Next Article in Journal
An Evaluation Model for Brain Ischemia Protection in Mice by Low-Intensity Pulsed Ultrasound Stimulation Based on Functional Cortico-Muscular Coupling
Previous Article in Journal
An Arthroscopic Robotic System for Meniscoplasty with Autonomous Operation Ability
 
 
Search for Articles:
Title / Keyword
Author / Affiliation / Email
Journal
Article Type
 
 
Advanced Search
 
Section
Special Issue
Volume
Issue
Number
Page
 
Journals
Bioengineering
Volume 12
Issue 5
10.3390/bioengineering12050540
bioengineering-logo
Submit to this Journal Review for this Journal Propose a Special Issue
► Article Menu

Article Menu

share Share announcement Help format_quote Cite question_answer Discuss in SciProfiles
first_page
settings
Order Article Reprints
Font Type:
Arial Georgia Verdana
Font Size:
Aa Aa Aa
Line Spacing:
Column Width:
Background:
Article

Modelling and Simulation of the Interactions Between the Cardiovascular System and the Combined Use of VA ECMO and IABP: Comparison Between Peripheral and Central Configurations

by
Beatrice De Lazzari
1,2,
Massimo Capoccia
3,
Roberto Badagliacca
4,
Marc O. Maybauer
5,6,7 and
Claudio De Lazzari
8,9,*
1
Human Movement and Sport Sciences, University of Rome “Foro Italico”, 00135 Rome, Italy
2
Interuniversity Centre of Bioengineering of the Human Neuromusculoskeletal System, University of Rome “Foro Italico”, 00135 Rome, Italy
3
Northern General Hospital, Sheffield Teaching Hospitals NHS Foundation Trust, Sheffield S5 7AU, UK
4
Department of Clinical, Internal Anesthesiology and Cardiovascular Sciences, “Sapienza” University of Rome, 00185 Rome, Italy
5
Department of Anaesthesiology and Intensive Care Medicine, Philipps University, 35043 Marburg, Germany
6
Critical Care Research Group, Prince Charles Hospital, University of Queensland, Brisbane, QLD 4072, Australia
7
Division of Critical Care Medicine, Department of Anesthesiology, University of Florida, Gainesville, FL 32611, USA
8
Institute of Clinical Physiology (IFC-CNR), National Research Council, 00185 Rome, Italy
9
Faculty of Medicine, Teaching University Geomedi, 0114 Tbilisi, Georgia
*
Author to whom correspondence should be addressed.
Bioengineering 2025, 12(5), 540; https://doi.org/10.3390/bioengineering12050540
Submission received: 21 March 2025 / Revised: 28 April 2025 / Accepted: 14 May 2025 / Published: 17 May 2025
(This article belongs to the Special Issue Numerical Simulation and AI in Biological Systems)
Browse Figures
Versions Notes

Abstract

:
Veno-arterial extracorporeal membrane oxygenation (VA ECMO) for the management of refractory cardiogenic shock (CS) has been widely used in recent years. Increased left ventricular (LV) afterload induced by retrograde flow remains a limiting factor, which is particularly evident during peripheral VA ECMO support. The concomitant use of the intra-aortic balloon pump (IABP) is an established strategy to achieve LV unloading during VA ECMO support. Nevertheless, there remains controversy about the combined use of IABP during central or peripheral VA ECMO in terms of beneficial effects and outcome. We developed a simulation setting to study left ventricular unloading with IABP during peripheral and central VA ECMO using CARDIOSIM©, an established software simulator of the cardiovascular system. The aim was to quantitatively evaluate potential differences between the two VA ECMO configurations and ascertain the true beneficial effects compared to VA ECMO alone. The combined use of central VA ECMO and IABP decreased left ventricular end systolic volume and left ventricular end diastolic volume by 5–10%; right ventricular end systolic volume and right ventricular end diastolic volume by 10–20%; left atrial end systolic volume and left atrial end diastolic volume by 5–10%. Up to 25% reduction in mean left atrial pressure, up to 15% reduction in pulmonary capillary wedge pressure and up to 25% reduction in mean pulmonary arterial pressure was observed. From an energetic point of view, left ventricular external work decreased by 10–15% whilst up to 40%vreduction in right ventricular external work was observed. The findings make central VA ECMO plus IABP the most appropriate combination for left and right ventricle unloading.

1. Introduction

The use of veno-arterial extracorporeal membrane oxygenation (VA ECMO) for the management of refractory cardiogenic shock (CS) has significantly increased in recent years [1]. Despite the established benefit of VA ECMO support, increased left ventricular (LV) afterload induced by retrograde flow remains a limiting factor which is particularly evident during peripheral VA ECMO insertion. Retrograde flow can significantly limit LV ejection leading to blood stasis and LV distension. Reduced or absent forward flow may also develop due to a mismatch between LV afterload, preload, and contractility. There is increasing evidence that LV unloading during VA ECMO support is beneficial [2]. The concomitant use of the intra-aortic balloon pump (IABP) is an established strategy for this purpose in view of its wide availability, ease of insertion and maintenance in the cardiac intensive care unit. Patients managed with the combined use of VA ECMO and IABP demonstrated significant lower in-hospital and 30-day mortality compared to those managed with VA ECMO alone without an increase in complications [3,4,5]. This matter has not been free of controversy. Despite increasing evidence confirming the beneficial effect of LV unloading on VA ECMO, there have been reports questioning its translation into better outcomes [6,7,8,9,10]. Nevertheless, the evidence supporting the combined use of VA ECMO and IABP in postcardiotomy failure and cardiogenic shock remains quite overwhelming [11,12,13,14,15,16]. VA ECMO support can be achieved either peripherally or centrally according to the needs and the context with some evidence supporting both approaches [17,18,19] although the combined use of peripheral VA ECMO and IABP has been questioned [20,21]. The effect of IABP on LV afterload and organ perfusion is complex and changes according to the degree of left ventricular systolic dysfunction. The crux of the balloon lies with the retrograde flow of peripheral VA ECMO. In the presence of severe left ventricular systolic dysfunction, the afterload may paradoxically increase during systole due to balloon deflation or “de-clamping” effect of the descending thoracic aorta. Balloon occlusion of the aorta in diastole may reduce VA ECMO-driven blood flow to the aortic root and arch attenuating myocardial and cerebral blood flow [22]. When the degree of LV systolic dysfunction is less, lower VA ECMO support is required and the impact of retrograde flow affecting the intended effect of IABP is less. The resultant pseudo-pulsatile flow induced by IABP would improve regional microcirculation [23,24]. The addition of IABP to central VA ECMO leads to the reduction in intracavitary cardiac pressure and work with potential for myocardial recovery in a pig model [25]. A mock circulation loop study of IABP and concomitant ECMO support during different degree of LV failure suggests a strong relationship between IABP efficacy and ventricular contractility inviting to careful selection when considering concomitant VA ECMO and IABP support [26]. Another experimental setting in a pig model has found higher coronary blood flow in central VA ECMO compared to peripheral VA ECMO regardless of flow conditions in the ascending aorta although the addition of IABP did not result in improved coronary blood flow but showed partial negative effect on the coronary arterial endothelial function [27]. Computational studies have focused on wall shear stress and modulation of pulsatility induced by IABP [28,29,30]. An in vitro study based on a silicon phantom model of the circulation has shown increased coronary blood flow on VA ECMO support with further improvement following IABP insertion particularly with reduced heart rate [31]. Given these considerations, we developed a simulation setting to study left ventricular unloading with IABP during peripheral and central VA ECMO. The aim was to quantitatively evaluate potential differences between the two VA ECMO configurations and ascertain the true beneficial effects compared to VA ECMO alone.

2. Materials and Methods

In this study, we assembled CARDIOSIM© [32,33] software platform (Ver. 7.3.2, developed at the Cardiovascular Numerical/Hybrid Modelling Lab—Rome Section of the Institute of Clinical Physiology of the Italian National Research Council) as shown in Figure 1. The numerical model reproducing the behaviour of both ventricles, atria, and septum has been previously described [34,35]. The numerical models of ascending and descending aorta with aortic arch, descending thoracic aorta (with thoracic resistance RTHOR), upper limbs and head, superior and inferior vena cava, renal and hepatic, splanchnic, abdominal and lower limbs circulation have also been described in detail [36].
The coronary circulation was modelled using resistance and compliance (RC) elements [37]. The network between the right ventricle and the left atria was reproduced using resistance, inertance and compliance (RLC) elements [35,38].
The numerical model reproducing central and peripheral VA ECMO configurations (Figure 1 and Figure 2) have been previously described [36]. Central VA ECMO draws blood from the right atrium (RA) and ejects it into the ascending aorta. Peripheral VA ECMO draws blood from the femoral vein (FV) and ejects it into the femoral artery (FA). For the purposes of the simulations, the two circuits have been configured as shown in Figure 2.
The IABP model, inserted in the arterial tree, is considered a flow source QIABP(t) as follows: during diastole the balloon inflates generating positive flow whilst during systole the balloon deflates leading to negative flow. The flow source QIABP(t) may be replaced by a pneumatic pressure source P(t), representing the compressed gas reservoir, and by resistance (R) representing the total gas delivery resistance of the system (Figure 1). The pneumatic source P(t) has been modelled describing the ejection and the filling phase separately as the air outflow from a high-pressure tank, connected to the pressure source, and the air outflow from a lower-pressure tank connected to the vacuum source [39].
In the first step of the study, a cardiogenic shock (CS) patient was reproduced in accordance with guidelines using the network configuration shown in Figure 1. The software simulator parameters were adjusted to obtain a systolic blood pressure < 90 mmHg, a systemic vascular resistance index (SVRi) < 1800 (dynes/sec/m2/cm−5), pulmonary capillary wedge pressure (PCWP) > 15 mmHg, and a cardiac index (CI) < 2.2 L/min/m2 [40,41,42]. In the second step, VA ECMO support was activated as central and peripheral configuration. In both conditions, the simulations were performed setting the pump rotational speed to 3000, 3500, and 4000 rpm, respectively. Finally, VA ECMO connected both centrally and peripherally with the same pump rotational speed was switched on in conjunction with IABP. Intra-aortic balloon counterpulsation was set with a drive pressure of 260 mmHg and vacuum pressure of −10 mmHg.
We investigated how the following haemodynamic variables were affected by central and peripheral VA ECMO, both with and without IABP support:
  • Minimum, maximum and mean values of left atrial pressure (LAP); aortic pressure (AoP) and pulmonary arterial pressure (PAP).
  • Pulmonary capillary wedge pressure (PCWP), which is an indirect estimate of left atrial pressure and therefore left ventricular filling pressure. This gives information about the severity of left ventricular failure, pulmonary hypertension and blood volume status.
  • Total flow (native plus assistance flow).
  • Coronary blood flow (CBF), which is the ratio between coronary perfusion pressure and coronary vascular resistance. Coronary perfusion pressure is defined as the difference between aortic diastolic pressure and left ventricular end-diastolic pressure.
  • Cardiac index (CI), which is the ratio between cardiac output and body surface area.
  • Left ventricular end systolic (diastolic) volume LVESV (LVEDV).
  • Right ventricular end systolic (diastolic) volume RVESV (RVEDV).
  • The systemic vascular resistance index (SVRi), which is the ratio between systemic vascular resistance and body surface area. Systemic vascular resistance is the ratio between pressure difference (mean arterial pressure minus central venous pressure) and cardiac output.
In addition, the following energetic variables were investigated:
  • ✓ Left (right) atrial pressure-volume loop area LA-PVLA (RA-PVLA);
  • ✓ Left (right) ventricular external work LVEW (RVEW);
  • ✓ Left (right) ventricular pressure-volume area LVPVA (RVPVA).
The pressure-volume area (PVA) is the total mechanical energy generated by ventricular contraction. More specifically, it is the sum of the external work (EW), given by the PV loop, and the elastic potential energy (PE). The same applies to atrial contraction. Data analysis included the assessment of the percentage variations in the assistance obtained under central and peripheral VA ECMO with or without IABP support, estimated in comparison to pathological conditions.

3. Results

Figure 3 shows the left and right ventricular pressure-volume loops (top panel) and the left atrial pressure-volume loop (bottom panel) of pathological conditions (dashed blue loops) and assisted conditions with central (red loops) and peripheral (black loops) VA ECMO support when the pump rotational speed was set to 3000 rpm. The figure’s bar graph gives the percentage changes in LVESV, LVEDV, RVESV, RVEDV, and left atrial end systolic (diastolic) volume LAESV (LAEDV) compared to pathological conditions during the two methods of assistance. When the pump rotational speed was set to 3000 rpm, peripheral VA ECMO increased LVESV, LVEDV, RVESV, RVEDV LAESV, and LAEDV by more than 14%, whereas central VA ECMO increased LVESV (≅14%), LVEDV (≅6%) and LAESV (≅10%), but decreased RVESV and LAEDV by 4% and RVEDV by 8%.
Figure 4 reports the effects on the left and right ventricular pressure-volume loops as well as the left atrial pressure-volume loop induced by the simultaneous activation of VA ECMO and IABP. The pathological left (right) ventricular pressure-volume loop (dashed blue line), the assisted central VA ECMO with IABP left (right) ventricular pressure-volume loop (red line) and the assisted peripheral VA ECMO with IABP left (right) ventricular pressure-volume loop (black line) are all presented in the top left (right) panel. The left atrial pressure-volume loop of pathological conditions (dashed blue loop), the assisted conditions with central (red loop) and peripheral (black loop) VA ECMO both in conjunction with IABP support are available in the left bottom panel. When IABP was applied in conjunction with central VA ECMO support, LVESV, LVEDV, RVESV, RVEDV, LAESV, and LAEDV decreased, whereas peripheral VA ECMO and IABP support would decrease LVESV and LAESV but increase LVEDV, RVESV, RVEDV, and LAEDV compared to pathological conditions.
Concomitant central VA ECMO (with pump rotational speed set to 3000 rpm) and IABP support reduced both left ventricular and left atrial ESVs and EDVs.
When central VA ECMO was applied with pump rotational speeds of 3000 and 3500 rpm, with or without IABP assistance, SVRi increased from 43.4% to 83.83% (top graph in Figure 5), while no effect was seen with peripheral VA ECMO support. The same bar graph shows a decrease in cardiac index with central VA ECMO support (for every rotational speed), even after concomitant IABP activation. When peripheral VA ECMO was active, CI increased up to 44.86% (for 3500 rpm and activated IABP). Systemic elastance (Ea) and the ratio between systemic elastance and systemic arterial elastance (Eas) decreased when peripheral VA ECMO and IABP were both activated; a negligible effect was observed in the absence of IABP support (bottom graph in Figure 5). Pulmonary elastance was negligible following both types of assistance. When central VA ECMO was used, percentage changes in Ea/Ees ranging from 27.31% to 52.42% (for a 3000 rpm) and percentage changes in systemic Ea ranging from 27.04% to 40.88% (for a 3500 rpm) were observed when IABP support was turned off. The percentage changes in terms of total blood flow increased when the rotating pump speed of VA ECMO increased in both peripheral and central configurations (top graph in Figure 6). IABP support produced a 15% increase in Ea and Ea/Ees during central VA ECMO and a 20% decrease during peripheral VA ECMO.
The percentage changes in CBF when peripheral (central) VA ECMO was applied ranged between 65.15% and 68.66% (55.82% and 61.30%) when the pump rotational speed was set to 4000 rpm either without or with IABP, respectively (Figure 6). For central (peripheral) VA ECMO, CBF increased from 24.32% (13.78%) to 44.69% (17.21%) when the pump rotational speed was set to 3000 rpm, again without and with IABP.
Figure 7 shows the percentage changes in cerebral blood flow under assisted conditions with central and peripheral VA ECMO, as well as with and without IABP support, related to pathological conditions. The cerebral perfusion in both VA ECMO configurations increased as the pump rotational speed increased. IABP support did not seem to affect cerebral perfusion significantly.
Figure 8 shows the percentage changes in the minimum values (panel A) of LAP, LVP, and AoP when central and peripheral VA ECMO was used with pump rotational speed set to 3000, 3500, and 4000 rpm with or without IABP. The minimum AoP value increased up to 64.62% (4000 rpm) when VA ECMO was connected centrally and the pump rotational speed was set to 3000, 3500, and 4000 rpm; IABP activation significantly reduced the minimum AoP values (panel A). Similar trends were observed when VA ECMO was connected peripherally either with or without IABP.
Even with active IABP, the minimum LAP value fell when VA ECMO was connected centrally, but the minimum LAP and LVP values increased for peripheral VA ECMO.
Panel B (Figure 8) shows that when central VA ECMO pump rotational speed increased, the maximal AoP values also increased. This effect was more evident when IABP support was switched on. Peripheral VA ECMO raised LAP, LVP, and AoP maximum values above 73.5% (4000 rpm). Nevertheless, this effect decreased when IABP and peripheral VA ECMO were activated simultaneously. The maximum LAP and LVP values were comparable to those in non-assisted conditions when IABP and central VA ECMO were activated simultaneously (for all pump rotational speeds) and when peripheral VA ECMO (3000 rpm) and IABP worked concomitantly.
Figure 9 shows the percentage changes in mean AoP value calculated in relation to pathological conditions for both central and peripheral VA ECMO assistance (with pump rotational speed set to 3000, 3500, and 4000 rpm), with and without IABP support.
The mean aortic pressure values increased in each condition when IABP assistance was present; the greatest increase occurred with peripheral VA ECMO when the pump speed was set to 4000 rpm.
The effect caused by central (top panel) and peripheral (bottom panel) VA ECMO support and IABP assistance on mean wedge and mean pulmonary arterial pressures and on minimum and maximum pulmonary arterial pressure is shown in Figure 10.
When VA ECMO was configured in central mode with high pump rotational speeds, the wedge drastically reduced; under these circumstances, IABP support appeared to have little effect on the wedge (top panel). Peripheral VA ECMO increased the wedge by approximately 50% (compared to pathological conditions) at a pump speed of 4000 rpm (bottom panel). The minimum, maximum, and mean pulmonary arterial pressures decreased up to 30% for central VA ECMO (with a pump rotational speed of 4000 rpm); when IABP and VA ECMO were activated simultaneously, the reduction was less (top panel). Peripheral VA ECMO with high pump rotational speed (4000 rpm) increased the minimum, mean, and maximum values of pulmonary arterial pressure up to 80%. These effects did not appear to be influenced by the presence of IABP. Figure 11 shows that central VA ECMO support reduced the right atrial pressure-volume loop area from 15% to 50.7% without IABP assistance (top panel). IABP activation with central VA ECMO led to the reduction in RA-PVLA by a maximum value of 38.3% (when pump rotational speed was set to 4000 rpm).
When simulating double assistance, the percentage decrease in comparison to the pathological state of LA-PVLA was more noticeable. Peripheral VA ECMO increased both RA-PVLA and LA-PVLA when the pump rotational speed increased, as seen in the bottom panel (Figure 11). Our simulations indicate that a minor increase in LA-PVLA was induced by IABP support.
The results of the simulation for LVEDV, LVESV, RVEDV, and RVESV are shown in Figure 12. The top (bottom) panel shows the percentage changes under assisted conditions with central (peripheral) VA ECMO driven at 3000, 3500, and 4000 rpm, as well as with and without IABP support, related to pathological conditions. When IABP assistance was not active, central VA ECMO (top panel) increased LVESV (LVEDV) from 12.7% to 26.7% (from 6.1% to 10.7%) whilst decreased RVESV (RVEDV) from 3.9% to 14.1% (from 7.5 to 22.7%). IABP activation caused a percentage drop in LVEDV, RVESV, and RVEDV for each pump rotational speed, whereas LVESV increased in percentage as the pump speed increased.
Peripheral VA ECMO (bottom panel) caused a similar percentage increase in LVESV, LVEDV, RVESV, and RVEDV at each pump speed (e.g., around 14% at 3000 rpm). IABP activation produced different percentage change increases in the four parameters (e.g., 16.7% in LVESV, 24.0% in LVEDV, 32.3% in RVESV, and 37.8% in RVEDV at 3500 rpm, respectively).
Figure 13 shows the effects induced on the energetic variables by central (peripheral) VA ECMO with and without IABP activation. IABP support combined with central VA ECMO reduced LVEW, RVEW, and RPVVA (top panel) at all pump rotational speeds. When the pump rotational speed was set to 4000 rpm, the reduction in percentage changes in LVPVA was negligible, whereas RVEW, RVPA, and LVEW decreased by 39.5%, 37.6%, and 15.6%, respectively. Simulations performed with only central VA ECMO assistance increased LVPVA up to 39.2% (pump rotational speed of 4000 rpm), and reduced RVEW and RVPVA up to 48.8% and 44.8%, respectively (pump rotational speed of 4000 rpm). LVEW, LVPVA, RVEW, and RVPVA significantly increased in simulations with only peripheral VA ECMO support (bottom panel); this effect became more evident as the pump rotational speed increased [43]. While RVEW and RVPVA seemed to be unaffected by the presence of IABP, concomitant IABP support decreased LVEW and LVPVA for all values of pump rotational speed.

4. Discussion

The use of VA ECMO support in critically ill patients remains a widely recognised approach despite current controversy about its beneficial effects and outcomes. The use of IABP to address LV unloading has been an appropriate and recognised course of action. Nevertheless, there remains additional controversy related to its use with either peripheral or central VA ECMO support. This has given us the motivation to review current views and shed some lights on the subject by answering the following question: Is there a real difference between central and peripheral VA ECMO when associated with IABP? We sought to address this question in the context of a simulation setting based on lumped parameter modelling and pressure-volume analysis. Initial simulations with pump rotational speed at 3000 rpm revealed that central VA ECMO support caused less LV and RV distension compared to peripheral VA ECMO with reduction in RVESV, RVEDV, and LAEDV as shown in Figure 3. When combined IABP and VA ECMO support was activated, central VA ECMO clearly unloaded both ventricles compared to peripheral VA ECMO as shown in Figure 4 and Figure 12. Central VA ECMO at 3000 and 3500 rpm would increase SVRi and decrease CI whilst peripheral VA ECMO would increase CI without any effect on SVRi. The concomitant use of IABP for both configurations did not make any significant difference. Central VA ECMO at 3000 and 3500 rpm increased systemic Ea up to 40% and Ea/Ees ratio up to 52%. The combined use of central VA ECMO and IABP would increase both parameters by only 15% (Figure 5). Peripheral VA ECMO at 3000 and 3500 rpm had a negligible effect on systemic Ea and Ea/Ees ratio whilst the combined use with IABP decreased both parameters by 20%. The effect of both VA ECMO configurations with or without IABP was negligible on pulmonary Ea (Figure 5). The Ea/Ees ratio reflects effective ventricular–arterial coupling, which can be defined as the provision of optimal cardiovascular flow reserve without compromising arterial blood pressure. Central VA ECMO alone seems to induce a more pronounced deleterious effect compared to peripheral VA ECMO. Arguably, the combined use of central VA ECMO and IABP seems to largely mitigate this negative effect. Central VA ECMO increased coronary blood flow (CBF) up to 55.82% with pump rotational speed at 4000 rpm. IABP addition would increase CBF up to 61.3% (Figure 6). Peripheral VA ECMO increased CBF up to 65.15% with the same rotational pump speed. The combined use with IABP would increase CBF up to 68.66% (Figure 6). The effect on cerebral blood flow appeared more pronounced under central VA ECMO support with low rotational speed (Figure 7). The use of peripheral VA ECMO alone or combined with IABP would increase left atrial pressure (LAP), left ventricular pressure (LVP) and aortic pressure (AoP). In contrast, central VA ECMO alone would not increase these parameters as much. The combined use of IABP would either reduce these parameters or increase them to a lesser extent (Figure 8 and Figure 9). Central VA ECMO alone would reduce pulmonary capillary wedge pressure (PCWP) and mean pulmonary artery pressure (PAP). The concomitant use of IABP would maintain this trend (Figure 10). Peripheral VA ECMO alone or combined with IABP would generate the opposite effect on PCWP and mean PAP (Figure 10).
The increased RV afterload following peripheral VA ECMO and IABP may have implications in the presence of RV dysfunction. VP ECMO with the use of ProtekDuo may have a role to play in this context given the complete bypass of the right ventricle [44,45,46].
The aim of the simulations remains to ascertain the effect of IABP when used with peripheral or central VA ECMO. The context in which they are used will have to be considered. If peripheral VA ECMO is initially used as a rescue procedure but access proves difficult, a central approach would have to be considered. Central VA ECMO for postcardiotomy failure following cardiac surgery would be the obvious choice. The approach is related to the context and obviously risks and complications have to be balanced. Taking into account their limitations, the outcome of our simulations clearly shows the superiority of central VA ECMO plus IABP compared to peripheral VA ECMO combined with IABP. Nevertheless, there would be situations requiring peripheral VA ECMO insertion which may warrant a different LV unloading approach such as the use of Impella 2.5 and 5.5 devices or atrial septostomy although risks and procedural complications would still need to be considered. Expertise in atrial septostomy and availability of Impella device may be significantly limited compared to IABP. Nevertheless, the use of the Impella device has played a major role due to its effectiveness and higher reduction in LVESV, LVEDV, left ventricular external work and left atrial pressure-volume loop area compared to IABP support [39].
From an energetic point of view, central VA ECMO alone or combined with IABP has a much more favourable profile compared to peripheral VA ECMO alone or combined with IABP (Figure 11 and Figure 13).
Although peripheral VA ECMO has been used more frequently even in postoperative cardiac patients [3,4,11,12], myocardial and cerebral blood flow remain negatively affected [21,22]. In contrast, the outcome of our simulations has revealed a favourable effect on coronary blood flow for both peripheral and central VA ECMO at 4000 rpm pump rotational speed, either alone or combined with IABP. A pump rotational speed at 3000 rpm would lead to a more pronounced effect on CBF under central VA ECMO alone or combined with IABP compared to peripheral VA ECMO alone or combined with IABP. A similar trend was observed for the cerebral blood flow under central VA ECMO support at 3000 rpm pump rotational speed, either alone or combined with IABP. Nevertheless, the overall haemodynamic and energetic analysis of our simulations support the use of central VA ECMO and IABP in line with previous experimental work [24,25,26,27,47]. We would not preclude the use of peripheral VA ECMO combined with IABP although central VA ECMO would be advisable in postcardiotomy failure patients or whenever feasible. The cannulation site remains a matter of preference although the femoral artery remains anatomically more favourable compared to the subclavian artery.
Although it can be argued that a patient-specific approach may give additional information, this is not the case in this context. At present, our aim remains to ascertain whether the use of IABP for LV unloading is appropriate when combined with peripheral or central VA ECMO. The outcome of our simulations is accurate enough to answer the original question related to which VA ECMO configuration is more appropriate when combined with IABP. We are considering the development of a patient-specific approach in the future. Evidence-based practice (EBP) dogmatically states that everything has to follow the outcome of rigorously designed randomised controlled clinical trials (RCTs). Nevertheless, there will always be grey areas without clear answers or treatments that have shown their beneficial effect despite the absence of the required evidence. EBP is meant to provide a secure ground for clinical decision-making which may not be realistic. EBP seeks to address uncertainty, but it cannot eliminate it. The results of trials are applicable, in general, but may not be completely suitable for a specific group of patients or even for the single patient. A limitation of the interpretation of RCTs is the apparent willingness to disregard the importance of the context and minimise the complexity of the individual patients involved [48]. As clinicians, we would like to have a solid ground for our decision-making but as a matter of fact this ground does not exist. A more personalised approach to treatment may add a different dimension with some potential advantages as long as it is considered in the appropriate context and not as a “magic bullet”. The purpose of a simulation approach is to reduce the need for clinical trials or optimise treatment and predict its outcome, which cannot be addressed through traditional prospective clinical trials [49]. At the same time, modelling is subject to limitations related to the assumptions made which have to be acknowledged following the interpretation of results. Our modelling approach consists of a combined use of modified time-varying elastance, lumped (0-order) parameter representation of the vascular system and pressure-volume analysis. This has led to the development of CARDIOSIM© with subsequent validation of its performance [50,51,52]. Additional complexity requires additional assumptions with their own limitations [53]. Therefore, a compromise between complexity, effectiveness and applicability of the model has to be made. The strength of lumped parameter modelling is its suitability for clinical applications given its ease of understanding and real time results as demonstrated by previous work of our group and others.

5. Conclusions

VA ECMO can provide effective circulatory support in critically ill patients due to cardiogenic shock. IABP is appropriate to unload the left ventricle and counteract the detrimental effect of full VA ECMO support. A combined use of central VA ECMO and IABP may be the preferred approach when feasible. The choice of VA ECMO configuration depends on the context for which risks and complications need to be balanced against the intended benefit. Nevertheless, the combined use of IABP and central VA ECMO gives a more beneficial effect in terms of haemodynamic and energetic parameters. Therefore, its use should be considered whenever possible. If peripheral VA ECMO is considered, IABP use has a potential detrimental effect requiring an alternative LV unloading strategy.

Author Contributions

Conceptualization, B.D.L. and C.D.L.; methodology, B.D.L., C.D.L. and R.B.; software, B.D.L. and C.D.L.; formal analysis, M.C., M.O.M. and R.B.; investigation, B.D.L., M.O.M. and M.C.; resources, C.D.L. and R.B.; data curation, B.D.L., M.C., R.B. and C.D.L.; writing—original draft preparation, B.D.L., M.O.M. and M.C.; writing—review and editing M.C., M.O.M. and R.B.; supervision, C.D.L., B.D.L., M.O.M. and M.C.; Funding acquisition, C.D.L. All authors have read and agreed to the published version of the manuscript.

Funding

REMOTE project (n. F/310117/01/X56) financed by the Italian Ministry of Economic Development.

Institutional Review Board Statement

Not applicable.

Informed Consent Statement

Not applicable.

Data Availability Statement

The research data is available at the Cardiovascular Numerical/Hybrid Modelling Lab—Rome Section of the Institute of Clinical Physiology of the Italian National Research Council.

Conflicts of Interest

The authors declare no conflicts of interest.

References

  1. Meani, P.; Gelsomino, S.; Natour, E.; Johnson, D.M.; Rocca, H.-P.B.L.; Pappalardo, F.; Bidar, E.; Makhoul, M.; Raffa, G.; Heuts, S. Modalities and Effects of Left Ventricle Unloading on Extracorporeal Life Support: A Review of the Current Literature. Eur. J. Heart Fail. 2017, 19, 84–91. [Google Scholar] [CrossRef] [PubMed]
  2. Lorusso, R.; Meani, P.; Raffa, G.M.; Kowalewski, M. Extracorporeal Membrane Oxygenation and Left Ventricular Unloading: What Is the Evidence? JTCVS Tech. 2022, 13, 101. [Google Scholar] [CrossRef]
  3. Nishi, T.; Ishii, M.; Tsujita, K.; Okamoto, H.; Koto, S.; Nakai, M.; Sumita, Y.; Iwanaga, Y.; Kobayashi, Y.; Hirata, K. Outcomes of VA-ECMO plus IABP versus VA-ECMO Alone for Treatment of Acute Myocardial Infarction Complicated by Cardiogenic Shock: Insight from the JROADDPC Registry. J. Am. Coll. Cardiol. 2022, 79, 954. [Google Scholar] [CrossRef]
  4. Li, Y.; Yan, S.; Gao, S.; Liu, M.; Lou, S.; Liu, G.; Ji, B.; Gao, B. Effect of an Intra-Aortic Balloon Pump with Venoarterial Extracorporeal Membrane Oxygenation on Mortality of Patients with Cardiogenic Shock: A Systematic Review and Meta-Analysis. Eur. J. Cardiothorac. Surg. 2019, 55, 395–404. [Google Scholar] [CrossRef]
  5. Vallabhajosyula, S.; O’Horo, J.C.; Antharam, P.; Ananthaneni, S.; Vallabhajosyula, S.; Stulak, J.M.; Eleid, M.F.; Dunlay, S.M.; Gersh, B.J.; Rihal, C.S. Concomitant Intra-Aortic Balloon Pump Use in Cardiogenic Shock Requiring Veno-Arterial Extracorporeal Membrane Oxygenation: A Systematic Review and Meta-Analysis. Circ. Cardiovasc. Interv. 2018, 11, e006930. [Google Scholar] [CrossRef]
  6. Björnsdóttir, B.; Biancari, F.; Dalén, M.; Dell’Aquila, A.M.; Jónsson, K.; Fiore, A.; Mariscalco, G.; El-Dean, Z.; Gatti, G.; Zipfel, S. Postcardiotomy Venoarterial Extracorporeal Membrane Oxygenation with and without Intra-Aortic Balloon Pump. J. Cardiothorac. Vasc. Anesth. 2022, 36, 2876–2883. [Google Scholar] [CrossRef] [PubMed]
  7. Hasde, A.I.; Sarıcaoğlu, M.C.; Dikmen Yaman, N.; Baran, Ç.; Özçınar, E.; Çakıcı, M.; İnan, M.B.; Akar, A.R. Comparison of Left Ventricular Unloading Strategies on Venoarterial Extracorporeal Life Support. Interact. Cardiovasc. Thorac. Surg. 2021, 32, 467–475. [Google Scholar] [CrossRef] [PubMed]
  8. Lin, L.-Y.; Liao, C.-W.; Wang, C.-H.; Chi, N.-H.; Yu, H.-Y.; Chou, N.-K.; Hwang, J.-J.; Lin, J.-L.; Chiang, F.-T.; Chen, Y.-S. Effects of Additional Intra-Aortic Balloon Counter-Pulsation Therapy to Cardiogenic Shock Patients Supported by Extra-Corporeal Membranous Oxygenation. Sci. Rep. 2016, 6, 23838. [Google Scholar] [CrossRef]
  9. Wang, D.; Chao, V.; Yap, K.H.; Tan, T.E. Does Concurrent Use of Intra-Aortic Balloon Pumps Improve Survival in Patients with Cardiogenic Shock Requiring Venoarterial Extracorporeal Membrane Oxygenation? Interact. Cardiovasc. Thorac. Surg. 2020, 30, 312–315. [Google Scholar] [CrossRef]
  10. Tepper, S.; Garcia, M.B.; Fischer, I.; Ahmed, A.; Khan, A.; Balsara, K.R.; Masood, M.F.; Itoh, A. Clinical Outcomes and Reduced Pulmonary Artery Pressure With Intra-Aortic Balloon Pump During Central Extracorporeal Life Support. ASAIO J. 2019, 65, 173–179. [Google Scholar] [CrossRef]
  11. Baran, C.; Ozcinar, E.; Kayan, A.; Dikmen, N.; Baran, C.S.; Inan, M.B. Comparison of ECMO, IABP and ECMO+ IABP in the Postoperative Period in Patients with Postcardiotomy Shock. J. Cardiovasc. Dev. Dis. 2024, 11, 283. [Google Scholar] [CrossRef] [PubMed]
  12. Chen, K.; Hou, J.; Tang, H.; Hu, S. Concurrent Initiation of Intra-Aortic Balloon Pumping with Extracorporeal Membrane Oxygenation Reduced in-Hospital Mortality in Postcardiotomy Cardiogenic Shock. Ann. Intensive Care 2019, 9, 1–7. [Google Scholar] [CrossRef] [PubMed]
  13. Kida, H.; Sotomi, Y.; Hikoso, S.; Nakatani, D.; Mizuno, H.; Suna, S.; Okada, K.; Kitamura, T.; Komukai, S.; Dohi, T. Prognostic Significance of Intra-Aortic Balloon Pumping Support in Patients with Acute Myocardial Infarction and Veno-Arterial Extracorporeal Membrane Oxygenation Therapy. J. Cardiol. 2022, 79, 179–185. [Google Scholar] [CrossRef]
  14. Loforte, A.; Murana, G.; Cefarelli, M.; Jafrancesco, G.; Sabatino, M.; Martin Suarez, S.; Pilato, E.; Pacini, D.; Grigioni, F.; Bartolomeo, R.D. Role of Intra-aortic Balloon Pump and Extracorporeal Membrane Oxygenation in Early Graft Failure after Cardiac Transplantation. Artif. Organs 2016, 40, E136–E145. [Google Scholar] [CrossRef] [PubMed]
  15. Nuding, S.; Werdan, K. IABP plus ECMO—Is One and One More than Two? J. Thorac. Dis. 2017, 9, 961. [Google Scholar] [CrossRef] [PubMed]
  16. Zeng, P.; Yang, C.; Chen, J.; Fan, Z.; Cai, W.; Huang, Y.; Xiang, Z.; Yang, J.; Zhang, J.; Yang, J. Comparison of the Efficacy of ECMO with or without IABP in Patients with Cardiogenic Shock: A Meta-Analysis. Front. Cardiovasc. Med. 2022, 9, 917610. [Google Scholar] [CrossRef]
  17. Bréchot, N.; Demondion, P.; Santi, F.; Lebreton, G.; Pham, T.; Dalakidis, A.; Gambotti, L.; Luyt, C.-E.; Schmidt, M.; Hekimian, G. Intra-Aortic Balloon Pump Protects against Hydrostatic Pulmonary Oedema during Peripheral Venoarterial-Extracorporeal Membrane Oxygenation. Eur. Heart J. Acute Cardiovasc. Care 2018, 7, 62–69. [Google Scholar] [CrossRef]
  18. Raffa, G.M.; Kowalewski, M.; Brodie, D.; Ogino, M.; Whitman, G.; Meani, P.; Pilato, M.; Arcadipane, A.; Delnoij, T.; Natour, E. Meta-Analysis of Peripheral or Central Extracorporeal Membrane Oxygenation in Postcardiotomy and Non-Postcardiotomy Shock. Ann. Thorac. Surg. 2019, 107, 311–321. [Google Scholar] [CrossRef]
  19. Xu, B.; Li, C.; Cai, T.; Cui, Y.; Du, Z.; Fan, Q.; Guo, D.; Jiang, C.; Xing, Z.; Xin, M. Intra-aortic Balloon Pump Impacts the Regional Haemodynamics of Patients with Cardiogenic Shock Treated with Femoro-femoral Veno-arterial Extracorporeal Membrane Oxygenation. ESC Heart Fail. 2022, 9, 2610–2617. [Google Scholar] [CrossRef]
  20. Tay, C.K.; Yoo, K.H.; Cho, Y.H. Intraaortic Balloon Pulsation in Peripheral Venoarterial Extracorporeal Membrane Oxygenation: More Is Not Always Better. Crit. Care Med. 2016, 44, e1251. [Google Scholar] [CrossRef]
  21. Yang, F.; Jia, Z.; Xing, J.; Wang, Z.; Liu, Y.; Hao, X.; Jiang, C.; Wang, H.; Jia, M.; Hou, X. Effects of Intra-Aortic Balloon Pump on Cerebral Blood Flow during Peripheral Venoarterial Extracorporeal Membrane Oxygenation Support. J. Transl. Med. 2014, 12, 106. [Google Scholar] [CrossRef] [PubMed]
  22. Bělohlávek, J.; Mlček, M.; Huptych, M.; Svoboda, T.; Havránek, Š.; Ošt’ádal, P.; Bouček, T.; Kovárník, T.; Mlejnský, F.; Mrázek, V. Coronary versus Carotid Blood Flow and Coronary Perfusion Pressure in a Pig Model of Prolonged Cardiac Arrest Treated by Different Modes of Venoarterial ECMO and Intraaortic Balloon Counterpulsation. Crit. Care 2012, 16, R50. [Google Scholar] [CrossRef]
  23. Jung, C.; Lauten, A.; Roediger, C.; Fritzenwanger, M.; Schumm, J.; Figulla, H.R.; Ferrari, M. In Vivo Evaluation of Tissue Microflow under Combined Therapy with Extracorporeal Life Support and Intra-Aortic Balloon Counterpulsation. Anaesth. Intensive Care 2009, 37, 833–835. [Google Scholar] [CrossRef] [PubMed]
  24. Petroni, T.; Harrois, A.; Amour, J.; Lebreton, G.; Brechot, N.; Tanaka, S.; Luyt, C.-E.; Trouillet, J.-L.; Chastre, J.; Leprince, P. Intra-Aortic Balloon Pump Effects on Macrocirculation and Microcirculation in Cardiogenic Shock Patients Supported by Venoarterial Extracorporeal Membrane Oxygenation. Crit. Care Med. 2014, 42, 2075–2082. [Google Scholar] [CrossRef] [PubMed]
  25. Djordjevic, I.; Liakopoulos, O.; Elskamp, M.; Maier-Trauth, J.; Gerfer, S.; Mühlbauer, T.; Slottosch, I.; Kuhn, E.; Sabashnikov, A.; Rademann, P. Concomitant Intra-Aortic Balloon Pumping Significantly Reduces Left Ventricular Pressure during Central Veno-Arterial Extracorporeal Membrane Oxygenation—Results from a Large Animal Model. Life 2022, 12, 1859. [Google Scholar] [CrossRef]
  26. Farag, J.; Stephens, A.F.; Chong, W.J.; Gregory, S.D.; Marasco, S.F. Intra-Aortic Balloon Pump Use with Extra Corporeal Membrane Oxygenation—A Mock Circulation Loop Study. ASAIO J. 2022, 68, 669–675. [Google Scholar] [CrossRef]
  27. Gerfer, S.; Djordjevic, I.; Maier, J.; Movahed, A.; Elskamp, M.; Kuhn, E.; Liakopoulos, O.; Wahlers, T.; Deppe, A.C. Endothelial and Hemodynamic Function in a Large Animal Model in Relation to Different Extracorporeal Membrane Oxygenation Cannulation Strategies and Intra-Aortic Balloon Pumping. J. Clin. Med. 2023, 12, 4038. [Google Scholar] [CrossRef]
  28. Gu, K.; Zhang, Y.; Gao, B.; Chang, Y.; Zeng, Y. Hemodynamic Differences between Central ECMO and Peripheral ECMO: A Primary CFD Study. Med. Sci. Monit. Int. Med. J. Exp. Clin. Res. 2016, 22, 717. [Google Scholar] [CrossRef]
  29. Gu, K.; Zhang, Z.; Gao, B.; Chang, Y.; Wan, F. Hemodynamic Effects of Perfusion Level of Peripheral ECMO on Cardiovascular System. Biomed. Eng. Online 2018, 17, 59. [Google Scholar] [CrossRef]
  30. Gu, K.; Gao, S.; Zhang, Z.; Ji, B.; Chang, Y. Hemodynamic Effect of Pulsatile on Blood Flow Distribution with VA ECMO: A Numerical Study. Bioengineering 2022, 9, 487. [Google Scholar] [CrossRef]
  31. Reymond, P.; Bendjelid, K.; Giraud, R.; Richard, G.; Murith, N.; Cikirikcioglu, M.; Huber, C. To Balloon or Not to Balloon? The Effects of an Intra-Aortic Balloon-Pump on Coronary Artery Flow during Extracorporeal Circulation Simulating Normal and Low Cardiac Output Syndromes. J. Clin. Med. 2021, 10, 5333. [Google Scholar] [CrossRef] [PubMed]
  32. De Lazzari, B.; Badagliacca, R.; Filomena, D.; Papa, S.; Vizza, C.D.; Capoccia, M.; De Lazzari, C. CARDIOSIM©: The First Italian Software Platform for Simulation of the Cardiovascular System and Mechanical Circulatory and Ventilatory Support. Bioengineering 2022, 9, 383. [Google Scholar] [CrossRef]
  33. De Lazzari, C.; Staltieri, D. CARDIOSIM© Website. 2021. Available online: https://Cardiosim.Dsb.Cnr.It (accessed on 29 May 2022).
  34. De Lazzari, C. Interaction between the Septum and the Left (Right) Ventricular Free Wall in Order to Evaluate the Effects on Coronary Blood Flow: Numerical Simulation. Comput. Methods Biomech. Biomed. Engin. 2012, 15, 1359–1368. [Google Scholar] [CrossRef]
  35. Capoccia, M.; Marconi, S.; Singh, S.A.; Pisanelli, D.M.; De Lazzari, C. Simulation as a Preoperative Planning Approach in Advanced Heart Failure Patients. A Retrospective Clinical Analysis. Biomed. Eng. Online 2018, 17, 52. [Google Scholar] [CrossRef]
  36. De Lazzari, B.; Iacovoni, A.; Mottaghy, K.; Capoccia, M.; Badagliacca, R.; Vizza, C.D.; De Lazzari, C. ECMO Assistance during Mechanical Ventilation: Effects Induced on Energetic and Haemodynamic Variables. Comput. Methods Programs Biomed. 2021, 202, 106003, Erratum in Comput. Methods Programs Biomed. 2021, 212, 106478. [Google Scholar] [CrossRef]
  37. De Lazzari, C.; De Lazzari, C. A Pumping Heart Coupled to Lumped Description of the Cardiovascular Compartments (CARDIOSIM©). In Modelling Cardiovascular System and Mechanical Circulatory Support; CNR: Roma, Italy, 2007; pp. 65–67. [Google Scholar]
  38. Capoccia, M.; Marconi, S.; De Lazzari, C. Decision-Making in Advanced Heart Failure Patients Requiring LVAD Insertion: Can Preoperative Simulation Become the Way Forward? A Case Study. J. Biomed. Eng. Inform. 2018, 4, 8–20. [Google Scholar]
  39. De Lazzari, B.; Capoccia, M.; Badagliacca, R.; Bozkurt, S.; De Lazzari, C. IABP versus Impella Support in Cardiogenic Shock: “In Silico” Study. J. Cardiovasc. Dev. Dis. 2023, 10, 140. [Google Scholar] [CrossRef]
  40. Vahdatpour, C.; Collins, D.; Goldberg, S. Cardiogenic Shock. J. Am. Heart Assoc. 2019, 8, e011991. [Google Scholar] [CrossRef] [PubMed]
  41. Alkhunaizi, F.A.; Smith, N.; Brusca, S.B.; Furfaro, D. The Management of Cardiogenic Shock From Diagnosis to Devices. A Narrat. Review. CHEST Crit. Care 2024, 2, 100071. [Google Scholar] [CrossRef]
  42. Sinha, S.S.; Morrow, D.A.; Kapur, N.K.; Kataria, R.; Roswell, R.O. 2025 Concise Clinical Guidance: An ACC Expert Consensus Statement on the Evaluation and Management of Cardiogenic Shock: A Report of the American College of Cardiology Solution Set Oversight Committee. J. Am. Coll. Cardiol. 2025, 85, 1618–1641. [Google Scholar] [CrossRef]
  43. Pankaj, J. Acute Haemodynamic Effects of Venoarterial Extracorporeal Membrane Oxygenation on Left Ventricular Mechano-energetics: The Ramp and Clamp Study. Interv. Cardiol. Rev. 2021, 16 (Suppl. S2), 1–22. [Google Scholar] [CrossRef]
  44. Brewer, J.M.; Capoccia, M.; Maybauer, D.M.; Lorusso, R.; Swol, J.; Maybauer, M.O. The ProtekDuo dual-lumen cannula for temporary acute mechanical circulatory support in right heart failure: A systematic review. Perfusion 2023, 38 (Suppl. S1), 59–67. [Google Scholar] [CrossRef] [PubMed]
  45. Maybauer, M.O.; Capoccia, M.; Maybauer, D.M.; Lorusso, R.; Swol, J.; Brewer, J.M. The ProtekDuo in ECMO configuration for ARDS secondary to COVID-19: A systematic review. Int. J. Artif. Organs 2023, 46, 93–98. [Google Scholar] [CrossRef]
  46. Capoccia, M.; Brewer, J.M.; Rackauskas, M.; Becker, T.K.; Maybauer, D.M.; Stukov, Y.; Lorusso, R.; Maybauer, M.O. Outcome of Veno-Pulmonary Extracorporeal Life Support in Lung Transplantation Using ProtekDuo Cannula: A Systematic Review and Description of Configurations. J. Clin. Med. 2024, 13, 4111. [Google Scholar] [CrossRef]
  47. Sauren, L.D.; Reesink, K.D.; Selder, J.L.; Beghi, C.; Van Der Veen, F.H.; Maessen, J.G. The Acute Effect of Intra-aortic Balloon Counterpulsation during Extracorporeal Life Support: An Experimental Study. Artif. Organs 2007, 31, 31–38. [Google Scholar] [CrossRef] [PubMed]
  48. Baumann, S.L. The Limitations of Evidence-Based Practice. Nurs. Sci. Q. 2010, 23, 226–230. [Google Scholar] [CrossRef]
  49. Doshi, D.; Burkhoff, D. Cardiovascular Simulation of Heart Failure Pathophysiology and Therapeutics. J. Card. Fail. 2016, 22, 303–311. [Google Scholar] [CrossRef]
  50. Saltarocchi, S. Simulation in Advanced Heart Failure with a View to Selection and Optimisation of Device Therapy. Int. J. Eng. Sci. Res. Tech. Thesis 2018. [Google Scholar] [CrossRef]
  51. De Lazzari, C.; Neglia, D.; Ferrari, G.; Bernini, F.; Micalizzi, M.; L’Abbate, A.; Trivella, M.G. Computer Simulation of Coronary Flow Waveforms during Caval Occlusion. Methods Inf. Med. 2009, 48, 113–122. [Google Scholar]
  52. De Lazzari, C.; Darowski, M.; Wolski, P.; Ferrari, G.; Tosti, G.; Pisanelli, D.M. In Vivo and Simulation Study of Artificial Ventilation Effects on Energetic Variables in Cardiosurgical Patients. Methods Inf. Med. 2005, 44, 98–105. [Google Scholar]
  53. Hester, R.L.; Iliescu, R.; Summers, R.; Coleman, T.G. Systems biology and integrative physiological modelling. J. Physiol. 2011, 589, 1053–1060. [Google Scholar] [CrossRef] [PubMed]
Bioengineering 12 00540 g001
Figure 1. Electric analogue of the cardiovascular system with intra-aortic balloon pump (IABP), central and peripheral VA ECMO. The different sections of ascending and descending aorta with aortic arch, descending thoracic aorta (with thoracic resistance RTHOR), upper limbs and head, superior and inferior vena cava, renal and hepatic, splanchnic, abdominal and lower limbs circulation have been modelled with resistance, inertance and compliance (RLC) elements [36]. The coronary circulation was modelled with RC elements. The numerical model reproducing central and peripheral VA ECMO configurations have been previously described [36].
Figure 1. Electric analogue of the cardiovascular system with intra-aortic balloon pump (IABP), central and peripheral VA ECMO. The different sections of ascending and descending aorta with aortic arch, descending thoracic aorta (with thoracic resistance RTHOR), upper limbs and head, superior and inferior vena cava, renal and hepatic, splanchnic, abdominal and lower limbs circulation have been modelled with resistance, inertance and compliance (RLC) elements [36]. The coronary circulation was modelled with RC elements. The numerical model reproducing central and peripheral VA ECMO configurations have been previously described [36].
Bioengineering 12 00540 g001
Bioengineering 12 00540 g002
Figure 2. Schematic representation of central and peripheral VA ECMO. The circuits have been slightly modified for the purposes of the simulations. Central VA ECMO draws blood from the right atrium (RA) and ejects it into the descending aorta (DA). Peripheral VA ECMO draws blood from the femoral vein (FV) and ejects it into the thoracic aorta (TA).
Figure 2. Schematic representation of central and peripheral VA ECMO. The circuits have been slightly modified for the purposes of the simulations. Central VA ECMO draws blood from the right atrium (RA) and ejects it into the descending aorta (DA). Peripheral VA ECMO draws blood from the femoral vein (FV) and ejects it into the thoracic aorta (TA).
Bioengineering 12 00540 g002
Bioengineering 12 00540 g003
Figure 3. Top left (right) panel shows the left (right) ventricular pressure-volume loops reproduced by CARDIOSIM© to simulate the pathological conditions (dashed blue line) and the assisted conditions with central (red line) and peripheral (black line) VA ECMO. The pump rotational speed was set to 3000 rpm. The bottom left panel shows the left atrial pressure-volume loops. The bar graph (bottom right panel) shows the percentage changes in assisted conditions compared to pathological conditions in terms of LVESV, LVEDV, RVESV, RVEDV, LAESV, and LAEDV.
Figure 3. Top left (right) panel shows the left (right) ventricular pressure-volume loops reproduced by CARDIOSIM© to simulate the pathological conditions (dashed blue line) and the assisted conditions with central (red line) and peripheral (black line) VA ECMO. The pump rotational speed was set to 3000 rpm. The bottom left panel shows the left atrial pressure-volume loops. The bar graph (bottom right panel) shows the percentage changes in assisted conditions compared to pathological conditions in terms of LVESV, LVEDV, RVESV, RVEDV, LAESV, and LAEDV.
Bioengineering 12 00540 g003
Bioengineering 12 00540 g004
Figure 4. Top left (right) panel shows the left (right) ventricular pressure-volume loops reproduced by CARDIOSIM© to simulate the pathological conditions (dashed blue line) and the assisted conditions with IABP in conjunction with central (red line) and peripheral (black line) VA ECMO, respectively. The pump rotational speed was set to 3000 rpm and the drive and vacuum IABP pressures were set to 260 mmHg and −10 mmHg, respectively. The bottom left panel shows the left atrial pressure-volume loops. The bar graph (bottom right panel) gives the percentage changes in assisted conditions compared to pathological conditions in terms of LVESV, LVEDV, RVESV, RVEDV, LAESV, and LAEDV.
Figure 4. Top left (right) panel shows the left (right) ventricular pressure-volume loops reproduced by CARDIOSIM© to simulate the pathological conditions (dashed blue line) and the assisted conditions with IABP in conjunction with central (red line) and peripheral (black line) VA ECMO, respectively. The pump rotational speed was set to 3000 rpm and the drive and vacuum IABP pressures were set to 260 mmHg and −10 mmHg, respectively. The bottom left panel shows the left atrial pressure-volume loops. The bar graph (bottom right panel) gives the percentage changes in assisted conditions compared to pathological conditions in terms of LVESV, LVEDV, RVESV, RVEDV, LAESV, and LAEDV.
Bioengineering 12 00540 g004
Bioengineering 12 00540 g005
Figure 5. Top bar graph shows the percentage changes in SVRi and cardiac index in assisted conditions with central and peripheral VA ECMO driven at 3000 and 3500 rpm, as well as with and without IABP support, in relation to pathological conditions. The bottom bar graph shows the percentage changes in systemic and pulmonary Ea and Ea/Ees in relation to pathological conditions.
Figure 5. Top bar graph shows the percentage changes in SVRi and cardiac index in assisted conditions with central and peripheral VA ECMO driven at 3000 and 3500 rpm, as well as with and without IABP support, in relation to pathological conditions. The bottom bar graph shows the percentage changes in systemic and pulmonary Ea and Ea/Ees in relation to pathological conditions.
Bioengineering 12 00540 g005
Bioengineering 12 00540 g006
Figure 6. The top (bottom) bar graph shows the percentage changes in blood flow and coronary blood flow (CBF) in assisted conditions with central (peripheral) VA ECMO driven at 3000, 3500, and 4000 rpm, as well as with and without IABP support, in relation to pathological conditions.
Figure 6. The top (bottom) bar graph shows the percentage changes in blood flow and coronary blood flow (CBF) in assisted conditions with central (peripheral) VA ECMO driven at 3000, 3500, and 4000 rpm, as well as with and without IABP support, in relation to pathological conditions.
Bioengineering 12 00540 g006
Bioengineering 12 00540 g007
Figure 7. Percentage changes in cerebral blood flow under assisted conditions with central and peripheral VA ECMO driven at 3000, 3500, and 4000 rpm, as well as with and without IABP support, in relation to pathological conditions.
Figure 7. Percentage changes in cerebral blood flow under assisted conditions with central and peripheral VA ECMO driven at 3000, 3500, and 4000 rpm, as well as with and without IABP support, in relation to pathological conditions.
Bioengineering 12 00540 g007
Bioengineering 12 00540 g008
Figure 8. The top bar graph (A) shows the percentage changes in minimum value of LAP (wedge), left ventricular pressure (LVP) and AoP in assisted conditions with central/peripheral VA ECMO driven at 3000, 3500, and 4000 rpm, as well as with and without IABP support, in relation to pathological conditions. Bar graph (B) shows percentage changes in maximum LAP, LVP, and AoP for central/peripheral VA ECMO with and without IABP support, in relation to pathological conditions.
Figure 8. The top bar graph (A) shows the percentage changes in minimum value of LAP (wedge), left ventricular pressure (LVP) and AoP in assisted conditions with central/peripheral VA ECMO driven at 3000, 3500, and 4000 rpm, as well as with and without IABP support, in relation to pathological conditions. Bar graph (B) shows percentage changes in maximum LAP, LVP, and AoP for central/peripheral VA ECMO with and without IABP support, in relation to pathological conditions.
Bioengineering 12 00540 g008
Bioengineering 12 00540 g009
Figure 9. Percentage changes in mean AoP value calculated in relation to pathological conditions for both central and peripheral VA ECMO assistance (with pump rotational speed set to 3000, 3500, and 4000 rpm), with and without IABP support.
Figure 9. Percentage changes in mean AoP value calculated in relation to pathological conditions for both central and peripheral VA ECMO assistance (with pump rotational speed set to 3000, 3500, and 4000 rpm), with and without IABP support.
Bioengineering 12 00540 g009
Bioengineering 12 00540 g010
Figure 10. Percentage changes in mean wedge value and minimum, mean, and maximum pulmonary arterial pressure values calculated in relation to pathological conditions for both central and peripheral VA ECMO assistance (with pump rotational speed set to 3000, 3500, and 4000 rpm), with and without IABP support.
Figure 10. Percentage changes in mean wedge value and minimum, mean, and maximum pulmonary arterial pressure values calculated in relation to pathological conditions for both central and peripheral VA ECMO assistance (with pump rotational speed set to 3000, 3500, and 4000 rpm), with and without IABP support.
Bioengineering 12 00540 g010
Bioengineering 12 00540 g011
Figure 11. Percentage changes in right and left atrial pressure-volume loop area in relation to pathological conditions for both central (top panel) and peripheral (bottom panel) VA ECMO assistance (with pump rotational speed set to 3000, 3500, and 4000 rpm), with and without IABP support.
Figure 11. Percentage changes in right and left atrial pressure-volume loop area in relation to pathological conditions for both central (top panel) and peripheral (bottom panel) VA ECMO assistance (with pump rotational speed set to 3000, 3500, and 4000 rpm), with and without IABP support.
Bioengineering 12 00540 g011
Bioengineering 12 00540 g012
Figure 12. The top (bottom) bar graph shows the percentage changes in LVESV, LVEDV, RVESV, and RVEDV under assisted conditions with central (peripheral) VA ECMO driven at 3000, 3500, and 4000 rpm, as well as with and without IABP support, in relation to pathological conditions.
Figure 12. The top (bottom) bar graph shows the percentage changes in LVESV, LVEDV, RVESV, and RVEDV under assisted conditions with central (peripheral) VA ECMO driven at 3000, 3500, and 4000 rpm, as well as with and without IABP support, in relation to pathological conditions.
Bioengineering 12 00540 g012
Bioengineering 12 00540 g013
Figure 13. The top (bottom) panel shows the percentage changes in left ventricular external work (LVEW), left ventricular pressure-volume area (LVPVA), right ventricular external work (RVEW) and right ventricular pressure-volume area (RVPVA)under assisted conditions with central (peripheral) VA ECMO driven at 3000, 3500, and 4000 rpm, as well as with and without IABP support, in relation to pathological conditions.
Figure 13. The top (bottom) panel shows the percentage changes in left ventricular external work (LVEW), left ventricular pressure-volume area (LVPVA), right ventricular external work (RVEW) and right ventricular pressure-volume area (RVPVA)under assisted conditions with central (peripheral) VA ECMO driven at 3000, 3500, and 4000 rpm, as well as with and without IABP support, in relation to pathological conditions.
Bioengineering 12 00540 g013
Disclaimer/Publisher’s Note: The statements, opinions and data contained in all publications are solely those of the individual author(s) and contributor(s) and not of MDPI and/or the editor(s). MDPI and/or the editor(s) disclaim responsibility for any injury to people or property resulting from any ideas, methods, instructions or products referred to in the content.

Share and Cite

MDPI and ACS Style

De Lazzari, B.; Capoccia, M.; Badagliacca, R.; Maybauer, M.O.; De Lazzari, C. Modelling and Simulation of the Interactions Between the Cardiovascular System and the Combined Use of VA ECMO and IABP: Comparison Between Peripheral and Central Configurations. Bioengineering 2025, 12, 540. https://doi.org/10.3390/bioengineering12050540

AMA Style

De Lazzari B, Capoccia M, Badagliacca R, Maybauer MO, De Lazzari C. Modelling and Simulation of the Interactions Between the Cardiovascular System and the Combined Use of VA ECMO and IABP: Comparison Between Peripheral and Central Configurations. Bioengineering. 2025; 12(5):540. https://doi.org/10.3390/bioengineering12050540

Chicago/Turabian Style

De Lazzari, Beatrice, Massimo Capoccia, Roberto Badagliacca, Marc O. Maybauer, and Claudio De Lazzari. 2025. "Modelling and Simulation of the Interactions Between the Cardiovascular System and the Combined Use of VA ECMO and IABP: Comparison Between Peripheral and Central Configurations" Bioengineering 12, no. 5: 540. https://doi.org/10.3390/bioengineering12050540

APA Style

De Lazzari, B., Capoccia, M., Badagliacca, R., Maybauer, M. O., & De Lazzari, C. (2025). Modelling and Simulation of the Interactions Between the Cardiovascular System and the Combined Use of VA ECMO and IABP: Comparison Between Peripheral and Central Configurations. Bioengineering, 12(5), 540. https://doi.org/10.3390/bioengineering12050540

Note that from the first issue of 2016, this journal uses article numbers instead of page numbers. See further details here.

Article Metrics

Back to TopTop