Fluid–structure interaction simulation of pulse propagation in arteries: Numerical pitfalls and hemodynamic impact of a local stiffening

Taelman, Liesbeth; Degroote, Joris; Swillens, Abigaïl; Vierendeels, Jan; Segers, Patrick

doi:10.1016/j.ijengsci.2013.12.002

Cited by 21 publications

(9 citation statements)

References 26 publications

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“…The dilatational wave speed = √( + 4 3 ⁄ )⁄ (Dassault Systèmes, 2012) was equal to 408 m/s, being sufficient to avoid interaction between longitudinal and shear wave modes. The material density was assumed 1200 kg/m 3 (Taelman et al, 2014 True stresses corresponding to the unloading part of the 10 th mechanical cycle were found using the formula:…”

Section: Anisotropic Materials Lawmentioning

confidence: 99%

A finite element model to study the effect of tissue anisotropy onex vivoarterial shear wave elastography measurements

Shcherbakova¹,

Debusschere²,

Caenen³

et al. 2017

Phys. Med. Biol.

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Abstract. Shear wave elastography (SWE) is an ultrasound (US) diagnostic method for measuring the stiffness of soft tissues based on generated shear waves (SWs). SWE has been applied to bulk tissues, but in arteries it is still under investigation. Previously performed studies in arteries or arterial phantoms demonstrated the potential of SWE to measure arterial wall stiffness -a relevant marker in prediction of cardiovascular diseases. This study is focused on numerical modelling of SWs in ex vivo equine aortic tissue, yet based on experimental SWE measurements with the tissue dynamically loaded while rotating the US probe to investigate the sensitivity of SWE to the anisotropic structure. A good match with experimental shear wave group speed results was obtained. SWs were sensitive to the orthotropy and nonlinearity of the material. The model also allowed to study the nature of the SWs by performing 2D FFT-based and analytical phase analyses. A good match between numerical group velocities derived using the time-of-flight algorithm and derived from the dispersion curves was found in the cross-sectional and axial arterial views. The complexity of solving analytical equations for nonlinear orthotropic stressed plates was discussed.

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Section: Anisotropic Materials Lawmentioning

confidence: 99%

A finite element model to study the effect of tissue anisotropy onex vivoarterial shear wave elastography measurements

Shcherbakova¹,

Debusschere²,

Caenen³

et al. 2017

Phys. Med. Biol.

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“…14 Impact of repaired CoA on proximal pressure As reported in [38], in which a physiological pressure pulse was imposed as a boundary condition to a straight, flexible tube including a local stiffening, no significant alteration of the proximal pressure is retrieved. This limited impact is comprehended by the analysis of the wave reflections induced by the stiffening.…”

Section: Impact Of Rigid Wall Modelingmentioning

confidence: 99%

Differential impact of local stiffening and narrowing on hemodynamics in repaired aortic coarctation: an FSI study

Taelman

Bols

Degroote

et al. 2015

Med Biol Eng Comput

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Even after successful treatment of aortic coarctation, a high risk of cardiovascular morbidity and mortality remains. Uncertainty exists on the factors contributing to this increased risk among which the presence of (1) a residual narrowing, leading to an additional resistance and (2) a less distensible zone disturbing the buffer function of the aorta. As the many interfering factors and adaptive physiologic mechanisms present in vivo prohibit the study of the isolated impact of these individual factors, a numerical fluid-structure interaction model is developed to predict central hemodynamics in coarctation treatment. The overall impact of a stiffening on the hemodynamics is limited, with a small increase in systolic pressure (up to 8 mmHg) proximal to the stiffening which is amplified with increasing stiffening and length. A residual narrowing, on the other hand, affects the hemodynamics significantly. For a short segment (10mm) the combination of a stiffening and narrowing (coarctation index 0.5) causes an increase in systolic pressure of 58 mmHg, with 31 mmHg due to narrowing and an additional 27 mmHg due to stiffening. For a longer segment (25 mm), an increase in systolic pressure of 50 mmHg is found, of which only 9 mmHg is due to stiffening.

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“…Here the arbitrary Lagrangian-Eulerian (ALE) formulation is applied to quantify the fluid-structure interaction. This formulation has been used by several researchers [12], [13]. In brief, the Eq.…”

Section: ) Fluid Domainmentioning

confidence: 99%

Ultrasound evaluation of an abdominal aortic fluid-structure interaction model

Traberg

Jensen

2014

2014 IEEE International Ultrasonics Symposium

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Abstract-Ultrasound measurements are used for evaluating biomechanics of the abdominal aorta (AA) predicted by a fluidstructure interaction (FSI) simulation model. FSI simulation models describe the complete arterial physiology by quantifying the mechanical response in the vessel wall caused by the percolating pulsating blood. But the predictability of FSI models needs validation for these to be usable for diagnostic purposes. Ultrasound measurements are suitable for such an evaluation as the wall displacement can be measured in vivo and compared to the wall displacement simulated in the FSI model. Spectral Doppler velocity data from 3 healthy male volunteers were used to construct inlet profiles for the FSI model. Simultaneously, wall movement was tracked and used for comparison to FSI model results. Ultrasound data were acquired using a scanner equipped with a research interface. The wall displacement was estimated by time shift estimation obtained from cross-correlation of signals to a fixed reference. The FSI model was constructed as a 2D axissymmetric pipe with lumen diameter predicted by B-mode images from each volunteer. Visual comparison of wall displacement over 1 cardiac cycle show agreement except for 1 volunteer (Male, 23 yrs.). The magnitude of the displacement in simulation, u fsi , and in vivo, u iv , is within the same order of magnitude for the young (u iv = 1.48 mm, u fsi = 1.12 mm) and middle-aged volunteer (u iv = 0.783 mm, u fsi = 1.31 mm). For the elderly volunteer the simulated displacement (u fsi = 0.975 · 10 −3 mm) is much smaller compared to in vivo (u iv = 0.979 mm). In conclusion, the FSI model predicts a much stiffer AA wall compared to measured displacements for the elderly volunteer. From the visual comparison in vivo wall motion is captured in the FSI model for 2 of the 3 volunteers.

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Fluid–structure interaction simulation of pulse propagation in arteries: Numerical pitfalls and hemodynamic impact of a local stiffening

Cited by 21 publications

References 26 publications

A finite element model to study the effect of tissue anisotropy onex vivoarterial shear wave elastography measurements

A finite element model to study the effect of tissue anisotropy onex vivoarterial shear wave elastography measurements

Differential impact of local stiffening and narrowing on hemodynamics in repaired aortic coarctation: an FSI study

Ultrasound evaluation of an abdominal aortic fluid-structure interaction model

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