This chapter is most relevant to Section F3(ii) from the 2017 CICM Primary Syllabus, which expects the exam candidates to be able to "define compliance (static, dynamic and specific)". This has been a popular topic for SAQs:
Most of these SAQs ask for a definition of compliance, as well as methods of measuring compliance. Question 14 from 2016 and Question 1(p.2) from the second paper of 2008 also asked for factors which affect compliance. Though it was not specifically asked for, the distinction between static and dynamic compliance seems to be an expected feature of a high-scoring definition, according to the examiner comments. Specific compliance has never been mentioned in any of the questions and appears to be absent from the vivas, or what little we know of them.
- Respiratory compliance is defined as the change in lung volume per unit change in transmural pressure gradient. It is usually about 100ml/cm H2O.
- Static compliance is defined as the change in lung volume per unit change in pressure in the absence of flow. It is composed of:
- Chest wall compliance (usually 200ml/cm H2O.
- Lung tissue compliance (also usually cm H2O.)
- Dynamic compliance is defined as the change in volume divided by change in pressure, measured during normal breathing, between points of apparent zero flow at the beginning and end of inspiration. Its components are:
- Chest wall compliance
- Lung tissue compliance
- Airway resistance (which makes it frequency-dependent)
- Frequency dependence of dynamic compliance is due to
- Pressue contribution from airway resistance
- Preferential distribution of flow into lung units with shorter time constants, a tendency which increases with shorter inspiratory times and increasing respiratory rates
- Specific compliance is compliance that is normalized by a lung volume, usually FRC. It is used to compare compliance between lungs of different volumes (eg. child and adult)
- Hysteresis is the term used to describe the difference between inspiratory and expiratory compliance. Lung volume at any given pressure during inhalation is less than the lung volume at any given pressure during exhalation.
- Hysteresis is present in both static and dynamic lung compliance curves
- Hysteresis develops due to:
- The effect of surfactant
- Relaxation of lung tissue
- Recruitment and derecruitment of alveoli
- Gas absrption during measurement
- Differences in expiratory and inspiratory air flow (for dynamic compliance)
- Factors which affect compliance can be divided into chest wall factors and lung factors:
Factors which Affect Respiratory Compliance Lung compliance Chest wall compliance
Increased lung compliance
- Lung surfactant
- Lung volume: compliance is at its highest at FRC
- Posture (supine, upright)
- Loss of lung conective tissue associated with age
Increased chest wall complance
- Ehler-Dahlos syndrome and other connective tissue diseases associated with increased connective tissue elasticity
- Rib resection
- Flail segment rib fractures
- Open chest (eg clamshell)
Decreased static lung compliance
- Loss of surfactant (eg. ARDS)
- Decreased lung elasticity
- Pulmonary fibrosis
- Pulmonary oedema
- Decreased functional lung volume
- Pneumonectomy or lobectomy
- Small stature
- Alveolar derecruitment
- Alveolar overdistension
Decreased dynamic lung compliance
- Increased airway resistance (eg. asthma)
- Increased air flow (increased resp rate)
Decreased chest wall compliance
- Structural abnormalities
- Kyphosis / scoliosis
- Pectus excavatum
- Circumferential burns
- Surgical rib fixation
- Functional abnormalities
- Muscle spasm, eg. seizure or tetanus
- Extrathoracic influences on chest/diaphragmatic excursion
- Abdominal compartment syndrome
- Prone position
In terms of published peer-reviewed resources, none is better than Scott Harris' article from 2005. It is available for free from Respiratory Care. It would be easy to stick with this free article as one's main source of information. The compliance section from Nunn's (p.29-31 of the 8th edition) is also worth reading, but does not contain any reference to specific compliance (not that it's ever come up in the written papers).
The 8th edition of Nunn's gives the following definition of lung compliance (p. 17):
"Lung compliance is defined as the change in lung volume per unit change in transmural pressure gradient (i.e. between the alveolus and pleural space)."
This closely resembles any other definition of lung compliance. For example, Guyton & Hall (13th ed) define it as "the extent to which the lungs will expand for each unit increase in transpulmonary pressure (if enough time is allowed to reach equilibrium)", which sounds like they were defining static compliance. For the most basic form, one may look to Levitzky's Pulmonary Physiology (8th ed.) which simply states that "compliance is defined as the change in volume divided by the change in pressure". For the purposes of abbreviating this concept even further to cut precious seconds from the answer writing time:
Compliance = ΔV / ΔP
Static compliance has been defined variably by many authors, but most of the definitions have a single common focus on the absence of flow and the time allowed for the mobile elements of the respiratory system to relax and come to rest. "A static P-V curve eliminates the resistive and impedance effects on pressure", explains Harris (2005); what's left, supposedly, is just the compliance of the lung, the unadulterated pressure-volume relationship. Borrowing and slightly modifying a definition from Miller's Anesthesia:
Static compliance is change in volume divided by change in pressure, measured in the absence of gas flow.
A definition like this suggests that to measure static compliance, all you need to do is stop the gas flow. In reality, this is usually not true. Say you are measuring compliance. The moment you close the respiratory circuit after inspiration, you will note a pressure drop which is due to the gas redistributing between lung units with different time-constants. Surely, you'd say, this is not a "static" process, and choose to wait some seconds before recording the measurement. However, as the seconds pass, you may note that the measured volume of the lung decreases. This is due to the fact that the gas contained within is being absorbed into the pulmonary circulation. Therefore, in the living human organism, there is never going to be a situation where a truly static pressure-volume relationship can be recorded, and Harris (2005) recommends the term "quasi-static" to describe them.
In terms of exam relevance, apart from the abovestated definition, one may safely expect to be asked to draw a diagram to represent the pressure and volume relationhsip of the human lung. If so, one could do worse than reproduce the famous relationship described by Rahn et al in 1946, which was for some reason the first of such efforts. "It is remarkable that physiologists have paid so little attention in the past to the mechanics of breathing that no adequate data are now on record concerning the pressure-volume characteristics of the chest and lungs in normal men", the authors complained. They acquired normal men, occluded their nostrils with cork stoppers, and measured their airway pressures at different fractions of their vital capacity (the subjects exhaled fully and then inspired a known volume of gas from the spirometer before performing a breath hold). With these manoeuvres, the following relationship was demonstrated:
The diagram above is identical to Figure 6 from the original paper, but it was gentrified slightly to modernise it for consumption by modern readers (nobody calls that volume "residual air" any more). It demonstrates the classical lung compliance curve, where the compliance is poor at low and high volumes, but optimal just above the FRC, i.e. in the range of the normal tidal volume.
Obviously, when you pump gas into a person's chest, the pressure-volume relationship is going to be a complex combination of several factors. Of these, the dominant players will be the chest wall and the tissues of the lung itself. When asked to desribe this concept, a CICM trainee would likely be expected to regurgitate this equation:
Where, predictably, CRS is the compliance of the respiratory system as a whole, CL is the compliance of the lung and CCW is the compliance of the chest wall. Usually, textbooks give normal values for these compliances; for the lung and chest wall, these are 200ml/cm H2O.
The compliance of the lungs and chest wall are related to the elastic properties of these structures, which are discussed in a chapter all of their own.
Under normal conditions (i.e where it is not filled with saline), the lung does not behave as an ideal system, i.e. the energy invested in its distension is not returned upon deflation. The upshot of this is that inflation and deflation have different pressure-volume relationships, and the difference between them is called "hysteresis", a term etymologically related to "lag" or shortcoming" which describes the dependence of a system's state upon its history. If one were completely unprepared for the questions "define hysteresis", one could easily break down and blather something like "the inspratory thing does not look like the expiratory thing", so it would probably be worth investing some time in memorising a more solid definition. Here's one from an excellent article by Escolar & Escolar (2004):
"The energy applied to the lung in inspiration is not recovered in expiration. The property of dissipating energy receives the name of hysteresis."
A pithier, more memorable definition is available from a much less reputable source:
"Lung volume at any given pressure during inhalation is less than the lung volume at any given pressure during exhalation"
It makes logical sense to expect something like this in a dynamic PV loop because of the effects of resistance (more on that later), but it is seen even in static compliance measurements. Here, a diagram from Harris (2004) demonstrates the hysteresis in a static PV loop using the supersyringe method. The added labels demonstrate that, for the same change in pressure, the expiratory compliance is lower:
Why does this happen? There are four main reasons.
In contrast to static compliance, the term "dynamic compliance" sounds like it refers to something vigorous and mobile. The definition of static compliance is easily repurposed to suit:
Dynamic compliance is change in volume divided by change in pressure, measured in the presence of gas flow.
Or, rather, it would be more accurate to say that, in the measurement of dynamic compliance, no effort is made to interrupt the natural rhythm of breathing with any sort of supersyringe. Instead, the pressures used to calculate dynamic compliance are those pressures at which flow naturally "stops" (for an instant), which for a mechanically ventilated patients are vaguely corresponding to peak inspiratory pressure (PIP) and end-expiratory pressure (PEEP). So, a more accurate definition would be,
Dynamic compliance is change in volume divided by change in pressure, measured during normal breathing, between points of apparent zero flow at the beginning and end of inspiration.
However, even when air flow has stopped at the mouth or in the ventilator circuit does not mean that it has stopped inside the lung, and at these points of apparent zero flow there is still some pendelluft going on inside the lung.
Now, at this stage it is also important (though probably not relevant for exam purposes) to point out that in fact the definition of dynamic compliance used here (and in many other resources) is not entirely accurate. Even though that is what the examiners want you to think, the inclusion of resistance in the definition makes dynamic compliance something of a misnomer. Or rather, it would be more accurate to say that the equation,
Cdyn = VT / (PIP - PEEP)
- VT is the tidal volume
- PIP is the peak inspiratory pressure
- PEEP is the positive end-expiratory pressure
does not measure a compliance of any sort, because resistance is included in the measurement.
Moreover, in any case the measurement of dynamic compliance which is usually performed by the mechanical ventilator during routine function is determined from constructing a pressure-volume loop during ventilation. That loop allows the ventilator to determine where the gas flow is zero, i.e. where the airway pressure and alveolar pressure is equal. The gradient of the line connecting these points is the dynamic compliance. The point of zero gas flow, however, is usually not the peak inspiratory pressure, but something closer to P1, the drop in pressure which occurs at the end of inspiration:
Thus, in a mechanically ventilated patient, the Cdyn is calculated as:
Cdyn = VT / (P1 - PEEP)
- VT is the tidal volume
- P1 is the pressure shortly after cessation of flow, which is slightly higher than the plateau pressure which would give you dynamic compliance
- PEEP is the positive end-expiratory pressure
In essence, it is the same compliance but measured during normal inspiration and expiration. Dynamic compliance is always lower than static compliance. The reason for this is that dynamic compliance, in addition to the usual chest wall pressure and lung pressure, also incorporates airflow resistance.
This is the main difference between static and dynamic compliance. There is airway resistance which increases the pressure at every volume, and this depends on the gas flow rate. Resistance increases with increasing airflow, especially as the flow turns turbulent. As such, the contribution of airway resistance to dynamic compliance increases as airflow increases, which in turn decreases compliance.
Another major difference between static and dynamic compliance is the lack of an equilibration pause at the time of measurement. With the static compliance measurement methods, one usually measures a lung when it is completely still, after a few seconds have allowed units with longer time-constants to become completely filled. Measurement of dynamic compliance happens on the fly, and there is no time for air to distribute to those slower lung units. The consequence of this is a higher pressure measured for unit volume, i.e. a lower lung compliance. Moreover, the shorter the inspiratory and expiratory time, the more this effect will influence dynamic compliance.
So. Dynamic compliance decreases with increasing airflow and a faster respiratory cycle. Both of these are present in tachypnoeic patients. The term typically used to describe this is "frequency dependence". Katsoulis et al (2016) demonstrated this beautifully in a group of asthmatic patients. Their graph (shamelessly stolen from the original paper) demonstrates the widening gap between static and dynamic compliance associated with increasing respiratory rate, particularly where there is small airways disease.
Apart from the abovementioned contribution of respiratory resistance to the total airway pressure here, dynamic compliance is also affected by the heterogeneity of time constants among lung units. A rapid inspiration will only have time to fill the "fast" alveoli, thereby generating pressure on the basis of the compliance of a relatively slow volume (the rest of the volume being "slow" alveoli). This will also add to the frequency dependence of dynamic compliance.
The need for the concept of specific compliance can be demonstrated by a simple thought experiment. Consider the pressure-volume relationship of a 20kg child. One might achieve vital capacity of perhaps 1L, at 20 cm H2O. Compare it to an adult, whose lung volume at 20 cm H2O might be 4L. Does this mean that the adult has higher lung compliance?
Of course, it does not. However, this demonstrates that the standard method of comparing lung compliance numbers tends to break down when one tries to compare compliance between patients who are comically mismatched in size. This is where specific compliance comes in. According to Harris (2005),
"Specific compliance is compliance that is normalized by a lung volume"
That normalising lung volume is usually the FRC. Thus, specific compliance can be expressed as:
where CTot is the total static lung compliance, and FRC can be substituted with any lung volume. Because you are dividing a value given in ml/cmH2O by a value in ml (FRC), the "ml"s cancel out, and the units used to measure specific compliance are cmH2O-1, or 1/cmH2O.
Because the chosen lung volume also scales with body size, this parameter should remain consistent irrespective of whether one is big or small. Consider: the child with their static lung compliance of 50ml/cmH2O and an FRC of 500ml would have a specific compliance of 50/500 = 0.1 cmH2O-1 . The large adult, with their compliance of 200ml/cmH2O and a larger FRC of 2000ml, would also have a specific compliance of 0.1 cmH2O-1. The normal human value for this variable is usually given as 0.05 cmH2O-1. This concept has some amazing applications in comparing the lung compliance characteristics of organisms of markedly different sizes. For one example, here is a graph from Fahlman et al (2014), comparing the specific compliance of seal species which vary in mass from 8kg (Phoca vitulina, harbour seal) to 228kg (Eumetopias jubatus, Steller sea lion):
Question 14 from 2016 and Question 1(p.2) from the second paper of 2008 asked about the factors which affect compliance. Particularly the question from 2008 was the one with the best model answer, which clearly stated what the examiners' expectations were. In summary, these factors are:
The effects of respiratory rate on dynamic compliance have been discussed already; the effects of surfactant are worth discussing separately.
Most textbooks find a way to fit lung surfactant into the category of things which affect static compliance. Usually, a graph is trotted out which demonstrates the effect an absence of surfactant has on the compliance of the lung. The reference for this is usually a famous 1971 paper by T.E. Morgan, but in fact the original experimental data weres published in 1929 by Kurt von Neergaard. Unfortunately, the original article from Zeitschrift fur die gesamte experimentelle Medizin can no longer be obtained by any reasonable (cheap) means, but the graph is sufficiently famous that one can find a version of it everywhere. In some cases, for example the diagram below from Radford (1964), one can even find the original experimental cat's serial number. For some reason, everybody always picks the graph from Cat 27.
Cat 27's lungs were first inflated and deflated with air. Then, they were submerged in saline and inflated with saline. The effect was substantial. In the saline-filled lung, the effect of the surfactant on the surface tension of the alveoli was obliterated, and only the elasticity of the lung itself was measured. The drowned lung was much more compliant than the air-filled lung.
However, this seems like an irrelevant diagram at this point. All it describes is that the presence of surface tension decreases lung compliance, and that without it the compliance of the lung tissue itself is excellent. It is well known that surfactant increases lung compliance, because water on its own has a surface tension so high that the alveoli would collapse en masse and lung compliance would be extremely poor. Surely, it would be better to illustrate this concept? A suitable diagram for this purpose comes from a paper by Lachmann et al (1980). The authors lavaged all the surfactant out of the lungs of rabbits, and thereby created conditions resembling ARDS (see their stolen graphs below).