The art criticism of Étienne Delécluze as exemplified in his reviews of the Paris Salons held between 1819 and 1827, considered in the context of the developing artistic, social and political situation of his time

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Simultaneous determination of the kinetics of cardiac output, systemic O(2) delivery, and lung O(2) uptake at exercise onset in men

We tested whether the kinetics of systemic O(2) delivery (QaO(2)) at exercise start was faster than that of lung O(2) uptake (Vo(2)), being dictated by that of cardiac output (Q), and whether changes in Q would explain the postulated rapid phase of the Vo(2) increase. Simultaneous determinations of beat-by-beat (BBB) Q and QaO(2), and breath-by-breath Vo(2) at the onset of constant load exercises at 50 and 100 W were obtained on six men (age 24.2 +/- 3.2 years, maximal aerobic power 333 +/- 61 W). Vo(2) was determined using Gronlund's algorithm. Q was computed from BBB stroke volume (Q(st), from arterial pulse pressure profiles) and heart rate (f(h), electrocardiograpy) and calibrated against a steady-state method. This, along with the time course of hemoglobin concentration and arterial O(2) saturation (infrared oximetry) allowed computation of BBB QaO(2). The Q, QaO(2) and Vo(2) kinetics were analyzed with single and double exponential models. f(h), Q(st), Q, and Vo(2) increased upon exercise onset to reach a new steady state. The kinetics of QaO(2) had the same time constants as that of Q. The latter was twofold faster than that of Vo(2). The Vo(2) kinetics were faster than previously reported for muscle phosphocreatine decrease. Within a two-phase model, because of the Fick equation, the amplitude of phase I Q changes fully explained the phase I of Vo(2) increase. We suggest that in unsteady states, lung Vo(2) is dissociated from muscle O(2) consumption. The two components of Q and QaO(2) kinetics may reflect vagal withdrawal and sympathetic activation

Phase I dynamics of cardiac output, systemic O2 delivery, and lung O2 uptake at exercise onset in men in acute normobaric hypoxia

We tested the hypothesis that vagal withdrawal plays a role in the rapid (phase I) cardiopulmonary response to exercise. To this aim, in five men (24.6+/-3.4 yr, 82.1+/-13.7 kg, maximal aerobic power 330+/-67 W), we determined beat-by-beat cardiac output (Q), oxygen delivery (QaO2), and breath-by-breath lung oxygen uptake (VO2) at light exercise (50 and 100 W) in normoxia and acute hypoxia (fraction of inspired O2=0.11), because the latter reduces resting vagal activity. We computed Q from stroke volume (Qst, by model flow) and heart rate (fH, electrocardiography), and QaO2 from Q and arterial O2 concentration. Double exponentials were fitted to the data. In hypoxia compared with normoxia, steady-state fH and Q were higher, and Qst and VO2 were unchanged. QaO2 was unchanged at rest and lower at exercise. During transients, amplitude of phase I (A1) for VO2 was unchanged. For fH, Q and QaO2, A1 was lower. Phase I time constant (tau1) for QaO2 and VO2 was unchanged. The same was the case for Q at 100 W and for fH at 50 W. Qst kinetics were unaffected. In conclusion, the results do not fully support the hypothesis that vagal withdrawal determines phase I, because it was not completely suppressed. Although we can attribute the decrease in A1 of fH to a diminished degree of vagal withdrawal in hypoxia, this is not so for Qst. Thus the dual origin of the phase I of Q and QaO2, neural (vagal) and mechanical (venous return increase by muscle pump action), would rather be confirmed

Factors determining the time course of VO2 max decay during badrest: implications for VO2 max limitation.

[no abstract available

Correction of cardiac output obtained by Modelflow from finger pulse pressure profiles with a respiratory method in humans

The beat-by-beat non-invasive assessment of cardiac output (Q\u2019, litre\ub7min-1) based on the arterial pulse pressure analysis called Modelflow\uae can be a very useful tool for quantifying the cardiovascular adjustments occurring in exercising humans. Q\u2019 was measured in nine young subjects at rest and during steady-state cycling exercise performed at 50, 100, 150 and 200 W by using Modelflow\uae applied to the Portapres\uae non-invasive pulse wave (Q\u2019 Modelflow) and by means of the open-circuit acetylene uptake (Q\u2019C2H2 Q values were correlated linearly (r = 0.784), but Bland\u2013Altman analysis revealed that mean Q\u2019Modelflow \u2013 Q\u2019C2H2 difference (bias) was equal to 1.83 litre \ub7 min-1 with an S.D. (precision) of 4.11 litre \ub7 min-1, and 95 % limits of agreement were relatively large, i.e. from - 6.23 to + 9.89 litre \ub7 min-1. Q\u2019 Modelflow values were then multiplied by individual calibrating factors obtained by dividing Q\u2019C2H2 by Q\u2019Modelflow for each subject measured at 150 W to obtain corrected Q\u2019 Modelflow (Q\u2019 corrected)values. Q\u2019 corrected valueswerecomparedwiththecorresponding Q\u2019 C2H2values, with values at 150 W ignored. Data were correlated linearly (r = 0.931) and were not significantly different. The bias and precision were found to be 0.24 litre \ub7 min-1 and 3.48 litre \ub7 min-1 respectively, and 95 % limits of agreement ranged from - 6.58 to + 7.05 litre \ub7 min-1. In conclusion, after correction by an independent method, Modelflow\uae was found to be a reliable and accurate procedure for measuring Q\u2019 in humans at rest and exercise, and it can be proposed for routine purposes

Correction of cardiac output obtained by Modelflow from finger pulse pressure profiles with a respiratory method in humans

The beat-by-beat non-invasive assessment of cardiac output (Q litre x min(-1)) based on the arterial pulse pressure analysis called Modelflow can be a very useful tool for quantifying the cardiovascular adjustments occurring in exercising humans. Q was measured in nine young subjects at rest and during steady-state cycling exercise performed at 50, 100, 150 and 200 W by using Modelflow applied to the Portapres non-invasive pulse wave (Q(Modelflow)) and by means of the open-circuit acetylene uptake (Q(C2H2)). Q values were correlated linearly ( r = 0.784), but Bland-Altman analysis revealed that mean Q(Modelflow) - Q(C2H2) difference (bias) was equal to 1.83 litre x min(-1) with an S.D. (precision) of 4.11 litre x min(-1), and 95% limits of agreement were relatively large, i.e. from -6.23 to +9.89 litre x min(-1). Q(Modelflow) values were then multiplied by individual calibrating factors obtained by dividing Q(C2H2) by Q(Modelflow) for each subject measured at 150 W to obtain corrected Q(Modelflow) (Qcorrected) values. Qcorrected values were compared with the corresponding Q(C2H2) values, with values at 150 W ignored. Data were correlated linearly ( r = 0.931) and were not significantly different. The bias and precision were found to be 0.24 litre x min(-1) and 3.48 litre x min(-1) respectively, and 95% limits of agreement ranged from -6.58 to +7.05 litre x min(-1). In conclusion, after correction by an independent method, Modelflow was found to be a reliable and accurate procedure for measuring Q in humans at rest and exercise, and it can be proposed for routine purposes

Cardiac output, O2 delivery and VO2 kinetics during step exercise in acute normobaric hypoxia

We hypothesised that phase II time constant (τ2) of alveolar O2 uptake ( [Formula: see text] ) is longer in hypoxia than in normoxia as a consequence of a parallel deceleration of the kinetics of O2 delivery ( [Formula: see text] ). To test this hypothesis, breath-by-breath [Formula: see text] and beat-by-beat [Formula: see text] were measured in eight male subjects (25.4±3.4yy, 1.81±0.05m, 78.8±5.7kg) at the onset of cycling exercise (100W) in normoxia and acute hypoxia ( [Formula: see text] ). Blood lactate ([La]b) accumulation during the exercise transient was also measured. The τ2 for [Formula: see text] was shorter than that for [Formula: see text] in normoxia (8.3±6.8s versus 17.8±3.1s), but not in hypoxia (31.5±21.7s versus 28.4 5.4±5.4s). [La]b was increased in the exercise transient in hypoxia (3.0±0.5mM at exercise versus 1.7±0.2mM at rest), but not in normoxia. We conclude that the slowing down of the [Formula: see text] kinetics generated the longer τ2 for [Formula: see text] in hypoxia, with consequent contribution of anaerobic lactic metabolism to the energy balance in exercise transient, witnessed by the increase in [La]b