Force-velocity relation and contractility in striated muscles.

Mashima, Hidenobu

doi:10.2170/jjphysiol.34.1

Cited by 23 publications

(12 citation statements)

References 51 publications

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“…and (5)) are expressed as functions of dimensionless length (' M and' T ), velocity (ṽ M ), and force (normalized by f M o ) so they can be scaled to model a variety of human and animal muscles [23,37]. We have developed default force curves for the musculotendon model that have been fit to experimental data [41][42][43][44][45][46]. These curves can be adjusted to model muscle and tendon whose characteristics deviate from these default patterns.…”

Section: Musculotendon Modelsmentioning

confidence: 99%

See 1 more Smart Citation

Flexing Computational Muscle: Modeling and Simulation of Musculotendon Dynamics

Millard¹,

Uchida²,

Seth

et al. 2013

Journal of Biomechanical Engineering

514

479

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Muscle-driven simulations of human and animal motion are widely used to complement physical experiments for studying movement dynamics. Musculotendon models are an essential component of muscle-driven simulations, yet neither the computational speed nor the biological accuracy of the simulated forces has been adequately evaluated. Here we compare the speed and accuracy of three musculotendon models: two with an elastic tendon (an equilibrium model and a damped equilibrium model) and one with a rigid tendon. Our simulation benchmarks demonstrate that the equilibrium and damped equilibrium models produce similar force profiles but have different computational speeds. At low activation, the damped equilibrium model is 29 times faster than the equilibrium model when using an explicit integrator and 3 times faster when using an implicit integrator; at high activation, the two models have similar simulation speeds. In the special case of simulating a muscle with a short tendon, the rigid-tendon model produces forces that match those generated by the elastic-tendon models, but simulates 2-54 times faster when an explicit integrator is used and 6-31 times faster when an implicit integrator is used. The equilibrium, damped equilibrium, and rigid-tendon models reproduce forces generated by maximally-activated biological muscle with mean absolute errors less than 8.9%, 8.9%, and 20.9% of the maximum isometric muscle force, respectively. When compared to forces generated by submaximally-activated biological muscle, the forces produced by the equilibrium, damped equilibrium, and rigid-tendon models have mean absolute errors less than 16.2%, 16.4%, and 18.5%, respectively. To encourage further development of musculotendon models, we provide implementations of each of these models in OpenSim version 3.1 and benchmark data online, enabling others to reproduce our results and test their models of musculotendon dynamics.

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Section: Musculotendon Modelsmentioning

confidence: 99%

“…[41,42]. Data points in panels (c) and (d) denote experimental data for the force-length [43,44] and force-velocity [45,46] curves. The default curves used in the musculotendon models are shown in comparison to these experimental data.…”

Section: Musculotendon Modelsmentioning

confidence: 99%

Flexing Computational Muscle: Modeling and Simulation of Musculotendon Dynamics

Millard¹,

Uchida²,

Seth

et al. 2013

Journal of Biomechanical Engineering

514

479

View full text Add to dashboard Cite

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“…The order of the ramp protocol was randomized. All experiments were conducted at a constant temperature of 12 • C ± 0.1 • C. At this temperature, the fibers proved very stable and able to withstand active ramp protocols over an extended period of time as well as prolonged activations (Ranatunga, 1982(Ranatunga, , 1984Bottinelli et al, 1996;Tomalka et al, 2017).…”

Section: Experimental Protocolmentioning

confidence: 99%

Cross-Bridges and Sarcomeric Non-cross-bridge Structures Contribute to Increased Work in Stretch-Shortening Cycles

et al. 2020

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Stretch-shortening cycles (SSCs) refer to the muscle action when an active muscle stretch is immediately followed by active muscle shortening. This combination of eccentric and concentric contractions is the most important type of daily muscle action and plays a significant role in natural locomotion such as walking, running or jumping. SSCs are used in human and animal movements especially when a high movement speed or economy is required. A key feature of SSCs is the increase in muscular force and work during the concentric phase of a SSC by more than 50% compared with concentric muscle actions without prior stretch (SSC-effect). This improved muscle capability is related to various mechanisms, including pre-activation, stretch-reflex responses and elastic recoil from serial elastic tissues. Moreover, it is assumed that a significant contribution to enhanced muscle capability lies in the sarcomeres itself. Thus, we investigated the force output and work produced by single skinned fibers of rat soleus muscles during and after ramp contractions at a constant velocity. Shortening, lengthening, and SSCs were performed under physiological boundary conditions with 85% of the maximum shortening velocity and stretch-shortening magnitudes of 18% of the optimum muscle length. The different contributions of cross-bridge (XB) and non-cross-bridge (non-XB) structures to the total muscle force were identified by using Blebbistatin. The experiments revealed three main results: (i) partial detachment of XBs during the eccentric phase of a SSC, (ii) significantly enhanced forces and mechanical work during the concentric phase of SSCs compared with shortening contractions with and without XB-inhibition, and (iii) no residual force depression after SSCs. The results obtained by administering Blebbistatin propose a titin-actin interaction that depends on XB-binding or active XB-based force production. The findings of this study further suggest that enhanced forces generated during the active lengthening phase of SSCs persist during the subsequent shortening phase, thereby contributing to enhanced

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“…From these the maximum velocity of unloaded muscle fibre or contractile element, V, , , is one of the most widely studied parameters (Mason et al 1970, Parmley et al 1972, Grossman et al 1972, Urschel et al 1980). Correspondence Even if its specificity as an index of contractility is questioned both on a theoretical and experimental basis (Pollack 1970, Brady 1979, Mashima 1984, only few, if any, other indices of contractility based on the fundamental principles of muscle contraction are currently available for intact heart examinations. O n the other hand, in a recent study V, , , has been suggested to be a valid parameter of contractility on the level of sarcomere (Daniels et al 1984).…”

mentioning

confidence: 99%

The automatic computation of pressure‐derived maximal shortening velocity (V_max) of the unloaded contractile element in the intact canine heart left ventricle

Kettunen

Timisjärvi

Kouvalainen

et al. 1986

Acta Physiologica Scandinavica

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Estimation of the maximum velocity (Vmax) of the contractile element of the intact left ventricular wall muscle demands extrapolation of the force-velocity curve to zero load. The present paper describes our on-line computation system for measuring and analysing pressure derived Vmax using both linear (Vmax-lin) and exponential (Vmax-exp) extrapolation methods. The developed pressure during isovolumetric phase of systole was used as an equivalent of the force. Testing on anaesthetized artificially ventilated dogs showed the exponential function to fit pressure-velocity data better than the straight line did. The Vmax-exp attained 15-35% greater values than Vmax-lin, but both responded almost equally when considered on the basis of linear regression analysis (r = 0.991, n = 725). Changes of contractility caused by i.v. infusion of isoproterenol, calcium chloride or propranolol were practically similar when assessed by either method of Vmax computation, or by dP/dtmax. Volume loading by dextran infusion increased not only dP/dtmax, by 33 +/- 13%, but also Vmax, up to 24 +/-. When arterial pressure was raised by phenylephrine infusion, or heart rate by atrial pacing, dP/dtmax increased significantly while Vmax remained unaltered. Hence, the linear and exponential dP/dtmax increased significantly while Vmax remained unaltered. Hence, the linear and exponential extrapolation procedures provided comparable values for Vmax, but the linear one due to its simplicity is more suited for on-line computation. The Vmax thus obtained is, however, not independent of the changes in preload.

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Force-velocity relation and contractility in striated muscles.

Cited by 23 publications

References 51 publications

Flexing Computational Muscle: Modeling and Simulation of Musculotendon Dynamics

Flexing Computational Muscle: Modeling and Simulation of Musculotendon Dynamics

Cross-Bridges and Sarcomeric Non-cross-bridge Structures Contribute to Increased Work in Stretch-Shortening Cycles

The automatic computation of pressure‐derived maximal shortening velocity (V_max) of the unloaded contractile element in the intact canine heart left ventricle

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Force-velocity relation and contractility in striated muscles.

Cited by 23 publications

References 51 publications

Flexing Computational Muscle: Modeling and Simulation of Musculotendon Dynamics

Flexing Computational Muscle: Modeling and Simulation of Musculotendon Dynamics

Cross-Bridges and Sarcomeric Non-cross-bridge Structures Contribute to Increased Work in Stretch-Shortening Cycles

The automatic computation of pressure‐derived maximal shortening velocity (Vmax) of the unloaded contractile element in the intact canine heart left ventricle

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Product

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The automatic computation of pressure‐derived maximal shortening velocity (V_max) of the unloaded contractile element in the intact canine heart left ventricle