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Lung Stress in Pulmonary & Extrapulmonary ARDS
Initially described in the late 1990s, the distinction between direct pulmonary insults [i.e. pulmonary ARDS] and indirect pulmonary insults [i.e. extra-pulmonary ARDS] is important . Additionally, direct pulmonary injury such as gastric acid aspiration may have a different molecular phenotype from indirect, extra-pulmonary affronts such as trauma or pancreatitis. Yet, for this discussion, the original, mechanical distinction is most important; i.e. the proportional differences in lung stress relative to total respiratory system stress.
The stiffness of the lungs and chest wall together may be quantified as the elastance of the respiratory system [Ers], while the stiffness of only the lungs is lung elastance [El]. In pulmonary ARDS, the ratio of the lung stiffness to the total respiratory system stiffness is high – upwards of 80% [El/Ers = 0.8] [2, 3]. By contrast, in extra-pulmonary ARDS, the relationship between lung stiffness and total system stiffness is low. This value can be as low as 20% [El/Ers = 0.2]. The El/Etot ratio is important for when it is multiplied by the pressure applied at the airway [e.g. the plateau pressure or P-High], the trans-pulmonary pressure [Ptp] – or stress – across the lung is given.Knowing the Ptp during a D-breath at P-High is important because it partially defines the envelope of the area under the pressure-volume curve – or work – applied to the lung by the ventilator . Critically, in a recent trial comparing APRV to conventional, low tidal volume ventilation [LTV] in ARDS, an apparent failure of randomization allocated a disproportionate number of patients with extra-pulmonary ARDS to APRV [only 25% had direct causes]; by contrast, 39% had pulmonary or direct causes of ARDS in the LTV group . Therefore, the APRV patients in this trial experienced less lung stress at any given airway pressure; accordingly, the favourable APRV findings – in my opinion – are tenuous.
Ergotrauma in APRV – a theoretical model
As previously described, the work performed on the lung during a single breath is divided into dynamic [e.g. gas flow] and static components [e.g. lung volume]. The summation of the dynamic and static work over time determines the mechanical power – in Joules per minute – applied to the lung [3, 5]. Thus, VILI secondary to mechanical power – ergotrauma – provides a powerful unification of multiple avenues of VILI research ; neither static pressure or volume alone drive VILI, but rather, baseline stretch [i.e. PEEP, auto-PEEP] as well as airway resistance, gas flow and respiratory rate are all mediators. Augmenting any of these variables boosts the power applied to the lung skeleton and, in theory, VILI risk. But how does this relate to P-APRV?
Firstly, the static work of the D-type breaths [Dstat], is defined by the envelope between the auto-PEEP generated at T-Low, and the Ptp generated at P-High [figure 2A & B]. But there is also a dynamic component to a D-type breath [i.e. Ddyn] that is described as gas flow multiplied by airway resistance. This parcel is illustrated to the right of the lung elastance curve. Notably, a D-breath in APRV demands gas volume delivered over a very short period of time – that is, a high inspiratory flow. Gas supplied swiftly supports turbulent flow which increases effective resistance and, therefore, dynamic work. Indeed, high flow rates are a known determinant of VILI .Secondly, B-type breaths must also be considered in the power calculation [see figures 2A & B]. Because B-breaths occur at P-High, they increase Ptp and lung volume beyond that of the D-breath. This additional work allotment, like a D breath, comprises static and dynamic elements. Ostensibly, the dynamic work is reduced at higher lung volume given tethering of airways. Yet, like the D-breath, the static and dynamic parcels of work must be multiplied by their rate to determine Joules/minute, or mechanical power. Crucially, the power for each spontaneous B-breath also includes the static work applied during the concurrent ventilator-applied D-breath; why? Using Hook’s Law as an analogy , consider a malleable material stretched from its baseline length (l) [e.g. (l) + x] and then extended repeatedly beyond x [i.e. repetitions between x and higher length y]. The total power applied is [(l) + y] multiplied by the stretch frequency. Thus, the work for a single B-breath is the static work of the D-breath plus the static and dynamic work of the B-breath. All of these parcels multiplied by the patient’s spontaneous respiratory rate equals the mechanical power of the B-breaths. From this analysis it is understood that the power applied to the directly-insulted lung can be very large in P-APRV. Empirical Evidence
There is sparse data for stress across the lung during APRV let alone mechanical power. In one report, a patient receiving F-APRV [with a relatively long P-Low] engaged in mostly D and B breaths – similar to what one would expect during P-ARPV . Importantly, an esophageal balloon was placed so both an approximation of lung stress [i.e. Ptp] was tracked with lung strain [i.e. lung volume]. Close inspection of the airway pressure curve relative to esophageal pressure [Pes] curve at the end of D and B-breaths reveals that both Ptp and lung volume doubled during a B-breath. This is consistent with increased stress and strain during spontaneous breathing in APRV [6, 7].
Work of breathing [WOB] in Joules per litre during APRV has been calculated in a small cohort of patients receiving F-APRV . One patient in this investigation – ‘subject 9’ – engaged in mostly B and D type breaths. Here, spontaneous WOB was 1.25 Joules/Litre while the ventilator delivered roughly 2.75 Joules/Litre of work for a total of roughly 4.0 J/L [recall that a normal work of breathing is 0.3 to 0.6 J/L ]. As minute ventilation was 12 L/min, the overall power applied to the lung was 48 Joules/minute! The power threshold for VILI is not known in humans; in a swine model, it was 12 J/min . As human lungs have twice the specific elastance as swine , one would expect this threshold to at least double in humans, but these comparisons are extremely tenuous.
Caveat and Conclusion
An intriguing investigation demonstrated that the fall in pleural pressure [Ppl] during spontaneous effort is not distributed evenly across all pleural surfaces in ARDS – as it does in health . Rather, the lower lobes experience disproportionately low Ppl leading to cryptic stress, strain and pendeluft – sloshing of air from the ventral to the dorsal lung units at the onset of inspiration. Crucially, the Ppl observed was much lower than the Pes; accordingly, the aforementioned calculations may actually underestimate the total power during B-type breaths. Nevertheless, the high auto-PEEP generated by APRV may diminish lower lobe stress and strain during spontaneous breathing .
Thus, widely opening the lung during inspiration and expiration reduces microstrain, but the pressure required can multiply the mechanical power experienced by the lung – especially if supplemented by spontaneous breaths. Evidence for aggressive recruitment – an attempt to reduce lung inhomogeneity and stress raisers – is revealing a cryptic cost. Should we adopt a lower threshold for prone position – which homogenizes stress raisers without increased power – than for initiation of APRV? Finally, should we be open to closing the lung and keeping it closed ?
Dr. Kenny is the cofounder and Chief Medical Officer of Flosonics Medical; he also the creator and author of a free hemodynamic curriculum at heart-lung.org
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