Muscles



Fig. 5.1
a Skeletal, b cardiac, and c smooth muscle cells. (From [67 ])



We will learn how muscles work and develop macroscopic, microscopic, and nanoscopic models of them [50, 52, 53, 60, 70, 82]. We will also re-examine some of the assumptions we made in earlier chapters involving muscle forces. In the next chapter we will learn more about how energy is used in muscles.


5.1 Skeletal Muscles in the Body


Figure 1.​8 shows many of the main skeletal muscles in the body.

Skeletal muscles account for $${\sim }43\%$$ of the typical body mass, or $$\sim $$30 kg of a 70 kg person. At rest, they use $$\sim $$18% of the body energy consumption rate (which is called the basal metabolic rate or BMR); they use much more during activities, such as motion. Of the total energy “burned” by skeletal muscle, only $$\sim $$25% is used for work, and this is the muscular efficiency. The other $$\sim $$75% is released as heat. (This inefficiency of the body does have a positive purpose—it is a consistent and very important source of body heat.)

The maximum muscle force $$F_{\mathrm {M}}$$ or tension T that a muscle can develop is $$ k_{\mathrm {M}}$$PCA, where PCA is the physiological cross-sectional area of the muscle. The range of the maximum values of $$ k_{\mathrm {M}}$$ is 20–100 N/cm$$^{2}$$ during isometric (constant length) conditions; the larger values are for muscles with the pinnate fiber structure that is described below. (See Fig. 5.46 below and Problem 5.2.) In the quadriceps, the forces are up to $$\sim $$70 N/cm $$^{2}$$ during running and jumping and $$\sim $$100 N/cm$$^{2}$$ under isometric conditions. We will discuss this more later.

Countermovements before sudden motion are known to increase athletic performance [63]. Quickly squatting before squat jumps leads to higher jumps. It is not known whether this pre-stretching allows more time for muscles to become active, optimizes sarcomere lengths and forces (see below), induces the activation of other muscles, or stores elastic energy in tendons, ligaments or the elastic components of muscles. This countermovement may be the reason why balls can be thrown faster with a windup during baseball pitching, and this might be due to the storage and subsequent release of elastic energy.

Sometimes the estimate that a maximum of $$\sim $$250–500 W are generated per kg of active muscle for isotonic conditions (constant tension) is used in calculations of motion (and $$1.75\times $$ this with pre-stretching) [13, 25, 78, 79]. Because this is averaged over the areas, lengths and speeds of the muscles that cause motion, we will usually use the muscle force per unit area in analysis.

Many muscles that cross the hip, knee, and ankle joints are important in locomotion. The relative significance of these leg muscles depends on the locations of their points of origin and insertion, lengths, and their PCAs. Quite a few of these muscles are depicted in Figs. 3.​3, 3.​4, 3.​5. (Analogous sets of musclesare involved in controlling our arms and hands, as seen below in Figs. 5.22 and 5.23.) The relative PCAs are given in Tables 5.1, 5.2, 5.3. In general, longer muscles enable larger angles of rotation about joints. The larger the muscle PCA, the more the muscle strength. Muscles with smaller PCAs can be important in providing stability.


Table 5.1
Percent PCA of muscles crossing the hip joint


























































Muscle

%PCA

Iliopsoas

9

Sartorius

1

Pectineus

1

Rectus femoris

7

Gluteus maximus

16

Gluteus medius

12

Gluteus minimus

6

Adductor magnus

11

Adductor longus

3

Adductor brevis

3

Tensor fasciae latae

1

Biceps femoris (long)

6

Semitendinosus

3

Semimembranosus

8

Piriformis

2

Lateral rotators

13


From [81], data from [76]



Table 5.2
Percent PCA of muscles crossing the knee joint











































Muscle

%PCA

Gastrocnemius

19

Biceps femoris (small)

3

Biceps femoris (long)

7

Semitendinosus

3

Semimembranosus

10

Vastus lateralis

20

Vastus medialis

15

Vastus intermedius

13

Rectus femoris

8

Sartorius

1

Gracilis

1


From [81], data from [76]



Table 5.3
Percent PCA of muscles crossing the ankle joint





































Muscle

%PCA

Soleus

41

Gastrocnemius

22

Flexor hallucis longus

6

Flexor digitorum longus

3

Tibialis posterior

10

Peroneus brevis

9

Tiabialis anterior

5

Extensor digitorum longus

3

Extensor hallucis longus

1


From [81], data from [76]



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Fig. 5.2
Three major biarticulate muscles of the leg, from left to right the gastrocnemius, hamstrings, and rectus femoris, along with moment-arm lengths about the joints at their proximal and distal ends. (From [81]. Reprinted with permission of Wiley)

As is clear from Figs. 1.​8 and 3.​2 and from Tables 5.1, 5.2, 5.3, many of these leg muscles pass over more than one joint. Figure 5.2 shows the three such major biarticulate (two joint) muscles in the leg. The forces exerted by the muscles on the bones at the points of origin and insertion are the same (Newton’s Third Law), but the torques are different at the proximal and distal joints because the moment arms are different. As seen in Fig. 5.2, the gastrocnemius is a knee flexor and ankle plantarflexor (extensor), with the torque about the latter joint greater because of its larger moment arm (5 cm vs. 3.5 cm). During stance the net effect of this muscle is to cause the leg to rotate posteriorly and to prevent the knee from collapsing. The hamstrings are extensors of the hip and flexors of the knee, with hip extension having twice the moment of knee flexion. During stance, this causes the thigh to rotate posteriorly and prevents the knee from collapsing. The rectus femoris of the quadriceps is a hip flexor and knee extensor, with a slightly larger moment about the hip. However, the major action of the quadriceps is knee extension because 84% of the quadriceps PCA is from other muscles, the uniarticulate knee extensors (and all of these muscles fire simultaneously). The net effect of these three major biarticulate muscles is the extension of all three leg joints, and they help prevent against collapse due to gravity. Coordinated motion of these muscles, such as the lengthening of one of these muscles and shortening of another, is needed to achieve the full range of rotation of these joints because of the limited change of muscle length of any one of them [81].


5.1.1 Types of Muscle Activity


Muscles can be activated under a wide range of conditions. When the muscle length changes, the angle of the joint for this inserted muscle changes, and there is motion at the end of the bone emanating from the joint. Because there is motion, mechanical work is done. This can be called “dynamic” work. When the muscle length does not change, i.e., isometric conditions, there is no rotation of the joint and no mechanical work is done. This is important because tension is still supplied by the muscle to resist outside forces, as needed in holding objects or standing upright. Energy is still expended by the muscle (for such “static” work) to produce the tension that resists the load.

Mechanical work is performed with joint motion for nonisometric contractions. In concentric contractions, the muscle develops enough tension to overcome the load and the muscle length shortens, causing joint movement. In ascending stairs the quadriceps contract and the leg straightens as a result of this concentric contraction. In eccentric contractions, the muscle does not develop enough tension to overcome the load and the muscle length still lengthens, sometimes slowing joint movement (on purpose). In descending stairs the quadriceps are activated but they still extend during this essential controlled (eccentric) braking of knee flexion in fighting gravity. Therefore , the same flexor muscles that contract concentrically during flexion can contract eccentrically during extension to decelerate the extension. Concentric contractions are said to do positive (mechanical) work, while eccentric contractions do negative work.

During isokinetic contraction, the velocity of muscle shortening or lengthening, and consequently also the angular speed of the joint, are constant. During isoinertial contraction, the resistive load on the muscle—due to the gravity force, applied forces, etc.—is constant. During isotonic contraction, the tension is constant. (This is an idealized condition because the muscle tension actually changes with length.)

In elbow flexion the biceps brachii and brachialis muscles contract and they are the agonists or prime movers of the action. The brachioradialis is a synergist muscle in the motion; such synergist muscles assist the motion and sometimes add fine tuning. The triceps brachii are the antagonists of this action, and oppose the prime movers.

During walking and running the quadriceps act eccentrically during early stance to prevent the collapse of the knee angle, and then concentrically to extend the knee as the leg rotates over the foot in midstance (and this is more so in walking). The ankle plantarflexors fire eccentrically during stance to help advance the leg rotation over the foot controllably, and then concentrically to assist push off.


5.2 The Structure of Muscles


Muscles have a fiber structure with successive levels of fiber-like substructures called fasciculi (fuh-sik’-you-lie). (A single one is a fasciculus (fuh-sik’-you-lus).) On a macroscopic basis, these fibers are arranged in one of several ways. This is illustrated in Fig. 5.3. It appears that the forces generated by individual muscle fibers and muscles can be added independently [65, 66].

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Fig. 5.3
Types of fiber arrangements in skeletal muscles, with a parallel and b pinnate fibers. (Based on [53])

In fusiform muscles the muscle fibers are parallel and they narrow and blend into tendons that attach to the skeleton. In parallel muscles the fibers are also parallel. They tend to be long, such as the sartorius—the longest muscle in the body, which spans from the hip to the tibia (Figs. 1.​8 and 5.4). (The fibers are also parallel in the rectus abdominis (the “abs”).) We will usually not differentiate between fusiform and parallel muscles because of their similar arrangement of muscle fibers. These muscles consist of many sarcomere components in series (see below), and as such they can become much shorter to produce much movement of bones for motion about joints, and they can do so quickly. In unipinnate muscles, parallel muscle fibers attach to tendons at an angle, such as with the flexor policis longus (poe-lee’-cis) in the lower hand/thumb and the extensor digitorium longus (di-gi-tor’-ee-um) in the lower leg/foot. In bipinnate muscles, such parallel muscle fibers attach to a tendon in two different directions, such as with the rectus femoris (fe-more’-is) in the thigh. These pinnate (or pennate or pinnation) structures resemble the structure of feathers and of some leaves on branches. The fibers attach on the central tendon at several angles in the multipinnate deltoid (shoulder) muscles. Many short muscle fibers can attach to such short tendons in pinnate muscles, leading to larger forces than for parallel muscles and more movement, but with less efficient use of the muscles forces (see below and Problem 5.17). The orbicularis oculi (or-bee-queue-lar’-is ok’-you-lie) about the eye are circular muscles, in which the muscle fibers are in a circle about the object. The pectoralis major (pec-tor-al’-is) in the upper chest (the “pects”) is a convergent muscle; such muscles are broad at their origin and narrow at insertion, leading to large forces near the insertion point. Examples of each of these muscle types in the body are shown in Fig. 5.4.

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Fig. 5.4
Examples of muscle fiber arrangements in the body. (From [58]. Used with permission)

The way the forces from muscle fibers add to give the total force on the attaching tendon differs for these different muscle structures. In parallel, fusiform muscles, all the force of the fibers is transmitted to the tendon. In pinnate muscles, the fibers are attached to the tendon at an angle $$ \theta $$, and only $$F\cos \theta $$ of the force $$\mathbf {F}$$ of each fiber is effectively transmitted. While this is a distinct disadvantage of the pinnate design, it has other relative advantages. Because the geometry allows fibers to attach along part of the length of the tendon (Fig. 5.5), many more fibers can be attached to the tendon. Also, this geometry allows the central tendon to move a longer distance than in the fusiform scheme, so the bones attached to the tendon can move more. This overcomes the limited change in length in the muscles that can limit the range of angular motion of bones about joints. These and related issues are addressed in Problem 5.17. The mass, fiber length, PCA, and pinnation angle $$\theta $$ for several muscles are given in Table 5.4.

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Fig. 5.5
Muscle fibers in pinnate muscles a before and b after fiber contraction with accompanying tendon movement



Table 5.4
Properties of some muscles


















































































Muscle

Mass (g)

Fiber length (cm)

PCA (cm$$^{2}$$)

Pinnation angle ($$^{\circ }$$)

Sartorius

75

38

1.9

0

Biceps femoris (long)

150

9

15.8

0

Semitendinosus

75

16

4.4

0

Soleus

215

3.0

58

30

Gastrocnemius

158

4.8

30

15

Tibialis posterior

55

2.4

21

15

Tibialis anterior

70

7.3

9.1

5

Rectus femoris

90

6.8

12.5

5

Vastus lateralis

210

6.7

30

5

Vastus medialis

200

7.2

26

5

Vastus intermedius

180

6.8

25

5


From [81], data from [76]

The microscopic components of the fibers are illustrated in Figs. 5.6 and 5.7, where the muscle belly of a fusiform muscle is seen to be composed of many parallel fasciculi. Each fasiculus is composed of many parallel muscle fibers (or muscle cells). Each muscle fiber is composed of many parallel myofibrils. Each myofibril is composed of myofilaments arranged into $$\sim $$2–3 $$\upmu $$m long units called sarcomeres (sar’-koe-meres). There are thick myofilaments with a serial arrangement of many myosin (my’-oh-sin) molecules and thin myofilaments with globules of F-actin (or actin) molecules that form twisting strands, which are surrounded by two other proteins: tropomyosin—which forms strands that twist about the actin strands—and troponin-T—which attaches at regular intervals to the actin and tropomyosin strands. Theinteraction between the myosin and actin proteins on adjacent myofilaments is the fundamental, chemical-induced, force-producing interaction in the muscle, which involves the hydrolysis of ATP and the change in conformation of the myosin.

In the large limb of an adult the muscle fibers are $$\sim $$50$$\,\upmu $$m in diameter. This diameter can double with weight training. Depending on the type of muscle, there are $${\sim }10^{4}$$$$10^{7}$$ muscle fibers per muscle (Table 5.5). There are $${\sim }1 \times 10^{4}$$$$1.7 \times 10^{5}$$ sarcomeres per muscle fiber, depending on the type of muscle (Table 5.6).

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Fig. 5.6
Organization of skeletal muscles, down to the myofibril level. See Fig. 5.7 for the structure of the myofibril. (From [68])


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Fig. 5.7
a Structure and substructure of the myofibril shown in Fig. 5.6, with the banded structure of sarcomeres (whose periodicity is denoted by the arrows). b The scanning electron micrograph of skeletal muscle shows the structure of bands and lines in sarcomeres. This is associated with the thick and thin filaments in (c) from the longitudinal perspective of (a) and (b), the transverse cross-section is seen in (d). (From [67])

The electron micrograph in Fig. 5.7 shows the banded myofilament structure that is also sketched in the figure. The A band is a wide dark, anisotropic region, while the I band is a wide light, isotropic region. There is a lighter H zone or band in the middle of the dark A band, and a darker M line in the middle of the H zone. The dark Z lines run through the light I bands.


Table 5.5
Number of muscle fibers in human muscles


































Muscle

Number of muscle fibers

First lumbrical

10,250

External rectus

27,000

Platysma

27,000

First dorsal interosseous

40,500

Sartorius

128,150

Brachioradialis

129,200

Tiabialis anterior

271,350

Medial gastrocnemius

1,033,000


Using data from [52]



Table 5.6
Number of sarcomeres in human muscles














































Muscle

Number of sarcomeres per fiber ($$\times $$10$$^{4}$$)

Person I

Person II

Person III

Tibialis posterior

1.1

1.5

0.8

Soleus

1.4



Medial gastrocnemius

1.6

1.5

1.5

Semitendinosus

5.8

6.6


Gracilis

8.1

9.3

8.4

Sartorius

15.3

17.4

13.5


Using data from [52]

Each sarcomere is bound between the adjacent Z lines. The dark A band in the center of each sarcomere consists of thick (myosin) myofilaments (or thick filaments), which are connected to each other in the central M line within the H zone. They are overlapped to some degree by the thin (actin) myofilaments (or thin filaments). There are thick filaments but no thin filaments in the central H zone. The light I band regions next tox the Z lines are the thin myofilaments in regions where they do not overlap the thick myofilaments; they are bound to each other at the Z line. This is shown schematically in Fig. 5.7.


5.3 Activating Muscles: Macroscopic View


Electrical stimuli lead to twitches in the muscles that temporarily increase the force exerted by them. These twitches are delayed by about 15 ms after the electrical stimulus. They peak $$\sim $$40 ms later, and then decay to zero $$\sim $$50 ms later (Fig. 5.8a, Table 5.7). The shape of a twitch can be modeled as


$$\begin{aligned} F(t)=F_{0} \frac{t}{T} \exp (-t/T) \end{aligned}$$

(5.1)
with twitch time T.

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Fig. 5.8
Two twitches stimulated at $$S_{1}$$ and $$S_{2}$$, with various delays. (Based on [53])



Table 5.7
Twitch time T, in ms
































Muscle

Typical mean time

Range of times

Triceps brachii

44.5

16–68

Biceps brachii

52.0

16–85

Tibialis anterior

58.0

38–80

Soleus

74.0

52–100

Medial gastrocnemius

79.0

40–110


Using data from [81]

By increasing the frequency of these stimuli and consequently of the twitches, there is an increase in the force exerted by the muscle (Fig. 5.8b, c). At a large enough frequency the twitches overlap to produce an almost steady level of force called unfused tetanus, and at an even higher frequency they produce a force that is constant in time called tetanus (Fig. 5.9). Roughly 50–60 electrical shocks per second are required to fully tetanize mammalian muscles at room temperature. This varies from about $$\sim $$30/s for the soleus muscle to $${\sim }300/$$s for eye muscles. (Also see Fig. 5.11 below.)

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Fig. 5.9
A twitch, and then a series of twitches leading to unfused tetanus, and at an even higher frequency leading to tetanus. (Based on [53])

There are three different types of muscle fibers, which differ in how fast they contract and their resistance to fatigue. They appear in different types of muscles in varying proportions (Fig. 5.10). For a given muscle type, their relative concentrations can be different in different people. Slow-twitch (ST) red fibers (Type I) have a long contraction time ($$\sim $$110 ms) and are very resistant to fatigue because they are aerobic, i.e., they use oxygen to produce ATP. These fibers are red because they have blood to supply oxygen. Fast-twitch (FT) fibers generally can create more force than ST fibers, and reach a peak tension in less time ($$\sim $$50 ms). FT red intermediate fibers (Type IIA) have a relatively short contraction time, an intermediate fatiguing rate, and aerobic generation of ATP. FT white fibers (Type IIB) have a short contraction time and fatigue quickly because they use anaerobic (i.e., no oxygen) processes to produce ATP. One of the reasons for the faster response of the fast twitch muscle is the larger neuron exciting it.

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Fig. 5.10
Photomicrograph of stained muscle cells from a human vastus lateralis muscle, showing ST Type I (dark) and FT Type II (lightly stained) cells, with fine lines showing boundaries added. (From [20]. Used with permission)


A114622_2_En_5_Fig11_HTML.gif


Fig. 5.11
Duration of isometric responses for different muscles with different FT and ST muscle fibers. (Based on [26])

The “average” muscle has roughly 50% ST fibers and 25% red and white FT fibers. The contraction time of a muscle depends on the proportion of FT and ST fibers. Figure 5.11 shows the twitch response for three types of muscles. The ocular muscles in the eye have mostly FT muscles and a response time of $${\sim }1/40$$ s. The gastrocnemius (gas-trok-nee’-mee-us) muscle has many FT muscles and a response time of $${\sim }1/15$$ s. The soleus (soh’-lee-us) muscle has many ST muscles and a response time of $${\sim }1/5$$ s.

All of this makes sense in terms of the body’s needs. The eye muscles must be fast for our needed rapid eye reflex. The gastrocnemius and soleus muscles in the upper calf are both connected to the Achilles (calcaneal) tendon in the foot, which is connected to the calcaneus bone in the heel. The soleus muscle is a broad calf muscle that is deep relative to the medial and lateral heads of the gastrocnemius muscle (see Figs. 1.​8b and 3.​5). The soleus muscle is used more for standing and stability, for which endurance and resistance to fatigue are important and a fast response is not very important. The gastrocnemius muscle is used mostly for jumping and running, for which a fast response is necessary, even at the expense of endurance. The relative fraction of ST and FT muscles in the knee for trained athletes is depicted in Fig. 5.12 and Table 5.8. Clearly, athletes in sports that require endurance—such as marathon runners—have a higher fraction of ST muscle fibers in muscles used in running, while those in sports that require speed and strength—such as sprint runners and weightlifters—have a higher fraction of FT muscles in those muscles heavily used in these activities. There is a similar correlation for the cross-sectional areas of these different muscle fibers.

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Fig. 5.12
Knee extension performance versus percentage of FT fibers in the knee. (Based on [21] and [73])



Table 5.8
Percentages of ST and FT muscle fibers in selected muscles in male (M) and female (F) athletes, along with the cross-sectional areas of these muscle fibers













































































































































Athlete

Gender

Muscle

%ST

%FT

ST area ($$\upmu $$m$$^{2}$$)

FT area ($$\upmu $$m$$^{2}$$)

Sprint runners

M

Gastrocnemius

24

76

5,878

6,034

F

Gastrocnemius

27

73

3,752

3,930

Distance runners

M

Gastrocnemius

79

21

8,342

6,485

F

Gastrocnemius

69

31

4,441

4,128

Cyclists

M

Vastus lateralis

57

43

6,333

6,116

F

Vastus lateralis

51

49

5,487

5,216

Swimmers

M

Posterior deltoid

67

33



Weightlifters

M

Gastrocnemius

44

56

5,060

8,910

M

Deltoid

53

47

5,010

8,450

Triathletes

M

Posterior deltoid

60

40



M

Vastus lateralis

63

37



M

Gastrocnemius

59

41



Canoeists

M

Posterior deltoid

71

29

4,920

7,040

Shot-putters

M

Gastrocnemius

38

62

6,367

6,441

Nonathletes

M

Vastus lateralis

47

53

4,722

4,709

F

Gastrocnemius

52

48

3,501

3,141


From [80]


5.3.1 Mechanical Model of the Active State of Muscles


We now develop a macroscopic model of muscles in the active state due to electrical stimulation by using the type of spring–dashpot models we employed to characterize viscoelasticity in Chap. 4. This model includes springs and dashpots to account for the passive properties of the muscle and tension generators to characterize the active state. While it mathematically characterizes the mechanical features of skeletal muscles acting against loads quite well, the individual components of the model may or may not describe muscle properties microscopically. For example, the viscosity represented by the dashpot does not model the effect of the viscosity of the fluid in a muscle very well. The parallel elastic element may, in fact, be due to the sarcolemma, which is the outer membrane surrounding the muscle fiber. The highly elastic protein, titin (see Fig. 5.18 below), forms a net-like structure about the thick and thin filaments, and may also contribute to this element. The hinge regions of myosin may contribute to a series elastic element. (In cardiac muscle, it is believed that connective tissue is the major part of the parallel elastic element.)

Figure 5.13a shows a mechanical model with a unit composed of a tension generator $$T_{0}(x,t)$$ in parallel with a dashpot with viscosity c and a spring with spring constant $$k_{\mathrm {parallel}}$$, that is in series with another spring with spring constant $$k_{\mathrm {series}}$$. The total length of the muscle is $$x^{T}=x^{E}+x$$, where $$x^{E}$$ is the equilibrium length and x is the displacement.

A114622_2_En_5_Fig13_HTML.gif


Fig. 5.13
Complete active state muscle model. (Based on [53])

One can show that this model (which is also depicted in Fig. 5.14a) is mathematically equivalent to the model shown in Fig. 5.14b in which there is a unit with a spring in series with a tension generator in parallel with a dashpot, and this unit is in parallel with another spring. They are mathematically equivalent in the sense that combinations of the components give the same model predictions. The spring constants and viscosity coefficients in the two models are not equal to each other, but are related to each other (see Problem 5.10). This representation of the model in (a) is exactly the same as the Kelvin/standard linear model, except that the dashpot is in parallel with the tension generator.

A114622_2_En_5_Fig14_HTML.gif


Fig. 5.14
Equivalent active state muscle models. The model in part a is the same as that in Fig. 5.13. (Based on [53])

We will examine the state of the muscle by solving a slightly simpler model, with only the spring with $$k_{\mathrm {series}}$$ (now called k for simplicity) in Fig. 5.15. Without the tension generator, this reduces to the Maxwell model . The tension generator supplies a tension that could depend on muscle length x and time t, $$T_{\mathrm {G}}=T_{\mathrm {G}}(x,t)$$. We will also assume that the total length of the muscle does not change, i.e., isometric conditions. This means that $$x^{\mathrm {T}}=x_{1}^{\mathrm {T} }+x_{2}^{\mathrm {T}}$$ is constant, where $$x_{1}^{\mathrm {T}}$$ is the length of the dashpot/tension generator and $$x_{2}^{\mathrm {T}}$$ is the length of the spring. For isometric conditions , we know that $$x(t)=0$$. Consequently, the tension generator $$T_{\mathrm {G}}=T_{\mathrm {G}}(t)$$. We will say this generator supplies the tension $$T_{0}$$ for specific durations of time.

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Fig. 5.15
Simpler active state muscle model. (Based on [53])

The total length of the dashpot/tension generator can be subdivided into the equilibrium length and the displacement $$x_{1}^{\mathrm {T}}=x_{1}^{\mathrm {E}}+x_{1}$$; for the spring we see that $$x_{2}^{\mathrm {T}}=x_{2}^{\mathrm {E}}+x_{2}$$. The force generated across the muscle is $$T=T(t)$$. This is equal to the tension across the spring


$$\begin{aligned} T=kx_{2} \end{aligned}$$

(5.2)
and is also equal to the sum of the tensions across the tension generator and dashpot, and so


$$\begin{aligned} T=T_{\mathrm {G}}+c\; \frac{\mathrm{d}x_{1}}{\mathrm{d}t}. \end{aligned}$$

(5.3)
(Refer to the discussions of the Maxwell and Voigt models of viscoelasticity in Chap. 4 for a more detailed explanation.)

Because $$x^{\mathrm {T}}=x_{1}^{\mathrm {T}}+x_{2}^{\mathrm {T}}$$ is constant, we see that $$\mathrm{d}x^{\mathrm {T}}/\mathrm{d}t=0$$. Also, because the equilibrium distances are constant


$$\begin{aligned} \frac{\mathrm{d}x}{\mathrm{d}t}=\frac{\mathrm{d}x_{1}}{\mathrm{d}t}+\frac{\mathrm{d}x_{2}}{\mathrm{d}t}=0. \end{aligned}$$

(5.4)
Equation (5.3) gives $$\mathrm{d}x_{1}/\mathrm{d}t=(T-T_{\mathrm {G}})/c $$ and the first derivative of (5.2) gives $$ \mathrm{d}x_{2}/\mathrm{d}t=(\mathrm{d}T/\mathrm{d}t)/k$$, and so (5.4) becomes


$$\begin{aligned} \frac{T-T_{\mathrm {G}}}{c }+\frac{1}{k}\frac{\mathrm{d}T}{\mathrm{d}t}=0 \end{aligned}$$

(5.5)
or


$$\begin{aligned} \frac{\mathrm{d}T(t)}{\mathrm{d}t}+\frac{T(t)}{\tau }=\frac{T_{\mathrm {G}}(t)}{\tau }, \end{aligned}$$

(5.6)
where $$\tau =c /k$$ is the relaxation time. T(t) is a function of t driven by $$T_{\mathrm {G}}(t)$$.

The general solution to this with $$T_{\mathrm {G}}(t)= \alpha $$ (a constant) for $$t>0$$” src=”http://basicmedicalkey.com/wp-content/uploads/2017/06/A114622_2_En_5_Chapter_IEq70.gif”></SPAN> and 0 for <SPAN id=IEq71 class=InlineEquation><IMG alt=, with tension T(0) at $$t=0$$, is


$$\begin{aligned} T(t)=\alpha +(T(0)-\alpha )\exp (-t/\tau )=T(0)\exp (-t/\tau )+\alpha ( 1-\exp (-t/\tau )). \end{aligned}$$

(5.7)
This can be proved by substituting this in (5.6) and checking the solution at $$t=0$$. (See Appendix C.)

Before the tension generator turns on, $$T_{\mathrm {G}}=0$$ and $$T(0)=0$$. At $$ t=0 $$, $$T_{\mathrm {G}}(t)=T_{0}(=\alpha )$$ for a period of time, during which time (5.7) is


$$\begin{aligned} T(t)=T_{0}(1-\exp (-t/\tau )), \end{aligned}$$

(5.8)
as shown in Fig. 5.16a.

A114622_2_En_5_Fig16_HTML.gif


Fig. 5.16
Solutions of the active state muscle model in Fig. 5.15 for the tension with excitation by a a step function, b a square pulse, and c a square wave. The text derives the solution after two sequential square pulses at time $$2t_{1}+t_{2}$$ in (c). (Based on [53])

If the tension generator turns off at time $$t_{1}$$, so $$T_{\mathrm {G}}(t)=0$$ for $$t>t_{1}$$” src=”http://basicmedicalkey.com/wp-content/uploads/2017/06/A114622_2_En_5_Chapter_IEq81.gif”></SPAN>, then the existing tension at <SPAN id=IEq82 class=InlineEquation><IMG alt=$$t_{1}$$ src= is


$$\begin{aligned} T(t_{1})=T_{0}(1-\exp (-t_{1}/\tau )), \end{aligned}$$

(5.9)
and (5.7) (now with $$\alpha =0$$) shows that the tension then decays at a rate $$\exp (-\varDelta t/\tau )$$, where $$\varDelta t=t-t_{1}$$. Therefore, for $$t>t_{1}$$” src=”http://basicmedicalkey.com/wp-content/uploads/2017/06/A114622_2_En_5_Chapter_IEq86.gif”></SPAN><br />
<DIV id=Equ10 class=Equation><br />
<DIV class=EquationContent><br />
<DIV class=MediaObject><IMG alt=

(5.10)
as is seen in Fig. 5.16b.

This is the model of a single twitch. We can consider sequences of two twitches separated in time one right after the other (see Fig. 5.16c). Say the activation is off for a time $$t_{2}$$ and is on again at $$t_{1}+t_{2}$$ for a time $$t_{1}$$ (until $$2t_{1}+t_{2}$$). Then the tension at the start of the second twitch is


$$\begin{aligned} T(t_{1}+t_{2})=T_{0}(1-\exp (-t_{1}/\tau ))\exp (-t_{2}/\tau ). \end{aligned}$$

(5.11)
For $$t_{1}+t_{2}<t<2t_{1}+t_{2}$$, the tension evolves as given by (5.7) with (5.11) used for the initial tension, $$\alpha =T_{0}$$, with t replaced by $$t-(t_{1}+t_{2})$$ on the right hand side of the equation (which is a new definition of the starting time). Therefore,


$$\begin{aligned} T(t)= & {} T_{0}\{1+[\exp (-t_{2}/\tau )-\exp (-(t_{1}+t_{2})/\tau )-1]\exp (-(t-(t_{1}+t_{2}))/\tau )\}\end{aligned}$$

(5.12)



$$\begin{aligned}= & {} T_{0}\{1-\exp (-t/\tau )+\exp (-(t-t_{1})/\tau )-\exp (-(t-(t_{1}+t_{2}))/\tau )\}. \end{aligned}$$

(5.13)
At the end of the second twitch $$t=2t_{1}+t_{2}$$, so


$$\begin{aligned} T(t)= & {} T_{0}\{1-\exp (-(2t_{1}+t_{2})/\tau )+\exp (-(t_{1}+t_{2})/\tau )-\exp (-t_{1}/\tau )\}\qquad \quad \end{aligned}$$

(5.14)



$$\begin{aligned}= & {} T_{0}[1-\exp (-t_{1}/\tau )][1+\exp (-(t_{1}+t_{2})/\tau )], \end{aligned}$$

(5.15)
which is $$(1+\exp (-(t_{1}+t_{2})/\tau )) \times $$ larger than at the end of the first twitch.

At the end of N such twitches, the tension is larger than at the end of the first twitch by a factor $$1+\exp (-(t_{1}+t_{2})/\tau )+\exp (-2(t_{1}+t_{2})/\tau )+\, \ldots \, +\exp (-N(t_{1}+t_{2})/\tau )$$, which for large N approaches $$1/[1-\exp (-(t_{1}+t_{2})/\tau )]$$. (The geometric sum $$ 1+x+x^{2}+x^{3}+\,\ldots \,\rightarrow 1/(1-x)$$ for $$0<x<1.$$) Therefore the total developed tension in the tetanized state is


$$\begin{aligned} T_{\mathrm {tetanized}}=T_{0}\,\frac{1-\exp (-t_{1}/\tau )}{1-\exp (-(t_{1}+t_{2})/\tau )}. \end{aligned}$$

(5.16)
If the pulses come right after each other, so $$t_{2}=0$$, this equation becomes $$T_{\mathrm {tetanized}}=T_{0}$$, which makes sense.

Figure  5.17 shows a more complete mechanical model of a muscle, with individual sarcomeres modeled.

A114622_2_En_5_Fig17_HTML.gif


Fig. 5.17
Schematic diagram of a muscle fiber that consists of the simpler models. This more complete muscle model is built from a distributed network of N sarcomeres. (Based on [15] and [61])


5.4 Passive Muscles


A passive or resting muscle with no electrical stimulation has mechanical properties that need to be understood as part of exploring the active state of the muscle because they affect muscle performance during activation. Experimentally it is found that passive muscles are non-Hookean, as in (4.​22). Equation (4.​27) showed that for larger strains, stress and strain are related by


$$\begin{aligned} \sigma =\mu ^{\prime }\exp (\alpha L/L_{0})-\mu , \end{aligned}$$

(5.17)
with $$\lambda =L/L_{0}=\epsilon +1$$ being the Lagrangian strain, where L is the muscle length and $$L_{0}$$ is the relaxed length.

Using this, the force across a passive muscle is related to stress by


$$\begin{aligned} F_{\mathrm {M}}=\sigma (\mathrm {PCA}) . \end{aligned}$$

(5.18)
Consequently, the force needed to maintain a passive muscle at a length L is


$$\begin{aligned} F_{\mathrm {M}}=(\mathrm {PCA})\mu ^{\prime }\exp (\alpha L/L_{0})-(\mathrm {PCA})\mu . \end{aligned}$$

(5.19)
For large strains, more general relations need to be used for this neo-Hookean regime and for defining strains. Chapter 4 and Problems 4.​204.​22 explain this further.


5.5 Active/Tetanized Muscles: Microscopic View


Unlike passive organ parts whose lengths change because of applied stresses, the lengths of muscles change and force is generated by the sliding of the thick filaments on the thin filaments, as seen in Figs. 5.18 and 5.19. Because the basic operating unit undergoing this motion is the sarcomere, which is $${\sim }2\,\upmu $$m long, these figures describe a microscopic view of muscle action.

A114622_2_En_5_Fig18_HTML.gif


Fig. 5.18
Schematic of the sliding filament mechanism in sarcomeres, with relative sliding of the thick and thin filaments, for sarcomeres of increasing length: 1.6, 2.2, 2.9, and 3.6 $$\upmu $$m (which roughly correspond to the sarcomeres highlighted in Fig. 5.19). Note that the elastic material titin is schematically shown to connect the thick filament to the structure; it plays an important role in the elastic properties of muscles. Also see Fig. 5.35. (From [68])


A114622_2_En_5_Fig19_HTML.gif


Fig. 5.19
Force versus sarcomere or muscle length, with schematics of the variation of the overlap of the thick (myosin) and thin (actin) filaments for different sarcomere lengths. The sarcomere and total muscle lengths scale the same way. The crossbridge between an actin and myosin molecule is also shown. (Based on [26, 53, 67, 71])

The maximum tension force that can be developed by a muscle depends on several quantities, including the current muscle length, the current rate of muscle contraction, and the physiological cross-sectional area (PCA) of the muscle . Under optimal conditions this force is $$\sim $$30 N/cm$$^{2}$$ for many muscles in most mammals.

The tension generated by a muscle when the two ends of the muscle are held fixed, called isometric conditions, is shown in Fig. 5.19. The maximum force generated by a muscle occurs at the optimal length $$L_{0}$$. (This occurs at a muscle length slightly longer than the initial or resting length $$L_{\mathrm {i}}$$, prior to activation.) This maximum level of force decreases to half of this value when the muscle length is 70% (shortened muscle) or 130% (lengthened muscle) of this optimal length. It is almost zero at 170% of this resting length. These observations refer to both the total length of the actual muscle and the length of each $${\sim }2\,\upmu $$m long sarcomere [12].

The physical basis of this tension is the extent of overlap of myosin and actin molecules on the thick and thin filaments. At the resting length the number of myosin/actin pair overlaps is at a maximum, and this number of overlapping pairs decreases when the sarcomere gets shorter or longer. These interactions of these pairs of molecules are known as crossbridges between the thick and thin filaments.

One consequence of changing muscle length is the concomitant changing of joint angle (Problem 5.16). Consequently, the generated force and resulting torque also depend on the joint angle. Figure 5.20 shows the force versus joint angle for several joints.

A114622_2_En_5_Fig20_HTML.gif


Fig. 5.20
Force versus angle for elbow and shoulder flexion and extension, and hip and knee flexion. Only some of these plots look like the classic force versus length locus (Fig. 5.19, converted to a plot versus joint angle) for a single muscle fiber or sarcomere. (Based on [20])


A114622_2_En_5_Fig21_HTML.gif


Fig. 5.21
Schematic of passive, developed (active), and total tension versus length for pinnate and parallel muscles. (Based on [5] and [53]. Also see [1])


A114622_2_En_5_Fig22_HTML.gif


Fig. 5.22
Extensor muscles of the forearm, with a posterior view of superficial muscles, b selected features of the hand, and c deeper muscles, along with selected arteries. Tendons extending to the hand are also seen. (From [57]. Used with permission)


A114622_2_En_5_Fig23_HTML.gif


Fig. 5.23
Flexor muscles of the forearm, with anterior views of the first (most superficial) layer in (a), the second layer in (b), and the third and fourth layers in (c). Tendons extending to the hand are also seen. (From [57]. Used with permission)


A114622_2_En_5_Fig24_HTML.gif


Fig. 5.24
It is difficult to clench your fist with a strongly flexed wrist (a) and straighten your fingers with a strongly hyperextended wrist (b). (From [4]. Copyright 1992 Columbia University. Reprinted with the permission of the press)


5.5.1 Total Muscle Tension


Figure 5.21 shows the total tetanized tension versus muscle length. It clearly looks different than the response shown in Fig. 5.19. Also shown in Fig. 5.21 is the passive tension versus muscle length. The contribution of the passive properties of muscle tissue cannot be ignored in modeling activated muscles. The passive component is given by (5.19), and it and the developed tension are added in Fig. 5.21 to give the total tension. In parallel, fusiform muscles, such as the sartorius muscle in the thigh, there are long muscle fibers with relatively little passive material. The maximum seen in the active part is still seen in the total muscle response (Fig. 5.21b). In pinnate muscles, such as the gastrocnemius muscle, there are short fibers and much connective tissue and so the passive material contribution is large and the maximum attributable to the developed portion alone is not seen (Fig. 5.21a).


5.5.2 Everyday Proof of the Limited Rangeof Useful Muscle Length


The decrease in the tension that muscle is able to develop when it is very short or long can be seen in simple demonstrations [4].

For most of us, it is hard to do pull ups (chin ups) or push ups with our arms fully extended, because in this beginning position the muscles we need to use are much longer than their resting length. It is much easier to start these exercises half-way through the motion, with the muscles nearer their resting length.

Grip a ball (or pen) tightly in one fist. Have someone of comparable physical dimensions try to grasp the ball from your fist. Hopefully (and quite likely) he or she cannot. Now use your other hand to push the top of your clenched fist down at the wrist, to flex your wrist downward as much as possible without inflicting undue pain. Now have your colleague try to grasp the ball. It should be a relatively simple task. Why? Before you usually make a fist the relevant muscles are initially near their resting length, but when your wrist is flexed, the relevant muscles are much too long to generate much tension. What is the exact origin of this?

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Jun 11, 2017 | Posted by in GENERAL & FAMILY MEDICINE | Comments Off on Muscles

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