An experimental and computational study of the inferior vena cava hemodynamics under respiratory-induced collapse of the infrarenal IVC
Introduction
Pulmonary embolism (PE) is the third most common cause of death from cardiovascular disease, after heart attack and stroke [1]. Usually associated with deep vein thrombosis (DVT), pulmonary embolism occurs when a venous thrombus embolizes and passes through the inferior vena cava (IVC) to the pulmonary arteries. Emboli occluding blood flow to one or both lungs can lead to impaired oxygenation, heart strain, and death [2].
IVC filters have been used for over five decades as an alternative to anticoagulation therapy to prevent PE. These devices are designed to intercept and trap large emboli before they reach the lungs while allowing blood to bypass freely. However, complications associated with IVC filters remain common, including failure in embolus capture, wall perforation, filter tilt or migration, and filter fracture [3].
As demonstrated by several in vitro [4], [5], [6] and computational [7], [8], [9], [10], [11], [12], [13] studies, an in-depth understanding of the IVC hemodynamics is crucial to assess both potential risks and benefits of IVC filters. On the one hand, in vitro studies [4], [5], [6] have investigated the fluid dynamics in IVCs partially occluded by a placed IVC filter and captured emboli. These studies revealed stagnant flow and recirculation regions downstream of the partially occluded IVC, which may promote further thrombus formation. On the other hand, computational studies have simulated the hemodynamics in unoccluded and partially occluded IVCs [7], [8], [9], [10], [11], [12], embolus transport and capture [8], filter positioning in idealized [13] and patient-specific IVC geometries [10], [13]. Two studies [14], [15] combined both in vitro experiments and computational fluid dynamics (CFD) to deepen the understanding of the hemodynamic performance of different IVC filters. Notably, Stewart and colleagues [14] were the first to use a compliant vena cava model for particle image velocimetry (PIV) flow visualization. They compared flow velocities between PIV and CFD, using the latter also to quantify IVC wall shear stresses (WSS).
Nonetheless, the hemodynamics during respiratory-induced partial collapse of the IVC that occurs during normal breathing and Valsalva maneuver have not yet been evaluated. We hypothesize that partial collapse of the IVC may have an important influence on the IVC hemodynamics. Indeed, during inspiration, positive pressure in the abdomen causes the infrarenal IVC to diminish in size, while during expiration a negative pressure causes the infrarenal IVC to expand [16]. Valsalva has an effect similar to that of inspiration, with even greater positive pressure and, thereby, greater collapse of the IVC [16].
The IVC collapsibility index (IVC-CI) quantifies the effect of normal breathing and Valsalva on the IVC cross-sectional shape and is defined as the difference between the end-expiratory (Dexp) and end-inspiratory (Dinsp) minor diameter of the IVC, divided by the Dexp [16], [17], [18], [19]. Clinically, the IVC-CI is used to evaluate a patient's intravascular volume status and can range from zero (no collapse during respiration, a possible indication of hypervolemia) to unity (full collapse during breathing, a possible indication of hypovolemia) [20]. Reported healthy (i.e., asymptomatic) IVC-CI values are approximately 0.3 to 0.4 during normal breathing (e.g., see control groups in [21], [22]) and 0.50 + /‒ 0.04 during Valsalva [16].
We investigate the impact of different levels of IVC collapse under both resting and exercise flow conditions by performing PIV measurements on a compliant model of the human IVC accompanied by numerical CFD simulations. In all experiments and simulations, the complex dynamics of IVC collapse are simplified by approximating the vessel walls as rigid and the flow as quasi-steady. The combination of in vitro and computational approaches allows us to partially validate our numerical CFD results, thus providing greater confidence in the additional fields (e.g wall shear stress [WSS]) that are relatively easily extracted from CFD results, but are difficult to obtain directly through PIV.
Section snippets
IVC model
In vitro experiments and CFD simulations are performed using an idealized model of the human IVC (Fig. 1(a)). The IVC model was created using SolidWorks (Dassault Systèmes, Vélizy-Villacoublay, France) and includes both iliac and renal veins (left and right, respectively), an infrarenal segment, and a suprarenal segment (Table 1). In the absence of collapse, all vessel cross sections are circular. Vessel diameters are representative of mean measurements found in the literature (Table 1). The
No collapse configuration
PIV Results - Under resting flow conditions, higher velocities occurred in the right iliac vein compared to the left iliac vein due to the 46% smaller cross-sectional area of the right iliac side (0.68 cm2 vs. 1.27 cm2; Fig. 3(a), midplane). Moreover, a jet developed within the IVC and progressively deviated towards the left wall moving downstream from the iliac bifurcation (Fig. 3(a)). The peak velocity of the jet reached approximately 0.3 m/s. On both the plus 25% and minus 25% planes, a jet,
Discussion
In the present study, we investigated the IVC fluid dynamics in configurations mimicking the physiological collapse that occurs during breathing and Valsalva using PIV experiments and numerical simulations. In particular, for the first time, we investigated the impact of different levels of IVC collapse, under resting and exercise conditions, on IVC hemodynamics and the sensitivity of the IVC hemodynamics to different distributions of the infrarenal flow. Additionally, overcoming the limiting
Acknowledgments
We would like to acknowledge the contributions of Frank Lynch, MD (Penn State Hershey Medical Center) for assisting in the planning of the compliant model and Brent Craven (U.S. Food and Drug Administration) for assisting in acquiring the computed tomography scans used to generate the computational model of the IVC. This research did not receive any specific grant from funding agencies in the public, commercial, or not-for-profit sectors.
Competing interests
None declared.
Funding
None.
Ethical approval
Not required.
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