Skeletal muscle contraction. The thorough definition of the contractile event requires both load acceleration and load mass to be known
© Grazi and Pozzati; licensee BioMed Central Ltd. 2010
Received: 12 March 2010
Accepted: 18 June 2010
Published: 18 June 2010
The scope of this work is to show that the correct and complete definition of the system of muscle contraction requires the knowledge of both the mass and the acceleration of the load.
The aim is achieved by making use of a model of muscle contraction that operates into two phases. The first phase considers the effects of the power stroke in the absence of any hindrance. In the second phase viscous hindrance is introduced to match the experimental speed and yield of the contraction. It is shown that, at constant force of the load, changing load acceleration changes the time course of the pre-steady state of myofibril contraction. The decrease of the acceleration of the load from 9.8 m.s-2 to 1 m.s-2 increases the time length of the pre-steady state of the contraction from a few microseconds to many hundreds of microseconds and decreases the stiffness of the active fibre.
We urge that in the study of muscle contraction both the mass and the acceleration of the load are specified.
Thus, at constant F2, changing m2, changes the driving acceleration, i.e. changes the time course of the pre-steady state of the contraction. This means that the characterization of muscle contraction requires the load to be defined both by its mass and by its acceleration.
A second question is whether two loads, characterized by the same force F2, by two different couples (m2' a2') and (m2" a2") induce the same or a different response of the muscle (power output, force and speed of contraction). In this work we try to answer the question by applying a model of muscle contraction [1, 2] to the data of He et al. . In short the model relates the experimental power output to the experimental speed of contraction by means of a constant, 1/k (s-1), that expresses the hindrance of the contractile system. As a matter of fact the actual mass and the actual acceleration of the load are unknown to He et al.  so we test different couples of these two parameters while keeping constant the experimental power output and the experimental speed of contraction. The result is that by decreasing the acceleration of the load the value of the constant, 1/k (s-1), decreases and the time length of the pre-steady state of the contraction increases. We conclude that a rigorous definition of muscle contraction requires the acceleration of the load to be known and that, at constant load force, the decrease of the acceleration of the load slows down the pre-steady state of the contraction.
For the convenience of the reader the model is summarized below together with an abbreviation section (Appendix 1).
The model operates into two phases. The first phase considers the effects of the power stroke in the absence of any hindrance, the result being a uniformly accelerated motion. In the second phase viscous hindrance is introduced to match the experimental speed (i.e. a uniform rate) and the experimental yield of the contraction. In short the model relates the experimental power output to the experimental speed of contraction by means of a constant 1/k (s-1) that expresses the hindrance of the contractile system. Data on the force - velocity curve and on the relative power outputs were taken from He et al. . In the studies of He et al.  the isotonic contraction of rabbit skeletal muscle fibres was initiated by releasing ATP via a laser pulse from caged ATP and maintaining a constant velocity of shortening. In our model, on the contrary, muscle fibres are subjected to the load concomitantly with the activation and, after a pre-steady state, attain the isotonic contraction. Our aim is not to mimic the experiment of He et al.  but to feed their stationary data to our model.
We are dealing with different conditions but we see no reason why the experimental data could not fit to our model.
where, ρ = 1.035 g.cm-3, is the density of frog sartorius muscle ; r = 25 nm, is the distance between the centers of two adjacent actin filaments; ls = 2.7 μm is the sarcomere length; 300, molecules in the tick filament; MWM, is the molecular mass of myosin, 520 kD , N, is the Avogadro's number.
F1, is the average force over the distance l at the beginning of the contraction and, l, is the sliding of thick and thin filaments past each other, provided that EATP is used up completely and that the movement occurs without hindrance.
where, aL, is the acceleration associated with the load.
The force generated by a single power stroke is, in general, much lower than F2 so that it is necessary to sum up the energy delivered by the power strokes. This is possible if the frequency of the power strokes exceeds a given level, so that not all the energy provided by a power stroke is used up before the following power stroke, performed by another attached cross-bridge, occurs. This condition is fulfilled if the space, l A , travelled in the time between two power strokes, is lower than, l = EATP/F1, so that the fraction left of the original energy, 1- |l A |/l, adds to the energy provided by the subsequent power stroke. To summarize, l, is constant, its value is defined by eqn. a3, where the value of F1 is that at the starting of the experiment. In the pre-steady state of the contraction both F1 and l A change. At the steady state both F1 and l A are constant the driving acceleration, ad, approaches zero. Thus bound cross-bridges make a translation of |l A | < l whose value changes with the progress of the contraction and becomes fairly constant at the steady state
where, tAT, is the time between the power strokes.
Thus at any cycle the energy available, the contractile force and the driving acceleration change. In the first cycle, ET = EATP and v = 0.
The hypothesis is thus made that the energy, EATP, is delivered uniformly in the period tAT.
The velocity of contraction and the ATPase rate constant as a function of the load
Contraction velocity, vvnm.s-1.hsl-1
ATPase rate constant, s-1
Where, n, is the number of thick filaments in the half sarcomere, 300 is the number of the myosin heads in the half sarcomere, 0.96 is the fraction of myosin heads involved in the process and, kAT, is the mean ATPase rate constant which changes with the load .
The first step was operated in the absence of viscous hindrance and in the presence of an external load. In this step the value of the initial F1 was determined. Initial F1 is the threshold force that must be reached by the cross-bridges in order to be able to prepare the contraction. If the threshold force is not reached the system does not reach a positive driving acceleration and the contraction does not start. The right value of the initial F1, in a given condition, is obtained by trials, starting from a low value of F1 and continuing with small increments until the threshold value is reached that initiates the contraction. Although laborious the procedure is quite accurate.
In the second step, once the value of the initial F1 has been found, the value of, k (s), capable to equate the calculated velocity, vV, to the observed velocity, vO, is determined. Also in this case the search for, k (s), is made by trials. The program is stopped at vV/vO < 1.001.
In the study of muscle contraction load and muscle are usually treated as a single system. It may therefore appear a non-sense to talk about the acceleration of the load. In our model, however, load and muscle are considered as separate systems at the beginning and merge as a single system at the moment of the contraction. Under these circumstances the effects of the changes of the acceleration of the load on the contraction can be traced.
Effect of the acceleration of the load on the initial F1
In this section it is shown that, at parity of the force F2, the decrease of the acceleration of the load (and the corresponding increase of the mass) decreases the initial F1 required to start the contraction.
where, sS, is the sarcomere cross-section and, P0, is the isometric tension per unit area.
where, F2, is the force generated by the load.
where, g, is the acceleration of gravity.
Effect of the mass and of the acceleration of the load on initial F1
Initial F1, pN (1)
Initial F1, pN (2)
Effect of the acceleration of the load on the pre-steady state
In this section it is shown that the decrease of the acceleration of the load (at parity of load force) delays the pre-steady state and decreases the apparent viscosity coefficient, 1/k (s-1).
load acceleration, 9.8 m.s-2; load mass, 6.277 10-9 kg. Under these conditions, to fit the P/P0, the ATPase rate and the steady rate of shortening of He et al. , F1 was adjusted to 3584 pN and k to 8.32 10-5 s.
load acceleration, 0.5158 m.s-2; load mass, 1.259 10-7 kg. Under these conditions, to fit the P/P0, the ATPase rate and the steady rate of shortening of He et al. , F1 was adjusted to 230 pN and k to 2.24 10-4 s.
Please notice that the product of the acceleration and of the load mass is exactly the same in the two cases.
Effects of the acceleration of the load on the initial stiffness of the active half sarcomere
In this section we show that the decrease of the acceleration of the load (at parity of load force) decreases the apparent stiffness of the half sarcomere.
The parameter k (s), related to the viscosity of the structure, is an important feature of the model. The viscosity originates from the interplay between water activity and the stiffness of the structure. In fact the water activity coefficient is altered by sarcomere stretching, by the cross-bridges attaching and detaching , by the formation of the network of filaments . In turn viscosity is related to water activity since any time water activity decreases (or protein osmotic pressure increases) viscosity (and stiffness) increase. Thus muscle contraction is ruled by the interplay between water activity, viscosity and stiffness .
As it was shown in our previous work  the model also predicts a cooperative behaviour between the elementary sarcomere units. This was tested by comparing the behaviour of virtual sarcomere composed by a different number of elementary units. It was found that the value of the initial F1 required to initiate the contraction increased with the decrease of the number of the elementary units. This suggests that the elementary units are cooperating to overcome the load.
When presenting our model for the first time [1, 2] we selected the acceleration of gravity as the load acceleration and the load was changed by changing the mass. As a result the pre-steady state of the contraction was estimated to be quite rapid, a few microseconds, thus beyond the possibility of an experimental check. We observe now that, at constant load, the time length of the pre-steady state of the contraction increases significantly with the decrease of the acceleration of the load. This time length may reach the sub-millisecond, thus allowing the prediction of our model to be tested experimentally.
He et al. , by measuring the steady rate of contraction and the accompanying ATPase rate, provided the values of the parameters (load, velocity of the isotonic contraction, power output) to be fed to our model. From those data and on the basis of our model we reconstructed the pre steady state of muscle contraction even though, as we stated already, our model and the muscle fibres of the experiment of He et al.  operate quite differently. We tacitly assumed the release of ATP from caged ATP to be immediate. The advantage of this choice is to test directly the time of reaction of the contractile apparatus, a time that appears much faster that it is usually believed. Being more realistic i.e. simulating a gradient of ATP concentration would make more complex the writing of the model but would not alter the main conclusion of this work: namely that changing the acceleration of the load changes the initial F1 and the time course of the pre-steady state of myofibril contraction.
where the relevance of the acceleration of the load is recognized.
The difference between our view and the classic view is partly explained by the fact that our model tests directly the contractile apparatus while experimental tests are "contaminated" by accessory compliances that slow down the phenomenon. We report small (0.04 - 0.784 nm) and very fast (40 - 131 μs) stretching of the half sarcomere. Stretching is mostly the result of the visco-elastic distortion of the lever arm plus the compliance of the thick and thin filaments. Stretching is not an all or none but a relatively continuous event. So it should not be surprising that the smaller the distortion the faster the event. Our experimental settings are presently unable to record extremely short stretches. This does not means that our model is wrong.
Many reports show that the ATPase rate depends on the load [3, 17–19]. No information however is available on the effect of the change of the mass-acceleration couple at constant load. Tentatively we assumed that, at constant load, muscle power output (i.e. the ATPase rate constant) and the steady rate of shortening do not change with the acceleration associated to the load. Nevertheless, owing to the very fine regulation of muscle contraction, we do not exclude that a change may occur. Perhaps the introduction of the acceleration of the load in the pre-steady could help unraveling some debated questions on muscle mechanism. It is clear however that to achieve this result the model should be confronted with experiments specifically addressed to those questions. It is sometime recognized, explicitly or implicitly, that, during acceleration, the load on the contracting muscle continuously changes because, as the mass accelerates, the force produced by the muscles changes due to force-velocity and length-tension effects. The changing muscle force in turn affects the acceleration of the load [20–22].
In general, however, in the studies on myofibril contraction very precise measurements of the force-length relationship are performed but no explicit mention of the value of the acceleration associated to the load is provided. Since the time length of the pre-steady state of the contraction is determined by the acceleration associated to the load we urge this parameter to be explicitly mentioned in the experiments.
In the studies on myofibril contraction very precise measurements of the force-length relationship are performed without mentioning the value of the acceleration associated to the load.
According to our model, with the decrease of this acceleration the time length of the pre-steady state of the contraction increases up to the millisecond thus allowing our predictions to be tested experimentally.
Furthermore both the initial F1 (the initial force needed to start the contraction) and the initial stiffness of the active myofibril decrease with the decrease of the acceleration of the load. Thus, at constant load, the decrease of the acceleration induces the decrease of the stiffness.
All these features strongly suggest that the value of the acceleration of the load should be mentioned in all the experiments on muscle contraction.
Appendix 1 - Abbreviations
acceleration of the load
free energy of hydrolisis of one molecule of ATP in muscle
energy left after the (i-1)th cycle
total energy available in the Ith cycle
force of the half sarcomere
- F2 :
force of the load
number of the cycles
- iVV :
increment of velocity in the time tAT
l = EATP/initial F1
l A space travelled in the absence of hindrance in the time between two power strokes
- lS :
l V space travelled in the presence of hindrance in the time between two power strokes
- 1/k (s-1) :
hindrance of the contractile system
- m1 :
mass of the mobile part of the half sarcomere
- m2 :
mass of the load
= 2000 number of the elementary units
tension per unit area
- P0 :
isometric tension per unit area
- r :
= 25 nm distance between the centers of two adjacent actin filaments
- sS :
- stv :
total space travelled in the presence of hindrnce
time between the power strokes
- tI :
time length of the cycles
- v :
velocity in the absence of hindrance
- vV :
velocity in the presence of hindrance
This work was supported by grants of the Ferrara University and of the Fondazione della Cassa di Risparmio di Ferrara.
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