Aortic stenosis is a very frequent heart pathology affecting 2-7
% of Europeans above
the age of 65. It is most
commonly the result of degenerative process, which lead to narrowing of the aortic valve or stenosis.
How does a
narrowed aortic valve change the P-V box?
The narrowing of the aortic valve means that the left ventricular emptying during systole is impaired.
This high
outflow resistance causes an increase in afterload (making the Ea line steeper). A large pressure
gradient
occurs across the aortic valve during ejection, which means that the peak systolic pressure in the left
ventricle greatly increases, making our P-V box taller. Left ventricle must now eject blood against a
greater-than-normal pressure. A consequence of this increased afterload is that less blood is ejected
into the
aorta during the ejection phase, causing the stroke volume to decrease (P-V box becomes narrower).
Because less
blood is ejected during systole, more volume remains in the ventricle and the end-systolic volume (ESV)
increases.
These are the initial and most basic changes that occur in the setting of aortic stenosis and are
depicted in
the example. If we were to look at the following cardiac cycles, we would see, that this larger than
normal ESV
is then added to the venous return in the next cardiac cycle, thereby increasing the end-diastolic
volume (EDV)
as well and shifting our P-V box slightly to the right. This increased EDV or preload increases the
force of
contraction by the Frank-Starling mechanism, helping the ventricle to, in part, overcome the increased
outflow
resistance. In mild stenosis this can be enough to compensate for increased afterload, however in
moderate or
severe cases stroke volume may be seriously reduced.
It is important to note, that the above described changes in P-V box do not account for cardiac and
systemic
compensatory mechanisms, which attempt to maintain normal arterial pressure and cardiac output.
Therefore the
changed P-V box represents what may occur under a given set of conditions.
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Acute myocardial infarction
Myocardial infarction is the result of a sudden blockage of a coronary artery which is supplying a part of the
heart, resulting in damage to the heart muscle. Therefore, there is a loss of myocardial tissue, but the
unaffected regions of the ventricle still function normally. This loss of the muscle tissue results in
reduction of ventricular contractility. This decreases the slope of the ESPVR line in the P-V box. This
reduced contractility also causes reduction of stroke volume (width of the box) and reduction in
pressure
generation (height of the box). In the following cardiac cycles, due to increased filling pressure, the
P-V
box also shifts rightward towards larger volumes - increased EDV (not seen in the example).
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Acute hemorrhage
Let’s imagine an accident in which a person lost a significant amount of blood in a short period of time. The
reduction of intravascular volume causes a decrease of end-diastolic volume, i.e. preload. This moves
the Ea
line in the P-V box toward lower volumes, without changing its slope. This in turn leads to a reduced
stroke
volume and lower generated pressure. These are the initial changes occurring in the setting of
acute
intravascular volume reduction (shown in the graph).
What follows is the activation of baroreceptor reflex
The baroreceptor mechanisms are fast, neurally mediated reflexes that attempt to keep arterial pressure
constant via changes in the output of the sympathetic and parasympathetic nervous systems to heart and
blood vessels. Pressure sensors – the baroreceptors – are located in the walls of the carotid sinus ant
the aortic arch and transmit information about blood pressure to cardiovascular vasomotor centers in the
brain stem. These vasomotor centers then coordinate a change in output of autonomic nervous system to
effect the desired change in arterial pressure. The effects on the cardiovascular system in response to
hemorrhage, which are described above, all work in the direction of increasing arterial pressure toward
normal.
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which increases the
sympathetic outflow to the heart
and blood vessels. The consequences of these autonomic reflexes are increased heart contractility
(steeper
ESPVR line), increased heart rate and TPR (both increasing the slope of the Ea line) and
constriction of the
veins, which reduces unstressed volume and thereby increases the venous return to contribute to
the increase
in cardiac output (Frank-Starling mechanism).
End-systolic elastance shows the slope angle of the end-systolic pressure volume relationship (ESPVR). It is a
measure of the heart contractility, resulting in a steeper slope when contractility is enhanced and vice versa.
Total peripheral resistance (TPR)
Total peripheral resistance is the resistance of the entire systemic vasculature that resists the flow of blood
and generates pressure. Increasing the resistance increases the slope of the Ea line and vice versa.
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In order to understand the connection between TPR, HR and Ea, we will derive the following equation.
We have to start with the definition of TPR:
TPR = (MAP – CVP)/CO
where MAP = mean arterial pressure, CVP = central venous pressure and CO = cardiac output. Cardiac output
represents the amount of blood pumped by heart in a single minute, therefore:
CO = SV x HR
where SV = stroke volume and HR = heart rate.
If we connect the two equations, we get the following:
TPR = (MAP – CVP) / (SV x HR)
At this point we must make a few assumptions. First, we assume that CVP = 0. We can do that because CVP is
generally around 0-5 mmHg and is negligible compared to MAP, which is around 100 mmHg. Secondly, we make an
assumption that MAP is approximately equal to end-systolic pressure (Pes) of the left ventricle. Following
these assumptions we can rewrite the equation as:
TPR = Pes / (SV x HR)
This can be rearranged as:
TPR x HR = Pes/SV
Why did we do that? If we look at the P-V loop, we can get the Pes/SV as the negative value of the slope of
the line connecting the EDV point on the volume axis and the end-systolic pressure-volume point. We define
that slope as the Ea – arterial elastance:
Ea = Pes/SV
If we combine the last two equations, we get:
Ea = TPR x HR
This means that the slope of the Ea line depends on changes in TPR and HR.
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Heart rate (HR)
The heart rate is an intrinsic quality of the heart. It directly shows how many electric signals the heart's
internal pacemaker produces, which results in a number of contractions per minute (BPM). It is strongly affected
by autonomic nervous system, with sympathetic stimulation increasing and parasympathetic stimulation decreasing
the heart rate. Increased heart rate causes Ea line to be steeper and vice versa.
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In order to understand the connection between TPR, HR and Ea, we will derive the following equation.
We have to start with the definition of TPR:
TPR = (MAP – CVP)/CO
where MAP = mean arterial pressure, CVP = central venous pressure and CO = cardiac output. Cardiac output
represents the amount of blood pumped by heart in a single minute, therefore:
CO = SV x HR
where SV = stroke volume and HR = heart rate.
If we connect the two equations, we get the following:
TPR = (MAP – CVP) / (SV x HR)
At this point we must make a few assumptions. First, we assume that CVP = 0. We can do that because CVP is
generally around 0-5 mmHg and is negligible compared to MAP, which is around 100 mmHg. Secondly, we make an
assumption that MAP is approximately equal to end-systolic pressure (Pes) of the left ventricle. Following
these assumptions we can rewrite the equation as:
TPR = Pes / (SV x HR)
This can be rearranged as:
TPR x HR = Pes/SV
Why did we do that? If we look at the P-V loop, we can get the Pes/SV as the negative value of the slope of
the line connecting the EDV point on the volume axis and the end-systolic pressure-volume point. We define
that slope as the Ea – arterial elastance:
Ea = Pes/SV
If we combine the last two equations, we get:
Ea = TPR x HR
This means that the slope of the Ea line depends on changes in TPR and HR.
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End-diastolic volume (EDV)
End-diastolic volume is a variable that represents the hearts ability to expand and fill with blood. It
represents the maximal ventricular volume prior to contraction. It is a direct result of the interplay between
end-diastolic elastance, end-diastolic (filling) pressure, and the duration of the filling phase.
Theory
Wiggers diagram and pressure-volume loop
To fully understand the pressure-volume loop, we will first take a look at the so-called Wiggers diagram, which
is a very useful tool in cardiac physiology for presenting the cardiac cycle. It usually integrates changes in
pressures of the left ventricle, left atrium and the aorta, ventricular volume, and electrocardiogram. It also
often contains depictions of sound phenomena. In this chapter, however, we will only focus on the pressure and
the volume of the left ventricle and from that derive the pressure-volume loop.
To generate the pressure-volume loop for the left ventricle, we plot left ventricular pressure against left
ventricular volume at multiple time points during the same cardiac cycle. Thus, points A, B, C, D, and F on the
P-V loop corelate with the dotted lines in the Wiggers diagram.
Cardiac cycle and the P-V loop:
Cardiac cycle is divided into two phases: the systole and the diastole. The systole comprises of isovolumetric
ventricular contraction (a), rapid ventricular ejection (b) and reduced ventricular ejection (c), i.e., the
interval A→D. The diastole includes isovolumetric ventricular relaxation (d), rapid ventricular filling (e) and
reduced ventricular filling (f), i.e., the interval D→A.
Point A on the P-V loop represents the state of left ventricle at the end of the diastole. Volume and pressure
in point A are therefore called the end-diastolic volume (EDV; 125 mL) and the end-diastolic pressure (10 mmHg).
As the cardiac cycle begins and the ventricle starts to contract, the pressure rises rapidly. Because all heart
valves are closed at that time, no blood can leave the ventricle, therefore the volume remains constant, thus
the name
“isovolumetric”
contraction (a).
The word isovolumetric contains the prefix iso-, derived from the Ancient Greek ἴσος (ísos), meaning equal.
Isovolumetric contraction is therefore one in which the volume of fluid (e.g. blood) remains constant.
In analogy, when talking about the skeletal muscle, we have a similar phenomenon called isometric contraction,
in which the skeletal muscle develops tension while remaining the same length. Example of that would be when
the muscle of your hand and forearm grip an object – muscles do not shorten, but the force they generate is
sufficient to prevent the object from being dropped.
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When the rising pressure in the left ventricle rises above the pressure in the aorta (80 mmHg), the aortic
valve opens (B). What follows is the rapid ventricular ejection (b), during which most of the stroke volume is
ejected into the aorta. Ventricular pressure reaches its maximum at point C (systolic pressure; 120 mmHg).
Myocardial excitation subsequently decreases and the ventricle no longer contracts, causing the ventricular
pressure to fall. Blood is still being ejected into the aorta but at a reduced rate - reduced ventricular
ejection (c). As ventricular pressure falls below that in the aorta (D), the aortic valve closes, producing the
second heart sound (S2). This also marks the end of the systole (A→D). Volume contained in the ventricle at this
point of the cardiac cycle is called the end-systolic volume – ESV (50 mL) and the pressure is end-systolic
pressure (100 mmHg). Due to muscle relaxation, left ventricular pressure continues to fall, but because all the
valves are closed, the volume remains the same - isovolumetric relaxation (d).
For etymology of the word look at isovolumetric contraction.
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When left ventricular pressure falls below the one in the left atrium, the mitral valve opens (E). This results
in rapid ventricular filling (e), during which left ventricular volume increases rapidly, pressure however
remains low, because the ventricle is relaxing further and thus highly compliant. Reduced ventricular filling
(f) is the longest phase of the cardiac cycle and is mostly affected when heart rate increases. Atrial systole
marks the end of the diastole (D→A), at which point ventricular volume is equal to EDV (A). At point A, when
left ventricular pressure rises above the one in the left atrium, the mitral valve closes, producing the first
heart sound (S1).
What information can we gain from the pressure-volume loop?
The width of this pressure-volume loop represents the difference between maximum (EDV) and minimum volume (ESV)
in the cardiac cycle. This difference between EDV and ESV represents the amount of blood ejected during a single
cardiac cycle and is called the stroke volume (SV). In our case, this equals 125 mL - 50 mL = 75 mL.
Another
value which we cannot directly see in the P-V loop, but can calculate it and with some experience also see in
the graph, is the ejection fraction (EF), which is the fraction of the end-diastolic volume that is
ejected by
the ventricle in one stroke volume. Thus EF = SV/EDV, which in our case equals to 75 mL/125 mL = 0.6 or 60 %.
Visually, this corresponds to the ratio between two lengths: the width of the SV divided by the distance between
the origin of the coordinate system and EDV.
At point B of the P-V loop, the ventricular pressure just exceeds the aortic pressure; this pressure therefore
reflects the pressure existing in the aorta at the onset of ejection and is called diastolic pressure
(Pd).
During the ejection phase, aortic and ventricular pressure are essentially equal; therefore the point of
greatest pressure on the loop also represents the greatest pressure in the aorta and is called systolic
pressure
(Ps). The pulse pressure (Pp), which is the difference between systolic pressure (Ps) at point C
and
diastolic
pressure (Pd) at point B, can therefore also be determined. In our case, it would be 40 mmHg (120 – 80 mmHg).
With the help of a pressure-volume loop we can also visualise time points when certain valve pathologies can be
heard during heart auscultation. I want to know
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If the aortic valve is narrowed (aortic stenosis), we may hear a murmur from point B to point D in
the P-V
diagram, during which the aortic valve is opened. This is caused by a turbulent flow of blood through a
narrowed valve. If the mitral valve is not closing properly (mitral regurgitation)
If we drew the P-V diagram for the mitral regurgitation, we could make an interesting observation. In
mitral regurgitation, as the left ventricle contracts, the blood is not only ejected into the aorta, but
a part of it also flows back into the left atrium, which means that there is no true isovolumetric
contraction (no straight vertical line in the P-V diagram), because the blood begins to flow back into
the left atrium as soon as the left ventricular pressure rises above the one in the left atrium.
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some blood may flow retrogradely into the left atrium during systole. This can be heard as a murmur from
point A to point E in the P-V diagram, during which the mitral valve is normally closed. These are the two
examples of systolic murmurs.
Similarly, during diastole, if the aortic valve does not close sufficiently (aortic regurgitation)
some blood flows back into the left atrium from the aorta, producing a diastolic murmur. On the P-V diagram
it can be visualised from point D to point B, during which the aortic valve is normally closed. If the
mitral valve is narrowed (mitral stenosis) we may hear a murmur from point E to point A, during which
time blood flows through a narrowed mitral valve into the left ventricle, producing a diastolic murmur.
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Duration of cardiac cycle phases
Although pressure-volume loop provides a useful visualization of the changing pressures and volumes during a
cardiac cycle, these representations of the cardiac function do not depict rates because the time scale is
eliminated in their construction. Therefore, a longer line in the P-V diagram does not mean that the particular
phase of the cardiac cycle lasts longer, which is shown in the picture below. The whole systole lasts
approximately 0.3 seconds and the total duration of the diastole is around 0.7 seconds, yet they appear almost
equally “long” on the P-V diagram.
IMPORTANT PHYSIOLOGICAL ENTITIES
Preload
Preload can be defined as the stretching of cardiac muscle prior to the systole imposed on the heart by initial
sarcomere length and end-diastolic volume. The Frank-Starling’s law of the heart
The German physiologist Otto Frank (1865 – 1944) first described the relationship between the pressure
developed during systole in a frog ventricle and volume present in the ventricle prior to systole. Building
on Frank’s observations, the British physiologist Ernest Henry Starling (1866 – 1927) demonstrated, in an
isolated dog heart, that the volume the ventricle ejected in systole was determined by the end-diastolic
volume (EDV).
Frank-Starling law of the heart (also known as Frank-Starling mechanism, Frank-Starling relationship) is
based on these landmark experiments. It states that the volume of blood ejected by the ventricle (stroke
volume) depends on the volume present in the ventricle at the end of diastole (end-diastolic volume).
As a larger volume of blood flows into the ventricle, it causes cardiac muscle fibers to stretch,
thereby increasing the force of the contraction. This ensures that the volume the heart ejects (cardiac
output) equals the volume it receives in venous return. However, the curve representing this relationship
is in the shape of an inverted letter U, meaning that after a certain end-diastolic volume, the force of
the ventricular contraction decreases. This is because the muscle fibers are stretched to even further
lengths and the overlap of thin and thick filaments decreases, resulting in weaker contraction.
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states that a greater fiber length causes the heart to deliver more mechanical energy, i.e., to contract
more, and it therefore focuses on preload. The direct effect of preload on the heart can be seen by regulating
the end-diastolic volume in our graph, where a higher end-diastolic volume, i.e., more blood in the ventricle at
the end of diastole, results in a higher stroke volume and higher generated pressure. Importantly, one cannot
simply raise the end-diastolic volume endlessly. One has to take into account the end-diastolic pressure volume
relationship (see below), which limits ventricular distention.
Afterload
Afterload portrays forces that the contracting myocytes must overcome. It may be defined as the tension or
stress developed in the ventricle wall during ejection. A convenient index of the opposing forces is arterial
pressure that opposes blood flow from the ventricles. However, under pathologic conditions when either the
mitral valve is incompetent (i.e., leaky) or the aortic valve is stenotic (i.e., constricted) afterload is also
determined by factors other than the properties of the arterial system. Myocytes that try to overcome a greater
afterload do so with a higher tension and contract more slowly than myocytes overcoming a lower afterload.
End-systolic pressure-volume relationship (ESPVR)
If one measured the pressure in the ventricle after systole (end-systolic pressure) for multiple cardiac cycles
with different end-diastolic volumes, provided other physiological parameters - such as contractility - would
not change, the end-systolic pressure values would fall along a line when plotted in a graph. This line is also
termed the end-systolic pressure-volume relationship (ESPVR), because it represents the relationship between
pressure and volume at an instant of maximal activation – end-systole. The steepness of the slope represents
cardiac contractility, where a steeper slope shows higher contractility, stroke volume and blood pressure
generated.
Here, we must point out that the ESPVR line is not actually completely linear, but is in fact curvilinear.
Although in situ end-systolic pressure-volume relations are approximately linear throughout a limited load
range, they often yield seemingly negative volume-axis intercepts (V0), and even V0 shifts with inotropic
interventions. As Kass et al. (1989) described in their study, curvilinearity can explain this frequent
observation of apparently negative V0 and large shifts in V0 with alterations in contractile state. In our graph
however, we have used the linear ESPVR model and a fixed volume-axis intercept (V0) for the sake of
simplification of this complex concept.
End-diastolic pressure-volume relationship is the relationship between pressure and volume in the ventricle at
the instant of complete relaxation (end-diastole). One could imagine the heart as an empty balloon, even when
there is no pressure on the wall, there is still some volume left in the opening. The volume at pressure 0 is
often referred to as V0 or unstressed volume (not the same as the V0 in ESPVR).
The volume axis intercept for the ESPVR and EDPVR line is not the same. We can try to understand this by
imagining having two balloons, one contracted and one relaxed. The contracted balloon represents the heart
at the end of systole (point D in the P-V diagram). If we fill this contracted balloon with different
volumes and measure pressures created inside, we form the ESPVR line, which gives us a slightly positive x
axis intercept – V0. Even when the heart is fully contracted, there is still some volume, which blood can
occupy before it generates any pressure – therefore the pressure at V0 is 0 mmHg.
On the other side we have a relaxed balloon, which represent the heart in its most relaxed state in the
diastole. Because this balloon is relaxed, slightly higher volume can be put into it before any pressure is
generated, therefore V0 for the EDPVR line is slightly higher as the one for the ESPVR line. Again, if we
fill this relaxed balloon with different volumes and measure the pressure inside, we construct the EDPVR
line.
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When the heart slowly begins to fill with blood, the pressure remains constantly low, until at some point it
begins to rise rapidly. This point is dependent on the heart’s intrinsic properties, such as compliance. The
EDPVR limits the distention of the heart’s ventricles during the diastole.
P-V loop → P-V box
Up to now, we have drawn and explained what the actual pressure-volume loop looks like. However, as in our
interactive model, you will often see a pressure-volume box being used instead to describe how changes in
different parameters affect the pressure and volume of the left ventricle. By converting to the simplified P-V
box (shown in the picture below), we lose some information from the P-V loop, such as systolic and diastolic
pressure or end-diastolic pressure, but make it easier to represent changes in certain parameters. There are
three parameters, which we can then tweak in order to change the shape of this P-V box. These are:
contractility of the heart, which changes the slope of the ESPVR line (Ees),
arterial elastance (Ea), whose slope can be changed by changing resistance (afterload) or the heart rate,
preload (EDV), which moves the Ea line to the left or right but does not change its slope, only its
intercept with the x-axis, i.e., preload.
Noteworthy, the part of the surface that is lost on top is roughly compensated for by the surface gained in the
bottom. Therefore, the surface area, which depicts the work of a cycle, does not change considerably.
References
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and Hall textbook of medical physiology. 13th ed. Philadelphia: Elsevier; 2016. p.115-22.
Burkhoff D. Mechanical properties of the heart and its interaction with the vascular system.
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Sagawa K. The end-systolic pressure-volume relation of the ventricle: definition, modifications and
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Asanoi H, Sasayama S, Kameyama T. Ventriculoarterial coupling in normal and failing heart in humans.
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