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The primary function of the cardiovascular system is to deliver blood to the tissues, which provides essential nutrients to the cells for metabolism and removes waste products from the cells. The heart serves as the pump, which, by contracting, generates the pressure to drive blood through a series of blood vessels. The vessels that carry blood from the heart to the tissues are the arteries, which are under high pressure and contain a relatively small percentage of the blood volume. The veins, which carry blood from the tissues back to the heart, are under low pressure and contain the largest percentage of the blood volume. Within the tissues, thin-walled blood vessels, called capillaries, are interposed between the arteries and veins. Exchange of nutrients, wastes, and fluid occurs across the capillary walls.
The cardiovascular system also is involved in several homeostatic functions: It participates in the regulation of arterial blood pressure; it delivers regulatory hormones from the endocrine glands to their sites of action in target tissues; it participates in the regulation of body temperature; and it is involved in the homeostatic adjustments to altered physiologic states such as hemorrhage, exercise, and changes in posture.
Figure 4.1 is a schematic diagram of the circuitry of the cardiovascular system. The left and right sides of the heart and the blood vessels are shown in relation to each other. Each side of the heart has two chambers, an atrium and a ventricle, connected by one-way valves, called atrioventricular (AV) valves. The AV valves are designed so that blood can flow only in one direction, from the atrium to the ventricle.
The left heart and right heart have different functions. The left heart and the systemic arteries, capillaries, and veins are collectively called the systemic circulation. The left ventricle pumps blood to all organs of the body except the lungs. The right heart and the pulmonary arteries, capillaries, and veins are collectively called the pulmonary circulation. The right ventricle pumps blood to the lungs. The left heart and right heart function in series so that blood is pumped sequentially from the left heart to the systemic circulation, to the right heart, to the pulmonary circulation, and then back to the left heart.
The rate at which blood is pumped from either ventricle is called the cardiac output. Because the two sides of the heart operate in series, the cardiac output of the left ventricle equals the cardiac output of the right ventricle in the steady state. The rate at which blood is returned to the atria from the veins is called the venous return. Again, because the left heart and the right heart operate in series, venous return to the left heart equals venous return to the right heart in the steady state. Finally, in the steady state, cardiac output from the heart equals venous return to the heart.
The blood vessels have several functions. They serve as a closed system of passive conduits, delivering blood to and from the tissues where nutrients and wastes are exchanged. The blood vessels also participate actively in the regulation of blood flow to the organs. When resistance of the blood vessels, particularly of the arterioles, is altered, blood flow to that organ is altered.
The steps in one complete circuit through the cardiovascular system are shown in Figure 4.1 . The circled numbers in the figure correspond with the steps described here.
Oxygenated blood fills the left ventricle. Blood that has been oxygenated in the lungs returns to the left atrium via the pulmonary vein. This blood then flows from the left atrium to the left ventricle through the mitral valve (the AV valve of the left heart).
Blood is ejected from the left ventricle into the aorta. Blood leaves the left ventricle through the aortic valve (the semilunar valve of the left side of the heart), which is located between the left ventricle and the aorta. When the left ventricle contracts, the pressure in the ventricle increases, causing the aortic valve to open and blood to be ejected forcefully into the aorta. (As noted previously, the volume of blood ejected from the left ventricle per unit time is called the cardiac output. ) Blood then flows through the arterial system, driven by the pressure created by contraction of the left ventricle.
Cardiac output is distributed among various organs. The total cardiac output of the left heart is distributed among the organ systems via sets of parallel arteries. Thus simultaneously, approximately 15% of the cardiac output is delivered to the brain via the cerebral arteries, 5% is delivered to the heart via the coronary arteries, 25% is delivered to the kidneys via the renal arteries, and so forth. Given this parallel arrangement of the organ systems, it follows that the total systemic blood flow must equal the cardiac output.
The percentage distribution of cardiac output among the various organ systems is not fixed, however. For example, during strenuous exercise, the percentage of the cardiac output going to skeletal and cardiac muscle increases, compared with the percentages at rest. There are three major mechanisms for achieving such changes in blood flow to an organ system. In the first mechanism, the cardiac output remains constant, but the blood flow is redistributed among the organ systems by the selective alteration of arteriolar resistance. In this scenario, blood flow to one organ can be increased at the expense of blood flow to other organs. In the second mechanism, the cardiac output increases or decreases, but the percentage distribution of blood flow among the organ systems is kept constant. Finally, in a third mechanism, a combination of the first two mechanisms occurs in which both cardiac output and the percentage distribution of blood flow are altered. This third mechanism is used, for example, in the response to strenuous exercise: Blood flow to skeletal and cardiac muscle increases to meet the increased metabolic demand by a combination of increased cardiac output and increased percentage distribution to skeletal and cardiac muscle.
Blood flow from the organs is collected in the veins. The blood leaving the organs is venous blood and contains waste products from metabolism, such as carbon dioxide (CO 2 ). This mixed venous blood is collected in veins of increasing size and finally in the largest vein, the vena cava. The vena cava carries blood to the right heart.
Venous return to the right atrium. Because the pressure in the vena cava is higher than in the right atrium, the right atrium fills with blood, called the venous return. In the steady state, venous return to the right atrium equals cardiac output from the left ventricle.
Mixed venous blood fills the right ventricle. Mixed venous blood flows from the right atrium to the right ventricle through the AV valve in the right heart, the tricuspid valve.
Blood is ejected from the right ventricle into the pulmonary artery. When the right ventricle contracts, blood is ejected through the pulmonic valve (the semilunar valve of the right side of the heart) into the pulmonary artery, which carries blood to the lungs. Note that the cardiac output ejected from the right ventricle is identical to the cardiac output that was ejected from the left ventricle. In the capillary beds of the lungs, oxygen (O 2 ) is added to the blood from alveolar gas, and CO 2 is removed from the blood and added to the alveolar gas. Thus the blood leaving the lungs has more O 2 and less CO 2 than the blood that entered the lungs.
Blood flow from the lungs is returned to the heart via the pulmonary vein. Oxygenated blood is returned to the left atrium via the pulmonary vein to begin a new cycle.
The term hemodynamics refers to the principles that govern blood flow in the cardiovascular system. These basic principles of physics are the same as those applied to the movement of fluids in general. The concepts of flow, pressure, resistance, and capacitance are applied to blood flow to and from the heart and within the blood vessels.
The total blood volume in a 70-kg male is approximately 5 L. Of this, normally, 85% is present in the systemic circulation, 10% is present in the pulmonary circulation, and 5% is present in the cardiac chambers at end of diastole. Of the blood volume in the systemic circulation, most (three-fourths) resides in the veins, and the remaining one-fourth resides in the arteries and capillaries; thus the systemic veins constitute a significant reservoir for the blood volume.
Blood vessel walls have the following components. The relative amount of each component varies between arteries, arterioles, capillaries, and veins, thus conveying their different functional properties.
Endothelial cells comprise a single layer that lines all blood vessels. Endothelial cells are connected by junctional complexes in arteries and, to a lesser extent, in veins. In capillaries, the “leakiness” of these junctional complexes varies, depending on the organ. Brain capillaries have narrow (“tight”) junctions that comprise the blood-brain barrier; small intestinal and glomerular capillaries have “fenestrated” capillaries, where the endothelial layer is perforated to allow passage of large volumes of fluid and solutes; liver capillaries have large gaps between endothelial cells.
Elastic fibers, comprised of an elastin core covered by microfibrils, convey the elastic properties of arteries, arterioles, and veins; they are not present in capillaries.
Collagen fibers are much stiffer than elastic fibers and are present in arteries, arterioles, and veins; they are not present in capillaries. Together with elastic fibers, collagen fibers are responsible for the passive tension of blood vessel walls.
Vascular smooth muscle cells are present in all blood vessels except capillaries. Contraction of vascular smooth muscle is responsible for active tension in blood vessels.
Blood vessels are the conduits through which blood is carried from the heart to the tissues and from the tissues back to the heart. In addition, some blood vessels (capillaries) are so thin walled that substances can exchange across them. The size of the various types of blood vessels and the histologic characteristics of their walls vary, as described above. These variations have profound effects on their resistance and capacitance properties.
Figure 4.2 is a schematic drawing of a vascular bed. The direction of blood flow through the vascular bed is from artery to arteriole, to capillaries, to venule, to vein. Figure 4.3 , a companion figure, is a graph showing the total cross-sectional area, the number of blood vessels at each level of the vasculature, and the percentage of the blood volume contained in each type of vessel.
Arteries. The aorta is the largest artery of the systemic circulation. Medium- and small-sized arteries branch off the aorta. The function of the arteries is to deliver oxygenated blood to the organs. The arteries are thick-walled structures with extensive development of elastic tissue, vascular smooth muscle, and connective tissue. The thickness of the arterial wall is a significant feature: The arteries receive blood directly from the heart and are under the highest pressure in the vasculature. The volume of blood contained in the arteries is called the stressed volume (meaning the blood volume under high pressure).
Arterioles. The arterioles are the smallest branches of the arteries. Their walls have an extensive development of vascular smooth muscle, and they are the site of highest resistance to blood flow.
The smooth muscle in the walls of the arterioles is tonically active (i.e., always contracted). It is extensively innervated by sympathetic adrenergic nerve fibers. α 1 -Adrenergic receptors are found on the arterioles of several vascular beds (e.g., skin and splanchnic vasculature). When activated, these receptors cause contraction, or constriction, of the vascular smooth muscle. Constriction produces a decrease in the diameter of the arteriole, which increases its resistance to blood flow. Less common, β 2 -adrenergic receptors are found in arterioles of skeletal muscle. When activated, these receptors cause dilation, or relaxation, of the vascular smooth muscle, which increases the diameter and decreases the resistance of these arterioles to blood flow.
Thus arterioles are not only the site of highest resistance in the vasculature, but they also are the site where resistance can be changed by alterations in sympathetic nerve activity, by circulating catecholamines, and by other vasoactive substances.
Capillaries. The capillaries are thin-walled structures lined with a single layer of endothelial cells, which is surrounded by a basal lamina. Capillaries are the site where nutrients, gases, water, and solutes are exchanged between the blood and the tissues and, in the lungs, between the blood and the alveolar gas. Lipid-soluble substances (e.g., O 2 and CO 2 ) cross the capillary wall by dissolving in and diffusing across the endothelial cell membranes. In contrast, water-soluble substances (e.g., ions) cross the capillary wall either through water-filled clefts (spaces) between the endothelial cells or through large pores in the walls of some capillaries (e.g., fenestrated capillaries).
Not all capillaries are perfused with blood at all times. Rather, there is selective perfusion of capillary beds, depending on the metabolic needs of the tissues. This selective perfusion is determined by the degree of dilation or constriction of the arterioles and precapillary sphincters (smooth muscle bands that lie “before” the capillaries). The degree of dilation or constriction is, in turn, controlled by the sympathetic innervation of vascular smooth muscle and by vasoactive metabolites produced in the tissues.
Venules and veins. Like the capillaries, the venules are thin-walled structures. The walls of the veins are composed of the usual endothelial cell layer and a modest amount of elastic tissue, vascular smooth muscle, and connective tissue. Because the walls of the veins contain much less elastic tissue than the arteries, the veins have a large capacitance (capacity to hold blood). In fact, the veins contain the largest percentage of blood in the cardiovascular system. The volume of blood contained in the veins is called the unstressed volume (meaning the blood volume under low pressure). The smooth muscle in the walls of the veins is, like that in the walls of the arterioles, innervated by sympathetic nerve fibers. Increases in sympathetic nerve activity, via α 1 -adrenergic receptors, cause contraction of the veins, which reduces their capacitance and therefore reduces the unstressed volume.
The velocity of blood flow is the rate of displacement of blood per unit time. The blood vessels of the cardiovascular system vary in terms of diameter and cross-sectional area. These differences in diameter and area, in turn, have profound effects on velocity of flow. The relationship between velocity, flow, and cross-sectional area (which depends on vessel radius or diameter) is as follows:
where
Velocity of blood flow (v) is linear velocity and refers to the rate of displacement of blood per unit time. Thus velocity is expressed in units of distance per unit time (e.g., cm/s).
Flow (Q) is volume flow per unit time and is expressed in units of volume per unit time (e.g., mL/s).
Area (A) is the cross-sectional area of a blood vessel (e.g., aorta) or a group of blood vessels (e.g., all of the capillaries). Area is calculated as A = πr 2 , where r is the radius of a single blood vessel (e.g., aorta) or the total radius of a group of blood vessels (e.g., all of the capillaries).
Figure 4.4 illustrates how changes in diameter alter the velocity of flow through a vessel. In this figure, three blood vessels are shown in order of increasing diameter and cross-sectional area. The flow through each blood vessel is identical, at 10 mL/s. However, because of the inverse relationship between velocity and cross-sectional area, as vessel diameter increases, the velocity of flow through the vessel decreases.
This example can be extrapolated to the cardiovascular system. Imagine that the smallest vessel represents the aorta, the medium-sized vessel represents all of the arteries, and the largest vessel represents all of the capillaries. The total blood flow at each level of blood vessels is the same and is equal to the cardiac output. Because of the inverse relationship between velocity and total cross-sectional area, the velocity of blood flow will be highest in the aorta and lowest in the capillaries. From the standpoint of capillary function (i.e., exchange of nutrients, solutes, and water), the low velocity of blood flow is advantageous because it maximizes the time for exchange across the capillary walls.
A man has a cardiac output of 5.5 L/min. The diameter of his aorta is estimated to be 20 mm, and the total cross-sectional area of his systemic capillaries is estimated to be 2500 cm 2 . What is the velocity of blood flow in the aorta relative to the velocity of blood flow in the capillaries?
To compare the velocity of blood flow in the aorta with the velocity in the capillaries, two values are needed for each type of blood vessel: the total blood flow (Q) and the total cross-sectional area (cm 2 ). The total flow at each level is the same and is equal to the cardiac output. The total cross-sectional area of the capillaries is given in the problem, and the cross-sectional area of the aorta must be calculated from its radius, which is 10 mm. Area = πr 2 = 3.14 × (10 mm) 2 = 3.14 × (1 cm) 2 = 3.14 cm 2 . Thus
Hence, velocity in the aorta is 800-fold that in the capillaries (1752 cm/min in the aorta compared with 2.2 cm/min in the capillaries). These calculations confirm the previous discussion concerning velocity of blood flow. The velocity of flow should be lowest in vessels with the largest total cross-sectional area (the capillaries) and highest in the vessels with the smallest total cross-sectional area (the aorta).
Blood flow through a blood vessel or a series of blood vessels is determined by two factors: the pressure difference between the two ends of the vessel (the inlet and the outlet) and the resistance of the vessel to blood flow. The pressure difference is the driving force for blood flow, and the resistance is an impediment to flow.
The relationship of flow, pressure, and resistance is analogous to the relationship of current (I), voltage (ΔV), and resistance (R) in electrical circuits, as expressed by Ohm’s law (Ohm’s law states that ΔV = I × R or I = ΔV/R). Blood flow is analogous to current flow, the pressure difference or driving force is analogous to the voltage difference, and hydrodynamic resistance is analogous to electrical resistance. The equation for blood flow is expressed as follows:
where
The magnitude of blood flow (Q) is directly proportional to the size of the pressure difference ( Δ P) or pressure gradient. The direction of blood flow is determined by the direction of the pressure gradient and always is from high to low pressure. For example, during ventricular ejection, blood flows from the left ventricle into the aorta and not in the other direction, because pressure in the ventricle is higher than pressure in the aorta. For another example, blood flows from the vena cava to the right atrium because pressure in the vena cava is slightly higher than in the right atrium.
Furthermore, blood flow is inversely proportional to resistance (R). Increasing resistance (e.g., by arteriolar vasoconstriction) decreases flow, and decreasing resistance (e.g., by arteriolar vasodilation) increases flow. The major mechanism for changing blood flow in the cardiovascular system is by changing the resistance of blood vessels, particularly the arterioles.
The flow, pressure, and resistance relationship also can be rearranged to determine resistance. If the blood flow and the pressure gradient are known, the resistance is calculated as R = ΔP/Q. This relationship can be applied to measure the resistance of the entire systemic vasculature (i.e., total peripheral resistance), or it can be used to measure resistance in a single organ or single blood vessel.
Total peripheral resistance. The resistance of the entire systemic vasculature is called the total peripheral resistance (TPR) or the systemic vascular resistance (SVR). TPR can be measured with the flow, pressure, and resistance relationship by substituting cardiac output for flow (Q) and the difference in pressure between the aorta and the vena cava for ΔP.
Resistance in a single organ. The flow, pressure, and resistance relationship also can be applied on a smaller scale to determine the resistance of a single organ. As illustrated in the following sample problem, the resistance of the renal vasculature can be determined by substituting renal blood flow for flow (Q) and the difference in pressure between the renal artery and the renal vein for ΔP.
Renal blood flow is measured by placing a flow meter on a woman’s left renal artery. Simultaneously, pressure probes are inserted in her left renal artery and left renal vein to measure pressure. Renal blood flow measured by the flow meter is 500 mL/min. The pressure probes measure renal arterial pressure as 100 mm Hg and renal venous pressure as 10 mm Hg. What is the vascular resistance of the left kidney in this woman?
Blood flow to the left kidney, as measured by the flow meter, is Q. The difference in pressure between the renal artery and renal vein is ΔP. The resistance to flow in the renal vasculature is calculated by rearranging the blood flow equation:
Rearranging and solving for R,
The blood vessels and the blood itself constitute resistance to blood flow. The relationship between resistance, blood vessel diameter (or radius), and blood viscosity is described by the Poiseuille equation. The total resistance offered by a set of blood vessels also depends on whether the vessels are arranged in series (i.e., blood flows sequentially from one vessel to the next) or in parallel (i.e., the total blood flow is distributed simultaneously among parallel vessels).
The factors that determine the resistance of a blood vessel to blood flow are expressed by the Poiseuille equation:
where
The most important concepts expressed in the Poiseuille equation are as follows: First, resistance to flow is directly proportional to viscosity (η) of the blood; for example, as viscosity increases (e.g., if the hematocrit increases), the resistance to flow also increases. Second, resistance to flow is directly proportional to the length (l) of the blood vessel. Third, and most important, resistance to flow is inversely proportional to the fourth power of the radius (r 4 ) of the blood vessel. This is a powerful relationship, indeed! When the radius of a blood vessel decreases, its resistance increases, not in a linear fashion but magnified by the fourth-power relationship. For example, if the radius of a blood vessel decreases by one-half, resistance does not simply increase twofold–it increases by 16-fold (2 4 )!
A man suffers a stroke caused by partial occlusion of his left internal carotid artery. An evaluation of the carotid artery using magnetic resonance imaging (MRI) shows a 75% reduction in its radius. Assuming that blood flow through the left internal carotid artery was 400 mL/min prior to the occlusion, what is blood flow through the artery after the occlusion?
The variable in this example is the diameter (or radius) of the left internal carotid artery. Blood flow is inversely proportional to the resistance of the artery (Q = ΔP/R), and resistance is inversely proportional to the radius raised to the fourth power (Poiseuille equation). The internal carotid artery is occluded, and its radius is decreased by 75%. Another way of expressing this reduction is to say that the radius is decreased to one-fourth its original size.
The first question is How much would resistance increase with 75% occlusion of the artery? The answer is found in the Poiseuille equation. After the occlusion, the radius of the artery is one-fourth its original radius; thus resistance has increased by 1/(1/4) 4 , or 256-fold.
The second question is What would the flow be if resistance were to increase by 256-fold? The answer is found in the flow, pressure, resistance relationship (Q = ΔP/R). Because resistance increased by 256-fold, flow decreased to 1/256, or 0.0039, or 0.39% of the original value. The flow is 0.39% of 400 mL/min, or 1.56 mL/min. Clearly, this is a dramatic decrease in blood flow to the brain, all based on the fourth-power relationship between resistance and vessel radius.
Resistances in the cardiovascular system, as in electrical circuits, can be arranged in series or in parallel ( Fig. 4.5 ). Whether the arrangement is series or parallel produces different values for total resistance.
Series resistance is illustrated by the arrangement of blood vessels within a given organ. Each organ is supplied with blood by a major artery and drained by a major vein. Within the organ, blood flows from the major artery to smaller arteries, to arterioles, to capillaries, to venules, to veins. The total resistance of the system arranged in series is equal to the sum of the individual resistances, as shown in the following equation and in Figure 4.5 . Of the various resistances in series, arteriolar resistance is by far the greatest. The total resistance of a vascular bed is determined, therefore, in large part by the arteriolar resistance. Series resistance is expressed as follows:
When resistances are arranged in series, the total flow at each level of the system is the same. For example, blood flow through the aorta equals blood flow through all the large systemic arteries, equals blood flow through all the systemic arterioles, equals blood flow through all the systemic capillaries. For another example, blood flow through the renal artery equals blood flow through all the renal capillaries, equals blood flow through the renal vein (less a small volume lost in urine). Although total flow is constant at each level in the series, the pressure decreases progressively as blood flows through each sequential component (remember Q = ΔP/R or ΔP = Q × R). The greatest decrease in pressure occurs in the arterioles because they contribute the largest portion of the resistance.
Parallel resistance is illustrated by the distribution of blood flow among the various major arteries branching off the aorta (see Figs. 4.1 and 4.5 ). Recall that the cardiac output flows through the aorta and then is distributed simultaneously, on a percentage basis, among the various organ systems. Thus there is parallel, simultaneous blood flow through each of the circulations (e.g., renal, cerebral, and coronary). The venous effluent from the organs then collects in the vena cava and returns to the heart. As shown in the following equation and in Figure 4.5 , the total resistance in a parallel arrangement is less than any of the individual resistances. The subscripts 1, 2, 3, and so forth refer to the resistances of cerebral, coronary, renal, gastrointestinal, skeletal muscle, and skin circulations. Parallel resistance is expressed as follows:
When blood flow is distributed through a set of parallel resistances, the flow through each organ is a fraction of the total blood flow. The effects of this arrangement are that there is no loss of pressure in the major arteries and that mean pressure in each major artery will be the same and be approximately the same as mean pressure in the aorta.
Another predictable consequence of a parallel arrangement is that adding a resistance to the circuit causes total resistance to decrease, not to increase. Mathematically, this can be demonstrated as follows: Four resistances, each with a numerical value of 10, are arranged in parallel. According to the equation, the total resistance is 2.5 (1/R total = 1/10 + 1/10 + 1/10 + 1/10 = 4/10). If a fifth resistance with a value of 10 is added to the parallel arrangement, the total resistance decreases to 2 (1/R total = 1/10 + 1/10 + 1/10 + 1/10 + 1/10 = 5/10).
On the other hand, if the resistance of one of the individual vessels in a parallel arrangement increases, then total resistance increases. This can be shown by returning to the parallel arrangement of four blood vessels where each individual resistance is 10 and the total resistance is 2.5. If one of the four blood vessels is completely occluded, its individual resistance becomes infinite. The total resistance of the parallel arrangement then increases to 3.333 (1/R total = 1/10 + 1/10 + 1/10 + 1/∞).
Ideally, blood flow in the cardiovascular system is laminar, or streamlined. In laminar flow, there is a smooth parabolic profile of velocity within a blood vessel, with the velocity of blood flow highest in the center of the vessel and lowest toward the vessel walls ( Fig. 4.6 ). The parabolic profile develops because the layer of blood next to the vessel wall adheres to the wall and, essentially, does not move. The next layer of blood (toward the center) slips past the motionless layer and moves a bit faster. Each successive layer of blood toward the center moves faster yet, with less adherence to adjacent layers. Thus the velocity of flow at the vessel wall is zero, and the velocity at the center of the stream is maximal. Laminar blood flow conforms to this orderly parabolic profile.
When an irregularity occurs in a blood vessel (e.g., at the valves or at the site of a blood clot), the laminar stream is disrupted and blood flow may become turbulent. In turbulent flow (see Fig. 4.6 ), the fluid streams do not remain in the parabolic profile; instead, the streams mix radially and axially. Because kinetic energy is wasted in propelling blood radially and axially, more energy (pressure) is required to drive turbulent blood flow than laminar blood flow. Laminar flow is silent, while turbulent flow is audible. For example, the Korotkoff sounds used in the auscultatory measurement of blood pressure are caused by turbulent flow. Blood vessel stenosis (narrowing) and cardiac valve disease can cause turbulent flow and often are accompanied by audible vibrations called murmurs.
The Reynolds number is a dimensionless number that is used to predict whether blood flow will be laminar or turbulent. It considers a number of factors including diameter of the blood vessel, mean velocity of flow, and viscosity of the blood. Thus
where
If Reynolds number (N R ) is less than 2000, blood flow will be laminar. If Reynolds number is greater than 2000, there is increasing likelihood that blood flow will be turbulent. Values of Reynolds number greater than 3000 always predict turbulent flow.
The major influences on Reynolds number in the cardiovascular system are changes in blood viscosity and changes in the velocity of blood flow. Inspection of the equation shows that decreases in viscosity (e.g., decreased hematocrit) cause an increase in Reynolds number. Likewise, narrowing of a blood vessel, which produces an increase in velocity of blood flow, causes an increase in Reynolds number.
The effect of narrowing a blood vessel (i.e., decreased diameter and radius) on Reynolds number is initially puzzling because, according to the equation, decreases in vessel diameter should decrease Reynolds number (diameter is in the numerator). Recall, however, that the velocity of blood flow also depends on diameter (radius), according to the earlier equation, v = Q/A or v = Q/πr 2 . Thus velocity (also in the numerator of the equation for Reynolds number) increases as radius decreases, raised to the second power. Hence, the dependence of Reynolds number on velocity is more powerful than the dependence on diameter.
Several clinical examples illustrate the application of Reynolds number in predicting turbulence.
Anemia is associated with a decreased hematocrit (decreased mass of red blood cells) and, because of turbulent blood flow, causes functional murmurs. Reynolds number, the predictor of turbulence, is increased in anemia due to decreased blood viscosity. A second cause of increased Reynolds number in patients with anemia is a high cardiac output, which causes an increase in the velocity of blood flow (v = Q/A).
Cardiac valvular disease causes narrowing of the valve, increased velocity of blood flow, and increased Reynolds number as described above. The increased Reynolds number predicts turbulence, which causes an audible vibration or murmur. (Blood flow through normal valves is silent.) Murmurs are graded, with grade 1 murmurs being barely audible with a stethoscope and grade 6 murmurs being so loud they can be heard without a stethoscope.
Atherosclerosis causes narrowing of arteries and increases blood flow velocity and Reynolds number. With advanced atherosclerotic disease, murmurs can be heard in every major artery, but are most easily detected in the carotid and femoral arteries. Arterial murmurs are called bruits.
Thrombi are blood clots in the lumen of a blood vessel. Thrombi decrease blood vessel diameter, which causes an increase in blood velocity, in Reynolds number, and in turbulence.
Shear is a consequence of the fact that blood travels at different velocities within a blood vessel (see Fig. 4.6 ). Shear occurs if adjacent layers of blood travel at different velocities; when adjacent layers travel at the same velocity, there is no shear. Thus shear is highest at the blood vessel wall, according to the following reasoning. Right at the wall, there is a motionless layer of blood (i.e., velocity is zero); the adjacent layer of blood is moving and therefore has a velocity. The greatest relative difference in velocity of blood is between the motionless layer of blood right at the wall and the next layer in. Shear is lowest at the center of the blood vessel, where the velocity of blood is highest but where the adjacent layers of blood are essentially moving at the same velocity. One consequence of shear is that it breaks up aggregates of red blood cells and decreases blood viscosity. Therefore at the wall, where shear rate is normally highest, red blood cell aggregation and viscosity are lowest.
The compliance or capacitance of a blood vessel describes the volume of blood the vessel can hold at a given pressure. Compliance is related to distensibility and is given by the following equation:
where
The equation for compliance states that the higher the compliance of a vessel, the more volume it can hold at a given pressure. Or, stated differently, compliance describes how the volume of blood contained in a vessel changes for a given change in pressure (ΔV/ΔP).
Figure 4.7 illustrates the principle of compliance and shows the relative compliance of veins and arteries. For each type of blood vessel, volume is plotted as a function of pressure. The slope of each curve is the compliance. Compliance of the veins is high; in other words, the veins hold large volumes of blood at low pressure. Compliance of the arteries is much lower than that of the veins; the arteries hold much less blood than the veins, and they do so at high pressure.
The difference in the compliance of the veins and the arteries underlies the concepts of unstressed volume and stressed volume. The veins are most compliant and contain the unstressed volume (large volume under low pressure). The arteries are much less compliant and contain the stressed volume (low volume under high pressure). The total volume of blood in the cardiovascular system is the sum of the unstressed volume plus the stressed volume (plus whatever volume is contained in the heart).
Changes in compliance of the veins cause redistribution of blood between the veins and the arteries (i.e., the blood shifts between the unstressed and stressed volumes). For example, if the compliance or capacitance of the veins decreases (e.g., due to venoconstriction), there is a decrease in the volume the veins can hold and, consequently, a shift of blood from the veins to the arteries: unstressed volume decreases and stressed volume increases. If the compliance or capacitance of the veins increases, there is an increase in the volume the veins can hold and, consequently, a shift of blood from the arteries to the veins: unstressed volume increases and stressed volume decreases. Such redistributions of blood between the veins and arteries have consequences for arterial pressure, as discussed later in this chapter.
Figure 4.7 also illustrates the effect of aging on compliance of the arteries. The characteristics of the arterial walls change with increasing age: The walls become stiffer, less distensible, and less compliant. (With age, increased cross-linking of collagen fibers in arterial walls stiffens their connections to other elements of the arterial wall.) At a given arterial pressure, the arteries can hold less blood. Another way to think of the decrease in compliance associated with aging is that in order for an “old artery” to hold the same volume as a “young artery,” the pressure in the “old artery” must be higher than the pressure in the “young artery.” Indeed, arterial pressures are increased in the elderly due to decreased arterial compliance.
Blood pressures are not equal throughout the cardiovascular system. If they were equal, blood would not flow, since flow requires a driving force (i.e., a pressure difference). The pressure differences that exist between the heart and blood vessels are the driving force for blood flow. Table 4.1 provides a summary of pressures in the systemic and pulmonary circulations.
Location | Mean Pressure (mm Hg) |
---|---|
Systemic | |
Aorta | 100 |
Large arteries | 100 (systolic, 120; diastolic, 80) |
Arterioles | 50 |
Capillaries | 20 |
Vena cava | 4 |
Right atrium | 0–2 |
Pulmonary | |
Pulmonary artery | 15 (systolic, 25; diastolic, 8) |
Capillaries | 10 |
Pulmonary vein | 8 |
Left atrium a | 2–5 |
a Pressures on the left side of the heart are difficult to measure directly. However, left atrial pressure can be measured by the pulmonary wedge pressure. With this technique, a catheter is inserted into the pulmonary artery and advanced into a small branch of the pulmonary artery. The catheter wedges and blocks all blood flow from that branch. Once the flow is stopped, the catheter senses the pressure in the left atrium almost directly.
Figure 4.8 is a profile of pressures within the systemic vasculature. First, examine the smooth profile, ignoring the pulsations. The smooth curve gives mean pressure, which is highest in the aorta and large arteries and decreases progressively as blood flows from the arteries, to the arterioles, to the capillaries, to the veins, and back to the heart. This decrease in pressure occurs as blood flows through the vasculature because energy is consumed in overcoming the frictional resistances.
Mean pressure in the aorta is high, averaging 100 mm Hg (see Table 4.1 and Fig. 4.8 ). This high mean arterial pressure is a result of two factors: the large volume of blood pumped from the left ventricle into the aorta (cardiac output) and the low compliance of the arterial wall. (Recall that a given volume causes greater pressure when compliance of the vessel is low.) The pressure remains high in the large arteries, which branch off the aorta, because of the high elastic recoil of the arterial walls. Thus little energy is lost as blood flows from the aorta through the arterial tree.
Beginning in the small arteries, arterial pressure decreases, with the most significant decrease occurring in the arterioles. At the end of the arterioles, mean pressure is approximately 30 mm Hg. This dramatic decrease in pressure occurs because the arterioles constitute a high resistance to flow. Since total blood flow is constant at all levels of the cardiovascular system, as resistance increases, downstream pressure must necessarily decrease (Q = ΔP/R, or ΔP = Q × R).
In the capillaries, pressure decreases further for two reasons: frictional resistance to flow and filtration of fluid out of the capillaries (refer to the discussion on microcirculation). When blood reaches the venules and veins, pressure has decreased even further. (Recall that because capacitance of the veins is high, the veins can hold large volumes of blood at this low pressure.) Pressure in the vena cava is only 4 mm Hg and in the right atrium is even lower at 0 to 2 mm Hg.
Further examination of Figure 4.8 reveals that although mean pressure in the arteries is high and constant, there are oscillations or pulsations of arterial pressure. These pulsations reflect the pulsatile activity of the heart: ejecting blood during systole, resting during diastole, ejecting blood, resting, and so forth. Each cycle of pulsation in the arteries coincides with one cardiac cycle.
Figure 4.9 shows an expanded version of two such cycles of pulsations in a large artery.
Diastolic pressure is the lowest arterial pressure measured during a cardiac cycle and is the pressure in the arteries during ventricular relaxation when no blood is being ejected from the left ventricle.
Systolic pressure is the highest arterial pressure measured during a cardiac cycle. It is the pressure in the arteries after blood has been ejected from the left ventricle during systole. The “blip” in the arterial pressure curve, called the dicrotic notch (or incisura ), is produced when the aortic valve closes. Aortic valve closure produces a brief period of retrograde flow from the aorta back toward the valve, briefly decreasing the aortic pressure below the systolic value.
Pulse pressure is the difference between systolic pressure and diastolic pressure. If all other factors are equal, the magnitude of the pulse pressure reflects the volume of blood ejected from the left ventricle on a single beat, or the stroke volume.
Pulse pressure can be used as an indicator of stroke volume because of the relationships between pressure, volume, and compliance. Recall that compliance of a blood vessel is the volume the vessel can hold at a given pressure (C = V/P). Thus assuming that arterial compliance is constant, arterial pressure depends on the volume of blood the artery contains at any moment in time. For example, the volume of blood in the aorta at a given time is determined by the balance between inflow and outflow of blood. When the left ventricle contracts, it rapidly ejects a stroke volume into the aorta, and the pressure rises rapidly to its highest level, the systolic pressure. Blood then begins to flow from the aorta into the rest of the arterial tree. Now, as the volume in the aorta decreases, the pressure also decreases. Arterial pressure reaches its lowest level, the diastolic pressure, when the ventricle is relaxed and blood is returning from the arterial system back to the heart.
With aging, the decreased compliance of arterial walls results in increased pulse pressure: the same stroke volume ejected into an “old” artery causes a larger increase in pressure than it does in a “young” artery.
Mean arterial pressure is the average pressure over a complete cardiac cycle and is calculated as follows:
Notice that mean arterial pressure is not the simple mathematical average of diastolic and systolic pressures. This is because a greater fraction of each cardiac cycle is spent in diastole than in systole. Thus the calculation of mean arterial pressure gives more weight to diastolic pressure than systolic pressure.
Interestingly, the pulsations in large arteries are even greater than the pulsations in the aorta (see Fig. 4.8 ). In other words, systolic pressure and pulse pressure are higher in the large arteries than in the aorta. It is not immediately obvious why pulse pressure should increase in the “downstream” arteries. The explanation resides in the fact that, following ejection of blood from the left ventricle, the pressure wave travels at a higher velocity than the blood itself travels (due to the inertia of the blood), augmenting the downstream pressure. Furthermore, at branch points of arteries, pressure waves are reflected backward, which also tends to augment pressure at those sites. (Given that blood flows from the aorta to the large arteries, it may seem odd that systolic pressure and pulse pressure are higher in the downstream arteries. We know that the direction of blood flow must be from high to low pressure and not the other way around! The explanation is that the driving force for blood flow in the arteries is the mean arterial pressure, which is influenced more by diastolic pressure than by systolic pressure (because a greater proportion of each cardiac cycle is spent in diastole). Note in Figure 4.8 that while systolic pressure is higher in the large arteries than in the aorta, diastolic pressure is lower; thus mean arterial pressure is lower downstream.)
Although systolic pressure and pulse pressure are augmented in the large arteries (compared with the aorta), from that point on, there is damping of the oscillations. The pulse pressure is still evident, but decreased, in the smaller arteries; it is virtually absent in the arterioles; and it is completely absent in the capillaries, venules, and veins. This damping and loss of pulse pressure occur for two reasons. (1) The resistance of the blood vessels, particularly the arterioles, makes it difficult to transmit the pulse pressure. (2) The compliance of the blood vessels, particularly of the veins, damps the pulse pressure—the more compliant the blood vessel, the more volume that can be added to it without causing an increase in pressure.
Several pathologic conditions alter the arterial pressure curve in a predictable way ( Fig. 4.10 ). As previously noted, pulse pressure is the change in arterial pressure that occurs when a stroke volume is ejected from the left ventricle into the aorta. Logically, then, pulse pressure will change if stroke volume changes, or if the compliance of the arteries changes.
Arteriosclerosis (see Fig. 4.10 ). In arteriosclerosis, plaque deposits in the arterial walls decrease the diameter of the arteries and make them stiffer and less compliant. Because arterial compliance is decreased, ejection of a stroke volume from the left ventricle causes a much greater change in arterial pressure than it does in normal arteries (C = ΔV/ΔP or ΔP = ΔV/C). Thus in arteriosclerosis, systolic pressure, pulse pressure, and mean pressure all will be increased.
Aortic stenosis (see Fig. 4.10 ). If the aortic valve is stenosed (narrowed), the size of the opening through which blood can be ejected from the left ventricle into the aorta is reduced. Thus stroke volume is decreased, and less blood enters the aorta on each beat. Systolic pressure, pulse pressure, and mean pressure all will be decreased.
Aortic regurgitation (not shown). When the aortic valve is incompetent (e.g., due to a congenital abnormality), the normal one-way flow of blood from the left ventricle into the aorta is disrupted. Instead, blood that was ejected into the aorta flows backward into the ventricle. Such retrograde flow can occur because the ventricle is relaxed (is at low pressure) and because the incompetent aortic valve cannot prevent it, as it normally does.
By the time blood reaches the venules and veins, pressure is less than 10 mm Hg; pressure will decrease even further in the vena cava and the right atrium. The reason for the continuing decrease in pressure is now familiar: The resistance provided by the blood vessels at each level of the systemic vasculature causes a fall in pressure. Table 4.1 and Figure 4.8 show the mean values for venous pressures in the systemic circulation.
Table 4.1 also compares pressures in the pulmonary circulation with pressures in the systemic circulation. As the table shows, the entire pulmonary vasculature is at much lower pressure than the systemic vasculature. The pattern of pressures within the pulmonary circulation is analogous to the systemic circulation, however. Blood is ejected from the right ventricle into the pulmonary artery, where pressure is highest. Thereafter, the pressure decreases as blood flows through the pulmonary arteries, arterioles, capillaries, venules, and veins and back to the left atrium.
An important implication of these lower pressures on the pulmonary side is that pulmonary vascular resistance is much lower than systemic vascular resistance. This conclusion can be reached by recalling that the total flow through the systemic and pulmonary circulations must be equal (i.e., cardiac output of the left and right hearts is equal). Because pressures on the pulmonary side are much lower than pressures on the systemic side, to achieve the same flow, pulmonary resistance must be lower than systemic resistance (Q = ΔP/R). (The pulmonary circulation is discussed in more detail in Chapter 5 .)
Cardiac electrophysiology includes all of the processes involved in the electrical activation of the heart: the cardiac action potentials; the conduction of action potentials along specialized conducting tissues; excitability and the refractory periods; the modulating effects of the autonomic nervous system on heart rate, conduction velocity, and excitability; and the electrocardiogram (ECG).
Ultimately, the function of the heart is to pump blood through the vasculature. To serve as a pump, the ventricles must be electrically activated and then contract. In cardiac muscle, electrical activation is the cardiac action potential, which normally originates in the sinoatrial (SA) node. The action potentials initiated in the SA node then are conducted to the entire myocardium in a specific, timed sequence. Contraction follows, also in a specific sequence. “Sequence” is especially critical because the atria must be activated and contract before the ventricles, and the ventricles must contract from apex to base for efficient ejection of blood.
The heart consists of two kinds of muscle cells: contractile cells and conducting cells. Contractile cells constitute the majority of atrial and ventricular tissues and are the working cells of the heart. Action potentials in contractile cells lead to contraction and generation of force or pressure. Conducting cells constitute the tissues of the SA node, the atrial internodal tracts, the AV node, the bundle of His, and the Purkinje system. Conducting cells are specialized muscle cells that do not contribute significantly to generation of force; instead, they function to rapidly spread action potentials over the entire myocardium. Another feature of the specialized conducting tissues is their capacity to generate action potentials spontaneously. Except for the SA node, however, this capacity normally is suppressed.
Figure 4.11 is a schematic drawing showing the relationships of the SA node, atria, ventricles, and specialized conducting tissues. The action potential spreads throughout the myocardium in the following sequence:
SA node. Normally, the action potential of the heart is initiated in the specialized tissue of the SA node, which serves as the pacemaker. After the action potential is initiated in the SA node, there is a specific sequence and timing for the conduction of action potentials to the rest of the heart.
Atrial internodal tracts and atria. The action potential spreads from the SA node to the right and left atria via the atrial internodal tracts. Simultaneously, the action potential is conducted to the AV node.
AV node. Conduction velocity through the AV node is considerably slower than in the other cardiac tissues. Slow conduction through the AV node ensures that the ventricles have sufficient time to fill with blood before they are activated and contract. Increases in conduction velocity of the AV node can lead to decreased ventricular filling and decreased stroke volume and cardiac output.
Bundle of His, Purkinje system, and ventricles. From the AV node, the action potential enters the specialized conducting system of the ventricles. The action potential is first conducted to the bundle of His through the common bundle. It then invades the left and right bundle branches and then the smaller bundles of the Purkinje system. Conduction through the His-Purkinje system is extremely fast, and it rapidly distributes the action potential to the ventricles. The action potential also spreads from one ventricular muscle cell to the next, via low-resistance pathways between the cells. Rapid conduction of the action potential throughout the ventricles is essential and allows for efficient contraction and ejection of blood.
The term normal sinus rhythm has a specific meaning. It means that the pattern and timing of the electrical activation of the heart are normal. To qualify as normal sinus rhythm, the following three criteria must be met: (1) The action potential must originate in the SA node. (2) The SA nodal impulses must occur regularly at a rate of 60 to 100 impulses per minute. (3) The activation of the myocardium must occur in the correct sequence and with the correct timing and delays.
The concepts applied to cardiac action potentials are the same concepts that are applied to action potentials in nerve, skeletal muscle, and smooth muscle. The following section is a summary of those principles, which are discussed in Chapter 1 :
The membrane potential of cardiac cells is determined by the relative conductances (or permeabilities) to ions and the concentration gradients for the permeant ions.
If the cell membrane has a high conductance or permeability to an ion, that ion will flow down its electrochemical gradient and attempt to drive the membrane potential toward its equilibrium potential (calculated by the Nernst equation). If the cell membrane has low conductance or permeability to an ion or is impermeable to the ion, that ion will make little or no contribution to the membrane potential.
By convention, membrane potential is expressed in millivolts (mV), and intracellular potential is expressed relative to extracellular potential; for example, a membrane potential of −85 mV means 85 mV, cell interior negative.
The resting membrane potential of cardiac cells is determined primarily by potassium ions (K + ). The conductance to K + at rest is high, and the resting membrane potential is close to the K + equilibrium potential. Since the conductance to sodium (Na + ) at rest is low, Na + contributes little to the resting membrane potential.
The role of Na + -K + ATPase is primarily to maintain Na + and K + concentration gradients across the cell membrane, although it makes a small direct electrogenic contribution to the membrane potential.
Changes in membrane potential are caused by the flow of ions into or out of the cell. For ion flow to occur, the cell membrane must be permeable to that ion. Depolarization means the membrane potential has become less negative. Depolarization occurs when there is net movement of positive charge into the cell, which is called an inward current. Hyperpolarization means the membrane potential has become more negative, and it occurs when there is net movement of positive charge out of the cell, which is called an outward current.
Two basic mechanisms can produce a change in membrane potential. In one mechanism, there is a change in the electrochemical gradient for a permeant ion, which changes the equilibrium potential for that ion. The permeant ion then will flow into or out of the cell in an attempt to reestablish electrochemical equilibrium, and this current flow will alter the membrane potential. For example, consider the effect of decreasing the extracellular K + concentration on the resting membrane potential of a myocardial cell. The K + equilibrium potential, calculated by the Nernst equation, will become more negative. K + ions will then flow out of the cell and down the now larger electrochemical gradient, driving the resting membrane potential toward the new, more negative K + equilibrium potential.
In the other mechanism, there is a change in conductance to an ion. For example, the resting permeability of ventricular cells to Na + is quite low, and Na + contributes minimally to the resting membrane potential. However, during the upstroke of the ventricular action potential, Na + conductance dramatically increases, Na + flows into the cell down its electrochemical gradient, and the membrane potential is briefly driven toward the Na + equilibrium potential (i.e., is depolarized).
Threshold potential is the potential difference at which there is a net inward current (i.e., inward current becomes greater than outward current). At threshold potential, the depolarization becomes self-sustained and gives rise to the upstroke of the action potential.
The ionic basis for the action potentials in the ventricles, atria, and Purkinje system is identical. The action potential in these tissues shares the following characteristics ( Table 4.2 ):
Long duration. In each of these tissues, the action potential is of long duration. Action potential duration varies from 150 ms in atria, to 250 ms in ventricles, to 300 ms in Purkinje fibers. These durations can be compared with the brief duration of the action potential in nerve and skeletal muscle (1–2 ms). Recall that the duration of the action potential also determines the duration of the refractory periods: The longer the action potential, the longer the cell is refractory to firing another action potential. Thus atrial, ventricular, and Purkinje cells have long refractory periods compared with other excitable tissues.
Stable resting membrane potential. The cells of the atria, ventricles, and Purkinje system exhibit a stable, or constant, resting membrane potential. (AV nodal and Purkinje fibers can develop unstable resting membrane potentials, and under special conditions, they can become the heart’s pacemaker, as discussed in the section on latent pacemakers.)
Plateau. The action potential in cells of the atria, ventricles, and Purkinje system is characterized by a plateau. The plateau is a sustained period of depolarization, which accounts for the long duration of the action potential and, consequently, the long refractory periods.
Cardiac Tissue | Action Potential Duration (ms) | Upstroke | Plateau | Phase 4 Depolarization |
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Figure 4.12 A and B illustrate the action potential in a ventricular muscle fiber and an atrial muscle fiber. An action potential in a Purkinje fiber (not shown) would look similar to that in the ventricular fiber, but its duration would be slightly longer. The phases of the action potential are described subsequently and correspond to the numbered phases shown in Figure 4.12 A and B. The ventricular action potential has also been redrawn in Figure 4.13 to show the ionic currents responsible for each phase. Some of this information also is summarized in Table 4.2 .
Phase 0, upstroke. In ventricular, atrial, and Purkinje fibers, the action potential begins with a phase of rapid depolarization, called the upstroke. As in nerve and skeletal muscle, the upstroke is caused by a transient increase in Na + conductance (g Na ) produced by depolarization-induced opening of activation gates on the Na + channels. When g Na increases, there is an inward Na + current (influx of Na + into the cell), or I Na , which drives the membrane potential toward the Na + equilibrium potential of approximately +65 mV. The membrane potential does not quite reach the Na + equilibrium potential because, as in nerve, the inactivation gates on the Na + channels close in response to depolarization (albeit more slowly than the activation gates open). Thus the Na + channels open briefly and then close. At the peak of the upstroke, the membrane potential is depolarized to a value of about +20 mV.
The rate of rise of the upstroke is called dV/dT. dV/dT is the rate of change of the membrane potential as a function of time, and its units are volts per second (V/s). dV/dT varies, depending on the value of the resting membrane potential. This dependence is called the responsiveness relationship. Thus dV/dT is greatest (the rate of rise of the upstroke is fastest) when the resting membrane potential is most negative, or hyperpolarized (e.g., −90 mV), and dV/dT is lowest (the rate of rise of the upstroke is slowest) when the resting membrane potential is less negative, or depolarized (e.g., −60 mV). This correlation is based on the relationship between membrane potential and the position of the inactivation gates on the Na + channel (see Chapter 1 ). When the resting membrane potential is relatively hyperpolarized (e.g., −90 mV), the voltage-dependent inactivation gates are open and many Na + channels are available for the upstroke. When the resting membrane potential is relatively depolarized (e.g., −60 mV), the inactivation gates on the Na + channels tend to be closed and fewer Na + channels are available to open during the upstroke. dV/dT also correlates with the size of the inward current (i.e., in ventricular, atrial, and Purkinje fibers, the size of the inward Na + current).
Phase 1, initial repolarization. Phase 1 in ventricular, atrial, and Purkinje fibers is a brief period of repolarization, which immediately follows the upstroke. Recall that, for repolarization to occur, there must be a net outward current. There are two explanations for the occurrence of the net outward current during phase 1. First, the inactivation gates on the Na + channels close in response to depolarization. When these gates close, g Na decreases and the inward Na + current (which caused the upstroke) ceases. Second, there is an outward K + current, caused by the large driving force on K + ions: At the peak of the upstroke, both the chemical and the electrical driving forces favor K + movement out of the cell (the intracellular K + concentration is higher than extracellular K + concentration, and the cell interior is electrically positive). Because the K + conductance (g K ) is high, K + flows out of the cell, down this steep electrochemical gradient.
Phase 2, plateau. During the plateau, there is a long period (150–200 ms) of relatively stable, depolarized membrane potential, particularly in ventricular and Purkinje fibers. (In atrial fibers, the plateau is shorter than in ventricular fibers.) Recall that for the membrane potential to be stable, inward and outward currents must be equal such that there is no net current flow across the membrane.
How is such a balance of inward and outward currents achieved during the plateau? There is an increase in calcium (Ca 2+ ) conductance (g Ca ), which results in an inward Ca 2+ current. Inward Ca 2+ current is also called slow inward current, reflecting the slower kinetics of these channels (compared with the fast Na + channels of the upstroke). The Ca 2+ channels that open during the plateau are L-type channels and are inhibited by the Ca 2+ channel blockers nifedipine, diltiazem, and verapamil. To balance the inward Ca 2+ current, there is an outward K + current, driven by the electrochemical driving force on K + ions (as described for phase 1). Thus during the plateau, the inward Ca 2+ current is balanced by the outward K + current, the net current is zero, and the membrane potential remains at a stable depolarized value. (See Fig. 4.13 , where during phase 2, the inward Ca 2+ current is shown as equal in magnitude to the outward K + current.)
The significance of the inward Ca 2+ current extends beyond its effect on membrane potential. This Ca 2+ entry during the plateau of the action potential initiates the release of more Ca 2+ from intracellular stores for excitation-contraction coupling. This process of so-called Ca 2+ -induced Ca 2+ release is discussed in the section on cardiac muscle contraction.
Phase 3, repolarization. Repolarization begins gradually at the end of phase 2, and then there is rapid repolarization to the resting membrane potential during phase 3. Recall that repolarization is produced when outward currents are greater than inward currents. During phase 3, repolarization results from a combination of a decrease in g Ca (previously increased during the plateau) and an increase in g K (to even higher levels than at rest). The reduction in g Ca results in a decrease in the inward Ca 2+ current, and the increase in g K results in an increase in the outward K + current (I K ), with K + moving down a steep electrochemical gradient (as described for phase 1). At the end of phase 3, the outward K + current is reduced because repolarization brings the membrane potential closer to the K + equilibrium potential, thus decreasing the driving force on K + .
Phase 4, resting membrane potential, or electrical diastole. The membrane potential fully repolarizes during phase 3 and returns to the resting level of approximately −85 mV. During phase 4, the membrane potential is stable again, and inward and outward currents are equal. The resting membrane potential approaches, but does not fully reach, the K + equilibrium potential, reflecting the high resting conductance to K + . The K + channels, and the resulting K + current, responsible for phase 4 are different from those responsible for repolarization in phase 3. In phase 4, the K + conductance is called g K1 and the K + current is called, accordingly, I K1 .
The stable membrane potential in phase 4 means that inward and outward currents are equal. The high conductance to K + produces an outward K + current (I K1 ), which has already been described. The inward current that balances this outward current is carried by Na + and Ca 2+ (see Fig. 4.13 ), even though the conductances to Na + and Ca 2+ are low at rest. The question may arise: How can the sum of inward Na + and Ca 2+ currents be the same magnitude as the outward K + current, given that g Na and g Ca are very low and g K1 is very high? The answer lies in the fact that, for each ion, current = conductance × driving force. Although g K1 is high, the driving force on K + is low because the resting membrane potential is close to the K + equilibrium potential; thus the outward K + current is relatively small. On the other hand, g Na and g Ca are both low, but the driving forces on Na + and Ca 2+ are high because the resting membrane potential is far from the Na + and Ca 2+ equilibrium potentials; thus the sum of the inward currents carried by Na + and Ca 2+ is equal to the outward current carried by K + .
The SA node is the normal pacemaker of the heart. The configuration and ionic basis for its action potential differ in several important aspects from those in atrial, ventricular, and Purkinje fibers (see Fig. 4.12 C). The following features of the action potential of the SA node are different from those in atria, ventricles, and Purkinje fibers: (1) The SA node exhibits automaticity; that is, it can spontaneously generate action potentials without neural input. (2) It has an unstable resting membrane potential, in direct contrast to cells in atrial, ventricular, and Purkinje fibers. (3) It has no sustained plateau.
The phases of the SA node action potential are described here and correspond to the numbered phases shown in Figure 4.12 C.
Phase 0, upstroke. Phase 0 (as in the other cardiac cells) is the upstroke of the action potential. Note that the upstroke is not as rapid or as steep as in the other types of cardiac tissues. The ionic basis for the upstroke in the SA node differs as well. In the other myocardial cells, the upstroke is the result of an increase in g Na and an inward Na + current. In the SA nodal cells, the upstroke is the result of an increase in g Ca and an inward Ca 2+ current carried primarily by L-type Ca 2+ channels. There are also T-type Ca 2+ channels in SA node, which carry part of the inward Ca 2+ current of the upstroke.
Phases 1 and 2 are absent.
Phase 3, repolarization. As in the other myocardial tissues, repolarization in the SA node is due to an increase in g K . Because the electrochemical driving forces on K + are large (both chemical and electrical driving forces favor K + leaving the cell), there is an outward K + current, which repolarizes the membrane potential.
Phase 4, spontaneous depolarization or pacemaker potential. Phase 4 is the longest portion of the SA node action potential. This phase accounts for the automaticity of SA nodal cells (the ability to spontaneously generate action potentials without neural input). During phase 4, the most negative value of the membrane potential (called the maximum diastolic potential ) is approximately −65 mV, but the membrane potential does not remain at this value. Rather, there is a slow depolarization, produced by the opening of Na + channels and an inward Na + current called I f . The “f,” which stands for funny, denotes that this Na + current differs from the fast Na + current responsible for the upstroke in ventricular cells. I f is turned on by repolarization from the preceding action potential, thus ensuring that each action potential in the SA node will be followed by another action potential. Once I f and slow depolarization bring the membrane potential to threshold, the Ca 2+ channels are opened for the upstroke.
The rate of phase 4 depolarization is one determinant of heart rate. If the rate of phase 4 depolarization increases, threshold is reached more quickly, the SA node will fire more action potentials per time, and heart rate will increase. Conversely, if the rate of phase 4 depolarization decreases, threshold is reached more slowly, the SA node will fire fewer action potentials per time, and heart rate will decrease. The effects of the autonomic nervous system on heart rate are based on such changes in the rate of phase 4 depolarization and are discussed later in the chapter.
The cells in the SA node are not the only myocardial cells with intrinsic automaticity; other cells, called latent pacemakers, also have the capacity for spontaneous phase 4 depolarization. Latent pacemakers include the cells of the AV node, bundle of His, and Purkinje fibers. Although each of these cells has the potential for automaticity, it normally is not expressed.
The rule is that the pacemaker with the fastest rate of phase 4 depolarization controls the heart rate. Normally, the SA node has the fastest rate of phase 4 depolarization, and therefore it sets the heart rate ( Table 4.3 ). Recall also that, of all myocardial cells, the SA nodal cells have the shortest action potential duration (i.e., the shortest refractory periods). Therefore SA nodal cells recover faster and are ready to fire another action potential before the other cell types are ready.
Location | Intrinsic Firing Rate (Impulses/min) |
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Sinoatrial node | 70–80 |
Atrioventricular node | 40–60 |
Bundle of His | 40 |
Purkinje fibers | 15–20 |
When the SA node drives the heart rate, the latent pacemakers are suppressed, a phenomenon called overdrive suppression, which is explained as follows: The SA node has the fastest firing rate of all the potential pacemakers, and impulses spread from the SA node to the other myocardial tissues in the sequence illustrated in Figure 4.11 . Although some of these tissues are potential pacemakers themselves (AV node, bundle of His, Purkinje fibers), as long as their firing rate is driven by the SA node, their own capacity to spontaneously depolarize is suppressed.
The latent pacemakers have an opportunity to drive the heart rate only if the SA node is suppressed or if the intrinsic firing rate of a latent pacemaker becomes faster than that of the SA node. Since the intrinsic rate of the latent pacemakers is slower than that of the SA node, the heart will beat at the slower rate if it is driven by a latent pacemaker (see Table 4.3 ).
Under the following conditions a latent pacemaker takes over and becomes the pacemaker of the heart, in which case it is called an ectopic pacemaker, or ectopic focus. (1) If the SA node firing rate decreases (e.g., due to vagal stimulation) or stops completely (e.g., because the SA node is destroyed, removed, or suppressed by drugs), then one of the latent sites will assume the role of pacemaker in the heart. (2) Or, if the intrinsic rate of firing of one of the latent pacemakers should become faster than that of the SA node, then it will assume the pacemaker role. (3) Or, if the conduction of action potentials from the SA node to the rest of the heart is blocked because of disease in the conducting pathways, then a latent pacemaker can appear in addition to the SA node.
In the heart, conduction velocity has the same meaning that it has in nerve and skeletal muscle fibers: It is the speed at which action potentials are propagated within the tissue. The units for conduction velocity are meters per second (m/s). Conduction velocity is not the same in all myocardial tissues: It is slowest in the AV node (0.01–0.05 m/s) and fastest in the Purkinje fibers (2–4 m/s), as shown in Figure 4.14 .
Conduction velocity determines how long it takes the action potential to spread to various locations in the myocardium. These times, in milliseconds, are superimposed on the diagram in Figure 4.14 . The action potential originates in the SA node at what is called time zero. It then takes a total of 220 ms for the action potential to spread through the atria, AV node, and His-Purkinje system to the farthest points in the ventricles. Conduction through the AV node (called AV delay ) requires almost one-half of the total conduction time through the myocardium. The reason for the AV delay is that, of all the myocardial tissues, conduction velocity in the AV node is slowest (0.01–0.05 m/s), making conduction time the longest (100 ms).
Differences in conduction velocity among the cardiac tissues have implications for their physiologic functions. For example, the slow conduction velocity of the AV node ensures that the ventricles do not activate too early (i.e., before they have time to fill with blood from the atria). On the other hand, the rapid conduction velocity of the Purkinje fibers ensures that the ventricles can be activated quickly and in a smooth sequence for efficient ejection of blood.
As in nerve and skeletal muscle fibers, the physiologic basis for conduction of cardiac action potentials is the spread of local currents (see Chapter 1 ). Action potentials at one site generate local currents at adjacent sites; the adjacent sites are depolarized to threshold as a result of this local current flow and fire action potentials themselves. This local current flow is the result of the inward current of the upstroke of the action potential. Recall that, in atrial, ventricular, and Purkinje fibers, this inward current of the upstroke is carried by Na + , and in the SA node, the inward current of the upstroke is carried by Ca 2+ .
Conduction velocity depends on the size of the inward current during the upstroke of the action potential. The larger the inward current, the more rapidly local currents will spread to adjacent sites and depolarize them to threshold. Conduction velocity also correlates with dV/dT, the rate of rise of the upstroke of the action potential, because dV/dT also correlates with the size of the inward current, as discussed previously.
Propagation of the action potential depends not only on the inward current of the upstroke to establish local currents but also on the cable properties of the myocardial fibers. Recall that these cable properties are determined by cell membrane resistance (R m ) and internal resistance (R i ). For example, in myocardial tissue, R i is particularly low because of low-resistance connections between the cells called gap junctions. Thus myocardial tissue is especially well suited to fast conduction.
Conduction velocity does not depend on action potential duration, a point that can be confusing. Recall, however, that action potential duration is simply the time it takes a given site to go from depolarization to complete repolarization (e.g., action potential duration in a ventricular cell is 250 ms). Action potential duration implies nothing about how long it takes for that action potential to spread to neighboring sites.
Excitability is the capacity of myocardial cells to generate action potentials in response to inward, depolarizing current. Strictly speaking, excitability is the amount of inward current required to bring a myocardial cell to the threshold potential. The excitability of a myocardial cell varies over the course of the action potential, and these changes in excitability are reflected in the refractory periods.
The physiologic basis for the refractory periods in myocardial cells is similar to that in nerve cells. Recall from Chapter 1 that activation gates on Na + channels open when the membrane potential is depolarized to threshold, permitting a rapid influx of Na + into the cell, which causes further depolarization toward the Na + equilibrium potential. This rapid depolarization is the upstroke of the action potential. However, inactivation gates on the Na + channels also close with depolarization (although they close more slowly than the activation gates open). Therefore during those phases of the action potential when the membrane potential is depolarized, a portion of the Na + channels will be closed and unavailable because the inactivation gates are closed. When the Na + channels are closed and unavailable, inward depolarizing current cannot flow through them, there can be no upstroke or action potential, and the cell is called refractory. Once repolarization occurs, the inactivation gates on the Na + channels open and now the Na + channels will be in the closed, but available state; the cell will once again be excitable and ready to fire another action potential.
Figure 4.15 is a familiar diagram showing an action potential in ventricular muscle, with the refractory periods now superimposed on it. The following refractory periods reflect differences in excitability over the duration of the action potential:
Absolute refractory period (ARP). For most of the duration of the action potential, the ventricular cell is completely refractory to fire another action potential. No matter how large a stimulus might be applied, the cell is incapable of generating a second action potential during the ARP, because most of the Na + channels are closed and unavailable to carry inward current. The ARP includes the upstroke, the entire plateau, and a portion of the repolarization. This period concludes when the cell has repolarized to approximately −50 mV.
Effective refractory period (ERP). The ERP includes, and is slightly longer than, the ARP. At the end of the ERP, the Na + channels start to recover (i.e., become available to carry inward current). The distinction between the absolute and ERPs is that absolute means absolutely no stimulus is large enough to generate another action potential; effective means that a conducted action potential cannot be generated (i.e., there is not enough inward current to conduct to the next site).
Relative refractory period (RRP). The RRP begins at the end of the ARP and continues until the cell membrane has almost fully repolarized. During the RRP, even more Na + channels have recovered to the closed, but available state and it is possible to generate another action potential, although a greater-than-normal stimulus is required. If another action potential is generated during the RRP, it will have an abnormal configuration and a shortened plateau phase.
Supranormal period (SNP). The SNP follows the RRP. It begins when the membrane potential is −70 mV and continues until the membrane is fully repolarized back to −85 mV. As the name suggests, the cell is more excitable than normal during this period. In other words, less inward current is required to depolarize the cell to the threshold potential. The physiologic explanation for this increased excitability is that the Na + channels are recovered (i.e., the inactivation gates are open again), and because the membrane potential is closer to threshold than it is at rest, it is easier to fire an action potential than when the cell membrane is at the resting membrane potential.
Table 4.4 summarizes the effects of the autonomic nervous system on the heart and blood vessels. For convenience, the autonomic effects on heart rate, conduction velocity, myocardial contractility, and vascular smooth muscle are combined into one table. The effects on cardiac electrophysiology (i.e., heart rate and conduction velocity) are discussed in this section, and the other autonomic effects are discussed in later sections.
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The effects of the autonomic nervous system on heart rate are called chronotropic effects. The effects of the sympathetic and parasympathetic nervous systems on heart rate are summarized in Table 4.4 and are illustrated in Figure 4.16 . Briefly, sympathetic stimulation increases heart rate and parasympathetic stimulation decreases heart rate.
Figure 4.16 A shows the normal firing pattern of the SA node. Recall that phase 4 depolarization is produced by opening Na + channels, which leads to a slow depolarizing, inward Na + current called I f . Once the membrane potential is depolarized to the threshold potential, an action potential is initiated.
Positive chronotropic effects are increases in heart rate. The most important example is that of stimulation of the sympathetic nervous system, as illustrated in Figure 4.16 B. Norepinephrine, released from sympathetic nerve fibers, activates β 1 receptors in the SA node. These β 1 receptors are coupled to adenylyl cyclase through a G s protein (see also Chapter 2 ). Activation of β 1 receptors in the SA node produces an increase in I f , which increases the rate of phase 4 depolarization. In addition, there is an increase in I Ca , which means there are more functional Ca 2+ channels and thus less depolarization is required to reach threshold (i.e., threshold potential decreases). Increasing the rate of phase 4 depolarization and decreasing the threshold potential means that the SA node is depolarized to threshold potential more frequently and, as a consequence, fires more action potentials per unit time (i.e., increased heart rate).
Negative chronotropic effects are decreases in heart rate. The most important example is that of stimulation of the parasympathetic nervous system, illustrated in Figure 4.16 C. Acetylcholine (ACh), released from parasympathetic nerve fibers, activates muscarinic (M 2 ) receptors in the SA node. Activation of muscarinic receptors in the SA node has two effects that combine to produce a decrease in heart rate. First, these muscarinic receptors are coupled to a type of G i protein called G K that inhibits adenylyl cyclase and produces a decrease in I f . A decrease in I f decreases the rate of phase 4 depolarization. Second, G K directly increases the conductance of a K + channel called K + -ACh and increases an outward K + current (similar to I K1 ) called I K-ACh . Enhancing this outward K + current hyperpolarizes the maximum diastolic potential so that the SA nodal cells are further from threshold potential. In addition, there is a decrease in I Ca , which means there are fewer functional Ca 2+ channels and thus more depolarization is required to reach threshold (i.e., threshold potential increases). In sum, the parasympathetic nervous system decreases heart rate through three effects on the SA node: (1) slowing the rate of phase 4 depolarization, (2) hyperpolarizing the maximum diastolic potential so that more inward current is required to reach threshold potential, and (3) increasing the threshold potential. As a result, the SA node is depolarized to threshold less frequently and fires fewer action potentials per unit time (i.e., decreased heart rate) ( Box 4.1 ).
A 72-year-old woman with hypertension is being treated with propranolol, a β-adrenergic blocking agent. She has experienced several episodes of light-headedness and syncope (fainting). An ECG shows sinus bradycardia: normal, regular P waves, followed by normal QRS complexes; however, the frequency of P waves is decreased, at 45/min. The physician tapers off and eventually discontinues the propranolol and then changes the woman’s medication to a different class of antihypertensive drugs. Upon discontinuation of propranolol, a repeat ECG shows a normal sinus rhythm with a frequency of P waves of 80/min.
The heart rate is given by the frequency of P waves. During treatment with propranolol, her heart rate was only 45 beats/min. The presence of P waves on the ECG indicates that the heart is being activated in the SA node, which is the normal pacemaker. However, the frequency of depolarization of the SA node is much lower than normal because she is being treated with propranolol, a β-adrenergic blocking agent. Recall that β-adrenergic agonists increase the rate of phase 4 depolarization in the SA node by increasing I f . β-Adrenergic antagonists, therefore, will decrease phase 4 depolarization and decrease the frequency at which the SA nodal cells fire action potentials.
The woman’s sinus bradycardia was an adverse effect of propranolol therapy. When propranolol was discontinued, her heart rate returned to normal.
The effects of the autonomic nervous system on conduction velocity are called dromotropic effects. Increases in conduction velocity are called positive dromotropic effects, and decreases in conduction velocity are called negative dromotropic effects. The most important physiologic effects of the autonomic nervous system on conduction velocity are those on the AV node, which, in effect, alter the rate at which action potentials are conducted from the atria to the ventricles. Recall, in considering the mechanism of these autonomic effects, that conduction velocity correlates with the size of the inward current of the upstroke of the action potential and the rate of rise of the upstroke, dV/dT.
Stimulation of the sympathetic nervous system produces an increase in conduction velocity through the AV node (positive dromotropic effect), which increases the rate at which action potentials are conducted from the atria to the ventricles. The mechanism of the sympathetic effect is increased I Ca , which is responsible for the upstroke of the action potential in the AV node (as it is in the SA node). Thus increased I Ca means increased inward current and increased conduction velocity. In a supportive role, the increased I Ca shortens the ERP so that the AV nodal cells recover earlier from inactivation and can conduct action potentials at the increased firing rate.
Stimulation of the parasympathetic nervous system produces a decrease in conduction velocity through the AV node (negative dromotropic effect), which decreases the rate at which action potentials are conducted from the atria to the ventricles. The mechanism of the parasympathetic effect is a combination of decreased I Ca (decreased inward current) and increased I K-ACh (increased outward K + current, which further reduces net inward current). Additionally, the ERP of AV nodal cells is prolonged. If conduction velocity through the AV node is slowed sufficiently (e.g., by increased parasympathetic activity or by damage to the AV node), some action potentials may not be conducted at all from the atria to the ventricles, producing heart block. The degree of heart block may vary: In the milder forms, conduction of action potentials from atria to ventricles is simply slowed; in more severe cases, action potentials may not be conducted to the ventricles at all.
The electrocardiogram (ECG or EKG) is a measurement of tiny potential differences on the surface of the body that reflect the electrical activity of the heart. Briefly, these potential differences or voltages are measurable on the body’s surface because of the timing and sequence of depolarization and repolarization of the heart. Recall that the entire myocardium is not depolarized at once: The atria depolarize before the ventricles; the ventricles depolarize in a specific sequence; the atria repolarize while the ventricles are depolarizing; and the ventricles repolarize in a specific sequence. As a result of the sequence and the timing of the spread of depolarization and repolarization in the myocardium, potential differences are established between different portions of the heart, which can be detected by electrodes placed on the body surface.
The configuration of a normal ECG is shown in Figure 4.17 . The nomenclature of the ECG is as follows: The various waves represent depolarization or repolarization of different portions of the myocardium and are given lettered names. Intervals and segments between the waves also are named. The difference between intervals and segments is that intervals include the waves, and segments do not. The following waves, intervals, and segments are seen on the ECG:
P wave. The P wave represents depolarization of the atria. The duration of the P wave correlates with conduction time through the atria; for example, if conduction velocity through the atria decreases, the P wave will spread out. Atrial repolarization is not seen on a normal ECG because it is “buried” in the QRS complex.
PR interval. The PR interval is the time from initial depolarization of the atria to initial depolarization of the ventricles. Thus the PR interval includes the P wave and the PR segment, an isoelectric (flat) portion of the ECG that corresponds to AV node conduction. Because the PR interval includes the PR segment, it also correlates with conduction time through the AV node.
Normally, the PR interval is 160 ms, which is the cumulative time from first depolarization of the atria to first depolarization of the ventricles (see Fig. 4.14 ). Increases in conduction velocity through the AV node decrease the PR interval (e.g., due to sympathetic stimulation), and decreases in conduction velocity through the AV node increase the PR interval (e.g., due to parasympathetic stimulation).
QRS complex. The QRS complex consists of three waves: Q, R, and S. Collectively, these waves represent depolarization of the ventricles. Note that the total duration of the QRS complex is similar to that of the P wave. This fact may seem surprising because the ventricles are so much larger than the atria; however, the ventricles depolarize just as quickly as the atria because conduction velocity in the His-Purkinje system is much faster than in the atrial conducting system.
T wave. The T wave represents repolarization of the ventricles.
QT interval. The QT interval includes the QRS complex, the ST segment, and the T wave. It represents first ventricular depolarization to last ventricular repolarization. The ST segment is an isoelectric portion of the QT interval that correlates with the plateau of the ventricular action potential.
Heart rate is measured by counting the number of QRS complexes (or R waves because they are most prominent) per minute. Cycle length is the R-R interval (the time between one R wave and the next). Heart rate is related to cycle length as follows:
If the R-R interval is 800 ms (0.8 s), what is the heart rate? If the heart rate is 90 beats/min, what is the cycle length?
The R-R interval is the cycle length. If the cycle length is 0.8 s, then the heart rate = 1/cycle length or 1.25 beats/s or 75 beats/min (1 beat/0.8 s). If the heart rate is 90 beats/min, then the cycle length = 1/heart rate or 0.66 s or 660 ms. A longer cycle length signifies a slower heart rate, and a shorter cycle length signifies a faster heart rate.
Changes in heart rate (and cycle length) change the duration of the action potential and, as a result, change the durations of the refractory periods and excitability. For example, if heart rate increases (and cycle length decreases), there is a decrease in the duration of the action potential. Not only will there be more action potentials per time, but those action potentials will have a shorter duration and shorter refractory periods. Because of the relationship between heart rate and refractory period, increases in heart rate may be a factor in producing arrhythmias (abnormal heart rhythms). As heart rate increases and refractory periods shorten, the myocardial cells are excitable earlier and more often.
There are several morphologic and functional differences between cardiac muscle and skeletal muscle, but the basic contractile machinery in the two cell types is similar.
As in skeletal muscle, the cardiac muscle cell is composed of sarcomeres . The sarcomeres, which run from Z line to Z line, are composed of thick and thin filaments. The thick filaments are composed of myosin, whose globular heads have actin-binding sites and ATPase activity. The thin filaments are composed of three proteins: actin, tropomyosin, and troponin. Actin is a globular protein with a myosin-binding site, which, when polymerized, forms two twisted strands. Tropomyosin runs along the groove of the twisted actin strands and functions to block the myosin-binding site. Troponin is a globular protein composed of a complex of three subunits; the troponin C subunit binds Ca 2+ . When Ca 2+ is bound to troponin C, a conformational change occurs, which removes the tropomyosin inhibition of actin-myosin interaction.
As in skeletal muscle, contraction occurs according to the sliding filament model, which states that when cross-bridges form between myosin and actin and then break, the thick and thin filaments move past each other. As a result of this cross-bridge cycling, the muscle fiber produces tension.
The transverse (T) tubules invaginate cardiac muscle cells at the Z lines, are continuous with the cell membranes, and function to carry action potentials to the cell interior. The T tubules form dyads with the sarcoplasmic reticulum, which is the site of storage and release of Ca 2+ for excitation-contraction coupling.
As in skeletal and smooth muscle, excitation-contraction coupling in cardiac muscle translates the action potential into the production of tension. The following steps are involved in excitation-contraction coupling in cardiac muscle. These steps correlate with the circled numbers shown in Figure 4.18 .
The cardiac action potential is initiated in the myocardial cell membrane, and the depolarization spreads to the interior of the cell via the T tubules. Recall that a unique feature of the cardiac action potential is its plateau (phase 2), which results from an increase in g Ca and an inward Ca 2+ current in which Ca 2+ flows through L-type Ca 2+ channels (dihydropyridine receptors) from extracellular fluid (ECF) to intracellular fluid (ICF).
Entry of Ca 2+ into the myocardial cell produces an increase in intracellular Ca 2+ concentration. This increase in intracellular Ca 2+ concentration is not sufficient alone to initiate contraction, but it triggers the release of more Ca 2+ from stores in the sarcoplasmic reticulum through Ca 2+ release channels (ryanodine receptors). This process is called Ca 2+ -induced Ca 2+ release, and the Ca 2+ that enters during the plateau of the action potential is called the trigger Ca 2+ . Two factors determine how much Ca 2+ is released from the sarcoplasmic reticulum in this step: the amount of Ca 2+ previously stored and the size of the inward Ca 2+ current during the plateau of the action potential.
Ca 2+ release from the sarcoplasmic reticulum causes the intracellular Ca 2+ concentration to increase even further. Ca 2+ now binds to troponin C , tropomyosin is moved out of the way, and the interaction of actin and myosin can occur. Actin and myosin bind, cross-bridges form and then break, the thin and thick filaments move past each other, and tension is produced. Cross-bridge cycling, fueled by adenosine triphosphate (ATP), continues as long as intracellular Ca 2+ concentration is high enough to occupy the Ca 2+ -binding sites on troponin C.
A critically important concept is that the magnitude of the tension developed by myocardial cells is proportional to the intracellular Ca 2+ concentration. Therefore it is a logical extension of this concept that hormones, neurotransmitters, and drugs that alter the inward Ca 2+ current during the action potential plateau or that alter sarcoplasmic reticulum Ca 2+ stores would be expected to change the amount of tension produced by myocardial cells.
Relaxation occurs when Ca 2+ is reaccumulated in the sarcoplasmic reticulum by the action of the Ca 2+ ATPase (SERCA). In addition, Ca 2+ , which entered the cell during the plateau of the action potential, is extruded from the cell by Ca 2+ ATPase and Ca 2+ -Na + exchange in the sarcolemmal membrane; these sarcolemmal transporters pump Ca 2+ out of the cell against its electrochemical gradient, with the Ca 2+ ATPase using ATP directly and the Ca 2+ -Na + exchanger using energy from the inward Na + gradient. As a result of these transport processes, the intracellular Ca 2+ concentration falls to resting levels, Ca 2+ dissociates from troponin C, actin-myosin interaction is blocked, and relaxation occurs.
Contractility, or inotropism, is the intrinsic ability of myocardial cells to develop force at a given muscle cell length. Agents that produce an increase in contractility are said to have positive inotropic effects. Positive inotropic agents increase both the rate of tension development and the peak tension. Agents that produce a decrease in contractility are said to have negative inotropic effects. Negative inotropic agents decrease both the rate of tension development and the peak tension.
Contractility correlates directly with the intracellular Ca 2+ concentration, which in turn depends on the amount of Ca 2+ released from sarcoplasmic reticulum stores during excitation-contraction coupling. The amount of Ca 2+ released from the sarcoplasmic reticulum depends on two factors: the size of the inward Ca 2+ current during the plateau of the myocardial action potential (the size of the trigger Ca 2+ ) and the amount of Ca 2+ previously stored in the sarcoplasmic reticulum for release. Therefore the larger the inward Ca 2+ current and the larger the intracellular stores, the greater the increase in intracellular Ca 2+ concentration and the greater the contractility.
The effects of the autonomic nervous system on contractility are summarized in Table 4.4 . Of these effects, the most important is the positive inotropic effect of the sympathetic nervous system.
Sympathetic nervous system. Stimulation of the sympathetic nervous system and circulating catecholamines have a positive inotropic effect on the myocardium (i.e., increased contractility). This positive inotropic effect has three important features: increased peak tension, increased rate of tension development, and faster rate of relaxation. Faster relaxation means that the contraction (twitch) is shorter, allowing more time for refilling. This effect, like the sympathetic effect on heart rate, is mediated via activation of β 1 receptors, which are coupled via a G s protein to adenylyl cyclase. Activation of adenylyl cyclase leads to the production of cyclic adenosine monophosphate (cAMP), activation of protein kinase A, and phosphorylation of proteins that produce the physiologic effect of increased contractility.
Two different proteins are phosphorylated to produce the increase in contractility. The coordinated actions of these phosphorylated proteins then produce an increase in intracellular Ca 2+ concentration. (1) There is phosphorylation of the sarcolemmal Ca 2+ channels that carry inward Ca 2+ current during the plateau of the action potential. As a result, there is increased inward Ca 2+ current during the plateau and increased trigger Ca 2+ , which increases the amount of Ca 2+ released from the sarcoplasmic reticulum. (2) There is phosphorylation of phospholamban, a protein that regulates Ca 2+ ATPase in the sarcoplasmic reticulum. Unphosphorylated phospholamban inhibits Ca 2+ ATPase. When phospholamban is phosphorylated by sympathetic stimulation, this inhibition is removed, Ca 2+ ATPase is stimulated, and there is greater uptake and storage of Ca 2+ by the sarcoplasmic reticulum. Increased Ca 2+ uptake by the sarcoplasmic reticulum has two effects: It causes faster relaxation (i.e., briefer contraction), and it increases the amount of stored Ca 2+ for release on subsequent beats.
Parasympathetic nervous system. Stimulation of the parasympathetic nervous system and ACh have a negative inotropic effect on the atria . This effect is mediated via muscarinic receptors, which are coupled via a G i protein called G K to adenylyl cyclase. Because the G protein in this case is inhibitory, contractility is decreased (opposite of the effect of activation of β 1 receptors by catecholamines). Two factors are responsible for the decrease in atrial contractility caused by parasympathetic stimulation. (1) ACh decreases I Ca and inward Ca 2+ current during the plateau of the action potential. (2) ACh increases I K-ACh , thereby shortening the duration of action potential and, indirectly, decreasing the inward Ca 2+ current (by shortening the plateau phase). Together, these two effects decrease the amount of Ca 2+ entering atrial cells during the action potential, decrease the trigger Ca 2+ , and decrease the amount of Ca 2+ released from the sarcoplasmic reticulum.
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