- Open Access
Influence of changes in ventricular systolic function and loading conditions on pulse contour analysis-derived femoral dP/dtmax
Annals of Intensive Care volume 9, Article number: 61 (2019)
- The Letter to the Editor to this article has been published in Annals of Intensive Care 2019 9:111
Femoral dP/dtmax (maximum rate of the arterial pressure increase during systole) measured by pulse contour analysis has been proposed as a surrogate of left ventricular (LV) dP/dtmax and as an estimator of LV systolic function. However, femoral dP/dtmax may be influenced by LV loading conditions. In this study, we evaluated the impact of variations of LV systolic function, preload and afterload on femoral dP/dtmax in critically ill patients with cardiovascular failure to ascertain its reliability as a marker of LV systolic function.
We performed a prospective observational study to evaluate changes in femoral dP/dtmax, thermodilution-derived variables (PiCCO2—Pulsion Medical Systems, Feldkirchen, Germany) and LV ejection fraction (LVEF) measured by transthoracic echocardiography during variations in dobutamine and norepinephrine doses and during volume expansion (VE) and passive leg raising (PLR). Correlations with arterial pulse and systolic pressure, effective arterial elastance, total arterial compliance and LVEF were also evaluated. In absolute values, femoral dP/dtmax deviated from baseline by 21% (201 ± 297 mmHg/s; p = 0.013) following variations in dobutamine dose (n = 17) and by 15% (177 ± 135 mmHg/s; p < 0.001) following norepinephrine dose changes (n = 29). Femoral dP/dtmax remained unchanged after VE and PLR (n = 24). Changes in femoral dP/dtmax were strongly correlated with changes in pulse pressure and systolic arterial pressure during dobutamine dose changes (R = 0.942 and 0.897, respectively), norepinephrine changes (R = 0.977 and 0.941, respectively) and VE or PLR (R = 0.924 and 0.897, respectively) (p < 0.05 in all cases). Changes in femoral dP/dtmax were correlated with changes in LVEF (R = 0.527) during dobutamine dose variations but also with effective arterial elastance and total arterial compliance in the norepinephrine group (R = 0.638 and R = − 0.689) (p < 0.05 in all cases).
Pulse contour analysis-derived femoral dP/dtmax was not only influenced by LV systolic function but also and prominently by LV afterload and arterial waveform characteristics in patients with acute cardiovascular failure. These results suggest that femoral dP/dtmax calculated by pulse contour analysis is an unreliable estimate of LV systolic function during changes in LV afterload and arterial load by norepinephrine and directly linked to arterial waveform determinants.
Current haemodynamic monitoring devices performing arterial pulse contour analysis can measure and monitor the maximum rate of rise of arterial pressure (dP/dtmax). By analogy with the left ventricle (LV) dP/dtmax, arterial dP/dtmax is supposed to reflect LV systolic function [1,2,3,4,5,6,7,8].
Several studies have suggested that measurements of arterial dP/dtmax obtained from radial [7, 9] and femoral [7, 10] arterial pressure waveforms were comparable to LV dP/dtmax and, in some cases, might be useful for predicting patient outcome . However, conflicting results regarding the comparability of LV dP/dtmax and arterial dP/dtmax have also been presented in both adults and children [12, 13]. Despite these uncertainties, arterial dP/dtmax is most often presented as a marker of LV systolic function in many off-the-shelf haemodynamic monitoring systems. Supportive literature is based on the observed good correlation between LV and arterial dP/dtmax during periods of haemodynamic stability [7,8,9, 12]. However, these good correlations documented on stable patients do not necessarily imply that femoral dP/dtmax provides an adequate evaluation of changes in LV systolic function during haemodynamic challenges.
Many physiological factors other than LV systolic function may influence arterial dP/dtmax, including the timing of the measurement relative to aortic valve opening, and the potential influences of cardiac preload and afterload (including its resistive and pulsatile components). To be considered a reliable marker of LV systolic function, arterial dP/dtmax should be unaffected by changes in these variables and should consistently respond to directional changes in LV systolic function.
Therefore, to assess the validity of arterial dP/dtmax as an index of LV systolic function and the relative contribution of changes in cardiac preload and afterload on its measurement, we studied the responses of femoral dP/dtmax during changes in the dose of dobutamine and norepinephrine, during passive leg raising (PLR) manoeuvre  and after intravascular fluid administration in critically ill patients with circulatory shock. We also compared these changes with markers of left ventricular afterload and with left ventricle ejection fraction (LVEF) measured by transthoracic echocardiography.
We performed a prospective observational study in two adult intensive care units (Servei de Medicina Intensiva, Corporació Sanitària Universitària Parc Taulí, Sabadell, Spain, and Service de Médecine intensive-réanimation, Hôpital de Bicêtre, Le Kremlin-Bicêtre, France). The study was approved by local ethics committees of both institutions (Comitè Ètic d’Investigació Clínica de la Corporació Sanitària Parc Taulí CEIC2013616 and Comité pour la Protection des Personnes Ile-de-France VII 2011A01696-35). All patients or next of kin gave their consent to participate to the study. Data in this manuscript are presented following the “Strengthening the Reporting of Observational Studies in Epidemiology” (STROBE) criteria for observational studies .
Inclusion criteria were age older than 18 years old and presence of at least one of the following signs of haemodynamic failure in the context of acute illness:
Systolic arterial pressure ≤ 90 mmHg or decreases of more than 50 mmHg in the last 3 h or mean arterial pressure ≤ 65 mmHg
Oliguria ≤ 0.5 mL/kg/h for more than 2 h
Blood lactate ≥ 2 mmol/L (or 22 mg/dL)
Central venous oxygen saturation ≤ 60%
Patients had to be monitored with a transpulmonary thermodilution device (PICCO2, Pulsion Medical Systems, Feldkirchen, Germany) and must present the need for a change in the dose of norepinephrine or dobutamine, or for volume expansion or a PLR test , as decided by the attending physicians.
Exclusion criteria were the evidence of a significant aortic stenosis with echocardiography (mean pressure gradient of the aortic valve ≥ 25 mmHg) and conditions precluding measurements of femoral dP/dtmax of sufficient quality such as over-damping or under-damping of the arterial pressure signal persisting after repeated flushes of the arterial line.
Arterial pressure was measured through an arterial catheter inserted in the femoral artery (PV2015L20-A, Pulsion Medical Systems, Feldkirchen, Germany). The catheter was connected to a PiCCO2 device, which automatically and continuously calculated femoral dP/dtmax. With this device, dP/dtmax was obtained from the uprising portion of the arterial curve, representing the steepest incline of the arterial trace in systole, and averaged over 12 s. After zeroing the arterial pressure transducer system and before each measurement, the arterial waveform signal quality was checked visually using a fast flush test to assess the adequacy of its damping . In case of damping, repeated flushes were performed until sufficient signal quality was acquired. Data were recorded automatically by the PICCO2 device, and synchronisation of measurements with interventions was performed manually and required the presence of the investigator team.
Transthoracic echocardiography was performed with a CX 50 device (Philips Healthcare, DA Best, The Netherlands) and used to estimate LV ejection fraction (LVEF). Measurements were taken by the same observer in all cases (SV) using the Simpson’s method from two- and four-chamber apical views. Endocardial contours were hand-drawn, and volumes were automatically averaged out over three consecutive cardiac cycles by the software to calculate LVEF.
All patients were equipped with a central venous catheter in the superior vena cava territory. Thermodilution measurements were taken by injection of a 15-mL cold saline bolus (< 8 °C) through the central venous catheter. The results of three consecutive thermodilution measurements were averaged . Cardiac output and stroke volume were measured through transpulmonary thermodilution  and indexed to body surface to provide cardiac index (CI), stroke volume index (SVI) and global end-diastolic volume index (GEDVi). Cardiac function index was obtained directly from the PiCCO2 device as a calculated variable (CFI = CI/GEDVi) .
To evaluate the resistive component of the arterial load, we calculated the systemic vascular resistance index (SVRi) as SVRi = (mean arterial pressure − central venous pressure)/cardiac index. To evaluate the pulsatile component of arterial loading, we calculated the total arterial compliance (TAC = stroke volume/arterial pulse pressure) . Pulse pressure was calculated as the systolic minus the diastolic arterial pressure. The effective arterial elastance was used as a global index of arterial load as previously described (Ea = 0.9 × systolic arterial pressure/stroke volume) .
Data were collected before and after haemodynamic interventions. Volume expansion was performed by infusing 500 mL 0.9% saline solution over 10 min. Although other fluids might be considered for volume expansion , 0.9% saline solution was used in the units at the time the study was performed. A PLR test was performed by moving the patient from the semi-recumbent position to a position where the trunk is horizontal and the legs are elevated at 45°, as previously described .
In patients receiving fluid, the post-intervention measurements were taken immediately after the end of volume expansion. In patients in whom a PLR test was performed, these measurements were taken at the time when the maximal PLR-induced change in CI, if any, had occurred. This usually occurs within 1 min . After the change in dose of norepinephrine or dobutamine, the post-interventions recording was performed after stabilisation of pulse contour-derived CI (for dobutamine) or of mean arterial pressure (for norepinephrine).
Patients could be included in the study as many times as therapeutic interventions were indicated by the attending physicians. Multiple measurements on the same patient could only be performed after sufficient time had passed between different manoeuvres to allow for stabilisation of haemodynamic variables and provided that the haemodynamic status of the patient had significantly changed when assessing the same type of interventions.
During norepinephrine dose variations, changes in Ea, TAC and SVRi were used to identify changes in arterial loading properties, while changes in systolic and mean arterial pressure were used to estimate changes in LV afterload. During dobutamine dose variations, changes in LVEF, CI and CFI were used to estimate changes in LV systolic function. Finally, during PLR and volume expansion, changes in central venous pressure (CVP) and GEDVi were used to track changes in LV preload.
We considered changes in femoral dP/dtmax induced by dobutamine dose variations as the main study variable. Using previous published data  and assuming a minimum required threshold of 10%, an α risk of 5% and a β risk of 20%, we estimated that the minimum number of paired measurements required for detecting a significant change in femoral dP/dtmax during variations in the dose of dobutamine was seven. We continued inclusions in the other study groups (changes in the dose of norepinephrine and PLR/VE) until this number was reached in both dobutamine subgroups (dose increases and decreases).
Normality of variables was assessed using the Kolmogorov–Smirnov test. Data are presented as mean ± standard deviation (SD) or medians and 25th–75th percentile, as appropriate. Data from norepinephrine and dobutamine dose changes were pooled (absolute values of increases and decreases were evaluated together and averaged), and absolute deviations from baseline values (called “changes” or “variations”) were presented as mean differences. Statistical comparisons were made using the paired Student’s t test or Wilcoxon rank test as appropriate. Percentages of change, rather than raw values alone, were presented in order to normalise baseline values. Correlation of changes in study variables during interventions was performed using Pearson’s correlation test. In order to evaluate the potential impact of repeated measurements of the same type on a single patient, we studied changes in femoral dP/dtmax during interventions using only one measurement per patient. Manoeuvres with the highest norepinephrine or dobutamine dose change were selected, as well as the first volume expansion or PLR performed in each patient. All statistical calculations were done using SPSS version 22 (International Business Machines, Armonk, NY, USA). Values of p < 0.05 were considered statistically significant.
Nineteen patients were included (68% male subjects) between March 2013 and January 2015, in whom 72 therapeutic interventions were analysed (162 data points). Arterial line damping problems were observed in five patients, representing nine interventions. In all cases, repeated flushing of the arterial line led to resolution of the damping effect, so that no patient was excluded due to this problem. Two interventions had to be rejected given repeatedly doubtful validity of the data due to patient movement and incorrect acquisition procedure (Additional file 1: Figure S1). The distribution of medical interventions was as follows: norepinephrine dose increase: 9 (13%), norepinephrine dose decrease: 20 (29%), PLR: 12 (17%), volume expansion: 12 (17%), dobutamine dose increase: 7 (10%), dobutamine dose decrease: 10 (14%). On average, 3.7 ± 2.0 interventions were collected in each patient (Additional file 1: Figure S1). Case demographics and clinical characteristics are presented in Table 1 and Additional file 1: Table S1. Baseline haemodynamic characteristics are presented in Table 2. The majority of interventions occurred during septic shock (54 cases; 77%), followed by cardiogenic shock (10 cases; 14%) and hypovolemic shock (6 cases; 9%). During 55 (79%) therapeutic interventions, patients were mechanically ventilated, in 25 (45%) of which patients were not fully adapted to mechanical ventilation. In 44 cases (67%), sinus rhythm was present.
Effects of dobutamine
Changes in the dose of dobutamine (n = 17 interventions; absolute dose variation = 4.3 ± 1.3 µg kg−1 min−1) induced an absolute deviation from baseline in femoral dP/dtmax of 21% and were correlated with changes in femoral dP/dtmax (R = 0.62; p = 0.008). Changes from baseline were also observed in CFI (7%), LVEF (20%), CI (12%) and heart rate (5%) (Table 3). SVI remained unchanged. While systolic arterial pressure and mean arterial pressure values did not vary, pulse pressure changed by 20%. SVRi changed by 5%; however, Ea and TAC presented no significant change. GEDVi and CVP also remained unchanged (Table 3).
When only one intervention per patient was considered, changes in the dose of dobutamine induced an absolute deviation from baseline in femoral dP/dtmax of 17% (1068 [748–1480] vs. 1254 [812–1672] mmHg−1 s−1; n = 8; p = 0.036).
Increases in the dose of dobutamine increased femoral dP/dtmax by 20% (Fig. 1; Additional file 1: Table S2) and reductions in the dose led to a decrease in femoral dP/dtmax of 28% (Fig. 1; Additional file 1: Table S2). Additional data from haemodynamic changes obtained before and after increases and decreases in dobutamine doses are presented in Additional file 1: Table S2 in the Supplemental Material.
The dobutamine-induced per cent changes in femoral dP/dtmax were significantly correlated with the per cent changes in CFI, LVEF and CI, but presented the highest correlation with systolic arterial pressure and pulse pressure (Additional file 1: Table S3).
Effects of changes in norepinephrine dose
Changes in the dose of norepinephrine (n = 29 interventions; absolute dose variation = 0.19 ± 0.16 µg kg−1 min−1) induced an absolute change from baseline in femoral dP/dtmax of 15% and were correlated with changes in femoral dP/dtmax (R = 0.47; p = 0.011). Arterial systolic, mean and pulse pressure also changed from baseline by 14, 11 and 9%, respectively. There were no significant variations in heart rate, CI and CFI (Table 3). LVEF presented a 11% change from baseline. Although SVI presented a significant change of 4%, CI remained unchanged. CVP and GEDVi also remained at baseline levels. Estimated Ea, TAC and SVRi changed by 9, 17 and 5%, respectively (Table 3).
When only one intervention per patient was considered, changes in the dose of norepinephrine induced an absolute change from baseline in femoral dP/dtmax of 11% (1134 [909–1457] vs. 1265 [1028–1623] mmHg−1 s−1; n = 13; p = 0.001).
Increases in the dose of norepinephrine increased femoral dP/dtmax by 16% (Fig. 1 and Additional file 1: Table S2) and reductions in the dose led to a decrease in femoral dP/dtmax of 8% (Fig. 1 and Additional file 1: Table S2). Additional data from haemodynamic changes obtained before and after increases and decreases in norepinephrine doses are presented in Additional file 1: Table S2 (Fig. 2).
The norepinephrine-induced per cent changes in femoral dP/dtmax were correlated with per cent changes in arterial systolic pressure, arterial pulse pressure, Ea and TAC (Additional file 1: Table S3).
Effects of volume expansion and passive leg raising
The PLR test and volume expansion (n = 24 interventions) did not induce significant changes in femoral dP/dtmax. Heart rate decreased by − 3%, and systolic arterial pressure increased by 9%, while mean arterial pressure and pulse pressure remained unchanged. LVEF did not change, but CFI significantly increased by 4%. In this subgroup, CI did not change from baseline but SVI increased significantly by 5%. CVP increased by 30%, while GEDVi remained at baseline values. Calculated Ea, TAC and SVRi also remained unchanged (Table 3).
When only one intervention per patient was considered, PLR and volume expansion did not modify femoral dP/dtmax (1161 [858–1404] vs. 1218 [1105–1379] mmHg−1 s−1; n = 14; p = 0.470).
The PLR and volume expansion-induced changes in femoral dP/dtmax presented the highest correlation with changes in pulse pressure and systolic arterial pressure (Additional file 1: Table S3).
The present study evaluated changes in pulse contour analysis-derived femoral dP/dtmax following haemodynamic interventions aimed at modifying LV systolic function and LV loading conditions (afterload and preload) in critically ill patients with acute circulatory failure. Changes in femoral dP/dtmax were strongly and consistently correlated with changes in arterial pressure waveform determinants across all interventions (arterial systolic pressure and pulse pressure). While femoral dP/dtmax changed during dobutamine infusion, thus suggesting a certain degree of relation with LV systolic function, femoral dP/dtmax also changed during norepinephrine dose variations and was correlated with changes in arterial systolic pressure, pulse pressure, TAC and Ea. Our results suggest that femoral dP/dtmax was mainly sensitive to ventricular loading conditions, specifically afterload, due to arterial load variations, and highly linked to changes in arterial pressure waveform, thus making it an unreliable tool to estimate LV systolic function in acute circulatory failure.
Femoral dP/dt max and LV systolic function
Pulse contour analysis is used at the bedside for estimating several haemodynamic variables. In particular, the arterial dP/dtmax is automatically displayed and is thought by many to be an indicator of LV systolic function. As expected, femoral dP/dtmax changed following dobutamine increases and decreases and was related to the direction and magnitude of the dose variation. Furthermore, although LVEF and CFI are not pure estimators of LV systolic function, femoral dP/dtmax changed coherently with these markers during dobutamine dose variations. Note that we assessed the LV systolic function not only with CFI, which is only an estimation of LVEF and which might be mathematically coupled with GEDVi , but also more directly, with LVEF measured by echocardiography. These results would suggest that femoral dP/dtmax retains a certain degree of relationship with LV systolic function. Also, it has been previously observed in animal models that LV dP/dtmax reflects cardiac contractility when adequate LV filling is achieved [24, 25]. In our study, femoral dP/dtmax remained unchanged during VE or PLR, which could be explained by an optimised LV preload status at the time of the intervention. This finding would suggest that, similarly to what has been previously observed [24, 25], femoral dP/dtmax is independent from cardiac preload changes, as it would be expected from a marker of LV systolic function.
Femoral dP/dt max, LV afterload and arterial load
Our results also indicated that femoral dP/dtmax is markedly influenced by changes in LV afterload (as estimated by changes in systolic and mean arterial pressure) during changes in the dose of norepinephrine. Unlike LV dP/dtmax, which is measured during the isovolumetric phase of LV contraction before aortic valve opening , femoral dP/dtmax takes place during the LV ejection phase and should therefore be more sensitive to changes in LV afterload. Our results support this hypothesis by evidencing not only significant changes in femoral dP/dtmax during changes in norepinephrine dose, but also significant correlations between changes in femoral dP/dtmax and changes in systolic and mean arterial pressure during such interventions. This demonstrates a dependence of femoral dP/dtmax with LV afterload, which may invalidate its utility as a marker of LV systolic function.
An interesting additional finding of the present study was the strong linear correlation observed between determinants of the arterial pressure waveform and femoral dP/dtmax. Our results indicate that femoral dP/dtmax maintained an almost one-to-one relationship with arterial pulse pressure and systolic arterial pressure, meaning that any change in the latter inevitably led to a change in the former. In other words, the higher the amplitude of the arterial waveform, the higher the velocity of the pressure increase, provided that heart rate remains almost constant and vice versa (constant cardiac cycle duration). As observed in our results, this relationship was strong and was observed even in cases where arterial loading conditions remained unchanged, such as during volume expansion and PLR. Therefore, any haemodynamic change affecting pulse pressure and systolic arterial pressure should, in principle, affect femoral dP/dtmax without any corresponding changes in LV contractility. It has been previously described that arterial system compliance, pulse wave reflection and arterial system impedance affect the peripheral arterial waveform [26,27,28,29]. We did not study pulse reflection waves in our patients, but we were able to confirm this hypothesis in our study by identifying a strong correlation of femoral dP/dtmax with determinants of arterial load (as estimated by Ea, TAC and SVRi) during norepinephrine dose variations.
Femoral dP/dt max in clinical practice
Our study challenges the previous belief that femoral dP/dtmax could be used as a reliable marker of LV systolic function at the bedside. This belief was based on the observed good correlation between LV and arterial dP/dtmax during periods of haemodynamic stability [7, 9, 12]. However, correlations alone lack the sufficient value to inform on the responses of femoral dP/dtmax to treatments during cardiovascular failure. The evaluation of dynamic changes during haemodynamic challenges in our study demonstrates that although femoral dP/dtmax is not completely independent from changes in LV systolic function, it is significantly affected by peripheral arterial properties and waveform characteristics.
Previous reports have also identified a strong relationship between femoral dP/dtmax and LV dP/dtmax during isolated changes in LV systolic function, independently from changes in LV loading conditions [10, 30]. In a recent study on healthy animals, Monge Garcia et al.  presented a thorough evaluation of arterial dP/dtmax and its relation to LV dP/dtmax and other markers of LV systolic function during changes in cardiac inotropic state, preload and afterload. Authors documented a positive relationship between femoral dP/dtmax and changes in LV systolic function, but also reported + 24% and − 33% changes in femoral dP/dtmax during increases or decreases in LV afterload induced by epinephrine and nitroprusside infusion, respectively, and a 20% reduction in femoral dP/dtmax during acute preload reductions induced by bleeding. Although authors conclude that the most relevant factor of femoral dP/dtmax was the change in LV systolic function, these observations also show the relevant effect of loading conditions on femoral dP/dtmax and corroborate our findings.
Therefore, it is only in cases in which one could reasonably expect that arterial loading properties and LV afterload are unchanged, that LV systolic function is the only factor modified and that femoral dP/dtmax might be used as a marker of LV systolic function. It must be admitted that such cases are uncommon in a constantly changing critically ill patient.
The present study has some limitations that warrant further discussion. First, the number of cases was small and the inclusion rate slow due to the need for specific recording equipment and need for manual synchronisation between interventions and data acquisition. Second, we did not compare measurements of femoral dP/dtmax with LV dP/dtmax. Nevertheless, the objective of the present study was to evaluate the responses of femoral dP/dtmax during haemodynamic challenges, and values of LV dP/dtmax would not have helped to fulfil such objective. Furthermore, LV catheterisation for the only purpose of the study would not have been acceptable from an ethical point of view. Alternatively, the estimation of LV dP/dtmax by echocardiography could have been performed. However, such an estimation at the bedside in critically ill patients is far from easy and may have provided unreliable measurements. Third, we did not use any device to evaluate and compensate damping of the arterial pressure signal as utilised by previous authors . However, such devices present their highest utility when high resolution of the arterial waveform is required, for example, for resonance wave analyses, which was not the case in our study. Furthermore, the absence of under- and over-damping phenomena was checked at the beginning of recordings. Fourth, while repetition of measurements on the same patient could be considered as a source of bias, we obtained the same pattern of responses to clinical interventions when only one measurement per patient was evaluated. Fifth, in order to obtain better information of potential causality and to homogeneously spread the interventions across patients, it would have been better to have followed a crossover interventional study design. However, this would have been unethical, since patients would have had to receive intravenous fluids, norepinephrine and dobutamine regardless of any clinical indication to receive such treatments. Sixth, respiratory cycle variations may alter LVEF. This potential source of bias was not taken into account when performing measurements. However, LVEF measurements were averaged over three cardiac cycles, which attenuated any respiratory variation. Furthermore, measurements were obtained during periods of haemodynamic stability and under controlled mechanical ventilation or non-distressed spontaneous ventilation, such that the respiratory variation of LVEF was probably negligible. Finally, a potential mathematical coupling between the measurement of femoral dP/dtmax and systolic arterial pressure or pulse pressure could be a point of concern. However, with the PiCCO2 device used in our study, femoral dP/dtmax was calculated at the moment of maximal pressure rise in the systolic phase of the arterial curve and was not averaged during a time segment of the curve. This approach likely discarded any potential mathematical coupling.
Femoral dP/dtmax calculated by pulse contour analysis is an unreliable estimate of LV systolic function as it is markedly sensitive to LV afterload variations and changes in arterial loading properties during acute changes in norepinephrine, and directly linked to arterial waveform characteristics.
Availability of data and materials
The datasets used and/or analysed during the current study are available from the corresponding author upon request.
passive leg raising
left ventricle ejection fraction
stroke volume index
global end-diastolic volume index
systemic vascular resistance index
total arterial compliance
effective arterial elastance
central venous pressure
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This study was supported by the clinical institutions in which it was developed. The research team performed this study as part of their regular clinical work.
Ethics approval and consent to participate
This study was approved by local ethics committees of both participating institutions (Comitè Ètic d’Investigació Clínica de la Corporació Sanitària Parc Taulí CEIC2013616 and Comité pour la Protection des Personnes Ile-de-France VII 2011A01696-35). All patients or next of kin gave their consent to participate to the study.
Consent for publication
Profs. XM and JLT are members of the medical advisory board of Pulsion Medical Systems. The remaining authors declare no conflicts of interest.
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This file contains a patient and interventions flow chart, additional information on population characteristics, pre- and post-intervention values of haemodynamic variables for the norepinephrine and dobutamine groups, as well as a correlation matrix between femoral dP/dtmax and other haemodynamic variables during studied interventions.
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Vaquer, S., Chemla, D., Teboul, J. et al. Influence of changes in ventricular systolic function and loading conditions on pulse contour analysis-derived femoral dP/dtmax. Ann. Intensive Care 9, 61 (2019). https://doi.org/10.1186/s13613-019-0537-4
- Haemodynamic monitoring
- Waveform analysis
- Ejection fraction