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The bioactive HFMs were then potted in a model gas exchange device (0.0084 m2) and tested in a recirculation loop with a CO2 inlet of 50 mmHg under steady blood flow.
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This paper presents a novel discrete-time linear parameter-varying model for gas exchange dynamics during cycling.
In the current study, Computational Fluid Dynamics (CFD) are utilized to model the gas exchange process and investigate the underlying phenomena behind trapping losses in a loop-scavenged FPLA.
The use of a two-parameter model of gas exchange to describe variation in the PaO2/FiO2 ratio has been investigated.
The data were analysed using two mathematical models of gas exchange: the 'effective shunt' model, used by Aboab and colleagues [ 6]; and the two-parameter model [ 11, 13, 14], the equations of which have been published previously ([ 14] electronic supplement).
More detailed models of gas exchange in the pulmonary capillaries have been explored by Whiteley et al. [20] (see also Whiteley et al. [21]) and Vadapalli et al. [22].
Using mathematical models describing gas exchange, previous authors have simulated values of the PaO2/FiO2 ratio and have shown them to vary with the FiO2 level [ 6- 8].
The measured noble gas patterns were interpreted using inverse modeling and conceptual gas exchange models and were compared to results of numerical simulations of gas bubble dissolution in water filled soil columns.
This model is a three-input-three-output physics-based control oriented model and consists of gas exchange sub-model and combustion sub-model.
Overheating problems again are cited by a new study (Gillooly, Allen & Charnov, 2006) that combines a recent gigantothermy model with an avian-like gas exchange model that takes bradymetabolism into account.
Heliox did neither allow for reduced minute volume ventilation in this model nor improve gas exchange.
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