This document summarizes a study that examined how electrical stimulation of the tibialis anterior and gastrocnemius muscles in rats affects ankle joint impedance. The study found that:
1) Ankle joint impedance and net torque at a given velocity were linearly related to the stimulation amplitude and frequency delivered to the two muscles.
2) Ankle net torque depended on the difference between tibialis anterior and gastrocnemius stimulation, while ankle impedance depended on the sum of their stimulation.
3) Ankle net torque and impedance increased linearly with increased velocity of ankle joint movement.
LOWER LIMB ANGULAR KINEMATICS AND HOW IT EFFECTS GAIT SPEEDJohn Joe Magee
This study examined the relationship between lower limb angular kinematics and gait speed. The researcher measured peak knee flexion in the stance and swing phases and peak plantarflexion in a participant walking at various speeds. Results showed no significant correlation between knee flexion in stance and speed. However, there was a strong positive correlation between knee flexion in swing and speed, as well as between plantarflexion and speed. These findings support previous research indicating that knee flexion in swing and plantarflexion are important mechanisms for achieving higher gait velocities.
11 kinematics and kinetics in biomechanicsLisa Benson
This document outlines the key topics to be covered in the BIOE 3200 biomechanics course for Fall 2015. Students will learn to define and distinguish between kinematics, which describes motion without regard to causes, and kinetics, which analyzes the forces that cause motion using Newton's laws. The course will teach how to draw free body diagrams, apply equations of motion, and use kinematic relationships to solve biomechanics problems involving subjects extending their legs as quickly as possible.
A STUDY ON THE MOTION CHANGE UNDER LOADED CONDITION INDUCED BY VIBRATION STIM...csandit
To assist not only motor function but also perception ability of elderly and/or handicapped
persons, the power-assist robots which have perception-assist function have been developed.
These robots can automatically modify the user’s motion when the robot detects inappropriate
user’s motion or a possibility of accident such as collision between the user and obstacles. For
this motion modification in perception-assist, some actuators of power-assist robot are used. On
the other hand, since some elderly persons, handicapped persons or some workers need not use
power-assist function but perception-assist function only, another new concept perception-assist
method was investigated in our previous study. In this perception-assist method, only vibrators
are used for generating motion change with kinesthetic illusion to assist perception-ability only.
In this study, since the perception-assist is often used during tasks under a loaded condition, the
features of motion change under the loaded condition are investigated.
IRJET- A Review on Biomechanics of Knee JointIRJET Journal
This document reviews the biomechanics of the knee joint. It discusses the role of the knee joint in allowing locomotion with minimal energy and stability over different terrains. The document outlines the movements of the knee including flexion, extension, and rotation. It describes the forces acting on the knee joint, which can be 2-3 times body weight during walking. The document provides an example calculation of the net joint forces and moments at the knee using inverse dynamics. It determines the horizontal and vertical reaction forces at the knee and calculates the net joint moment to be 592.3 Nm, indicating knee extension.
#9_2-Anthropometry in Occupational Biomechanics.pdfadithya
Anthropometry is the scientific measurement of human body dimensions. It is used to collect data on human physical characteristics to inform product and workplace design. Some key goals of anthropometry are to describe population characteristics and communicate standardized data to engineers. Variability between individuals is due to genetic and environmental factors like age, sex, ethnicity, occupation, and more. Both static and dynamic body measurements are taken, with static referring to fixed postures and dynamic capturing body motions. Measurement devices include calipers, tapes, scales and more advanced techniques like 3D scanning. Anthropometric data is used to model aspects like reach distances. It is also used to estimate body segment parameters which describe segments as rigid bodies defined by properties like mass, length
This study aims to define gait for shoulder-produced locomotion using the double-poling technique from sledge hockey. A solid-static prototype mimicking the average male torso was used to determine baseline measures during the preparation phase. The prototype's trajectory and reaction forces supported that preparation initiation should begin slightly below the horizon to produce the greatest force. Results from sledge hockey players and able-bodied controls will be used to illustrate the complete seated gait cycle, including phases for static-start, start cycle, contact, and recovery. This evidence could improve training and rehabilitation for people who use their shoulders for mobility.
The document summarizes key aspects of human gait, including the gait cycle, phases of stance and swing, joint motions, muscle functions, shock absorption, energy conservation, and analysis methods. The gait cycle consists of stance and swing phases, with stance further divided into initial contact, loading response, mid stance, terminal stance, and preswing. Key motions include plantarflexion during loading response, dorsiflexion during single support, and plantarflexion at toe-off. Muscles like the quadriceps and hamstrings function to control knee motion and absorb shock during gait. Analysis methods examine motion, forces, electromyography, work, and energy expenditure to evaluate gait.
Running with a weighted backpack, or rucking, significantly increases knee joint reaction forces compared to running without weight. Researchers had a subject run on a treadmill at 3.35 m/s without weight and 1.79 m/s with a 20.43 kg ruck. Peak knee joint reaction forces were 3,823.5 N without weight and 6,458.8 N with weight, a difference of over 2,600 N. While this study was limited to one subject, it demonstrates that increased load from rucking raises joint forces and can impact military personnel, backpackers, and recreational ruckers.
LOWER LIMB ANGULAR KINEMATICS AND HOW IT EFFECTS GAIT SPEEDJohn Joe Magee
This study examined the relationship between lower limb angular kinematics and gait speed. The researcher measured peak knee flexion in the stance and swing phases and peak plantarflexion in a participant walking at various speeds. Results showed no significant correlation between knee flexion in stance and speed. However, there was a strong positive correlation between knee flexion in swing and speed, as well as between plantarflexion and speed. These findings support previous research indicating that knee flexion in swing and plantarflexion are important mechanisms for achieving higher gait velocities.
11 kinematics and kinetics in biomechanicsLisa Benson
This document outlines the key topics to be covered in the BIOE 3200 biomechanics course for Fall 2015. Students will learn to define and distinguish between kinematics, which describes motion without regard to causes, and kinetics, which analyzes the forces that cause motion using Newton's laws. The course will teach how to draw free body diagrams, apply equations of motion, and use kinematic relationships to solve biomechanics problems involving subjects extending their legs as quickly as possible.
A STUDY ON THE MOTION CHANGE UNDER LOADED CONDITION INDUCED BY VIBRATION STIM...csandit
To assist not only motor function but also perception ability of elderly and/or handicapped
persons, the power-assist robots which have perception-assist function have been developed.
These robots can automatically modify the user’s motion when the robot detects inappropriate
user’s motion or a possibility of accident such as collision between the user and obstacles. For
this motion modification in perception-assist, some actuators of power-assist robot are used. On
the other hand, since some elderly persons, handicapped persons or some workers need not use
power-assist function but perception-assist function only, another new concept perception-assist
method was investigated in our previous study. In this perception-assist method, only vibrators
are used for generating motion change with kinesthetic illusion to assist perception-ability only.
In this study, since the perception-assist is often used during tasks under a loaded condition, the
features of motion change under the loaded condition are investigated.
IRJET- A Review on Biomechanics of Knee JointIRJET Journal
This document reviews the biomechanics of the knee joint. It discusses the role of the knee joint in allowing locomotion with minimal energy and stability over different terrains. The document outlines the movements of the knee including flexion, extension, and rotation. It describes the forces acting on the knee joint, which can be 2-3 times body weight during walking. The document provides an example calculation of the net joint forces and moments at the knee using inverse dynamics. It determines the horizontal and vertical reaction forces at the knee and calculates the net joint moment to be 592.3 Nm, indicating knee extension.
#9_2-Anthropometry in Occupational Biomechanics.pdfadithya
Anthropometry is the scientific measurement of human body dimensions. It is used to collect data on human physical characteristics to inform product and workplace design. Some key goals of anthropometry are to describe population characteristics and communicate standardized data to engineers. Variability between individuals is due to genetic and environmental factors like age, sex, ethnicity, occupation, and more. Both static and dynamic body measurements are taken, with static referring to fixed postures and dynamic capturing body motions. Measurement devices include calipers, tapes, scales and more advanced techniques like 3D scanning. Anthropometric data is used to model aspects like reach distances. It is also used to estimate body segment parameters which describe segments as rigid bodies defined by properties like mass, length
This study aims to define gait for shoulder-produced locomotion using the double-poling technique from sledge hockey. A solid-static prototype mimicking the average male torso was used to determine baseline measures during the preparation phase. The prototype's trajectory and reaction forces supported that preparation initiation should begin slightly below the horizon to produce the greatest force. Results from sledge hockey players and able-bodied controls will be used to illustrate the complete seated gait cycle, including phases for static-start, start cycle, contact, and recovery. This evidence could improve training and rehabilitation for people who use their shoulders for mobility.
The document summarizes key aspects of human gait, including the gait cycle, phases of stance and swing, joint motions, muscle functions, shock absorption, energy conservation, and analysis methods. The gait cycle consists of stance and swing phases, with stance further divided into initial contact, loading response, mid stance, terminal stance, and preswing. Key motions include plantarflexion during loading response, dorsiflexion during single support, and plantarflexion at toe-off. Muscles like the quadriceps and hamstrings function to control knee motion and absorb shock during gait. Analysis methods examine motion, forces, electromyography, work, and energy expenditure to evaluate gait.
Running with a weighted backpack, or rucking, significantly increases knee joint reaction forces compared to running without weight. Researchers had a subject run on a treadmill at 3.35 m/s without weight and 1.79 m/s with a 20.43 kg ruck. Peak knee joint reaction forces were 3,823.5 N without weight and 6,458.8 N with weight, a difference of over 2,600 N. While this study was limited to one subject, it demonstrates that increased load from rucking raises joint forces and can impact military personnel, backpackers, and recreational ruckers.
This document discusses diarthrodial joints and joint motion. It identifies important connective tissue structures in diarthrodial joints like synovial fluid, articular cartilage, meniscus, ligaments, tendons, and muscles. These structures provide lubrication, load distribution, joint stability, and transmission of forces. Joints allow six degrees of freedom consisting of three translations and three rotations. Applying statics to joint biomechanics problems requires assumptions like known axes of rotation and muscle attachments, negligible friction, and consideration of only two-dimensional forces. Anthropometric data provides average human body measures used in the analysis.
NSCA National Conference (2013) Podium Presentationcoachademia
This study examined changes in medial gastrocnemius (MG) muscle-tendon interaction following 8 weeks of resistance training in 11 trained males. Following training, MG muscle elongation increased more than MG tendon elongation at hopping frequencies of 2.5 Hz and 3.0 Hz. While ankle joint strength increased, ankle joint stiffness decreased at these hopping frequencies. The results suggest that short-term resistance training disproportionately increases muscle strength relative to tendon stiffness, leading to greater reliance on the tendon during fast stretch-shortening cycle tasks.
This study investigated the preparation phase of the seated double poling cycle in sledge hockey through biomechanical analysis. A solid-static prototype representing an adult male was used with motion capture and force plates to measure kinematics and kinetics. Results showed peak impact forces occurred before 5 milliseconds post contact. Forces were greatest when preparation began slightly below the horizon. Data provides baseline measures to understand preparation phase importance and insights to improve sledge hockey performance and shoulder joint health.
Biomechanics is the study of how forces affect living organisms during movement. It uses concepts from physics like mechanics, kinematics, and kinetics to understand human motion. Biomechanists study biomechanics to improve athletic performance and prevent injuries by understanding how forces impact the body during different activities. They analyze both the description of movement through kinematics and the causes of motion through kinetics.
Effect of Ankle Immobilization on Able-Bodied Gait to Model Bilateral Transti...Antonia Nepomuceno
This study investigated how immobilizing the ankles of able-bodied individuals in a neutral position affects their gait. Nine able-bodied subjects walked without and with ankle casts at normal and fast speeds. Kinematics and kinetics were compared between conditions and to data from bilateral transtibial amputees. With casts, ankle range of motion decreased significantly while trunk motion increased. Ankle power generation during pre-swing also decreased substantially. To compensate, hip power generation increased. The gait patterns with ankle casts resembled those of bilateral transtibial amputees, suggesting restricted ankle motion generates compensatory mechanisms seen in their gait.
1) The study compared the effects of two forms of telerehabilitation training on ankle function after stroke - ankle tracking training (Track group) versus repetitive ankle movements (Move group).
2) Ankle dorsiflexion during gait increased significantly more for the Track group than the Move group after training. Brain activation patterns also differed between the groups.
3) Forced learning through ankle tracking was found to produce greater improvements in ankle function during walking compared to simple forced use of the ankle. Telerehabilitation was deemed a feasible approach for stroke rehabilitation.
This presentation summarizes research on the relationships between forearm girth, grip strength, thigh girth, and vertical jump height. Six subjects were measured for height, weight, forearm girth, grip strength, thigh girth, and vertical jump. Strong positive correlations were found between forearm girth and grip strength. However, a negative correlation was found between thigh girth and vertical jump height, contrary to the initial hypothesis. The results provide insights for athletes and clinicians on how to assess muscular strength and power.
Discus throwing performances and medical classification of wheelchair athlete...Ciro Winckler
CHOW, J. W.; MINDOCK, L. A. Discus throwing performances and medical classification of wheelchair athletes. Medicine and Science in Sports and Exercise, v. 31, n. 9, p. 1272-1279, 1999.
This lecture discusses introductory mechanics models and constitutive models for biomaterials. The objectives are to establish biomaterial constitutive models, determine biomechanical response to load, analyze prosthetic design, and estimate health status of living tissues under stress. The lecture covers introductory mechanics modeling including stress analysis, normal and pure bending. Methods of biomechanics including analytical, experimental, and numerical techniques like FEM are presented. Constitutive models including elastic behavior, Hooke's law, elastic constants, material anisotropy, orthotropy, transverse isotropy, and isotropy are discussed.
This study examined how varying ankle stiffness affects gait and muscle activity. Healthy individuals walked on a treadmill and overground with the anklebot applying different stiffnesses. Kinematic data and electromyography of four ankle muscles were measured. Results showed that increased stiffness reduced ankle inversion/eversion range of motion while decreased stiffness increased it. Soleus muscle activity significantly increased with decreased stiffness. Walking overground produced greater ankle and knee motions than treadmill walking. Understanding how ankle stiffness impacts gait can provide insights into locomotion.
This study aimed to compare quadriceps muscle activation and perceived exertion during the leg press and Smith machine squat exercises. The researchers measured muscle activation via EMG and perceived exertion ratings in athletes performing each exercise across a range of loads. They developed predictive equations to determine equivalent loads between exercises that produce the same muscle activation and perceived exertion. The muscle activation equation was less accurate due to individual variability, while the perceived exertion equation was more accurate as it reflects the overall exertion of each exercise rather than specific muscles. These equations provide a new tool to convert loads between exercises over a training period.
The new MTS cadaveric fixture was successfully manufactured to meet all design goals. It allows for 45 degrees of freedom in plantarflexion and dorsiflexion. The fixture can withstand loads up to 70kg and securely fix the ankle at a set angle without additional rotation during loading. The design also allows for easy exchange of cadaver limbs without complete disassembly.
Functional calibration is a technique to determine joint centers and axes by using marker trajectory data from movement trials rather than assumptions. For the hip, validation studies have found functional calibration performs about as well as regression equations in adults but regression equations outperform it in children with cerebral palsy. For the knee, functional calibration may be more repeatable than relying on marker placement since knee joint centers are difficult to identify visually. Overall, functional calibration of the knee is preferable to assumptions but it has not been easily implemented in commercial motion analysis software.
This study investigated hip muscle activation during common closed-chain rehabilitation exercises and running in runners. Electromyography was used to measure gluteus maximus and medius activation during a resisted hip external rotation exercise, single leg squat with trunk rotation, forward lunge with resisted abduction, and running. The forward lunge elicited the highest hip muscle activation, but activation was still substantially less than during running. While the exercises activated the hip muscles more than non-weight bearing exercises, there remains a disconnect between activation during exercises and running. Further research is needed to identify exercises that more closely mimic muscle demands during running.
This document provides an overview of biomechanics and its key concepts. It discusses how biomechanics studies the forces acting on the human body both internally from muscles and externally. It covers the history and academic backgrounds of biomechanics. The key concepts of kinematics and kinetics are explained, including concepts like displacement, velocity, acceleration, forces, torque, inertia, and momentum. Ground reaction forces and their analysis are also discussed.
This document summarizes a study that performed a 3D finite element analysis of the human femur bone. The analysis used a 3D CAD model of the femur obtained from medical scans. The model was meshed and material properties were assigned to different bone tissues. Nonlinear analyses were conducted to simulate loads on the femur during normal activities. Results were compared to previous studies to validate the model. The study found that cancellous bone tissue reduces stresses in the femur, with its absence causing stresses almost double the amount.
1. The document discusses developing an active assistive device using functional electrical stimulation (FES) to restore gait and promote movement rehabilitation for individuals with drop foot.
2. The technical objectives are to develop an FES actuator, an FES assistive platform, and to model the dynamics of electrically stimulated leg muscles affected by drop foot.
3. Preliminary trials show the FES system can correctly deliver stimulation and detect walking phases to correct drop foot, and modeling electrically stimulated muscles is important for advanced closed-loop control strategies.
This document summarizes a study that examined the effectiveness of retro walking (backward walking) in patients with chronic osteoarthritis of the knee. 30 patients with grade 3 knee osteoarthritis underwent 10 minutes of retro walking per day on an inclined treadmill for 10 days. Outcome measures assessed before and after the intervention included pain, stiffness, physical function via the WOMAC index, knee extension lag, dynamic balance, and parameters of forward walking. The results showed statistically significant improvements in all outcome measures following the retro walking intervention. The study concluded that retro walking is an effective approach for reducing symptoms and improving physical function in patients with osteoarthritis of the knee.
Adding stiffness to the foot through shoes and insoles during walking:
1. Decreased the amount of energy dissipated by the foot and increased the gear ratio of the foot-ankle complex.
2. Increased soleus muscle peak force production and decreased soleus fascicle shortening speed, altering the muscle's force-velocity behavior.
3. Despite changes to soleus muscle mechanics, increased whole-body metabolic cost, likely due to the added force demand placed on the plantar flexor muscles.
Tibial Insert Micromotion of Various Knee Devices-J of Knee surgery-2010 vol ...Safia Bhimji
This study developed a novel method to quantify rotational micromotion of modular tibial inserts under physiologic loading conditions. Testing was conducted on four total knee designs incorporating fluid environment and off-axis loading. Results showed that under walking and stair climbing loads, the full peripheral capture design experienced the most micromotion due to higher constraint, while the design with a rotational stabilizing island demonstrated the least motion. Micromotion increased with higher torques applied, with significant differences between designs.
This document discusses diarthrodial joints and joint motion. It identifies important connective tissue structures in diarthrodial joints like synovial fluid, articular cartilage, meniscus, ligaments, tendons, and muscles. These structures provide lubrication, load distribution, joint stability, and transmission of forces. Joints allow six degrees of freedom consisting of three translations and three rotations. Applying statics to joint biomechanics problems requires assumptions like known axes of rotation and muscle attachments, negligible friction, and consideration of only two-dimensional forces. Anthropometric data provides average human body measures used in the analysis.
NSCA National Conference (2013) Podium Presentationcoachademia
This study examined changes in medial gastrocnemius (MG) muscle-tendon interaction following 8 weeks of resistance training in 11 trained males. Following training, MG muscle elongation increased more than MG tendon elongation at hopping frequencies of 2.5 Hz and 3.0 Hz. While ankle joint strength increased, ankle joint stiffness decreased at these hopping frequencies. The results suggest that short-term resistance training disproportionately increases muscle strength relative to tendon stiffness, leading to greater reliance on the tendon during fast stretch-shortening cycle tasks.
This study investigated the preparation phase of the seated double poling cycle in sledge hockey through biomechanical analysis. A solid-static prototype representing an adult male was used with motion capture and force plates to measure kinematics and kinetics. Results showed peak impact forces occurred before 5 milliseconds post contact. Forces were greatest when preparation began slightly below the horizon. Data provides baseline measures to understand preparation phase importance and insights to improve sledge hockey performance and shoulder joint health.
Biomechanics is the study of how forces affect living organisms during movement. It uses concepts from physics like mechanics, kinematics, and kinetics to understand human motion. Biomechanists study biomechanics to improve athletic performance and prevent injuries by understanding how forces impact the body during different activities. They analyze both the description of movement through kinematics and the causes of motion through kinetics.
Effect of Ankle Immobilization on Able-Bodied Gait to Model Bilateral Transti...Antonia Nepomuceno
This study investigated how immobilizing the ankles of able-bodied individuals in a neutral position affects their gait. Nine able-bodied subjects walked without and with ankle casts at normal and fast speeds. Kinematics and kinetics were compared between conditions and to data from bilateral transtibial amputees. With casts, ankle range of motion decreased significantly while trunk motion increased. Ankle power generation during pre-swing also decreased substantially. To compensate, hip power generation increased. The gait patterns with ankle casts resembled those of bilateral transtibial amputees, suggesting restricted ankle motion generates compensatory mechanisms seen in their gait.
1) The study compared the effects of two forms of telerehabilitation training on ankle function after stroke - ankle tracking training (Track group) versus repetitive ankle movements (Move group).
2) Ankle dorsiflexion during gait increased significantly more for the Track group than the Move group after training. Brain activation patterns also differed between the groups.
3) Forced learning through ankle tracking was found to produce greater improvements in ankle function during walking compared to simple forced use of the ankle. Telerehabilitation was deemed a feasible approach for stroke rehabilitation.
This presentation summarizes research on the relationships between forearm girth, grip strength, thigh girth, and vertical jump height. Six subjects were measured for height, weight, forearm girth, grip strength, thigh girth, and vertical jump. Strong positive correlations were found between forearm girth and grip strength. However, a negative correlation was found between thigh girth and vertical jump height, contrary to the initial hypothesis. The results provide insights for athletes and clinicians on how to assess muscular strength and power.
Discus throwing performances and medical classification of wheelchair athlete...Ciro Winckler
CHOW, J. W.; MINDOCK, L. A. Discus throwing performances and medical classification of wheelchair athletes. Medicine and Science in Sports and Exercise, v. 31, n. 9, p. 1272-1279, 1999.
This lecture discusses introductory mechanics models and constitutive models for biomaterials. The objectives are to establish biomaterial constitutive models, determine biomechanical response to load, analyze prosthetic design, and estimate health status of living tissues under stress. The lecture covers introductory mechanics modeling including stress analysis, normal and pure bending. Methods of biomechanics including analytical, experimental, and numerical techniques like FEM are presented. Constitutive models including elastic behavior, Hooke's law, elastic constants, material anisotropy, orthotropy, transverse isotropy, and isotropy are discussed.
This study examined how varying ankle stiffness affects gait and muscle activity. Healthy individuals walked on a treadmill and overground with the anklebot applying different stiffnesses. Kinematic data and electromyography of four ankle muscles were measured. Results showed that increased stiffness reduced ankle inversion/eversion range of motion while decreased stiffness increased it. Soleus muscle activity significantly increased with decreased stiffness. Walking overground produced greater ankle and knee motions than treadmill walking. Understanding how ankle stiffness impacts gait can provide insights into locomotion.
This study aimed to compare quadriceps muscle activation and perceived exertion during the leg press and Smith machine squat exercises. The researchers measured muscle activation via EMG and perceived exertion ratings in athletes performing each exercise across a range of loads. They developed predictive equations to determine equivalent loads between exercises that produce the same muscle activation and perceived exertion. The muscle activation equation was less accurate due to individual variability, while the perceived exertion equation was more accurate as it reflects the overall exertion of each exercise rather than specific muscles. These equations provide a new tool to convert loads between exercises over a training period.
The new MTS cadaveric fixture was successfully manufactured to meet all design goals. It allows for 45 degrees of freedom in plantarflexion and dorsiflexion. The fixture can withstand loads up to 70kg and securely fix the ankle at a set angle without additional rotation during loading. The design also allows for easy exchange of cadaver limbs without complete disassembly.
Functional calibration is a technique to determine joint centers and axes by using marker trajectory data from movement trials rather than assumptions. For the hip, validation studies have found functional calibration performs about as well as regression equations in adults but regression equations outperform it in children with cerebral palsy. For the knee, functional calibration may be more repeatable than relying on marker placement since knee joint centers are difficult to identify visually. Overall, functional calibration of the knee is preferable to assumptions but it has not been easily implemented in commercial motion analysis software.
This study investigated hip muscle activation during common closed-chain rehabilitation exercises and running in runners. Electromyography was used to measure gluteus maximus and medius activation during a resisted hip external rotation exercise, single leg squat with trunk rotation, forward lunge with resisted abduction, and running. The forward lunge elicited the highest hip muscle activation, but activation was still substantially less than during running. While the exercises activated the hip muscles more than non-weight bearing exercises, there remains a disconnect between activation during exercises and running. Further research is needed to identify exercises that more closely mimic muscle demands during running.
This document provides an overview of biomechanics and its key concepts. It discusses how biomechanics studies the forces acting on the human body both internally from muscles and externally. It covers the history and academic backgrounds of biomechanics. The key concepts of kinematics and kinetics are explained, including concepts like displacement, velocity, acceleration, forces, torque, inertia, and momentum. Ground reaction forces and their analysis are also discussed.
This document summarizes a study that performed a 3D finite element analysis of the human femur bone. The analysis used a 3D CAD model of the femur obtained from medical scans. The model was meshed and material properties were assigned to different bone tissues. Nonlinear analyses were conducted to simulate loads on the femur during normal activities. Results were compared to previous studies to validate the model. The study found that cancellous bone tissue reduces stresses in the femur, with its absence causing stresses almost double the amount.
1. The document discusses developing an active assistive device using functional electrical stimulation (FES) to restore gait and promote movement rehabilitation for individuals with drop foot.
2. The technical objectives are to develop an FES actuator, an FES assistive platform, and to model the dynamics of electrically stimulated leg muscles affected by drop foot.
3. Preliminary trials show the FES system can correctly deliver stimulation and detect walking phases to correct drop foot, and modeling electrically stimulated muscles is important for advanced closed-loop control strategies.
This document summarizes a study that examined the effectiveness of retro walking (backward walking) in patients with chronic osteoarthritis of the knee. 30 patients with grade 3 knee osteoarthritis underwent 10 minutes of retro walking per day on an inclined treadmill for 10 days. Outcome measures assessed before and after the intervention included pain, stiffness, physical function via the WOMAC index, knee extension lag, dynamic balance, and parameters of forward walking. The results showed statistically significant improvements in all outcome measures following the retro walking intervention. The study concluded that retro walking is an effective approach for reducing symptoms and improving physical function in patients with osteoarthritis of the knee.
Adding stiffness to the foot through shoes and insoles during walking:
1. Decreased the amount of energy dissipated by the foot and increased the gear ratio of the foot-ankle complex.
2. Increased soleus muscle peak force production and decreased soleus fascicle shortening speed, altering the muscle's force-velocity behavior.
3. Despite changes to soleus muscle mechanics, increased whole-body metabolic cost, likely due to the added force demand placed on the plantar flexor muscles.
Tibial Insert Micromotion of Various Knee Devices-J of Knee surgery-2010 vol ...Safia Bhimji
This study developed a novel method to quantify rotational micromotion of modular tibial inserts under physiologic loading conditions. Testing was conducted on four total knee designs incorporating fluid environment and off-axis loading. Results showed that under walking and stair climbing loads, the full peripheral capture design experienced the most micromotion due to higher constraint, while the design with a rotational stabilizing island demonstrated the least motion. Micromotion increased with higher torques applied, with significant differences between designs.
This document summarizes a research paper presented at the 2015 Florida Conference on Recent Advances in Robotics. The paper discusses the design of an actively powered ankle-foot prosthetic for transtibial amputees. Currently available passive prosthetics do not provide enough power and torque throughout the gait cycle. The proposed design uses a series elastic actuator and uni-directional spring configuration to provide natural ankle motion at a lower cost than existing active prosthetics. Gait modeling and biomechanics data were used to simulate the design and compare its torque-angle curve to that of a natural ankle. The goal is for the design to reduce costs while improving mobility for transtibial amputees.
1. Researchers developed a neuromuscular control algorithm for a powered foot-ankle prosthesis based on the "winding filament hypothesis" (WFH) model of muscle contraction.
2. The WFH algorithm was tested during level walking, stair ascent, descent, and backwards walking. Results found the algorithm produced ankle torque profiles similar to an existing controller and human ankle during walking. It also matched profiles of able-bodied individuals during stair ascent with only ankle angle input.
3. Preliminary results found stair descent and backwards walking were limited by mechanical constraints of the prosthesis design. Overall, the bio-inspired WFH algorithm demonstrated more robust control of the prosthesis during different locomotion tasks
1) The study examined the effects of different heel lift heights (0.64 cm, 1.27 cm, 2.54 cm, 3.18 cm) on back squat performance and biomechanics in one male participant.
2) Preliminary results found that trunk lean was lowest at heel heights above 0.64 cm, suggesting weightlifting shoes with heels over 0.64 cm may reduce risk of back injury during squats.
3) Increasing heel height reduced ankle range of motion but increased peak ankle flexion, indicating a more vertical shank position conducive to proper squat form. Knee displacement did not significantly change with heel height.
The document is a cover sheet for a student submitting an assignment on static analysis of the ankle joint. It includes the student's personal details, module details, and a signed declaration stating the work is their own. The full assignment analyzes the ankle joint under single leg stance, single leg tip-toe stance, and with the foot suspended in mid-air using free body analysis to determine joint and muscle forces. It finds the joint reaction force is 1.8 times body weight for single leg stance and 2.5 times for tip-toe stance, and only 0.02 times body weight when suspended horizontally.
The document compares the effects of two surgical procedures - hamstring tendon lengthening and hamstring tendon transfer - on correcting crouch knee in children with cerebral palsy. Hamstring tendon lengthening improves knee extension but can increase pelvic tilt and decrease hip and knee power. Hamstring tendon transfer provides better kinematic and kinetic outcomes, increasing hip power and correcting pelvic tilt. Long-term studies show hamstring tendon transfer maintains improvements while lengthening results may deteriorate over time. Overall, hamstring tendon transfer appears to have more positive and lasting impacts on gait.
This document proposes two concepts: 1) A linearly actuated capsule endoscope mechanism to improve upon existing SMA actuated designs. It presents the conceptual design and mathematical modeling of this mechanism. 2) A simulated intestine environment that uses porcine intestine to test capsule designs in physiologically realistic conditions, including peristaltic contractions. It describes a proposed two degree of freedom system using weights and pulleys to actuate fresh intestine and mimic the forces inside the human small intestine. This would allow for improved in-vitro testing of capsule endoscope designs.
Effect of a_knee_ankle_foot_orthosis_on_knee.10huda alfatafta
The KAFO significantly reduced knee varus angle and the first peak of the external knee adduction moment during walking compared to no orthosis. It also reduced the knee adduction angular impulse during stair ascent compared to no orthosis. No significant differences were found between the custom and off-the-shelf knee valgus braces for any measures. The KAFO showed greater improvements in knee alignment and loading than the knee valgus braces for this individual with varus knee alignment.
This document discusses testing methods for total ankle and shoulder replacement implants. It notes that while testing methods are standardized for knee and hip implants, extremity implants like ankle and shoulder prosthetics have not been as extensively tested. The document outlines current testing procedures for these implants, which typically use modified knee or hip simulators. It discusses adapting simulators to test total ankle replacements, including setting up fixtures and inputting motion profiles. Testing procedures for total shoulder replacements are also described, such as using a hip simulator with custom fixtures to simulate shoulder motion. The document stresses the need for more research on in vivo joint motions and forces to further improve testing methods for these implants.
This study investigated the effect of knee joint angle on plantar flexor performance in resistance-trained and untrained men. Seventeen participants performed plantar flexion contractions at 90 degrees of knee flexion and 10 degrees of extension while torque was measured. There were no significant differences found in torque or rate of torque development between the knee positions or between the trained and untrained groups. The calibration process of the new dynamometer was found to be reliable.
Motor unit conduction velocity during sustained contraction of the vastus med...Nosrat hedayatpour
The aim of the study was to analyze motor unit conduction
velocity at varying force in the distal part of the
vastus medialis muscle during sustained contraction.
This document describes a study that used a dual spinal cord lesion paradigm in cats to investigate spinal locomotor plasticity after partial spinal cord injury (SCI). The paradigm involved first performing a hemisection at thoracic level T10, followed by a complete spinalization at T13 three weeks later. The findings showed that major changes occurred in the spinal locomotor circuitry between the two lesions. This suggests that plastic changes at the spinal cord level could contribute to recovery of locomotion after partial SCI. The dual lesion paradigm provides insights into how the spinal cord circuitry adapts following incomplete SCI when some descending pathways remain intact.
- The study examined the effects of gastrocnemius (calf muscle) fatigue on ankle joint kinetics during the squat jump in 5 trained male basketball players.
- Participants performed squat jumps before and after a calf raise protocol to induce gastrocnemius fatigue. Kinematic and kinetic data of the foot segment was analyzed.
- Results showed no significant difference in foot segment power between pre- and post-fatigue jumps, indicating that bi-articular muscle fatigue did not reduce segmental kinetics.
- The conclusion is that the gastrocnemius acts to transfer energy between segments rather than generate work, so its fatigue did not decrease ankle joint power during the squat jump.
Orthodontic movement using pulsating force induced peizoelctricityEdwardHAngle
Pulsating forces were applied to a patient's maxillary molar to induce piezoelectricity and accelerate tooth movement. Piezoelectricity generates charges when bone deforms under mechanical stress, inducing microcurrents that may stimulate bone remodeling. A device applied 30 oz peak (20 oz average) pulsating forces at 0.7 Hz to the test tooth, and 18 oz continuous force to the control tooth. Over 180 hours, the pulsed tooth moved 0.056 inches, more than the control. Mobility was also lower for the pulsed tooth. Precise measurements showed pulsating forces may achieve faster, less painful orthodontic tooth movement through piezoelectric effects.
The document discusses a study that tested whether a Constant Force Resistive Exercise Unit (CFREU) machine could maintain muscle strength over 10 weeks as effectively as free weights. 9 subjects were split into CFREU and free weight groups and performed leg exercises 3 times per week. The CFREU group saw significantly greater improvements in strength gains compared to the free weight group. The results suggest the CFREU machine was as effective or possibly more effective than free weights at maintaining muscle strength over time.
This study designed and tested a passive lower leg exoskeleton with a linear damper parallel to the ankle joint. The goal was to reduce joint torques during landing and make landing safer. A computational model was used to aid in device design. Subjects were tested dropping from 0.71m while wearing the exoskeleton with no, low, or high damping. Results showed the low damping decreased peak ankle torque by 12% and high damping decreased it by 30% compared to no damping, indicating the device reduced joint torques during landing.
Correlation between conventional clinical tests and a new movement assessment...Stavros Litsos
Correlation between conventional clinical tests and a new movement assessment battery - Bachelor thesis
Despite the complexity of movements performed in sports, physical examination is today done by conventional tests that evaluate joints and muscles individually (e.g. Smith press test, Figure1). Our study used a new movement assessment battery of 20 reach tests, which incorporates the complexity and diversity of natural human movements, taking into consideration that joints are interdependent in a movement and that the planes and sequences of a movement change during its performance. The purpose of this study was to determine whether or not there is a correlation between conventional mobility tests and the new assessment battery.
Seated Human Spine Response Prediction to Vertical Vibration via Artificial...abdulaziznaser2012
Harmonic vibration and shock can create health problem in long term especially in heavy duty machineries such as bus, truck, agricultural tractor and mine excavators. People are interested in remove this undesirable vibration by seat suspension systems. In design of seat suspension biodynamic models are necessary, and having that can help to researchers to predict human body behavior. Artificial neural network is a new computation method which is good for this purpose. In this study, an artificial neural network model was established based on experimental data to represent response of spine to the vertical vibration. The accuracy of this model is high (over 90%) in comparison to previous models like as lumped or finite elements models. Also, weight and height are considered in this model as inputs. Achieved bio dynamic ANN model can be used in other research purpose such as seat suspension optimization or adaptive seat suspension control systems.
The document summarizes an experiment that calculated and compared the joint moments at the hip and knee during high-bar and low-bar squatting using motion analysis and force plates. For high-bar squats, the knee moment was slightly higher than the hip moment. For low-bar squats, the moments were nearly equal. Ground reaction forces were more equally distributed between legs for high-bar squats. Future work could use more subjects and heavier loads to better detect differences between techniques.
1. ACTIVE CONTRIBUTIONS TO ANKLE-JOINT IMPEDANCE IN RATS
by
David Morrison
has been approved
April 2010
APPROVED (printed name, signature)
___________________________________,__________________________________, Director
___________________________________,_____________________________, Second Reader
___________________________________,______________________________, Third Reader
Honors Thesis Committee
ACCEPTED:
_______________________________________
Dean, the Barrett Honors College
2. Abstract
During legged locomotion, the mechanical properties of joints and legs (i.e. force,
impedance) are modulated to achieve task-level movement dynamics. A ‘tuned’
musculoskeletal system can contribute to stable locomotion. Joint and leg mechanics
reflect both passive properties and the properties of active muscle. However, the
sensitivity of joint-level impedance to different patterns of muscle activity have not been
well characterized in rodents. Therefore, we examined the relationship between muscle
activity and ankle joint impedance in the laboratory rat. In deeply anesthetized animals,
we stimulated the tibialis anterior (TA) and gastrocnemius (GAS) muscles with acute
implanted electrodes, using 40 Hz trains of 0.2 ms square wave pulses while the ankle
joint was attached to a position-controlled force transducer. The ankle was subject to
sinusoidal angular displacements at 5 frequencies between 1-10 Hz. TA and GAS were
stimulated using currents ranging from 0.0-5.0 mA for 3 seconds, with 30 seconds rest
periods between trials. Static forces were estimated by averaging transducer output
during the last 0.5 seconds, and impedance properties calculated from force changes and
phase relative to the position changes. Net ankle torque depended on the difference
between TA and GAS stimulation while ankle impedance depended on the sum of TA
and GAS stimulation. This behavior is predicted by the pre-stressed two-spring joint
model.
Introduction
Biologically-inspired SLIP-based (spring-loaded inverted pendulum) walking
mechanics have proven effective for stable, high performance locomotion in legged
robots while also simplifying the controller (Raibert 1986). These robots, such as the
3. “Big Dog” from Boston Dynamics, are capable of stabilizing large disturbances and
handling rough terrain. Despite these successes, the principles that motivated the design
of these robots and their control have not been applied to neuroprosthesis to restore
locomotion to individuals with spinal cord injury (SCI).
Tuning leg compliance allows SLIP-based robots to locomote over a variety of
terrains with simplified control. Given that joint torque is required to generate
movement, a key control objective for an impedance-based controller should be
generating a range of leg compliances for a given joint torque. Previous studies
examining the relationship between joint-level impedance and electrical stimulation have
only stimulated one muscle (Flaherty 1994). Therefore, this study intends to characterize
how extensor and flexor muscle activity can act to tune leg compliance in biological
neuromechanical systems by measuring ankle-joint impedance in rats, whose locomotion,
like humans, can be described by the SLIP model.
Towards this end, we tested the hypotheses that (i) ankle-joint impedance and (ii)
net torque at a given velocity are a linear function of the stimulation amplitude and
frequency delivered to the gastrocnemius (GAS) and tibialis anterior (TA) muscles.
Furthermore, we hypothesize that ankle net torque and impedance will increase linearly
with velocity.
We moved the ankle joint through a small sinusoidal movement using a range of
speeds (5 even intervals between 1-10 Hz) and stimulation patterns (Current: 5 even
intervals between 0.0-5.0 mA) to the TA and GAS muscles and collected force data.
4. Materials and Methods
Ankle joint impedance data were collected in four female Wistar rats (200-240 g)
aged 3 to 12 months over a period of six months. The rats were housed individually in a
university animal care facility with 12-hour light and dark cycles and provided access to
food and water ad libitum. The animals were treated in accordance with US Public
Health Service Guide for the Care and Use of Laboratory Animals and the Institutional
Animal Care and Use committees at ASU approved all surgical and experimental
protocols.
2.1 Experimental Setup
Designing a device capable of accurately measuring the impedance and providing
consistent force mapping of the electrically stimulated ankle-joint in the laboratory rat
was central to the success of this experiment. However, there are three primary problems
facing effective data collection in an impedance experiment. First, the potential for high-
frequency noise in impedance data collection is greater than in static force data collection
because the limb is moved through a small range of motion at high accelerations.
Second, the moments generated by muscles are dependent in part on force-length
properties of the muscles involved. Third, a predictable angular displacement of the
ankle must be achieved to calculate impedance. Therefore, our experimental device was
designed to reduce noise in the data, control the muscle length of the tibialis anterior
(TA) and gastrocnemius (GAS), and provide a predictable angular displacement at the
ankle.
In order to reduce noise in the impedance data, efforts were made to constrain the
ankle and knee and to create a stable scaffolding for the force transducer. For ankle
5. constraint, we custom-designed an adjustable foot grabber to anchor the foot shank to the
force lever. This confined movement to the saggital plane and gave the foot a firm
connection to the force collection device. To reduce knee movement, the ankle’s axis of
rotation was placed at the axis of rotation of the force transducer. Assuming a rigid foot
shank and sufficient inertia coming from the hip joint, vertical displacement of the knee
and rotation about the frontal axis of the knee was avoided. Finally, the force transducer
was screwed into a rigid scaffolding to avoid noise that could result from an unstable data
collection device.
Fig. 1. (a) Picture of the rat in the experimental rig. Rat is suspended in a sling while its ankle is
connected to the force transducer by a custom-designed adjustable foot grabber. (b) Shows experimental
rig without the rat. The metal dowel extending to the superior edge of the right-leg hole was intended to
constrain the knee
To control the length of the TA and GAS, the experimental rig was designed to
control the angle of the ankle and knee. The orientation of the ankle was effectively
controlled by the orientation of the adjustable force transducer arm. The knee angle
could be modified by adjusting the vertical position of the force transducer or the
horizontal position of the rat.
In order to produce a predictable angular displacement of the ankle, we placed the
ankle’s axis of rotation in line with the axis of rotation of the force transducer. Provided
the knee and tibial leg shank did not move during the trial, the angular displacement of
a b
6. the rat’s ankle was assumed to be the same as the displacement of the force transducer
(about 2o
).
2.2 Experimental Procedures
Rats were anesthetized using 2% isoflurane and 2% oxygen, enough to suppress
the toe pinch reflex. Once anesthetized, the rat’s right leg was shaved and cleaned using
isopropyl alcohol and iodine. The lower one-third of the tibia, medial malleolus,
calcaneus, and first metatarsal were marked in ink and photographed so that ankle angle
could be later determined (adapted from Varejao 2002).
The rat was then placed in the experimental rig (Fig. 1a) while still under
anesthesia. The rig attached the rat’s foot to a force transducer with a rotational
component (Aurora Scientific 305 C-LR), placing the malleolus at the center of rotation
of the force transducer, and the foot along the central axis of the force-transducer lever.
Once in the rig, sterilized acute intramuscular electrodes were inserted in the proximal
and distal third of the tibialis anterior (TA) and lateral gastrocnemius (GAS) (four in
total), the primary muscles for ankle dorsiflexion and plantarflexion.
The TA and GAS were subjected 3-s trials of monophasic cathodic stimulation
while the force transducer moved the ankle through a small sinusoidal range of motion,
with 30 s between stimulation trials. The stimulation train used a pulse duration of 200
μs at 40 Hz at an amplitude ranging from 0.0-5.0 mA in five even intervals. This range
of stimulation amplitude extended to about ten times over twitch threshold measures for
the TA and GAS, as measured by Jung et al. (2009). Twitch threshold was not measured
in this experiment. However, minimal recruitment threshold, detailed later, was tested
for. The force transducer moved the ankle at a frequency ranging from 1-10 Hz in five
7. even intervals. Single-muscle control trials (2.5 mA TA/0 mA GAS, 0 mA TA/2.5 mA
GAS at 5.5 Hz) were run every 20 trials to assess the role of fatigue and electrode
stability during the course of the experiment. There were 137 trials run each completed
experiment.
Two adjustments were made from initial trials (pre-11/09) and later trials (post
11/09)—the foot attachment device was changed and attempts were made to constrain the
knee (Fig. 1b), which was unconstrained in initial trials. The hip was unconstrained for
all trials. One experiment was captured by high-speed camera (Miro Phantom) at 100
frames per second to verify to effectiveness of the experimental device.
2.4 Data Analysis
Average static force
Average static force was measured each trial by averaging the force during the
last .5 s of the trial, thereby eliminating the force transient at the beginning of each trial
(Jung et. al, 2009). Trials were zeroed according to the passive trials, and therefore
average static force represents only the active contribution to force, ignoring gravity,
inertia, and passive viscoelastic characteristics of the ankle.
Impedance
Impedance was measured by using principal components analysis. The slope of
the first principal component describes the best fit to the in-phase relationship between
force and length. The slope of this line was taken to represent mechanical stiffness.
Impedance properties were also calculated by fitting a Voigt model to the following
equation.
θθθ kbJ ++
8. Controls
In order to improve the predictability of the average static force and impedance
data, a series of controls were run to account for the shortcomings in the stimulation
protocol for this experiment. Those controls are the following
i) Experiment by experiment comparison: Since the electrode placement varied from
experiment to experiment, specific parameters (e.g. the relationship between current
and force) also differed among experiments. For this reason, parameters were
calculated separately for each experimental session.
ii) Errant trials: Since the TA and GAS current was set manually in the 30 s in between
each trial, errors sometimes occurred, and were recorded in a notebook. These trials
were removed from the data
iii) Electrode stability: Since the electrodes could potentially move during the
experiment, electrode stability was assessed by comparing control trials across the
experiment (Fig. 2) and by examining recruitment curves in MATLab (Appendix Id).
Stable electrodes showed a consistent recruitment curve and stable force production
throughout the experiment. Experiments that showed electrode instability were not
used.
Fig. 2. Control trials for the GAS in
our 1/30 experiment. Reveals
electrode stability throughout the
experiment and a steady-state
fatigue setting in at the time of the
second control trial.
Gastrocnemius
0
0.1
0.2
0.3
0.4
0.5
0 2 4 6 8 10
Control trial number
Force
9. iv) Steady-state fatigue (App. Ic): Since 30 s may not have been enough time for
stimulated muscles to fully recover, we based the figures in our experiment off of
muscles in a predictable state of metabolic fatigue. Fig. 2 shows that this steady-state
fatigue sets by the second set of control trials, or twenty trials in. Therefore, the first
20 trials of each experiment were eliminated for mapping purposes.
v) Minimal recruitment threshold testing (App. Ib): Due to the minimally-invasive
methods used to implant the intramuscular electrodes, we were not able to place the
electrodes directly on the motor point of the target muscles. So, although our
stimulation levels were up to ten times above twitch threshold for the pulse frequency
we used (Jung 2009), we did not always see recruitment at our lowest stimulation
current, 1.2 mA. To test for minimal recruitment threshold, averaged single-muscle
forces at 1.2 mA were tested for statistical difference from passive trials. For
experiments that did not pass threshold testing, single-muscle trials at 1.2 mA or dual-
muscle trials containing a muscle at 1.2 mA were relabeled as passive.
vi) Recruitment of antagonistic muscles (App. Ia): single-muscle stimulation data were
examined for “force reversal”, or a reversal in the force from a demonstrated linear
trend to detect recruitment of antagonistic muscles. The only stimulation setting that
revealed this tendency was the TA at 5.0 mA. These trials were removed from
single-muscle average force data for the TA, but kept in all other data sets.
Fig. 3. Graph plotting net force against TA current.
5.0 mA stimulation condition shows a reversal in a
demonstrated trend in linear, owed to and termed
"antagonistic muscle recruitment"
Tibialis Anterior
-0.20
-0.15
-0.10
-0.05
0.00
0.0 1.0 2.0 3.0 4.0 5.0 6.0
TA current (mA)
Netforce
10. Results
(Note—Any data reported but not displayed here is displayed in the Appendix)
I) EXPERIMENTAL APPARATUS GOALS—ANALYSIS BY HIGH-SPEED
CAMERA
A high-speed camera was employed on one of our trials to assess whether or not
we successfully constrained the ankle and the knee. The camera revealed that at high
GAS stimulations, the ankle lifted very slightly out of line with the rotational axis of the
force transducer, revealing a degree of foot shank compliance that had not been
anticipated. It is possible that this could have resulted in up and down oscillation of the
knee, but further examination by software is needed to confirm this. The knee, however,
remained steady on most trials and oscillated back and forth on a few trials. The
relationship between this behavior and stimulation and perturbation parameters could not
be discerned. To determine actual ankle angular displacement, frames at the top and
bottom of the force transducer’s oscillation were selected and measured. Unfortunately,
the standard of error for the methods used (± 5o
) was considerably greater than the
displacement we were attempting to measure (about 2o
).
II) AVERAGE STATIC FORCE
Single-muscle
Current
Average force of the GAS and TA calculated from single-muscle stimulation
trials (Fig. 4) showed a strong linear correlation with stimulation amplitude (TA, r2
= .95,
.87, GAS, r2
= .92 for both). One set of GAS stimulation trials was better described by a
quadratic model (r2
= .96). In the TA trials, the 5.0 mA stimulation condition was
removed because of non-linearity due to antagonistic muscle recruitment (the complete
11. Gastrocnemius
y = 0.0709x + 0.0095
R
2
= 0.9232
0.00
0.10
0.20
0.30
0.40
0.50
0 2 4 6
GAS current (mA)
Netforce
Tibialis Anterior
y = -0.0312x + 0.0107
R
2
= 0.8686
-0.20
-0.15
-0.10
-0.05
0.00
0.05
0 1 2 3 4
TA current (mA)
Netforce
Fig. 4. Single-muscle stimulation trials plotting current amplitude against net ankle force. (a) is the GAS
while (b) is the TA, both well described by a linear relationship. (b) has the 5.0 mA stimulation condition
removed due to antagonistic recruitment.
data can be viewed in Appendix, Ia). For the GAS trials, the 1.2 mA stimulation
condition was removed because of non-linearity due to minimal threshold recruitment.
Trials here included all force transducer velocities.
Velocity
Force transducer velocity had no discernible relationship with average static
force. If differences existed, the data set was too small to detect the differences.
Dual-muscle
Current
Dual-muscle force (Fig. 5) was well predicted by a plane (r2
= .89, .84) based on
the difference between flexor and extensor stimulation.
F = -k1(TAstim) + k2(GASstim)
Where k1 and k2 are constants and TAstim and GASstim are current amplitudes.
III) IMPEDANCE
Single-muscle
Current
Current demonstrated a strong linear relationship with impedance (TA, r2
= .75, .
79, GAS, r2
= .86, .92) in single-muscle trials (Fig. 6). It is important to note that the TA
a b
12. Fig. 5. A 3-D plot of the TA and GAS
current against net ankle force. The
data is well-characterized by a plane,
reflecting to the linear nature of the
single-muscle stimulation trials. The
relationship between net force and TA
and GAS is described by the function of
the difference between the two control
variables. Figure does contain the 5.0
mA stimulation condition for the tibialis
anterior.
5.0 mA stimulation condition, excluded from average static force analysis due to
antagonistic muscle recruitment, was kept for this analysis. This is because of correlation
between impedance and net recruitment, and not net force. Additionally, it is important
to note that the GAS variance appears inflated due to the grouping of the 1.2 mA
stimulation condition as “passive.”
Tibialis Anterior
y = 0.0018x + 0.0079
R
2
= 0.7909
0
0.005
0.01
0.015
0.02
0.025
0 2 4 6
TA stim (mA)
Instantaneous
impedance
Gastrocnemius
y = 0.0112x + 0.0109
R
2
= 0.9197
0
0.01
0.02
0.03
0.04
0.05
0.06
0.07
0.08
0 1 2 3 4 5 6
GAS current (mA)
Impedance
Fig. 6. Graphs plotting TA (a) and GAS (b) current amplitude against instantaneous impedance. Both are
well characterized by linear relationships, including the tibialis anterior (a), which displayed antagonistic
recruitment at the 5.0 mA stimulation condition .
a b
13. Average static force
Correlation of average static force with impedance (Fig. 7) in single-muscle trials
ranged from weak in TA trials (r2
= .55, .21) to strong in GAS trials (r2
= .82, .94). This
reflects antagonist recruitment in the TA at high stimulation, and mostly agonist
recruitment for all GAS stimulation amplitudes. Like the current vs. impedance data, all
stimulation conditions were kept in the data set.
Velocity
A relationship between velocity and impedance could not be confirmed, although
the TA velocity vs. impedance graph seems to suggest a trend towards increasing
impedance with speed.
Dual muscle
Current vs. impedance
In dual-muscle trials, current vs. impedance data (Fig. 8) could be described by a
plane (r2
= .91, .85) based on the interaction of summed extensor and flexor stimulation.
F = k1(TAstim) + k2(GASstim)
Fig. 7. Graph plotting net force production
against impedance in the tibialis anterior. Weak
correlation coefficient is explained by
antagonistic recruitment, which decreases net
force production and increases instantaneous
impedance. Points deviating most from the line
to the top are exclusively from the 5.0 mA
stimulation condition.
Tibialis Anterior
y = -0.0668x + 0.0127
R
2
= 0.2122
0
0.005
0.01
0.015
0.02
0.025
0.03
0.035
-0.2 -0.15 -0.1 -0.05 0 0.05
Net force
Impedance
14. Fig. 8. A 3-D plot of the TA and GAS current
against instantaneous impedance. The data is
well described by a plane, reflecting the linear
nature of the single muscle trials. The
relationship between TA and GAS current and
instantaneous impedance is described by a sum
of the variables, whereas the relationship of the
said variables to net force was based upon the
difference between the variables.
Discussion
Our hypotheses that (i) ankle impedance and (ii) net ankle torque could be
described by linear functions of current to the ankle flexors (TA) and extensors (GAS) in
both single and dual-stimulation conditions were supported by the results of this study,
while the role of velocity in ankle impedance and net torque could not be verified. The
relationship between joint impedance and torque fit predictions described by a simple
pre-stressed two-spring model. The role of velocity matched expectations for average
static torque at the ankle, but impedance was not shown to respond as would be expected
by the force-velocity properties of the Hill model of muscle.
Ankle impedance, torque, and a pre-stressed two-spring model
A simple pre-stressed two-spring model can be used to predict joint torque and
impedance behavior. In work by Thales Souza (2009), a pre-stressed two-spring model
was successfully used to describe the behavior of passive properties in the human ankle.
Here, we adapted the same model to predict behavior in an active stimulation setting (Fig.
9).
15. Fig. 9. A drawing of the pre-stressed two-spring model
of the joint, used to predict torque and impedance
behavior at a two-muscle joint. F1 and F2 represent the
force generated by their respective springs (muscles). y
is the change in muscle length resulting from a position
change in the shank (foot shank) extending below the
fulcrum from T0 to T1 or T2, which reflect positions of
maximum and minimum torque.
In this figure, there are two springs (muscles) on either side of a "see-saw"
(muscle moment arms about a joint axis), while a third projection (in our case, the foot
shank) extends out below. If we ignore changes in l1 and l2,net torque T will be
proportional to the difference between the force generated by the right (F1)and left (F2)
springs.
T F1 – F2
This is intuitive and well recognized, and, indeed, our net torque model for dual-
stimulation trials follow this format, with F1 representing the GAS and F2 representing
the TA.
Impedance is less intuitive, and requires a longer derivation. The basic formula for
impedance, as described by Dudek (2006), is given by the equation,
Z = (Fmax-Fmin)/(xmax-xmin)
So, with respect to our model, let us consider a force maximum (T1) and force minimum
(T2), each occurring a distance ± x from a point T, directly resulting in a length change ± y
in the springs.. So, in our model, impedance will be given by
16. Imp = (T1 – T2)/2x
T1 and T2 will be given by the difference of the opposing springs at each displacement
T1 = F1' – F2' T2 = F1" – F2"
And the force of each spring at T1 and T2 will be given by
F1' = k1(x1 – y) F1" = k1(x1 + y)
F2' = k2(x2 + y) F2" = k2(x2 – y)
Substitute these into our impedance equation
Imp = [(F1' – F2') – (F1" – F2")]/2x
rearrange,
Imp = [(F1' – F1") + (F2" – F2')]/2x
substitute again and simplify
Imp = {[k1(x1 – y) – k1(x1 + y)] +[k2(x2 – y) – k2(x2 + y)]}/2y
Imp = –2y(k1 – k2)/2x
Assuming both lever arm displacement x and spring length change y are directly related
and constant from trial to trial, then
Imp = – (k1 – k2)
Imp = k1 + k2
and you have an equation which predicts that impedance in a two-muscle system will be
determined by the sum of the spring constants, which, in our case, is the stimulation
amplitude. This behavior describes the relationship seen in our 3D dual-muscle current
vs. impedance graphs (Fig. 8), and also describes the poor relationship observed between
static force and impedance in the single-muscle TA trials (Fig. 7), which displayed
antagonistic recruitment in our controls. However, with the same data in the impedance
17. vs. current graph, the TA yields linear behavior, further emphasizing the point that
impedance can be predicted by the summed stimulation, or recruitment about the joint.
Velocity, torque, and impedance
A relationship between velocity, torque, and impedance could not be discerned.
Through the lens of the Hill model of muscle, we would expect velocity and net torque in
our experiment to be unrelated considering our methods. In our experiment, we collected
average force data by oscillating the foot shank back and forth at a variety of speeds, and
Fig. 10. A force-velocity curve, used to describe the expected relationship between velocity, impedance,
and torque. Velocity was not expected to affect the average force values, since differences in eccentric and
concentric force production would be averaged out. The curve also predicts that impedance will increase
with respect to velocity, although this could not be verified in our data.
then averaged the last 0.5 s of data. On a force-velocity curve, what we did may have
looked like Fig. 10. Given the low velocities at work (maximal angular velocities were
100-400 times less than in vivo ankle joint velocities, calculated from position data in
Varejao, 2002), it is probable that the displacements here were traveling along the small,
linear region on either side of the isometric axis. Since the forces were averaged, any
effect of velocity on net torque would be averaged out.
However, force-velocity relationships do predict an effect on impedance. As
speeds increase, the difference between the maximum eccentric force exerted and lowest
concentric force exerted would grow. Additionally, this would create more velocity
18. dependent character, and increase our damping constant. The force-velocity data could
not be discerned from our impedance graphs, but it may be detectable in our
damping/stiffness data (not analyzed).
Implications of linear relationship between stimulation current and avg. force,
impedance
Since a plane could be fitted to dual-muscle stimulation trials to predict force
output (Fig. 5), there were a range of different flexor/extensor stimulation patterns that
yield the same net torque, as given by the intersection of an xy plane level with the torque
on the z axis with this plane. Take that line and impose it upon the dual-muscle
impedance graph, and you have the range of impedances possible for that torque. This
will be important so that individuals with this controller can adjust leg stiffness
depending on terrain, while still executing the necessary torque for locomotion.
Controller with adjustable leg stiffness still has much work to go before it is realized
(limb-level stiffness vs. joint level stiffness), but this experiment seems to suggest that a
key component of this puzzle may have a simple solution.
Conclusion
The results of this experiment indicate that while net ankle torque in the
laboratory rat is predicted by the difference between extensor and flexor stimulation,
ankle impedance is predicted by the summed stimulation (recruitment) about the joint.
These findings are supported by the pre-stressed two-spring joint model, which suggests
that, in spite of protocol limitations, the experiment succeeded in establishing general
relationships between impedance, torque, and flexor and extensor stimulation amplitude.
19. Limitations
In our experiment, our stimulation protocol and impedance device were sufficient
to characterize relationships between stimulation, torque, and impedance. However,
there are several issues with both our stimulation protocol and impedance device that
need to be addressed in order to get repeatable data for use in functional electrical
stimulation, which is the ultimate goal.
First, a couple of changes to the experimental rig need to be made in order to
control knee angle and introduce knee constraint. The revised rig ought to be as drawn
below.
Fig. 11. A rough schematic of a future rat-lever orientation, which will facilitate knee-angle control and
constraint.
In this configuration, a pin runs from the force transducer up to another lever, to which
the rat’s leg is fixed. The stimulated leg is now facing the user, making the angle of the
knee measurable, and moving the rat vertically from the lever gives a chance to introduce
knee constraint, perhaps by velcroing the thigh to a pummel horse. However, since the
force transducer will be less mobile (now attached to another fixed lever, the rat position
will now have to be adjustable up/down as well.
Next, the displacement of the ankle must be known. Although this could be
accomplished in the current rig, it requires writing computer software that tracks the
20. markings about the rat’s ankle. These displacements will need to be averaged and
considered for the impedance calculations.
Lastly, the stimulation protocol has to yield consistent results from trial to trial.
To do this, the rodent-model stimulation protocol outlined by Jung would be appropriate.
Following this protocol, it will also be possible to better characterize results at low-level
stimulations, which were not well-characterized here.
Future directions
The basic pre-stressed two-spring joint model outlined above has shown to be
useful for basic behavioral predictions at the ankle joint. It can be integrated with active
muscle force-length characteristics (variable x) and a pre-stressed two-spring model for
passive behavior to yield more realistic joint level behavior. This model should be
developed and tested experimentally.
21. REFERENCES
Dudek, D.M., and Full, R.J. (2006). Passive mechanical properties of legs from running
insects. The Journal of Experimental Biology, 209, 1502-1515. doi: 1.1242/jeb.02146
Ferrarin, M., and Pedotti, A. (2000). The relationship between electrical stimulus and
joint torque: a dynamic model. IEEE Transactions on Rehabilitation Engineering,
8(3), 342-352. Retrieved from Web of Science database.
Flaherty, B., Robinson, C., Agarwal, G. (1994, May). Determining appropriate models
for joint control using surface electrical stimulation of soleus in spinal cord-injury.
Medical and Biological Engineering & Computing, 32(3), 273-282.
Jung, R., Ichihara, K., Venkatasubramanian, G., and Abbas, J. (2009). Chronic
neuromuscular electrical stimulation of paralyzed hindlimbs in a rodent model.
Journal of Neuroscience Methods, 183, 241-254. Retrieved from Web of Science
database.
Lynch, C.L., and Popovic, M.R. (2008, Apr.). Functional electrical stimulation: closed-
loop control of induced muscle contractions. IEEE Control Systems Magazine, 40-5.
doi: 1.1109/MCS.2007.914689
Raibert, M.H. (1986). Legged robots. Communications of the ACM, 29(6), 499-514.
Retrieved from Web of Science database.
Souza, T.R., Fonseca, S.T., Goncalves, G.G., Ocarino, J.M., Mancini, M.C. (2009, Oct.).
Prestress revealed by passive co-tension at the ankle joint. Journal of Biomechanics,
42(14), 2374-2380. Retrieved from Web of Science database.
Varejao, A.S.P., Cabrita, A.M., Meek, M.F., Bulas-Cruz, J., Gabriel, R.C., Filipe, V.M.
(2002, Nov.). Motion of the foot and ankle during the stance phase in rats. Muscle &
Nerve, 26(5), 630-635. Retrieved from Web of Science database
22. APPENDIX
I.) CONTROLS
a. Antagonistic recruitment
b. GAS and TA threshold stimulation test
c. Electrode stability and steady state fatigue
d. Erratic recruitment
II.) AVERAGE STATIC FORCE
a. Single-muscle
i. Vs. current
ii. Vs. velocity
b. Dual-muscle vs. current
III.) IMPEDANCE
a. Single-muscle
i. Vs. current
ii. Vs. static force
iii. Vs. Velocity
b. Dual-muscle vs. current
I.) CONTROLS
a. Antagonistic recruitment
Antagonistic recuitment: TA, 1/30
-0.16
-0.14
-0.12
-0.1
-0.08
-0.06
-0.04
-0.02
0
0 1 2 3 4 5 6
TA current (mA)
Netforce
Series1
Antagonistic recruitment: TA, 10/23
y = -0.0156x - 0.0095
R2
= 0.4314
-0.20
-0.15
-0.10
-0.05
0.00
0.05
0 1 2 3 4 5 6
TA current (mA)
Netforce
Net force
Linear (Net force)
b. GAS and TA threshold stimulation test
1/30 Threshold stimulation test: GAS
-0.004
-0.002
0
0.002
0.004
0.006
1
Passive vs. 1.2 mA
Forceaverage
Passive
1.2 mA
1/30 Threshold stimulation test: TA
-0.09
-0.08
-0.07
-0.06
-0.05
-0.04
-0.03
-0.02
-0.01
0
0.01
1
Passive vs. 1.2 mA
Forceaverage
Passive
1.2 mA
23. 10/23 Threshold stimulation test: GAS
-0.008
-0.006
-0.004
-0.002
0
0.002
0.004
0.006
0.008
1
Passive vs 1.2 mA
Forceaverage
Passive
1.2 mA
10/23 Threshold stimulation test: TA
-0.02
-0.015
-0.01
-0.005
0
0.005
0.01
1
Passive vs 1.2 mA
Forceaverage
Passive
1.2 mA
c. Electrode stability and steady state fatigue
Gastrocnemius
0
0.1
0.2
0.3
0.4
0.5
0 2 4 6 8 10
Control trial number
Force
TA control trials
-0.1
-0.08
-0.06
-0.04
-0.02
0
0 2 4 6 8
Trial number
Force
TA 2.5 GAS 0.0
d. Erratic recruitment (Bad/Good)
II.) AVERAGE STATIC FORCE
a. Single-muscle
i. Vs. current
SM trial: TA (5.0 rmvd)
y = -0.0279x
R2
= 0.9537
-0.14
-0.12
-0.1
-0.08
-0.06
-0.04
-0.02
0
0.02
0 1 2 3 4
TA current (mA)
Netforce
Net force
Linear (Net force)
SM Trials: GAS
y = 0.0909x - 0.0152
R2
= 0.9226
y = 0.0134x2
+ 0.0317x + 0.0045
R2
= 0.9642
-0.1
0
0.1
0.2
0.3
0.4
0.5
0.6
0.7
0 2 4 6
GAS current (mA)
Netforce
Net Force
Linear (Net Force)
Poly. (Net Force)
24. Gastrocnemius
y = 0.0709x + 0.0095
R
2
= 0.9232
0.00
0.10
0.20
0.30
0.40
0.50
0 2 4 6
GAS current (mA)
Netforce
Tibialis Anterior
y = -0.0312x + 0.0107
R
2
= 0.8686
-0.20
-0.15
-0.10
-0.05
0.00
0.05
0 1 2 3 4
TA current (mA)
Netforce
ii. Vs. velocity
Effect of velocity on GAS force
-0.1
0
0.1
0.2
0.3
0.4
0.5
0.6
0.7
0 1 2 3 4 5 6
GAS current (mA)
Netforce
1.0 Hz
3.2 Hz
5.5 Hz
7.8 Hz
10.0 Hz
Effect of velocity on TA force production
-0.16
-0.14
-0.12
-0.1
-0.08
-0.06
-0.04
-0.02
0
0 1 2 3 4 5 6
TA current (mA)
Netforce
1.0 Hz
3.2 Hz
5.5 Hz
7.8 Hz
10.0 Hz
Effect of Velocity of TA Force
-0.16
-0.14
-0.12
-0.10
-0.08
-0.06
-0.04
-0.02
0.00
0.02
0 1 2 3 4 5 6
TA current (mA)
Netforce
1 Hz
3.2 Hz
5.5 Hz
7.8 Hz
10.0 Hz
Effect of Velocity of GAS force production
-0.10
0.00
0.10
0.20
0.30
0.40
0.50
0 1 2 3 4 5 6
GAS current (mA)
Netforce
1 Hz
3.2 Hz
5.5 Hz
7.8 Hz
10 Hz
b. Dual-muscle vs. current
25. III.) IMPEDANCE
a. Single-muscle
iii. Vs. current
Tibialis Anterior
y = 0.0018x + 0.0079
R
2
= 0.7909
0
0.005
0.01
0.015
0.02
0.025
0 2 4 6
TA stim (mA)
Instantaneous
impedance Gastrocnemius
y = 0.0112x + 0.0109
R
2
= 0.9197
0
0.01
0.02
0.03
0.04
0.05
0.06
0.07
0.08
0 1 2 3 4 5 6
GAS current (mA)
Impedance
TA SM trials: Current vs. Impedance
y = 0.003x + 0.0086
R2
= 0.7536
0.00
0.01
0.01
0.02
0.02
0.03
0.03
0.04
0 2 4 6
TA current (mA)
Impedance
Net force
Linear (Net force)
GAS SM Trials: Current vs. Impedance
y = 0.0074x + 0.0135
R2
= 0.8592
0.00
0.01
0.02
0.03
0.04
0.05
0.06
0 2 4 6
GAS current (mA)
Impedance
TA 0.0
Linear (TA 0.0)
iv. Vs. static force
TA SM Trials: Net Force vs. Impedance
y = -0.0619x + 0.0085
R2
= 0.5522
0
0.005
0.01
0.015
0.02
0.025
-0.2 -0.15 -0.1 -0.05 0 0.05
Net Force
Instantaneousimpedance
GAS 0.0
Linear (GAS 0.0)
GAS SM Trials: Net Force vs. Impedance
y = 0.1116x + 0.0148
R
2
= 0.8219
0
0.01
0.02
0.03
0.04
0.05
0.06
0.07
0.08
0.09
-0.2 0 0.2 0.4 0.6 0.8
Net force
Impedance
TA 0.0
Linear (TA 0.0)
Tibialis Anterior
y = -0.0668x + 0.0127
R
2
= 0.2122
0
0.005
0.01
0.015
0.02
0.025
0.03
0.035
-0.2 -0.15 -0.1 -0.05 0 0.05
Net force
Impedance
GAS SM Trials: Net Force vs. Impedance
y = 0.1049x + 0.0124
R2
= 0.9417
0
0.01
0.02
0.03
0.04
0.05
0.06
0.07
-0.2 0 0.2 0.4 0.6
Net force
Impedance
TA 0.0
Linear (TA 0.0)
26. v. Vs. velocity
Effect of velocity on TA impedance
y = 0.0016x + 0.0083
5.5Hz R2
= 0.513
y = 0.0006x + 0.0089
1.0Hz R2
= 0.7571
y = 0.0023x + 0.0071
3.2Hz R2
= 0.8941
y = 0.0018x + 0.0082
7.8Hz R2
= 0.8695
y = 0.0025x + 0.0053
10 Hz R2
= 0.8559
0
0.005
0.01
0.015
0.02
0.025
0 2 4 6
TA current (mA)
Impedance
1.0 Hz
3.2 Hz
5.5 Hz
10.0 Hz
7.8 Hz
Linear (5.5 Hz)
Linear (1.0 Hz)
Linear (3.2 Hz)
Linear (7.8 Hz)
Linear (10.0 Hz)
b. Dual-muscle vs. current