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Review

Blood Flow Modeling in Coronary Arteries: A Review

by
Violeta Carvalho
1,
Diana Pinho
1,2,3,4,†,
Rui A. Lima
1,2,*,
José Carlos Teixeira
1 and
Senhorinha Teixeira
5
1
MEtRICs Research Center, Mechanical Engineering Department, University of Minho, Campus de Azurém, 4800-058 Guimarães, Portugal
2
CEFT, Faculdade de Engenharia da Universidade do Porto (FEUP), R. Dr. Roberto Frias, 4200-465 Porto, Portugal
3
Research Centre in Digitalization and Intelligent Robotics (CeDRI), Instituto Politécnico de Bragança, Campus de Santa Apolónia, 5300-253 Bragança, Portugal
4
Center for MicroElectromechanical Systems (CMEMS-UMinho), University of Minho, Campus de Azurém, 4800-058 Guimarães, Portugal
5
ALGORITMI Centre (CAlg), University of Minho, 4800-058 Guimarães, Portugal
*
Author to whom correspondence should be addressed.
†
Current Affiliation: INL—International Iberian Nanotechnology Laboratory, Av. Mestre José Veiga, 4715-330 Braga, Portugal
Fluids 2021, 6(2), 53; https://doi.org/10.3390/fluids6020053
Submission received: 29 November 2020 / Revised: 10 January 2021 / Accepted: 20 January 2021 / Published: 23 January 2021
(This article belongs to the Special Issue Computational Biofluid Mechanics)
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Abstract

:
Atherosclerosis is one of the main causes of cardiovascular events, namely, myocardium infarction and cerebral stroke, responsible for a great number of deaths every year worldwide. This pathology is caused by the progressive accumulation of low-density lipoproteins, cholesterol, and other substances on the arterial wall, narrowing its lumen. To date, many hemodynamic studies have been conducted experimentally and/or numerically; however, this disease is not yet fully understood. For this reason, the research of this pathology is still ongoing, mainly, resorting to computational methods. These have been increasingly used in biomedical research of atherosclerosis because of their high-performance hardware and software. Taking into account the attempts that have been made in computational techniques to simulate realistic conditions of blood flow in both diseased and healthy arteries, the present review aims to give an overview of the most recent numerical studies focused on coronary arteries, by addressing the blood viscosity models, and applied physiological flow conditions. In general, regardless of the boundary conditions, numerical studies have been contributed to a better understanding of the development of this disease, its diagnosis, and its treatment.

Graphical Abstract

1. Introduction

Cardiovascular diseases are responsible for a critical number of deaths every year worldwide, accounting for nearly 31% of all deaths, most of which are associated with atherosclerosis, a disease that causes unusual hemodynamic conditions in arteries [1,2,3]. Briefly, atherosclerosis is a silent, multifactorial, and complex disease initiated when lipids and immune cells are accumulated in the arterial wall, resulting in the formation of a plaque [4,5]. This has been correlated to local biological, biomechanical, and systemic factors [6,7,8]. Among these factors, local hemodynamics has been indicated as the major cause [9,10,11]. In particular, wall shear stress (WSS) is a well-known predictor of coronary atherosclerosis progression. While regions of low wall shear stress have been commonly recognized as prone to plaque development, high values of WSS are related to plaque destabilization [12,13,14,15,16]. Moreover, a recent study has also proved that patients with COVID-19 are at high risk for thrombotic arterial and venous occlusions. Considering the mortality rate caused by this virus itself until today and its relation with atherosclerosis development, this becomes an even more complex situation [17].
Although the presence of this pathology has quite serious damage regardless of the arteries affected, the situation is aggravated when this pathology develops in coronary arteries. When those are affected, the agglomeration of fatty materials creates an occlusion, which restricts the blood flow to the heart muscle leading to a decreased supply of blood, oxygen, and other vital nutrients fundamental for the proper functioning of this organ. Eventually, the reduced blood flow may cause chest pain or a heart attack if there is a complete blockage of the artery [18,19]. A common approach used to treat this pathology is balloon angioplasty and placement of an intracoronary stent. This allows restoring the blood flow keeping the artery open, nevertheless, the risk of restenosis is still present [20,21].
Considering the global impact of this disease, it is of utmost importance to obtain deeper knowledge about the blood flow hemodynamics. For this reason, extensive research has been done in this area, by applying either experimental and/or numerical methods. Although numerous experimental hemodynamic studies are found in the literature, by applying either in vitro [22,23,24,25,26,27,28], in vivo [29,30,31,32,33], or ex vivo [34,35,36] approaches, there are some drawbacks associated as reported elsewhere [19,37,38,39,40,41]. For this reason, lately, computational approaches have been the preferred method of several researchers [42,43,44,45,46]. These have become a valuable tool for evaluating and predicting the disease formation, and also for testing the performance of new devices for its treatment. By having the capability of constructing more realistic virtual models, getting fast and accurate results, and thoroughly testing different physiological conditions, some limitations of hemodynamic experimental techniques used can be overcome by the computational models [45,47,48,49,50,51]. However, this does not mean that those models can completely replace experimental tests since it is still quite challenging to perform realistic blood flow modeling [52].
Due to several advantages of using numerical simulations, computational atherosclerosis studies have gained popularity in recent years [53]. In general, to perform numerical simulations three main steps have to be accomplished, the pre-processing, the solver, and the post-processing. Firstly, it is necessary to define the geometry of the problem, followed by the mesh generation. Secondly, the fluid properties of blood, the flow physics model, and the boundary conditions are defined in order to solve the mathematical model. Finally, after the problem being solved, the results are analyzed. These steps are drafted as follows in Figure 1.
Over the years, researchers have modeled blood flow within arteries by using different geometries, diverging in two directions, using either stenotic geometries with idealized shapes (e.g., half-sphere [54], ellipsoid [55], gaussian equation [56], cosine function [57], among others proposed by the authors themselves [58,59]) or realistic coronary artery models extracted from patient’s medical data [60,61,62,63,64,65].
After defining the geometry, the blood properties have to be set to solve the problem accurately. Blood is a complex mixture of cells, proteins, lipoproteins, and ions which are transports nutrients and wastes. Due to the presence of red blood cells, the viscosity of blood is increased and affects the behavior of the fluid. Moreover, although considering the blood as a Newtonian fluid is generally accepted as a good approximation for large vessels, in the microcirculatory system, and also in the presence of stenosis, the assumption is not true. At these locations, the non-Newtonian behavior is more evident due to the ability of red blood cells to form aggregates, termed rouleaux, at low shear rates. Moreover, other aspects that should be taken into account are the cyclic nature of the heart pump, which creates pulsatile conditions, and also the elastic behavior observed in the arteries’ wall [66,67,68].
Although the aforementioned characteristics of blood, namely, the vessel wall elasticity, non-Newtonian viscosity, and particles in the fluid, and body forces are physiologically relevant, the analysis of blood flow can be greatly simplified by neglecting some of the properties [68]. For this reason, in the literature, there is a vast diversity of articles that apply different boundary conditions to simulate blood flow, and attention must be taken since the performance of CFD models is directly dependent on the blood rheology, physiological flow conditions, mechanical properties of blood vessels, among other mechanical and biological factors set to solve the problem. In this regard, in the present paper, a review of the geometries, boundary conditions, and flow properties proposed by several authors for coronary models is provided by discussing and presenting the current knowledge on the advantages and also the drawbacks of blood viscosity models and physiological flow conditions available.

2. Blood Flow Studies in Coronary Arteries

Despite the progress done in experimental studies and blood flow measurement techniques, there are still some challenges associated with them [19]. For instance, in vitro WSS measurements are extremely difficult to perform and the velocity measurements have high associated errors. These, combined with other complications of directly measuring quantities of interest, have motivated the use of computer simulations to predict them in silico [69].
The earliest numerical detailed studies solving the flow problem in constricted tubes were conducted by Lee and Fung (1970) [70]. After that, other studies in this field conducted by Caro et al., (1971) [71], Glagov et al., (1989) [72], and Ku et al., (1985) [73] are important references in this area and should be highlighted. Ever since, CFD approaches have been progressively adopted by most researchers as the preferred technique for numerical modeling of hemodynamics. Owing to the continued growth of computational power, these have become an increasingly reliable tool for measuring biomechanical factors vital for clinical decision-making and surgical planning. However, the proper selection of the flow boundary conditions has to be done, otherwise, the findings can be considered uncertain, weak, and unrealistic [74]. In this regard, the different geometries, boundary conditions, and flow characteristics applied by some researchers in the last ten years are summarized in Table 1.
From the above-mentioned investigations, it can be seen that, regardless of the type of geometry, the majority of authors consider that the blood is a non-Newtonian fluid, usually approximated by the Carreau model, with a laminar behavior. Regarding the boundary conditions, in most cases, the wall is considered rigid, and at the inlet, a pulsatile velocity is applied. At the outlet, the condition set mainly depends on the study, but either the default conditions are maintained, or pressures are applied, time-dependent or constant values.

2.1. Geometrical Parameters and Stenosis Severity

Before studying directly stenotic coronary arteries, some authors have dedicated their time to study the effect of geometrical parameters, such as the branch curvatures, tortuosities, and the angulations of the arteries, and relating them to the development of atherosclerosis, by resorting to idealized geometries, or the combination of patient-specific models with idealized ones [6,87,89]. In general, regardless of the type of geometry, it has been shown that there is a direct correlation between wide angulation in the coronary artery branches and hemodynamic changes, such as disturbed flow and low WSS, possibly inducing the development of atherosclerosis [87,89]. Although consistent observations between idealized and patient-specific models have been demonstrated by Chaichana et al., (2011) [89], the same is not true when talking about the arteries’ curvature and tortuosity, since small variations can lead to different hemodynamic simulated results [6]. It was shown that the specific curvature of each branch of the coronary bifurcation affects the hemodynamics of the remaining three branches, which can cause an increase in atherosusceptibility [6]. In view of this, it can be verified that the selection of the geometrical parameters of the artery model plays an important role and can lead to different hemodynamic results.
Nevertheless, when the aim is to investigate the effect of stenosis severity, the results presented in the literature have shown to be in good agreement independently of the model used, idealized, or patient-specific. Generally, an increase in the velocity and WSS at the stenosis throat is observed. This increased WSS can disturb the plaque formed and lead to plaque rupture, and consequently to heart failure. Besides the WSS, other shear stress indices have been studied such as the time average wall shear stress (TAWSS), and the oscillatory stress index (OSI). While the TAWSS has the same trend as WSS, the OSI distribution has a maximum value in the region downstream of the stenosis. Moreover, in this location, the prevalence of recirculation zones is also verified [60,64,75,86,90,91]. Both high OSI, low WSS, and disturbed flows in the post stenotic section are important factors that can promote the formation of atherosclerotic plaques [59,68,92].
A different way to study the effect of stenosis in blood flow hemodynamics was addressed by Doutel et al., (2018) [93]. They developed a methodology to create three-dimensional irregular stenosis with different degrees of occlusion in artery models for both numerical and in vitro hemodynamic studies. This methodology is quite interesting since it allows the creation of realistic stenosis in a fast way for hemodynamic studies. Furthermore, the authors proved that the irregular shape of the stenosis and their specific morphology affects the flow field, creating diverse values of WSS for each case.

2.2. Newtonian and Non-Newtonian Assumptions

Besides the effect of stenosis, several studies have emphasized the importance of considering the non-Newtonian behavior of blood and selecting the proper model to better represent the in vivo conditions [56,94]. An interesting study was undertaken by Razavi et al. (2011) [56], in which six non-Newtonian models and a Newtonian model were compared. The data obtained showed that the power-law model produces higher deviations in comparison with other models, overstating the non-Newtonian behavior, regarding the velocity and WSS values. On the other hand, the generalized power-law and modified-Casson models are more similar to the Newtonian state, though, they underestimate the non-Newtonian behavior. In contrast to the previous models, the Carreau and Carreau–Yasuda models represented moderate IG values (cut-off value above which flow can be assumed as non-Newtonian), demonstrating to be the suitable models to mimic the blood behavior. Other authors have also compared Newtonian and non-Newtonian models. Chaichana et al., (2012) [60] compared the effect of the non-Newtonian power-law generalized model with a Newtonian fluid; however, similar results were obtained for both cases, in terms of velocity fields and WSS measurements. On the other hand, Gaudio et al. (2018) [91] compared the Newtonian and non-Newtonian Carreau–Yasuda model. Their results showed that the velocity for the Carreau–Yasuda model is slightly lower when compared to the Newtonian model, but the non-Newtonian effects are most important in shear stress indices distributions. Carvalho et al., (2020) [78] have similar results; however, they used the Carreau non-Newtonian model. Another interesting study was performed by Pinto et al., (2020) [95]. They investigated several viscoelastic models, namely the Generalized Oldroyd-B (GOB) model, the Multi-mode Giesekus and Simplified Phan-Thien/Tanner (sPTT) models in order to conclude which model is the most accurate to simulate the blood flow, and compared those with the Carreau model and also with a Newtonian model. The authors verified that the non-linear viscoelastic multi-mode models (Giesekus and sPTT) cause an overall reduction of the velocity in regions of higher velocity gradients. In general, the researchers concluded that the sPTT model should be the preferred option since the Giesekus model introduces the second normal stress difference, which so far has not been reported for blood.

2.3. Turbulence Modeling and Wall Assumptions

Although various investigations consider the blood flow as laminar, due to the pulsatile nature of blood flow through arteries, and the presence of stenosis, the transition from laminar to turbulent flow condition can occur. For this reason, some authors have explored some turbulent models in computational simulations [42,59,64,77,78,86,96]. By observing Table 1 it can be seen that the majority uses or the standard k-ω or the k-ω SST turbulent model. The main difference between these two models is that the SST model accounts for the laminar to turbulent transition, and it seems to be the most suitable for blood flow studies [64,97]. However, in a study conducted by Straatman et al. (2016) [97], both models were compared with experimental data, and the k-ω SST turbulent model provided the best overall results.
Furthermore, hemodynamic studies mainly assume the wall to be rigid, however, over the years, fluid-structure interaction (FSI) has received increasing interest due to its ability to simultaneously model blood flow and arterial wall deformations [79,81,98,99,100,101]. Among the several investigations that have emerged in this area, one of the most cited works in the literature was performed by Torii et al. (2009) [99], wherein the effects of compliance in WSS calculations were studied. Although more recent studies have been conducted to evaluate if there are significant differences between flexible and rigid walls, the main results are in good agreement. It is stated that there are negligible differences in TAWSS and OSI values, although, in the distal region of the artery, differences in instantaneous WSS profiles and velocity measurements were perceptible [57,99]. Regardless of the interesting results obtained in the literature, since arteries have a high degree of stiffness, in most cases, the effects of elasticity are very small, and thus, an assumption of rigid tube flow is reasonable [68].

3. Conclusions and Future Perspectives

Due to the great progress that has been made recently in the development of CFD methods, these have become extremely fundamental for hemodynamic studies, allowing researchers to obtain a better understanding of atherosclerosis in a rapid and accurate fashion. However, there are still unsolved challenges that have to be addressed in future hemodynamic studies. In the present review, the application of computational simulations by using different physiological conditions of blood flow, several rheological models, and boundary conditions, were discussed.
Although huge advancements have been made in imaging techniques to obtain patient-specific images, this step is time-consuming, and it is still a challenging task for all researchers. For this reason, nowadays, idealized models continue to be widely used by researchers, since these allow to obtain important and relevant results, without requiring much computational time and without the need to collect the medical images, which is highly time-consuming. In this regard, a promising study was proposed by Doutel et al., (2018) [93] wherein artificial, but realistic stenosis can be generated.
It was also noted that, although the modelling of blood as a Newtonian fluid is a good approximation for large vessels with high shear rates, the assumption of non-Newtonian behavior of blood flow has been increasingly used in the presence of stenosis. From the overall studies, the most used models are the Carreau and the Carreau-Yasuda, and these have also been indicated as the most appropriate to simulate the blood rheology by Razavi et al., (2011) [56]. Nevertheless, currently, one cannot say which is the right model, because there is not yet enough evidence in the literature to prove which model fully expresses the complex nature of blood rheology and its dependence on many biological factors [50]. Accordingly, it is of great importance to obtain proper models for CFD analysis that take into account the non-Newtonian behavior of blood. For this purpose, more experimental studies are needed. Regarding the boundary conditions, few studies have evaluated the impact of using different inlet and outlet boundary conditions [74,102], and therefore, it would be interesting, in future studies, to investigate what are the profiles more adequate to study the blood flow behavior in coronary arteries.
Despite the great efforts that have been made so far, the blood has been mainly modeled as a single-phase fluid. However, blood is a mixture of plasma, red blood cells, white blood cells, and platelets. Therefore, the consideration of multiphase models is of great importance when modeling atherosclerotic lesions. Although some studies have already applied these models [42,83,103,104,105], the research is still in the beginning. Moreover, it should be also noted that the use of these models is a promising option for studying nanoparticle-mediated targeted drug delivery treatment of atherosclerosis. In this context, a promising study was conducted by Zhang et al., (2020) [83]. The authors used an Eulerian-Lagrangian approach coupled with FSI to investigate the impact of plaque morphology on magnetic nanoparticles targeting under the action of an external field.
Due to the continuous improvements acquired in computational methods, in the following years more amazing and complex hemodynamic studies will be performed. The work of Zhao et al. (2019) [82] should be highlighted since their numerical approach has a great potential to achieve more realistic simulations. They have simulated 4D hemodynamic profiles of time-resolved blood flow. The results proved that these simulations can provide extensive information about blood flow, both qualitatively and quantitatively that may be advantageous for future investigations of clinical diagnosis and treatment of atherosclerosis.
To conclude, although computational methods have been extensively used for atherosclerosis investigations in recent years, they are expected to become more popular and more effective to simulate the blood flow in the cardiovascular system, and consequently, they will promote medical innovation at an affordable cost. However, to this end, active collaborations between engineers and medical staff are needed to assure the successful application of this technique in atherosclerosis treatment.

Author Contributions

Conceptualization, V.C. and S.T.; Writing-Original Draft Preparation, V.C.; Writing—Review and Editing, V.C., D.P., R.A.L., J.C.T. and S.T.; Supervision, R.A.L. and S.T.; Funding Acquisition, J.C.T., R.A.L. and S.T. All authors have read and agreed to the published version of the manuscript.

Funding

This work was supported through the R&D Units Project Scope: UIDB/00319/2020, UIDB/04077/2020, NORTE-01-0145-FEDER-030171, and NORTE-01-0145-FEDER-029394, funded by COMPETE2020, NORTE 2020, PORTUGAL 2020, and FEDER.

Conflicts of Interest

The authors declare no conflict of interest.

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Fluids 06 00053 g001 550
Figure 1. Main steps performed in numerical simulations.
Figure 1. Main steps performed in numerical simulations.
Fluids 06 00053 g001
Table
Table 1. Numerical studies of hemodynamics and the respective assumptions for numerical simulations.
Table 1. Numerical studies of hemodynamics and the respective assumptions for numerical simulations.
GeometrySchematic RepresentationModeling ApproachesFluidBoundary ConditionsAuthors
WallInletOutlet
Idealized Fluids 06 00053 i001LaminarNon-Newtonian (Carreau-Yasuda)RigidTime-dependent velocity profileZero gauge pressureKashyap et al., (2020) [6]
Idealized Fluids 06 00053 i002LaminarNewtonianRigidTime-dependent mass flow profileZero surface tensionBiglarian et al., (2019) [75]
Idealized Fluids 06 00053 i003LaminarNon-Newtonian (Cross model)Rigid and FlexibleConstant inlet velocityConstant pressure outlet (10 kPa)Mulani et al., (2015) [57]
Idealized Fluids 06 00053 i004LaminarNewtonianRigid and FlexibleTime-dependent flowrate profileTime-dependent pressure profileWu et al., (2015) [58]
Idealized Fluids 06 00053 i005LaminarNewtonianRigidConstant inlet velocity (fully developed parabolic profile)Constant pressure outlet (13 kPa)Kenjereš et al., (2019) [76]
Idealized Fluids 06 00053 i006LaminarNewtonianRigidConstant inlet velocityZero gauge pressure Carvalho et al., (2020) [47]
Idealized Fluids 06 00053 i007k-ω turbulent modelNon-Newtonian (Carreau model)RigidSpiral boundary conditionwith a parabolic velocity profileZero gauge pressureKabir et al., (2018) [77]
Idealized Fluids 06 00053 i008k-ω turbulent model (SST)Non-Newtonian (Carreau model)RigidTime-dependent velocity profileZero gauge pressureCarvalho et al., (2020) [42]
Idealized Fluids 06 00053 i009k-ω turbulent model (SST)Non-Newtonian (Carreau model)Rigid Time-dependent velocity profileZero gauge pressure Carvalho et al., (2020) [59,78]
Idealized Fluids 06 00053 i010N.A1NewtonianFlexibleTime-dependent velocity profileTime-dependent pressure profileJahromi et al., (2019) [79]
Idealized Fluids 06 00053 i011LaminarNewtonianRigidTime-dependent velocity profileFlow partition implied in Murray’s lawDoutel et al., (2018) [11]
Patient-specific Fluids 06 00053 i012LaminarNon-Newtonian (Generalized power-law model) and NewtonianRigid Time-dependent flow rate profileTime-dependent pressure profileChaichana et al., (2012) [60]
Patient-specific Fluids 06 00053 i013LaminarNon-Newtonian (Carreau model)Rigid Time-dependent velocity profileTime-dependent pressure profileLiu et al., (2015) [80]
Patient-specific Fluids 06 00053 i014LaminarNewtonianRigid and Flexible Time-dependent pressure profileParabolic velocity profileSiogkas et al., (2014) [81]
Patient-specific Fluids 06 00053 i015N.ANewtonianRigid Time-dependent pressure profileConstant pressure outlet (9.85 kPa) Zhao et al., (2019) [82]
Patient-specific Fluids 06 00053 i016LaminarNon-Newtonian (Carreau model) Rigid Time-dependent velocity profileFlow partition implied in Murray’s lawPandey et al., (2020) [43]
Patient-specific Fluids 06 00053 i017LaminarNon-Newtonian (Carreau model)Rigid Various time-dependent velocity profilesFlow partition implied in Murray’s lawRizzini et al., (2020) [74]
Patient-specific Fluids 06 00053 i018N.ANon-Newtonian (Power-law model)Rigid Time-dependent velocity profilePressure outlet (N.A)Zhang et al., (2020) [83]
Patient-specific Fluids 06 00053 i019k-ω turbulent model (SST)Non-Newtonian (Bird-Carreau model)Rigid Time-dependent velocity profileConstant pressure outlet (10 kPa) Kamangar et al., (2019) [64]
Patient-specific Fluids 06 00053 i020LaminarNewtonianRigidTime-dependent flow rate profileTwo-Element Windkessel ModelLo et al., (2019) [84]
Patient-specific and Idealized Fluids 06 00053 i021LaminarNewtonian and Non-Newtonian (Carreau model)Rigid Constant inlet velocity and Time-dependent velocity profileN.ADoutel et al., (2019) [85]
Patient-specific and Idealized Fluids 06 00053 i022k-ω turbulent model (SST)Non-Newtonian (Carreau model)Rigid Time-dependent velocity profileOutflow conditionMahalingam et al., (2016) [86]
Patient-specific and Idealized Fluids 06 00053 i023N.ANon-Newtonian (Carreau model) Rigid Time-dependent velocity profileConstant pressure outlet (10 kPa) Rabbi et al., (2020) [87]
Patient-specific and Idealized Fluids 06 00053 i024LaminarNewtonianRigidConstant inlet mass flow and Time-dependent flow rateZero gauge pressureMalota et al., (2018) [88]
N.A—Not available. All images were adapted from [6,11,42,43,47,57,58,59,60,64,74,75,76,77,78,79,80,81,82,83,84,85,86,87,88].
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Carvalho, V.; Pinho, D.; Lima, R.A.; Teixeira, J.C.; Teixeira, S. Blood Flow Modeling in Coronary Arteries: A Review. Fluids 2021, 6, 53. https://doi.org/10.3390/fluids6020053

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Carvalho V, Pinho D, Lima RA, Teixeira JC, Teixeira S. Blood Flow Modeling in Coronary Arteries: A Review. Fluids. 2021; 6(2):53. https://doi.org/10.3390/fluids6020053

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Carvalho, Violeta, Diana Pinho, Rui A. Lima, José Carlos Teixeira, and Senhorinha Teixeira. 2021. "Blood Flow Modeling in Coronary Arteries: A Review" Fluids 6, no. 2: 53. https://doi.org/10.3390/fluids6020053

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