A closed-loop approach to the study of the baroreflex dynamics during posture changes at rest and at exercise in humans.

We hypothesized that during rapid uptilting at rest, due to vagal withdrawal, arterial baroreflex sensitivity (BRS) may decrease promptly and precede the operating point (OP) resetting, whereas different kinetics are expected during exercise steady state, due to lower vagal activity than at rest. To test this, eleven subjects were rapidly (<2 s) tilted from supine (S) to upright (U) and vice versa every 3 min, at rest and during steady-state 50 W pedaling. Mean arterial pressure (MAP) was measured by finger cuff (Portapres) and R-to-R interval (RRi) by electrocardiography. BRS was computed with the sequence method both during steady and unsteady states. At rest, BRS was 35.1 ms·mmHg-1 (SD = 17.1) in S and 16.7 ms·mmHg-1 (SD = 6.4) in U (P < 0.01), RRi was 901 ms (SD = 118) in S and 749 ms (SD = 98) in U (P < 0.01), and MAP was 76 mmHg (SD = 11) in S and 83 mmHg (SD = 8) in U (P < 0.01). During uptilt, BRS decreased promptly [first BRS sequence was 19.7 ms·mmHg-1 (SD = 5.0)] and was followed by an OP resetting (MAP increase without changes in RRi). At exercise, BRS and OP did not differ between supine and upright positions [BRS was 7.7 ms·mmHg-1 (SD = 3.0) and 7.7 ms·mmHg-1 (SD = 3.5), MAP was 85 mmHg (SD = 13) and 88 mmHg (SD = 10), and RRi was 622 ms (SD = 61) and 600 ms (SD = 70), respectively]. The results support the tested hypothesis. The prompt BRS decrease during uptilt at rest may be ascribed to a vagal withdrawal, similarly to what occurs at exercise onset. The OP resetting may be due to a slower control mechanism, possibly an increase in sympathetic activity.

Baroreflex responses during dry resting and exercise apnoeas in air and pure oxygen.

PURPOSE: We analysed the characteristics of arterial baroreflexes during the first phase of apnoea (φ1). METHODS: 12 divers performed rest and exercise (30 W) apnoeas (air and oxygen). We measured beat-by-beat R-to-R interval (RRi) and mean arterial pressure (MAP). Mean RRi and MAP values defined the operating point (OP) before (PRE-ss) and in the second phase (φ2) of apnoea. Baroreflex sensitivity (BRS, ms·mmHg-1) was calculated with the sequence method. RESULTS: In PRE-ss, BRS was (median [IQR]): at rest, 20.3 [10.0-28.6] in air and 18.8 [13.8-25.2] in O2; at exercise 9.2[8.4-13.2] in air and 10.1[8.4-13.6] in O2. In φ1, during MAP decrease, BRS was lower than in PRE-ss at rest (6.6 [5.3-11.4] in air and 7.7 [4.9-14.3] in O2, p < 0.05). At exercise, BRS in φ1 was 6.4 [3.9-13.1] in air and 6.7 [4.1-9.5] in O2. After attainment of minimum MAP (MAPmin), baroreflex resetting started. After attainment of minimum RRi, baroreflex sequences reappeared. In φ2, BRS at rest was 12.1 [9.6-16.2] in air, 12.9 [9.2-15.8] in O2. At exercise (no φ2 in air), it was 7.9 [5.4-10.7] in O2. In φ2, OP acts at higher MAP values. CONCLUSION: In apnoea φ1, there is a sudden correction of MAP fall via baroreflex. The lower BRS in the earliest φ1 suggests a possible parasympathetic mechanism underpinning this reduction. After MAPmin, baroreflex resets, displacing its OP at higher MAP level; thus, resetting may not be due to central command. After resetting, restoration of BRS suggests re-establishment of vagal drive.

Breath holding as an example of extreme hypoventilation: experimental testing of a new model describing alveolar gas pathways.

NEW FINDINGS: What is the central question of this study? We modelled the alveolar pathway during breath holding on the hypothesis that it follows a hypoventilation loop on the O2 -CO2 diagram. What is the main finding and its importance? Validation of the model was possible within the range of alveolar gas compositions compatible with consciousness. Within this range, the experimental data were compatible with the proposed model. The model and its characteristics might allow predictions of alveolar gas composition whenever the alveolar ventilation goes to zero; for example, static and dynamic breath holding at the surface or during ventilation/intubation failure in anaesthesia. ABSTRACT: According to the hypothesis that alveolar partial pressures of O2 and CO2 during breath holding (BH) should vary following a hypoventilation loop, we modelled the alveolar gas pathways during BH on the O2 -CO2 diagram and tested it experimentally during ambient air and pure oxygen breathing. In air, the model was constructed using the inspired and alveolar partial pressures of O2 ( PIO2 and PAO2 , respectively) and CO2 ( PICO2 and PACO2 , respectively) and the steady-state values of the pre-BH respiratory exchange ratio (RER). In pure oxygen, the model respected the constraint of PACO2=-PAO2+PIO2 . To test this, 12 subjects performed several BHs of increasing duration and one maximal BH at rest and during exercise (30 W cycling supine), while breathing air or pure oxygen. We measured gas flows, PAO2 and PACO2 before and at the end of all BHs. Measured data were fitted through the model. In air, PIO2  = 150 ± 1 mmHg and PICO2  = 0.3 ± 0.0 mmHg, both at rest and at 30 W. Before BH, steady-state RER was 0.83 ± 0.16 at rest and 0.77 ± 0.14 at 30 W; PAO2  = 107 ± 7 mmHg at rest and 102 ± 8 mmHg at 30 W; and PACO2  = 36 ± 4 mmHg at rest and 38 ± 3 mmHg at 30 W. By model fitting, we computed the RER during the early phase of BH: 0.10 [95% confidence interval (95% CI) = 0.08-0.12] at rest and 0.13 (95% CI = 0.11-0.15) at 30 W. In oxygen, model fitting provided PIO2 : 692 (95% CI = 688-696) mmHg at rest and 693 (95% CI = 689-698) mmHg at 30 W. The experimental data are compatible with the proposed model, within its physiological range.

Effect of Lower Body Negative Pressure on Phase I Cardiovascular Responses at Exercise Onset.

We hypothesised that vagal withdrawal and increased venous return interact in determining the rapid cardiac output (CO) response (phase I) at exercise onset. We used lower body negative pressure (LBNP) to increase blood distribution to the heart by muscle pump action and reduce resting vagal activity. We expected a larger increase in stroke volume (SV) and smaller for heart rate (HR) at progressively stronger LBNP levels, therefore CO response would remain unchanged. To this aim ten young, healthy males performed a 50 W exercise in supine position at 0 (Control), -15, -30 and -45 mmHg LBNP exposure. On single beat basis, we measured HR, SV, and CO. Oxygen uptake was measured breath-by-breath. Phase I response amplitudes were obtained applying an exponential model. LBNP increased SV response amplitude threefold from Control to -45 mmHg. HR response amplitude tended to decrease and prevented changes in CO response. The rapid response of CO explained that of oxygen uptake. The rapid SV kinetics at exercise onset is compatible with an increased venous return, whereas the vagal withdrawal conjecture cannot be dismissed for HR. The rapid CO response may indeed be the result of two independent yet parallel mechanisms, one acting on SV, the other on HR.

Gas exchange and cardiovascular responses during breath-holding in divers.

To check whether the evolution of alveolar pressures of O2 (PAO2) and CO2 (PACO2) explains the cardiovascular responses to apnoea, eight divers performed resting apnoeas of increasing duration in air and in O2. We measured heart rate (fH), arterial pressure (AP), and peripheral resistances (TPR) beat-by-beat, PAO2 and PACO2 at the end of each apnoea. The three phases of the cardiovascular response to apnoea were observed. In O2, TPR increase (9 ±â€¯4 mmHg min l-1) and fH decrease (-11 ±â€¯8 bpm) were lower than in air (15 ±â€¯5 mmHg min l-1 and -28 ±â€¯13 bpm, respectively). At end of maximal apnoeas in air, PAO2 and PACO2 were 50 ±â€¯9 and 48 ±â€¯5 mmHg, respectively; corresponding values in O2 were 653 ±â€¯8 mmHg and 55 ±â€¯5 mmHg. At end of phase II, PAO2 and PACO2 in air were 90 ±â€¯13 mmHg and 42 ±â€¯4 mmHg respectively; corresponding values in O2 were 669 ±â€¯7 mmHg and 47 ±â€¯6 mmHg. The PACO2 increase may trigger the AP rise in phase III.

Experimental validation of the 3-parameter critical power model in cycling.

PURPOSE: The three-parameter model of critical power (3-p) implies that in the severe exercise intensity domain time to exhaustion (Tlim) decreases hyperbolically with power output starting from the power asymptote (critical power, wcr) and reaching 0 s at a finite power limit (w0) thanks to a negative time asymptote (k). We aimed to validate 3-p for short Tlim and to test the hypothesis that w0 represents the maximal instantaneous muscular power. METHODS: Ten subjects performed an incremental test and nine constant-power trials to exhaustion on an electronically braked cycle ergometer. All trials were fitted to 3-p by means of non-linear regression, and those with Tlim greater than 2 min also to the 2-parameter model (2-p), obtained constraining k to 0 s. Five vertical squat jumps on a force platform were also performed to determine the single-leg (i.e., halved) maximal instantaneous power. RESULTS: Tlim ranged from 26 ± 4 s to 15.7 ± 4.9 min. In 3-p, with respect to 2-p, wcr was identical (177 ± 26 W), while curvature constant W' was higher (17.0 ± 4.3 vs 15.9 ± 4.2 kJ, p < 0.01). 3-p-derived w0 was lower than single-leg maximal instantaneous power (1184 ± 265 vs 1554 ± 235 W, p < 0.01). CONCLUSIONS: 3-p is a good descriptor of the work capacity above wcr up to Tlim as short as 20 s. However, since there is a discrepancy between estimated w0 and measured maximal instantaneous power, a modification of the model has been proposed.

Cardiovascular responses to dry apnoeas at exercise in air and in pure oxygen.

If, as postulated, the end of the steady state phase (φ2) of cardiovascular responses to apnoea corresponds to the physiological breaking point, then we may hypothesize that φ2 should become visible if exercise apnoeas are performed in pure oxygen. We tested this hypothesis on 9 professional divers by means of continuous recording of blood pressure (BP), heart rate (fH), stroke volume (QS), and arterial oxygen saturation (SpO2) during dry maximal exercising apnoeas in ambient air and in oxygen. Apnoeas lasted 45.0 ±â€¯16.9 s in air and 77.0 ±â€¯28.9 s in oxygen (p < 0.05). In air, no φ2 was observed. Conversely, in oxygen, a φ2 of 28 ±â€¯5 s duration appeared, during which systolic BP (185 ±â€¯29 mmHg), fH (93 ±â€¯16 bpm) and QS (91 ±â€¯16 ml) remained stable. End-apnoea SpO2 was 95.5 ±â€¯1.9% in air and 100% in oxygen. The results support the tested hypothesis.

Dynamics of the RR-interval versus blood pressure relationship at exercise onset in humans.

PURPOSE: The dynamics of the postulated phenomenon of exercise baroreflex resetting is poorly understood, but can be investigated using closed-loop procedures. To shed light on some mechanisms and temporal relationships participating in the resetting process, we studied the time course of the relationship between the R-R interval (RRi) and arterial pressure with a closed-loop approach. METHODS: On ten young volunteers at rest and during light exercise in supine and upright position, we continuously determined, on single-beat basis, RRi (electrocardiography), and arterial pressure (non-invasive finger pressure cuff). From pulse pressure profiles, we determined cardiac output (CO) by Modelflow, computed mean arterial pressure (MAP), and calculated total peripheral resistance (TPR). RESULTS: At exercise start, RRi was lower than in quiet rest. As exercise started, MAP fell to a minimum (MAPm) of 72.8 ± 9.6 mmHg upright and 73.9 ± 6.2 supine, while RRi dropped. The initial RRi versus MAP relationship was linear, with flatter slope than resting baroreflex sensitivity, in both postures. TPR fell and CO increased. After MAPm, RRi and MAP varied in opposite direction toward exercise steady state, with further CO increase. CONCLUSION: These results suggest that, initially, the MAP fall was corrected by a RRi reduction along a baroreflex curve, with lower sensitivity than at rest, but eventually in the same pressure range as at rest. After attainment of MAPm, a second phase started, where the postulated baroreflex resetting might have occurred. In conclusion, the change in baroreflex sensitivity and the resetting process are distinct phenomena, under different control systems.

Alveolar gas composition during maximal and interrupted apnoeas in ambient air and pure oxygen.

INTRODUCTION: We tested the hypothesis that the alveolar gas composition at the transition between the steady phase II (φ2) and the dynamic phase III (φ3) of the cardiovascular response to apnoea may lay on the physiological breaking point curve (Lin et al., 1974). METHODS: Twelve elite divers performed maximal and φ2-interrupted apnoeas, in air and pure oxygen. We recorded beat-by-beat arterial blood pressure and heart rate; we measured alveolar oxygen and carbon dioxide pressures (PAO2 and PACO2, respectively) before and after apnoeas; we calculated the PACO2 difference between the end and the beginning of apnoeas (ΔPACO2). RESULTS: Cardiovascular responses to apnoea were similar compared to previous studies. PAO2 and PACO2 at the end of φ2-interrupted apnoeas, corresponded to those reported at the physiological breaking point. For maximal apnoeas, PACO2 was less than reported by Lin et al. (1974). ΔPACO2 was higher in oxygen than in air. CONCLUSIONS: The transition between φ2 and φ3 corresponds indeed to the physiological breaking point. We attribute this transition to ΔPACO2, rather than the absolute PACO2 values, both in air and oxygen apnoeas.

Cardiovascular responses to dry resting apnoeas in elite divers while breathing pure oxygen.

PURPOSE: We hypothesized that the third dynamic phase (ϕ3) of the cardiovascular response to apnoea requires attainment of the physiological breaking point, so that the duration of the second steady phase (ϕ2) of the classical cardiovascular response to apnoea, though appearing in both air and oxygen, is longer in oxygen. METHODS: Nineteen divers performed maximal apnoeas in air and oxygen. We measured beat-by-beat arterial pressure, heart rate (fH), stroke volume (SV), cardiac output (Q˙). RESULTS: The fH, SV and Q˙ changes during apnoea followed the same patterns in oxygen as in air. Duration of steady ϕ2 was 105 ± 37 and 185 ± 36 s, in air and oxygen (p<0.05), respectively. At end of apnoea, arterial oxygen saturation was 1.00 ± 0.00 in oxygen and 0.75 ± 0.10 in air. CONCLUSIONS: The results support the tested hypothesis. Lack of hypoxaemia during oxygen apnoeas suggests that, if chemoreflexes determine ϕ3, the increase in CO2 stores might play a central role in eliciting their activation.

A new interpolation-free procedure for breath-by-breath analysis of oxygen uptake in exercise transients.

INTRODUCTION: Interpolation methods circumvent poor time resolution of breath-by-breath oxygen uptake (VO2) kinetics at exercise onset. We report an interpolation-free approach to the improvement of poor time resolution in the analysis of VO2 kinetics. METHODS: Noiseless and noisy (10% Gaussian noise) synthetic data were generated by Monte Carlo method from pre-selected parameters (Exact Parameters). Each data set comprised 10 (VO2)-on transitions with noisy breath distribution within a physiological range. Transitions were superposed (no interpolation, None), then analysed by bi-exponential model. Fitted model parameters were compared with those from interpolation methods (average transition after Linear or Step 1-s interpolations), applied on the same data. Experimental data during cycling were also analysed. The 95% confidence interval around a line of parameters' equality was computed to analyse agreement between exact parameters and corresponding parameters of fitted functions. RESULTS: The line of parameters' equality stayed within confidence intervals for noiseless synthetic parameters with None, unlike Step and Linear, indicating that None reproduced Exact Parameters. Noise addition reduced differences among pre-treatment procedures. Experimental data provided lower phase I time constants with None than with Step. CONCLUSION: In conclusion, None revealed better precision and accuracy than Step and Linear, especially when phenomena characterized by time constants of <30 s are to be analysed. Therefore, we endorse the utilization of None to improve the quality of breath-by-breath [Formula: see text] data during exercise transients, especially when a double exponential model is applied and phase I is accounted for.

Effects of step duration in incremental ramp protocols on peak power and maximal oxygen consumption.

PURPOSE: Morton (J Sport Sci 29:307-309, 2011) proposed a model of the peak power attained in ramp protocol ([Formula: see text]) that included critical power (CP) and anaerobic capacity as constants, and mean ramp slope (S) as variable. Our hypothesis is that [Formula: see text] depends only on S, so that Morton's model should be applicable in all types of ramps. The aim of this study was to test this hypothesis by validating Morton's model using stepwise ramp tests with invariant step increment and increasing step duration. METHODS: Sixteen men performed six ramp tests with 25 W increments. Step duration was: 15, 30, 60, 90, 120 and 180 s. Maximal oxygen consumption ([Formula: see text]) and [Formula: see text] were identified as the highest values reached during each test. An Åstrand-type test was also performed. We measured oxygen consumption and ventilatory variables, together with lactate and heart rate. RESULTS: [Formula: see text] was the same in all tests; [Formula: see text] was significantly lower the longer the step duration, and all values differed from the maximal power of the Åstrand-type test ([Formula: see text]). Morton's model yielded an excellent fitting, with mean CP equal to 198.08 ± 37.46 W and anaerobic capacity equal to 16.82 ± 5.69 kJ. CONCLUSIONS: Morton's model is a good descriptor of the mechanics of ramp tests. Further developments of Morton's model demonstrated that, whereas [Formula: see text] is a protocol-dependent variable, the difference between [Formula: see text] and CP is a constant, so that their values do not depend on the protocol applied.

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.

Energetics of running in top-level marathon runners from Kenya.

On ten top-level Kenyan marathon runners (KA) plus nine European controls (EC, equivalent to KA), we measured maximal oxygen consumption (VO2max) and the energy cost of running (Cr) on track during training camps at moderate altitude, to better understand the KA dominance in the marathon. At each incremental running speed, steady-state oxygen consumption (VO2) was measured by telemetric metabolic cart, and lactate by electro-enzymatic method. The speed requiring VO2 = VO2max provided the maximal aerobic velocity (νmax). The energy cost of running was calculated by dividing net VO2 by the corresponding speed. The speed at lactate threshold (ν(ΘAN)) was computed from individual Lâ(b) versus speed curves. The sustainable VO2max fraction (Fd) at ν(ΘAN) (F(ΘAN)) was computed dividing nu(ΘAN) by νmax. The Fd for the marathon (Fmar) was determined as Fmar = 0.92 F(ΘAN). Overall, VO2max (64.9 ± 5.8 vs. 63.9 ± 3.7 ml kg(-1) min(-1)), νmax (5.55 ± 0.30 vs. 5.41 ± 0.29 m s(-1)) and Cr (3.64 ± 0.28 vs. 3.63 ± 0.31 J kg(-1) m(-1)) resulted the same in KA as in EC. In both groups, Cr increased linearly with the square of speed. F(ΘAN) was 0.896 ± 0.054 in KA and 0.909 ± 0.068 in EC; Fmar was 0.825 ± 0.050 in KA and 0.836 ± 0.062 in EC (NS). Accounting for altitude, running speed predictions from present data are close to actual running performances, if F(ΘAN) instead of Fmar is taken as index of Fd. In conclusion, both KA and EC did not have a very high VO2max, but had extremely high Fd, and low Cr, equal between them. The dominance of KA over EC cannot be explained on energetic grounds.

Cardiovascular time courses during prolonged immersed static apnoea.

To define the dynamics of cardiovascular adjustments to apnoea during immersion, beat-to-beat heart rate (HR) and systolic (SBP) and diastolic (DBP) blood pressures were recorded in six divers during and after prolonged apnoeas while resting fully immersed in 27 degrees C water. Apnoeas lasted 215 +/- 35 s. Compared to control values, HR decreased by 20 beats min(-1) and SBP and DBP increased by 23 and 17 mmHg, respectively, in the initial 20 +/- 3 s (phase I). Both HR and BP remained stable during the following 92 +/- 15 s (phase II). Subsequently, during the final 103 +/- 29 s, SBP and DBP increased linearly to values about 60% higher than control, whereas HR remained unchanged (phase III). Cardiac output (Q') decreased by 35% in phase I and did not further change in phases II and III. Compared to control, total peripheral resistances were twice and three times higher than control, respectively, at the end of phases I and III. After resumption of breathing, HR and BP returned to control values in 5 and 30 s, respectively. The time courses of cardiovascular adjustments to immersed breath-holding indicated that cardiac response took place only at the beginning of apnoea. In contrast, vascular responses showed two distinct adjustments. This pattern suggests that the chronotropic control via the baroreflex is modified during apnoea. These cardiovascular changes during immersed static apnoea are in agreement with those already reported for static dry apnoeas.

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.

Heart rate and blood pressure time courses during prolonged dry apnoea in breath-hold divers.

To define the dynamics of cardiovascular adjustments to apnoea, beat-to-beat heart rate (HR) and blood pressure and arterial oxygen saturation (SaO(2)) were recorded during prolonged breath-holding in air in 20 divers. Apnoea had a mean duration of 210 +/- 70 s. In all subjects, HR attained a value 14 beats min(-1) lower than control within the initial 30 s (phase I). HR did not change for the following 2-2.5 min (phase II). Then, nine subjects interrupted the apnoea (group A), whereas 11 subjects (group B) could prolong the breath-holding for about 100 s, during which HR continuously decreased (phase III). In both groups, mean blood pressure was 8 mmHg above control at the end of phase I; it then further increased by additional 12 mmHg at the end of the apnoea. In both groups, SaO(2) did not change in the initial 100-140 s of apnoea; then, it decreased to 95% at the end of phase II. In group B, SaO(2) further diminished to 84% at the end of phase III. A typical pattern of cardiovascular readjustments was identified during dry apnoea. This pattern was not compatible with a role for baroreflexes in phase I and phase II. Further readjustment in group B may imply a role for both baroreflexes and chemoreflexes. Hypothesis has been made that the end of phase II corresponds to physiological breakpoint.

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 Grønlund'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.

The effects of beta1-adrenergic blockade on cardiovascular oxygen flow in normoxic and hypoxic humans at exercise.

At exercise steady state, the lower the arterial oxygen saturation (SaO(2)), the lower the O(2) return (QvO(2)). A linear relationship between these variables was demonstrated. Our conjecture is that this relationship describes a condition of predominant sympathetic activation, from which it is hypothesized that selective beta1-adrenergic blockade (BB) would reduce O(2) delivery (QaO(2)) and QvO(2). To test this hypothesis, we studied the effects of BB on QaO(2) and QvO(2) in exercising humans in normoxia and hypoxia. O(2) consumption VO(2), cardiac output Q, CO(2) rebreathing), heart rate, SaO(2) and haemoglobin concentration were measured on six subjects (age 25.5 +/- 2.4 years, mass 78.1 +/- 9.0 kg) in normoxia and hypoxia (inspired O(2) fraction of 0.11) at rest and steady-state exercises of 50, 100, and 150 W without (C) and with BB with metoprolol. Arterial O(2) concentration (CaO(2)), QaO(2) and QvO(2) were then computed. Heart rate, higher in hypoxia than in normoxia, decreased with BB. At each VO(2), Q was higher in hypoxia than in normoxia. With BB, it decreased during intense exercise in normoxia, at rest, and during light exercise in hypoxia. SaO(2) and CaO(2) were unaffected by BB. The QaO(2) changes under BB were parallel to those in Q.QvO(2) was unaffected by exercise in normoxia. In hypoxia the slope of the relationship between QaO(2) and VO(2) was lower than 1, indicating a reduction of QvO(2) with increasing workload. QvO(2) was a linear function of SaO(2) both in C and in BB. The line for BB was flatter than and below that for C. The resting QvO(2) in normoxia, lower than the corresponding exercise values, lied on the BB line. These results agree with the tested hypothesis. The two observed relationships between QvO(2) and SaO(2) apply to conditions of predominant sympathetic or vagal activation, respectively. Moving from one line to the other implies resetting of the cardiovascular regulation.

Cardiac output by Modelflow method from intra-arterial and fingertip pulse pressure profiles.

Modelflow, when applied to non-invasive fingertip pulse pressure recordings, is a poor predictor of cardiac output (Q, litre x min(-1)). The use of constants established from the aortic elastic characteristics, which differ from those of finger arteries, may introduce signal distortions, leading to errors in computing Q. We therefore hypothesized that peripheral recording of pulse pressure profiles undermines the measurement of Q with Modelflow, so we compared Modelflow beat-by-beat Q values obtained simultaneously non-invasively from the finger and invasively from the radial artery at rest and during exercise. Seven subjects (age, 24.0 +/- 2.9 years; weight, 81.2 +/- 12.6 kg) rested, then exercised at 50 and 100 W, carrying a catheter with a pressure head in the left radial artery and the photoplethysmographic cuff of a finger pressure device on the third and fourth fingers of the contralateral hand. Pulse pressure from both devices was recorded simultaneously and stored on a PC for subsequent Q computation. The mean values of systolic, diastolic and mean arterial pressure at rest and exercise steady state were significantly ( P < 0.05) lower from the finger than the intra-arterial catheter. The corresponding mean steady-state Q obtained from the finger (Qporta) was significantly ( P < 0.05) higher than that computed from the intra-arterial recordings (Qpia). The line relating beat-by-beat Qporta and Qpia was y =1.55 x -3.02 ( r2 = 0.640). The bias was 1.44 litre x min(-1) and the precision was 2.84 litre x min(-1). The slope of this line was significantly higher than 1, implying a systematic overestimate of Q by Qporta with respect to Qpia. Consistent with the tested hypothesis, these results demonstrate that pulse pressure profiles from the finger provide inaccurate absolute Q values with respect to the radial artery, and therefore cannot be used without correction with a calibration factor calculated previously by measuring Q with an independent method.