Total knee arthroplasty has been effective in reducing pain, but less so in restoring function, especially for activities requiring deep knee flexion. The philosophy of this dissertation was that more functionally effective and optimally designed artificial knees could be created for high flexion activities, if the knee joint kinematics and joint contact forces applied during finite element testing, knee simulator testing, and fatigue testing were more physiologically accurate. The objective of this work was to determine knee joint kinematics and contact forces that could be used in high flexion total knee replacement design and pre-clinical testing. Knee kinematics were determined during high flexion activities for total knee replacement patients and asymptomatic subjects by tracking the motion of skin-mounted sensors. In addition, a protocol was developed to determine the effect of soft tissue artefact on the accuracy of the skin-mounted sensor system in high flexion. The ranges of motion determined for the studied activities can be used as a benchmark to measure the functional success of high flexion total knee replacements. Tibiofemoral joint contact forces were estimated during high flexion activities of daily living using a simple, non-invasive, inverse dynamics based model. The accuracy of the joint contact force estimates was investigated by comparing the estimated forces to in vivo forces measured directly using implanted instrumented tibial components. The comparison showed that the model underestimates the measured axial joint contact force, most likely because the model neglects antagonistic muscle co-contraction. The measured and modeled joint contact forces and the measured knee kinematics could be used to form industry standards for knee simulator and fatigue testing to ensure that the implants are being tested physiologically. Healthy target populations can be studied using the methods outlined in this thesis to define testing standards for target populations: Kinematics can be determined as they were in this work for a group of Middle Eastern subjects, and the non-invasive inverse dynamics based model (with some consideration for the underestimation of forces) could be used to determine the tibiofemoral joint contact forces that the implant might be subjected to during activities of daily living. / Thesis (Ph.D, Mechanical and Materials Engineering) -- Queen's University, 2010-10-25 11:33:06.162

TAMBORINDEGUY, A. C. Avaliação da força e do momento tibiofemoral durante a pedalada: uma orientação para a reabilitação. Dissertação de Mestrado. Programa de pós-graduação em ciências do movimento humano. Escola de Educação Física. Universidade Federal do Rio Grande do Sul. Durante o processo de reabilitação de lesões na articulação do joelho o ciclo ergômetro tem sido amplamente utilizado. No entanto, existem poucos estudos que orientem a sua utilização de forma a evitar sobrecargas às estruturas lesionadas. O presente estudo tem como objetivo comparar o comportamento das componentes de compressão e de cisalhamento anterior e posterior da força intersegmentar e do momento resultante tibiofemoral durante a pedalada no ciclo ergômetro em situações usuais da reabilitação de lesões do joelho. Participaram deste estudo nove sujeitos saudáveis do sexo masculino. O protocolo constou da avaliação de três diferentes alturas do selim (altura do trocânter, 3 cm para baixo e 3 cm para cima desta), duas cadências (40 e 70 rpm) e três cargas de trabalho (0, 5 e 10 N) relacionadas à realidade da reabilitação. Um pedal instrumentado e um sistema de cinemetria foram utilizados para o cálculo do modelo biomecânico bidimensional. Foram analisadas as médias do pico de compressão da força intersegmentar, dos picos do valor máximo e mínimo de cisalhamento da força intersegmentar e o pico dos momentos flexor e extensor durante oito ciclos de pedalada. Os resultados obtidos demonstram que o aumento da carga de trabalho causa um aumento na média do pico de compressão e do pico máximo de cisalhamento da força intersegmentar. As médias do pico de compressão foram de -44,94 (±3,12) N para 0 N, -53,21 (±4,56) N para 5 N e -76,50 (±5,69) N para 10 N. As médias do pico máximo de cisalhamento foram de 61,32 (±5,60) N para O N, 71,21 (±7,73) N para 5 N e 93,89 (±9,10) N para 10 N. O aumento das cargas de trabalho também causou um aumento do pico do momento flexor resultante que teve valores médios de 12,77 (±1,68) Nm para 0 N, 16,90 (±2,49) Nm para 5 N e 25,40 (±3,25) Nm para 10 N. O pico do momento extensor aumentou com a diminuição da altura do selim. As médias do pico do momento extensor nas posições do selim na altura do trocânter, 3 cm abaixo e 3 cm acima foram de, -10,15 (±0,58) Nm, -11,09 (±0,55) Nm e -9,68 (±0,58) Nm, respectivamente. O pico do momento extensor aumentou com o aumento da cadência de pedalada e com o incremento da carga de trabalho de 5 para 10 N. As médias do pico do momento extensor foram de -10,12 (±0,57) Nm para 40 rpm, de - 10,49 (±0,56) Nm para 70 rpm, -10,19 (±0,57) Nm para 5 N e de -10,53 (±0,60) Nm para 10 N. Portanto, pedalar com uma carga de 0 N, com o selim posicionado 3 cm acima da altura do trocânter e na cadência de 40 rpm resulta em menor sobrecarga articular e muscular. / TAMBORINDEGUY, A. C. Assessment of force and moment during cycling: an orientation to rehabilitation. Master thesis. Graduation Program in Human Movement Sciences. School of Physical Education. Federal University of Rio Grande do Sul. During knee injuries rehabilitation process the cycle ergometer has been largely used. However, there are few studies orienting their use avoiding overload damaged structures. The aim of the present study was to compare the effects of compression and shear force components and resultant joint moment in ergometer cycling at different saddle height, cadence and workload during rehabilitation seasons. Nine healthy male volunteers participated in this study. Protocol consisted of evaluation of three differents saddle heights (trochanter height, 3 cm downward and 3 cm upward from trochanter height), two cadences (40 and 70 rpm) and three workloads (0, 5 and 10 N). An instrumented pedal and a motion system were used to calculate the twodimensional biomechanical model. Mean peak compressive intersegmental force, maximum and minimum mean peak shear force, and mean peak extensor and flexor moment during eight pedaling cycles were analyzed. Results demonstrated that changes in workload interfere in mean peak compressive force as well in maximum mean peak shear intersegmentar force. Mean peak compressive were -44.94 (±3.12) N for 0 N, -53.21 (±4.56) N for 5 N and -76.50 (±5.69) N for 10 N. Maximum mean peak shear were 61.32 (±5.60) N for O N, 71.21 (±7.73) N for 5 N and 93.89 (±9.10) N for 10 N. Mean peak flexor moment increased as workload increase (12.77 (±1.68) Nm for 0 N, 16.90 (±2.49) Nm for 5 N and 25.40 (±3.25) Nm for 10 N). Mean peak extensor moment increased at saddle positioned 3 cm downward. Results were - 10.15 (±0.58) Nm, -11.09 (±0.55) Nm, and -9.68 (±0.58) Nm, for trochanteric height, 3 cm downward, and 3 cm upward, respectively. Mean peak extensor moment increased as cadence and workload increased (from -10.12 (±0.57) Nm at 40 rpm to - 10.49 (±0.56) Nm at 70 rpm; from -10.19 (±0.57) Nm at 5 N to -10.53 (±0.60) Nm at 10 N, respectively). Therefore, pedaling at 0 N with saddle positioned 3 cm upward from trochanter height at 40 rpm results in lower joint and muscle overload.

TAMBORINDEGUY, A. C. Avaliação da força e do momento tibiofemoral durante a pedalada: uma orientação para a reabilitação. Dissertação de Mestrado. Programa de pós-graduação em ciências do movimento humano. Escola de Educação Física. Universidade Federal do Rio Grande do Sul. Durante o processo de reabilitação de lesões na articulação do joelho o ciclo ergômetro tem sido amplamente utilizado. No entanto, existem poucos estudos que orientem a sua utilização de forma a evitar sobrecargas às estruturas lesionadas. O presente estudo tem como objetivo comparar o comportamento das componentes de compressão e de cisalhamento anterior e posterior da força intersegmentar e do momento resultante tibiofemoral durante a pedalada no ciclo ergômetro em situações usuais da reabilitação de lesões do joelho. Participaram deste estudo nove sujeitos saudáveis do sexo masculino. O protocolo constou da avaliação de três diferentes alturas do selim (altura do trocânter, 3 cm para baixo e 3 cm para cima desta), duas cadências (40 e 70 rpm) e três cargas de trabalho (0, 5 e 10 N) relacionadas à realidade da reabilitação. Um pedal instrumentado e um sistema de cinemetria foram utilizados para o cálculo do modelo biomecânico bidimensional. Foram analisadas as médias do pico de compressão da força intersegmentar, dos picos do valor máximo e mínimo de cisalhamento da força intersegmentar e o pico dos momentos flexor e extensor durante oito ciclos de pedalada. Os resultados obtidos demonstram que o aumento da carga de trabalho causa um aumento na média do pico de compressão e do pico máximo de cisalhamento da força intersegmentar. As médias do pico de compressão foram de -44,94 (±3,12) N para 0 N, -53,21 (±4,56) N para 5 N e -76,50 (±5,69) N para 10 N. As médias do pico máximo de cisalhamento foram de 61,32 (±5,60) N para O N, 71,21 (±7,73) N para 5 N e 93,89 (±9,10) N para 10 N. O aumento das cargas de trabalho também causou um aumento do pico do momento flexor resultante que teve valores médios de 12,77 (±1,68) Nm para 0 N, 16,90 (±2,49) Nm para 5 N e 25,40 (±3,25) Nm para 10 N. O pico do momento extensor aumentou com a diminuição da altura do selim. As médias do pico do momento extensor nas posições do selim na altura do trocânter, 3 cm abaixo e 3 cm acima foram de, -10,15 (±0,58) Nm, -11,09 (±0,55) Nm e -9,68 (±0,58) Nm, respectivamente. O pico do momento extensor aumentou com o aumento da cadência de pedalada e com o incremento da carga de trabalho de 5 para 10 N. As médias do pico do momento extensor foram de -10,12 (±0,57) Nm para 40 rpm, de - 10,49 (±0,56) Nm para 70 rpm, -10,19 (±0,57) Nm para 5 N e de -10,53 (±0,60) Nm para 10 N. Portanto, pedalar com uma carga de 0 N, com o selim posicionado 3 cm acima da altura do trocânter e na cadência de 40 rpm resulta em menor sobrecarga articular e muscular. / TAMBORINDEGUY, A. C. Assessment of force and moment during cycling: an orientation to rehabilitation. Master thesis. Graduation Program in Human Movement Sciences. School of Physical Education. Federal University of Rio Grande do Sul. During knee injuries rehabilitation process the cycle ergometer has been largely used. However, there are few studies orienting their use avoiding overload damaged structures. The aim of the present study was to compare the effects of compression and shear force components and resultant joint moment in ergometer cycling at different saddle height, cadence and workload during rehabilitation seasons. Nine healthy male volunteers participated in this study. Protocol consisted of evaluation of three differents saddle heights (trochanter height, 3 cm downward and 3 cm upward from trochanter height), two cadences (40 and 70 rpm) and three workloads (0, 5 and 10 N). An instrumented pedal and a motion system were used to calculate the twodimensional biomechanical model. Mean peak compressive intersegmental force, maximum and minimum mean peak shear force, and mean peak extensor and flexor moment during eight pedaling cycles were analyzed. Results demonstrated that changes in workload interfere in mean peak compressive force as well in maximum mean peak shear intersegmentar force. Mean peak compressive were -44.94 (±3.12) N for 0 N, -53.21 (±4.56) N for 5 N and -76.50 (±5.69) N for 10 N. Maximum mean peak shear were 61.32 (±5.60) N for O N, 71.21 (±7.73) N for 5 N and 93.89 (±9.10) N for 10 N. Mean peak flexor moment increased as workload increase (12.77 (±1.68) Nm for 0 N, 16.90 (±2.49) Nm for 5 N and 25.40 (±3.25) Nm for 10 N). Mean peak extensor moment increased at saddle positioned 3 cm downward. Results were - 10.15 (±0.58) Nm, -11.09 (±0.55) Nm, and -9.68 (±0.58) Nm, for trochanteric height, 3 cm downward, and 3 cm upward, respectively. Mean peak extensor moment increased as cadence and workload increased (from -10.12 (±0.57) Nm at 40 rpm to - 10.49 (±0.56) Nm at 70 rpm; from -10.19 (±0.57) Nm at 5 N to -10.53 (±0.60) Nm at 10 N, respectively). Therefore, pedaling at 0 N with saddle positioned 3 cm upward from trochanter height at 40 rpm results in lower joint and muscle overload.

TAMBORINDEGUY, A. C. Avaliação da força e do momento tibiofemoral durante a pedalada: uma orientação para a reabilitação. Dissertação de Mestrado. Programa de pós-graduação em ciências do movimento humano. Escola de Educação Física. Universidade Federal do Rio Grande do Sul. Durante o processo de reabilitação de lesões na articulação do joelho o ciclo ergômetro tem sido amplamente utilizado. No entanto, existem poucos estudos que orientem a sua utilização de forma a evitar sobrecargas às estruturas lesionadas. O presente estudo tem como objetivo comparar o comportamento das componentes de compressão e de cisalhamento anterior e posterior da força intersegmentar e do momento resultante tibiofemoral durante a pedalada no ciclo ergômetro em situações usuais da reabilitação de lesões do joelho. Participaram deste estudo nove sujeitos saudáveis do sexo masculino. O protocolo constou da avaliação de três diferentes alturas do selim (altura do trocânter, 3 cm para baixo e 3 cm para cima desta), duas cadências (40 e 70 rpm) e três cargas de trabalho (0, 5 e 10 N) relacionadas à realidade da reabilitação. Um pedal instrumentado e um sistema de cinemetria foram utilizados para o cálculo do modelo biomecânico bidimensional. Foram analisadas as médias do pico de compressão da força intersegmentar, dos picos do valor máximo e mínimo de cisalhamento da força intersegmentar e o pico dos momentos flexor e extensor durante oito ciclos de pedalada. Os resultados obtidos demonstram que o aumento da carga de trabalho causa um aumento na média do pico de compressão e do pico máximo de cisalhamento da força intersegmentar. As médias do pico de compressão foram de -44,94 (±3,12) N para 0 N, -53,21 (±4,56) N para 5 N e -76,50 (±5,69) N para 10 N. As médias do pico máximo de cisalhamento foram de 61,32 (±5,60) N para O N, 71,21 (±7,73) N para 5 N e 93,89 (±9,10) N para 10 N. O aumento das cargas de trabalho também causou um aumento do pico do momento flexor resultante que teve valores médios de 12,77 (±1,68) Nm para 0 N, 16,90 (±2,49) Nm para 5 N e 25,40 (±3,25) Nm para 10 N. O pico do momento extensor aumentou com a diminuição da altura do selim. As médias do pico do momento extensor nas posições do selim na altura do trocânter, 3 cm abaixo e 3 cm acima foram de, -10,15 (±0,58) Nm, -11,09 (±0,55) Nm e -9,68 (±0,58) Nm, respectivamente. O pico do momento extensor aumentou com o aumento da cadência de pedalada e com o incremento da carga de trabalho de 5 para 10 N. As médias do pico do momento extensor foram de -10,12 (±0,57) Nm para 40 rpm, de - 10,49 (±0,56) Nm para 70 rpm, -10,19 (±0,57) Nm para 5 N e de -10,53 (±0,60) Nm para 10 N. Portanto, pedalar com uma carga de 0 N, com o selim posicionado 3 cm acima da altura do trocânter e na cadência de 40 rpm resulta em menor sobrecarga articular e muscular. / TAMBORINDEGUY, A. C. Assessment of force and moment during cycling: an orientation to rehabilitation. Master thesis. Graduation Program in Human Movement Sciences. School of Physical Education. Federal University of Rio Grande do Sul. During knee injuries rehabilitation process the cycle ergometer has been largely used. However, there are few studies orienting their use avoiding overload damaged structures. The aim of the present study was to compare the effects of compression and shear force components and resultant joint moment in ergometer cycling at different saddle height, cadence and workload during rehabilitation seasons. Nine healthy male volunteers participated in this study. Protocol consisted of evaluation of three differents saddle heights (trochanter height, 3 cm downward and 3 cm upward from trochanter height), two cadences (40 and 70 rpm) and three workloads (0, 5 and 10 N). An instrumented pedal and a motion system were used to calculate the twodimensional biomechanical model. Mean peak compressive intersegmental force, maximum and minimum mean peak shear force, and mean peak extensor and flexor moment during eight pedaling cycles were analyzed. Results demonstrated that changes in workload interfere in mean peak compressive force as well in maximum mean peak shear intersegmentar force. Mean peak compressive were -44.94 (±3.12) N for 0 N, -53.21 (±4.56) N for 5 N and -76.50 (±5.69) N for 10 N. Maximum mean peak shear were 61.32 (±5.60) N for O N, 71.21 (±7.73) N for 5 N and 93.89 (±9.10) N for 10 N. Mean peak flexor moment increased as workload increase (12.77 (±1.68) Nm for 0 N, 16.90 (±2.49) Nm for 5 N and 25.40 (±3.25) Nm for 10 N). Mean peak extensor moment increased at saddle positioned 3 cm downward. Results were - 10.15 (±0.58) Nm, -11.09 (±0.55) Nm, and -9.68 (±0.58) Nm, for trochanteric height, 3 cm downward, and 3 cm upward, respectively. Mean peak extensor moment increased as cadence and workload increased (from -10.12 (±0.57) Nm at 40 rpm to - 10.49 (±0.56) Nm at 70 rpm; from -10.19 (±0.57) Nm at 5 N to -10.53 (±0.60) Nm at 10 N, respectively). Therefore, pedaling at 0 N with saddle positioned 3 cm upward from trochanter height at 40 rpm results in lower joint and muscle overload.

No description available.

It is estimated that approximately 10-12% of the adult population suffers from osteoarthritis (OA), with long reaching burdens personally and socioeconomically. OA also causes mild discomfort to severe pain in those suffering from the disease. The incidence rate of OA for individuals with transtibial amputations is much than average in the tibiofemoral joint (TF). It is well understood that abnormal articular cartilage stress, whether that be magnitude or location, increases the risk of developing OA. Finite element (FE) simulations can predict stress in the TF joint, many studies throughout the years have validated the technology used for this purpose. This thesis is the first to successfully validate a procedure for creating subject-specific FE models for transtibial amputees to simulate the TF joint in gait, cycling and elliptical exercises. Maximum tibial cartilage pressure was extracted post-simulation and compared to historical data. The body weight normalized contact pressure on the tibial articular cartilage for the two amputee participants was larger in magnitude than the control participant in all but the medial compartment in cycling. Additionally, cycling exercise produced the smallest values of contact pressure with elliptical and gait producing similar max values but different areas of effect. The results from this thesis align with the body of work preceding it and further the goal of a FE model that predicts in-vivo articular cartilage stress in the TF joint. Future studies can further refine this methodology and create additional subject-specific models to allow for a statistical analysis of the observed differences to find if the results are significantly different. Refining the methodology could include investigating the full effect of the damping factor on contact pressure and exploring alternative methods of mesh generation.

The prevalence of knee osteoarthritis, a degenerative joint disease characterized by the degradation of articular cartilage, is correlated with the rise in obesity. The rising rates of obesity in children and adults highlight the need for identifying a sustainable physical activity that promotes fitness while mitigating initiation and progression of osteoarthritis. The objective of this study was to determine an effective rehabilitation and lifelong fitness sustainment exercise regimen that minimize risk of osteoarthritis in individuals with high body mass index (BMI). The aim was to examine knee medial and lateral contact forces in gait and cycling training. Gait at self-selected speeds and cycling at moderate resistance were studied using motion analysis in normal BMI and high BMI participants. Individuals with high BMI exhibited abnormal kinematics and increased kinetics in gait but neutral knee abduction-adduction angles, lower knee contact forces, and balanced mediolateral force distribution in cycling. The combination of maladaptive kinetics (excessive cartilage loading) and altered kinematics (primarily knee adduction angles) observed in gait for the high BMI cohort demonstrate the profound adverse effect of weight bearing and impact exercises on knee biomechanics. Exercise rehabilitation modalities should aim to minimize cartilage loading, correct altered knee angles, and prioritize balanced mediolateral force distributions in individuals with high BMI. Cycling, a non-weight bearing and low impact exercise, addresses all these factors because it constrains kinematic patterns with the pedals and carries significant body weight on the saddle.

No description available.

No description available.

Articular cartilage covers the articulating ends of diarthrodial joints. It plays a vital role in the function of the musculoskeletal system by allowing almost frictionless motion to occur between the articular surfaces of a diarthrodial joint. Study of cartilage contact behavior will help to understand the intrinsic biomechanical properties related to cartilage degeneration and related pathology. In order to study the mechanical behavior of the cartilage a FEM based computational model of the knee-joint was developed from MRI data. A heuristic algorithm was developed based on Image processing techniques using Evolve2D toolbox and edge detection. An indigenous path following algorithm to capture minute details of bone and soft tissue curvature was developed using Image Processing Toolbox of Matlab. Parts including femur, tibia, femoral and tibial cartilages, lateral & medial menisci were extracted as a point cloud from each of the slices and rendered into a 3D model using GUI driven CAD package RHINOCEROS 4.0. Commercial FE software HYPERMESH 9.0 was used to develop FE model from geometric model. Cartilage and Menisci were modeled using eight node hexahedral elements and bones were modeled using four node quadrilateral elements. Bones were assumed to be rigid. Cartilage and menisci were assumed to be linearly elastic, isotropic and homogenous. The knee joint was subjected to a uniaxial compressive load with tibia remaining fixed and femur subjected to two primary boundary conditions: 1.Flexion - extension and Varus - Valgus rotation constrained; 2.Only Varus - Valgus rotation constrained. Parameters such as contact area, contact pressure, contact force, centre of contact pressure, mises stress distribution; maximum and minimum principal stresses were studied at maximum compressive load condition and also in intermittent steps. This model considered both geometric and contact non-linearity. From the FE analysis, it was observed that peak contact deformation and contact area on both femoral and tibial medial cartilage was found to be greater than the lateral side under full extension condition. More than 50% of the load transmission was through the medial side - which could be an indication of cartilage degeneration. Deformation of lateral meniscus was more than the medial meniscus under angular constrained conditions. Loading history during intermittent steps suggested that contact area on lateral tibial cartilage increased with load, indicating joint asymmetry. These results indicate the importance of the rotational constraints (boundary conditions) and represent more accurate physiological behavior of knee joint. Role of menisci in this study was analyzed, which indicated that consideration of menisci is essential in biomechanical estimation of load transmission. In conclusion, detailed segmentation to develop geometric model, precise boundary conditions & time dependent behavior of cartilage and menisci helped in understanding knee joint load bearing capacity to a better accuracy and can potentially give rise to designing better cartilage implants.