Cardiac activation

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Chapter 2 Cardiac activation

REQUIREMENTS FOR AN EFFECTIVE HEART

As a foundation from which to explore the responses of the circulation to exercise and environment, it is worthwhile to review the characteristics that the heart requires in order to fulfil its role as a pump. At least most of the material covered in this first section is probably familiar to you from earlier courses, but it may be helpful to have it set out again. As you read through the first section of this chapter, use the simulated records in Figure 2.1 to remind yourself of the sequences of electrical and mechanical events that make up the cardiac cycle.

Rhythmic excitation

For a muscular pump to provide continuous blood flow through the circulation there must be a system that guarantees generation of muscle action potentials at regular intervals. The normal rhythm generator or pacemaker is a small group of cells that lies high in the wall of the right atrium, constituting the so-called sinoatrial node. The membranes of these cells have an unusually high sodium conductance and contain metabolic pumps that progressively reduce potassium conductance. These two properties together result in the membrane potential depolarizing gradually towards zero in what is termed the pacemaker potential, rather than them having a stable resting membrane potential of around −70 mV as is characteristic of the normal cardiac muscle cells. Since the threshold membrane potential for action potential initiation is around −40 mV, the pacemaker cells fire an action potential as soon as they depolarize to this threshold. As in any excitable cell, the action potential activates a delayed potassium efflux and this repolarizes the cells to around −70 mV but, once these voltage-gated potassium channels close, the membrane starts to depolarize once more and initiates another action potential.

The period between successive action potentials in a sinoatrial node cell at 37° C (98.5° F) is around 600 ms, giving an inherent frequency of cardiac excitation of about 100 beats/min. In the intact body, however, the slope of the pacemaker potential is subject to tonic influences by thoracic sympathetic nerves that increase the slope and speed up heart rate (tachycardia) and vagal parasympathetic nerves that reduce the slope and slow the heart down (bradycardia). In a resting subject, both of these neural inputs are continuously active but the bradycardic effect of the parasympathetic input predominates, so that resting heart rate is normally less than 100 beats/min and typically around 65–75 beats/min.

Guaranteed time for filling

After ventricular contraction finishes and the heart relaxes, there must be time for the ventricles to relax completely so that they can refill. Thus, a safety mechanism must exist to guard against another action potential causing re-excitation while some muscle cells are still contracted. To achieve this the voltage-gated calcium channels in the endocardial muscle cells nearest to the conducting system have longer cycle times than those in the more superficial muscle layers, with correspondingly longer plateau phases and refractory periods. Thus, the cells that are coupled to the Purkinje system will remain electrically non-excitable until the rest of the ventricular muscle has repolarized and relaxed. The difference in channel cycle time between endocardium and epicardium is due at least partly to the higher pressure that is exerted on membranes of the endocardial cells when the heart wall contracts.

An additional safety factor is that the action potential plateau of the Purkinje fibres themselves is significantly longer than that of any ventricular myocardial cell, so that a second impulse is unlikely even to reach the ventricular myocardium until this has relaxed entirely.

Existence of a finite relaxation period is a prerequisite for nutritional perfusion of the ventricular myocardium. The coronary arteries that supply the heart arise from the aorta and so the pressure gradient responsible for coronary blood flow is essentially identical to that generated by the left ventricle. Because ventricular ejection must involve at least equivalent pressure being developed within the left ventricular wall, the left coronary arteries are mechanically occluded during the ejection phase of the cardiac cycle (termed systole) and nutritional perfusion can occur only during the relaxation phase (termed diastole). As will be discussed in Chapter 8 (p. 95), coronary perfusion of the right ventricle is more continuous, since the ventricular pressure developed there is much lower than systemic arterial pressure, and so the vasculature is perfused during systole as well as diastole.

Coordination of right and left outputs

Since the systemic and pulmonary circulations are in series, they must each pump identical volumes of blood per unit time. It is, therefore, essential that both ventricles eject blood simultaneously. This coordinated timing is ensured by the fact that the Purkinje system conveys action potentials simultaneously to the apices of both ventricles. Even with exact timing, however, the left ventricle needs to generate a far greater ejection pressure than the right ventricle in order to eject the same volume of blood, because the systemic vasculature has a much higher resistance than does the pulmonary vasculature. To provide the extra degree of pressurization, the left ventricle is wrapped with an additional spiral layer of muscle.

Increased venous return, for example in response to lying down, will produce a corresponding rise in end-diastolic ventricular volume. If the volume of blood ejected with each systolic contraction (the stroke volume) remained constant, there would be progressive pooling of blood in the heart and a progressive fall in cardiac output, so it is important that stroke volume can be matched automatically to ventricular filling. This is achieved by the resting length of all ventricular muscle fibres being substantially below the length that would correspond to optimal actin/myosin crossbridging and development of maximal active shortening. With increased filling, the increased resting sarcomere length that results from passive stretch of the ventricular wall will therefore result in increased active tension. This phenomenon is known as the Frank-Starling relationship.

MONITORING ELECTRICAL ACTIVITY OF THE HEART

Basis of the electrocardiogram

Timecourses and amplitudes of events

When voltage is recorded between two points in an excitable tissue, the electrode towards which a wave of membrane depolarization is moving becomes positive relative to the other electrode, while a wave of repolarization causes the reverse voltage difference. During excitation of the heart, the sequence of electrical events is highly predictable. Continual measurement of voltage difference across the heart can, therefore, be used to identify the timing of depolarization of atria and ventricles, while the magnitude of voltage changes indicates the volume of muscle that is involved. The characteristic voltage record obtained is termed the electrocardiogram, or ECG, and the sequence of electrical events that occurs during cardiac excitation can be tracked by identifying each of the phases of the ECG waveform with a specific letter (Fig. 2.2).

With normal excitation originating from the sinoatrial node, measurement of the time between the beginning of atrial depolarization (beginning of P wave) and the entry of action potentials into the muscle of the ventricular apices (beginning of R wave) is always between 120 and 200 ms. Most of this delay is due to action potential travel through the slowly conducting A/V pathway, producing the so-called P–R interval which provides an index of the efficiency of this path. Ventricular excitation occurs by simultaneous entry of action potentials into both apices and coordinated spread of depolarization over both ventricles. This process takes only 60–80 ms and is indicated by the duration of the QRS complex. Once ventricular depolarization is complete the muscle cells all remain depolarized for the duration of the action potential plateau and then progressively repolarize, producing the T wave. This sequence produces an initial isoelectric period typically around 150 ms in duration while all cells are depolarized, and then a T wave whose timecourse of around 200 ms represents the range of action potential durations in different regions of the ventricular wall.

Since the endocardial cells have longer plateau durations than the epicardial cells, the sequence of repolarization between the different muscle layers is in the reverse order to the sequence of depolarization. For this reason, the voltage polarity of the T wave is usually the same as that of the R wave. In hearts with hypertrophied ventricles, however, greater epicardial intramural pressure is produced during contraction and the differences in plateau duration between epicardial and endocardial regions are reduced. As a result the ventricular cells tend to repolarize in the same sequence as they depolarized, producing an inverted T wave.

Orientations of ECG recording

The voltage changes occurring across the heart spread without diminution throughout the highly conductive medium of the body interior and can be detected from the body surface, so long as electrolyte-rich liquid is rubbed into the skin under the recording electrodes in order to overcome the high electrical resistance of the epidermis. Recording can be made most simply between right and left arms (Lead II) or between one arm and the left leg (Leads I and III). This so-called frontal lead system allows detection of impulse movement across the heart either horizontally or in a semi-vertical direction. Usually, the primary concerns for human physiologists are simply to have a signal large enough for you to be certain whether or not the sequence of excitation is normal, and to be able to reliably trigger a ratemeter from the R wave. Lead II usually provides the best record for these purposes but, because different people’s hearts have different vertical-horizontal orientations, larger signals are seen with one of the other lead orientations in some individuals.

Electrical activity moving at right angles to the orientation of the ECG electrodes produces no voltage signal, so frontal leads provide only limited information on the three-dimensional spread of activity through the heart. For this purpose, it is necessary to also record voltage differences between the heart and different points along the ventrodorsal diameter of the chest. The standard points used are six locations ranging from the right side of the sternum overlying the right ventricle (Lead V1), to the left axilla overlying the left ventricle (Lead V6). With these leads, one would expect to see a positive R wave in V6, but a reversed R wave in V1 reflecting the relative muscle masses in the two ventricles. So it is not surprising that at one or two of the intermediate locations, where the recording electrodes overlie the interventricular septum, the R wave appears bipolar. The chest leads are particularly useful for recognizing changes in absolute muscle volume in one or other ventricle, which alters the pattern of R wave polarity between the six locations. In addition, the R wave in V6 is the largest in amplitude of any lead but never normally exceeds 2.5 mV. An R wave from this lead that is 3 mV or more in height can, therefore, be used as a reliable index of left ventricular hypertrophy, and constitutes one of the indices for assessing training-induced cardiovascular adaptation in athletes (see Chapter 11, p. 131).

Arrhythmias in the normal heart

The term arrhythmia refers to any deviation of heart rate from a steady value between the limits of 60–100 beats/min. So, strictly speaking, heart rate is arrhythmic whenever it fluctuates or is outside the 60–100 beats/min range. Despite its popular connotations, therefore, arrhythmia does not necessarily imply abnormal cardiac function.

Training bradycardia

Chronic aerobic activity results in a progressive fall in resting heart rate. With moderate activity the reduction is typically only 5–10 beats/min and occurs over several weeks’ activity. With the more intense levels of training associated with competitive aerobic exercise, resting rate continues to fall to values that may be as low as 30–35 beats/min in elite athletes. The mechanisms that underlie this progressive training bradycardia will be examined in Chapter 11 (p. 133). As with exercise tachycardia, extreme bradycardia makes the ECG record look strange (Fig. 2.3B). However, its normality can be confirmed easily by checking that the PR interval is normal and that there is a consistent sequence of P, R and T waves. Note that, without an ECG, it would be impossible to know whether somebody with a very slow heart rate is a normal, athletically fit person or has some cardiac abnormality that slows down the heart beat.

Respiratory sinus arrhythmia

Heart rate shows a sinusoidal oscillation during the respiratory cycle, with a relative tachycardia developing during inspiration and waning during expiration. This oscillation is due to the fact that vagal drive to the sinoatrial node falls progressively as inspiration progresses. Two inhibitory inputs to the vagal centre in the hindbrain are involved, one from stretch receptors in the lung and one from inspiratory neurons in the hindbrain respiratory centre. As the discharges of both these inhibitory pathways are proportional to the amount of inspiratory effort, the magnitude of sinus arrhythmia is much greater during deep than shallow breathing. Even at rest, however, there is typically a variation of at least 5–10 beats/min in individuals below the age of 30. A representative example of sinus arrhythmia can be seen in Figure 4.3 (p. 37).

By middle age, little or no heart rate variability is seen except during deep breathing and with further ageing the variability disappears altogether. This decline is not due to alteration in resting vagal tone (since resting heart rate does not change substantially with age), but probably involves changes in gain of the central input pathways to the vagal centre. Damage to the vagus is a common early component of peripheral nerve degeneration in patients with type I diabetes and, therefore, the magnitude of sinus arrhythmia in younger diabetics is a useful index in assessing their clinical status.

The bradycardia that results from chronic physical training is accompanied by increased magnitude of sinus arrhythmia, probably reflecting the increased range over which altered vagal tone can alter heart rate. In fact, the absolute magnitude of the arrhythmia has been suggested to provide a quantitative index of fitness, similar to that derived from measurement of image (Lopes & White 2006).

Abnormal arrhythmias

Damage from altered plasma electrolyte levels, from inadequate local blood flow (ischaemia) or from local trauma can affect pacemaker function, integrity of the cardiac conducting system or membrane excitability and any of these changes will be reflected in the ECG pattern. Detailed clinical assessment of ECGs is the responsibility of a cardiologist, but all physiologists who are involved with human subjects should be able to spot the most obvious abnormal arrhythmias so that they can decide whether a subject should be excluded from a programme that involves added cardiovascular demand. A good-quality 12-lead ECG record will allow the following abnormal patterns to be identified.

Absence of P waves

Normal atrial muscle can only be activated once by a single sinoatrial impulse, because the prolonged plateau phase of the atrial action potential maintains it in a refractory state. If, however, the conduction velocity of the action potential is slowed by local hypoxia, or the distance needed for the action potential to travel around the atrial wall is increased because the atria have been stretched, or the action potential plateau phase duration is reduced by altered channel cycling, then a single action potential may circulate through the tissue over and over again and cause repetitive but uncoordinated contractions. This phenomenon is termed atrial fibrillation.

Atrial fibrillation has relatively little effect on the efficiency of cardiac pumping because most ventricular filling has occurred before atrial systole (Fig. 2.1). But it does create a potential problem. Instead of the atrial contents being regularly ejected, some blood tends to lie stationary in the extremities of the atrial chambers. When blood is stagnant, it tends to form clots and cell aggregates (thrombi) (see also Chapter 5, p. 48). If these thrombi are mobilized into the cardiac output, for instance during the vigorous respiratory effort of exercise, then they may occlude vessels in the coronary or cerebral circulation, causing a heart attack or stroke. Individuals with evidence of atrial fibrillation should, therefore, not be recruited into exercise programmes without careful clinical assessment.

Atrial fibrillation can be identified by two characteristics. First, no P wave exists because the action potentials that spread through the atria do not all travel in the same direction and so do not produce a reproducible voltage deflection on the ECG trace. Second, heart rate varies widely from beat to beat, in an unpredictable pattern (Fig. 2.4). This is because the disorganized direction of action potential travel means that they arrive at the A/V node at irregular intervals, with some arriving while the node cells are still in their refractory period from the previous action potential. In all other arrhythmias that involve varying heart rate there is either a progressive rise and fall in frequency (see Sinus arrhythmia, above) or intermittent insertion of extra R waves into an otherwise regular sequence (see Ventricular extrasystole, below).

Abnormal relationship between P and R waves

Damage to the cells of the A/V node may occur due to local ischaemia, inflammation, physical pressure by scar tissue or local calcification. This can have either of two separate effects on impulse conduction. In some cases there is slowing of action potential propagation with prolongation of the P–R interval beyond the normal upper limit of 200 ms, typically to 300–400 ms (Fig. 2.5A). In other cases, the effect of the damage is not to slow conduction velocity, but instead to slow calcium channel cycle time, so that following passage of one action potential the node is still refractory when the next impulse arrives. As a result, only every second or third action potential enters the ventricle and the ECG shows QRS complexes and T waves associated only with every second or third P wave (Fig. 2.5B).

If the nodal cells are damaged severely enough then they are unable to propagate impulses at all, and ventricles and atria become electrically insulated from each other. Although the sinoatrial node continues to discharge and, therefore, P waves occur at their normal frequency, ventricular activation can originate only from within the ventricular system. The intraventricular Purkinje system contains a number of cells that have similar membrane properties to those of the sinoatrial cells but depolarize much more slowly. These cells normally never reach action potential threshold before they are activated by an impulse arriving from the A/V node. When this is prevented, however, these slower pacemakers can take over control of ventricular rhythm with frequencies in the range of 30–45 beats/min. The result is QRS complexes and T waves at a much lower frequency than that of the P waves and with no consistent association between P and R waves (Fig. 2.5C).

Clearly, lack of synchrony between atrial and ventricular pumping frequency denotes a heart that is not likely to be able to accommodate efficiently to demands for increased output. Individuals in whom you suspect A/V block should, therefore, not be recruited into exercise programmes without referral to a cardiologist.

Abnormal QRS complexes

Normally, action potentials travel from the A/V node down the Purkinje fibres on left and right sides of the interventricular septum. This produces simultaneous depolarization of both ventricles, with a QRS complex that is never more than 80 ms in duration. The synchronization of ventricular depolarization can be disrupted by damage to one of the branches of the Purkinje system, so that one ventricle is activated before the other. Alternatively, arrival of impulses through the conducting system may be normal, but an area of ventricular muscle may be damaged (usually by ischaemia) so that the sequence of spread of action potentials through the ventricular syncytium is disrupted. Any of these changes will result in a longer period being taken for ventricular depolarization, with concomitant widening of the QRS complex and usually some loss of the sharp ‘spikiness’ of the R wave.

Sometimes in a normal heart, the membrane of a cell within the ventricular Purkinje system or the ventricular muscle becomes hyperexcitable and generates an action potential. This causes an additional QRS complex and an extra ventricular contraction. Such a so-called extrasystole can be distinguished by two characteristics. First, the fact that it originates from a site distal to the Purkinje system means that activation of the myocardium follows a different route to normal, producing a QRS complex that has a different shape and is longer in duration. Second, the action potential plateau produces a refractory state in the myocardial cells that prevents activation by the next normal action potential, so an extrasystole is followed by a longer than normal pause before the next contraction. This is termed a compensatory pause.

Case history

imageBrian K, a sedentary male, heavy smoker, 50 years old, volunteered for an exercise training study. His ECG was recorded at rest and part of the record is shown above.