal bearing and talar components were generated using Solidworks software (DS Solidworks Corp., Concord, MA) conferring to information provided by the Small Bone Innovations, Inc. All three components were chosen according to patients (tibial component 32 × 30mm; mobile-bearing thickness of 10 mm; talar component 34 × 35mm). The virtual positioning of implant and operation was done using Rhinoceros software (Robert McNeel& Associates, Seattle, WA). In the case of the optimally positioned implant component, the tibial implant was set to perpendicular to the anatomic axis of the tibia. The anterior direction was set by the bisection of the medial and lateral gutters. Medial/lateral implant placement matches the medial gutter corner, and the anterior/posterior implant placement matches at the anterior edge of the tibia for optimal positioning. Using these bony landmarks and references, the authors positioned the tibial component and other implant components in Rhinoceros software, accordingly. Finally, all bones and implant components were imported in ANSYS FE software v 17 for further processes as similar to the intact model. In order to understand the influence of different material on bone remodelling, three prosthetic FE models namely, model 1 (tibial and talar components were assigned with Cobalt–Chromium–Molybdenum, and meniscal bearing was UHMWPE), model 2 (tibial and talar components were assigned with ceramic, and meniscal bearing was UHMWPE) and model 3 (tibial and talar components were assigned with ceramic and meniscal bearing was CFR-PEEK) were developed. In the case of the intact model, a constant thickness of cartilage was developed between all bones (Mondal and Ghosh 2017). Total 16 numbers of ligaments were modelled around the ankle joint by following the same procedure as similar to the earlier study by the corresponding author (Mondal and Ghosh 2017).