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Modelling the maximum voluntary joint torque/angular velocity relationship in human movement

TLDR
The maximum voluntary knee extensor torque that can be exerted may be modelled accurately as the product of functions defining the maximum torque and the maximum voluntary activation level.
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This article is published in Journal of Biomechanics.The article was published on 2006-01-01 and is currently open access. It has received 101 citations till now. The article focuses on the topics: Torque & Angular velocity.

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Citations
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Journal ArticleDOI

Maximum voluntary joint torque as a function of joint angle and angular velocity: Model development and application to the lower limb

TL;DR: This model provides an efficient method by which strength variations with joint angle and angular velocity may be incorporated into comparisons between joint torques calculated by inverse dynamics and the maximum available joint torque.
Journal ArticleDOI

Constraints on the complete optimization of human motion.

TL;DR: It is suggested that it is currently not possible to identify the complete optimal solution for a given motor activity.
Journal ArticleDOI

On the Shape of the Force-Velocity Relationship in Skeletal Muscles: The Linear, the Hyperbolic, and the Double-Hyperbolic

TL;DR: Current evidence suggests that the F-V relation in skeletal muscles follows a double-hyperbolic pattern, with a breakpoint located at very high forces/low velocities, which may be a direct consequence of the kinetic properties of myofilament cross-bridge formation.
Journal ArticleDOI

Evaluation of a torque-driven model of jumping for height

TL;DR: In this paper, an 8-segment torque-driven subject-specific computer simulation model of the takeoff phase in running jumps for height was used to evaluate an optimization procedure to evaluate a running jump performed by an elite male high jumper.
References
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Journal ArticleDOI

The heat of shortening and the dynamic constants of muscle

TL;DR: In this article, a more accurate and rapid technique for muscle heat measurement was proposed, and some astonishingly simple and accurate relations have been found, which determine the effect of load on speed of shortening, allow the form of the isometric contraction to be predicted, and are the basis of the so-called "visco-elasticity" of skeletal muscle.
Book

Simulated annealing

Journal ArticleDOI

Minimizing multimodal functions of continuous variables with the “simulated annealing” algorithm—Corrigenda for this article is available here

TL;DR: A new global optimization algorithm for functions of continuous variables is presented, derived from the “Simulated Annealing” algorithm recently introduced in combinatorial optimization, which is quite costly in terms of function evaluations, but its cost can be predicted in advance, depending only slightly on the starting point.
Journal ArticleDOI

Muscle activation during maximal voluntary eccentric and concentric knee extension

TL;DR: The data suggest that under certain high-tension loading conditions (especially during eccentric muscle actions), the neural drive to the agonist muscles was reduced, despite maximal voluntary effort, to protect the musculoskeletal system from an injury that could result if the muscle was to become fully activated under these conditions.
Related Papers (5)
Frequently Asked Questions (19)
Q1. What are the contributions in "Modelling the maximum voluntary joint torque / angular velocity relationship in human movement" ?

The aim of this study was to model this “ differential activation ” in order to calculate the maximum voluntary knee extensor torque as a function of knee angular velocity. 

The variation in maximum muscle force with the rate of change of muscle length is a fundamental characteristic of skeletal muscle. 

A torque model was developed using a four parameter function to express maximum joint torque at full activation as a function of joint angular velocity. 

In the concentric phase tetanic muscle force decreases hyperbolically with increasing speed of shortening to approach zero at maximum shortening velocity (Hill, 1938). 

In the eccentric phase maximum muscle force increases rapidly to around 1.5 times the isometric value with increasing speed of lengthening and then plateaus for higher velocities (Harry et al., 1990). 

The accuracy of such simulations is dependent upon realistic torques being generated by the muscle representations and this is the focus of the present paper. 

Establishing appropriate lower and upper bounds for ωmax would offset the lack of high velocity concentric torque data to some extent. 

They found that EMG activity was lower under eccentric loading than concentric loading and did not appear to change across eccentric velocities, while EMG increased with increasing concentric velocities. 

There were only two free parameters as T0 was set equal to the average of the torques corresponding to crank velocities of ± 50os-1 and again Tmax was fixed at 1.5 times the value of T0 . 

The hyperbola representing the concentric phase was a rotational equivalent of the classic hyperbola of Hill (1938) and an inverted rectangular hyperbola was used to represent the eccentric phase. 

Consequently at a joint angular velocity of zero the activation level of Subject 2 was 0.90 compared to a level of 0.78 for Subject 1. 

This resulted in a set of 18 “maximal” joint torques and joint angular velocities that were less noisy than the original maximum torque values and were independent of joint angle. 

As a consequence the seven parameter function of Subject 1 shows a pronounced plateau for low concentric velocities whereas that of Subject 2 is closer to a hyperbola with concave curvature for all concentric velocities (Figures 3a, 4a). 

In order to estimate the likely error in each parameter the torque deviations from the seven parameter fit were calculated by subtracting the fitted torque value from the maximal torque at each angular velocity. 

Thus the seven parameter function may be used for both maximal and submaximal activities so long as there is a basis for generating an appropriate relative activation profile. 

These deviations were then added to the fitted torque values at the corresponding angular velocities to generate eight new maximal torque / angular velocity data sets which were used to produce eight new seven parameter fits. 

The three data points corresponding to high concentric velocities in Figure 3a suggest that a higher value for ωmax might be more appropriate and that setting a higher lower bound in the optimisation procedure might reduce this problem. 

In the eccentric phase the relationship between T and ω was given by the rectangular hyperbola:max eT )( ET + ω−ω = (if ω ≤ 0) (3)where: )( . kT)TT(cmaxcmax00max e ω+ωωω− =ω , e0max )TT(E ω−−= and k = ratio of the slopes of theeccentric and concentric functions at ω = 

For movements which require primarily concentric muscle action such as squat jumps (van Soest et al., 1993) there will be maximal activation only for higher concentric velocities and the Hill relationship may be adequate providing appropriate muscle parameters are used.