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Effects of intima stiffness and plaque morphology on peak cap stress
BioMedical Engineering OnLinevolume 10, Article number: 25 (2011)
Rupture of the cap of a vulnerable plaque present in a coronary vessel may cause myocardial infarction and death. Cap rupture occurs when the peak cap stress exceeds the cap strength. The mechanical stress within a cap depends on the plaque morphology and the material characteristics of the plaque components. A parametric study was conducted to assess the effect of intima stiffness and plaque morphology on peak cap stress.
Models with idealized geometries based on histology images of human coronary arteries were generated by varying geometric plaque features. The constructed multi-layer models contained adventitia, media, intima, and necrotic core sections. For adventitia and media layers, anisotropic hyperelastic material models were used. For necrotic core and intima sections, isotropic hyperelastic material models were employed. Three different intima stiffness values were used to cover the wide range reported in literature. According to the intima stiffness, the models were classified as stiff, intermediate and soft intima models. Finite element method was used to compute peak cap stress.
The intima stiffness was an essential determinant of cap stresses. The computed peak cap stresses for the soft intima models were much lower than for stiff and intermediate intima models. Intima stiffness also affected the influence of morphological parameters on cap stresses. For the stiff and intermediate intima models, the cap thickness and necrotic core thickness were the most important determinants of cap stresses. The peak cap stress increased three-fold when the cap thickness was reduced from 0.25 mm to 0.05 mm for both stiff and intermediate intima models. Doubling the thickness of the necrotic core elevated the peak cap stress by 60% for the stiff intima models and by 90% for the intermediate intima models. Two-fold increase in the intima thickness behind the necrotic core reduced the peak cap stress by approximately 25% for both intima models. For the soft intima models, cap thickness was less critical and changed the peak cap stress by 55%. However, the necrotic core thickness was more influential and changed the peak cap stress by 100%. The necrotic core angle emerged as a critical determinant of cap stresses where a larger angle lowered the cap stresses. Contrary to the stiff and intermediate intima models, a thicker intima behind the necrotic core increased the peak cap stress by approximately 25% for the soft intima models. Adventitia thickness and local media regression had limited effects for all three intima models.
For the stiff and intermediate intima models, the cap thickness was the most important morphological risk factor. However for soft intima models, the necrotic core thickness and necrotic core angle had a bigger impact on the peak cap stress. We therefore need to enhance our knowledge of intima material properties if we want to derive critical morphological plaque features for risk evaluation.
Atherosclerosis is a cardiovascular disease that is characterized by local thickening of the vessel wall, or plaque formation. A subset of atherosclerotic plaques, called vulnerable plaques, is characterized by lipid accumulation in the vessel wall, with a thin fibrous cap separating the necrotic core from the lumen (figure 1) . Rupture of the cap of a vulnerable plaque in a coronary artery is the underlying cause of the majority of acute myocardial infarctions and sudden coronary deaths [2, 3].
Rupture of a cap occurs when the mechanical stress in the cap exceeds its strength. The determinants of the stress distribution in a plaque are the loading conditions, the plaque geometry and the material properties of the plaque constituents. Variations in these factors affect the stress values and the stress distribution in the cap significantly. Therefore, detailed investigations of these features are essential to reveal biomechanical risk factors for plaque rupture.
The possible role of local mechanical stress as a predictor for plaque rupture [4–6] instigated many studies to explore the effects of various geometric plaque features on the cap stresses. Some studies concentrated on real plaque geometries obtained from intravascular ultrasound [7, 8], magnetic resonance [9, 10], or histology images [11–15] whereas others used idealized geometries [16–19]. The influence of the cap thickness has been investigated most extensively. In several computational studies, it was demonstrated that the stresses in the cap increase exponentially with decreasing cap thickness [8, 9, 18]. However, the large variation of cap thickness of ruptured plaques  indicates that cap thickness is not the only relevant geometric plaque feature. This was illustrated in a comprehensive parameter study by Ohayon et al. . They showed that the size of the necrotic core also has a significant influence on cap stresses, and speculated that the thickness of the lipid core may be as critical for plaque rupture as the cap thickness.
It is likely that besides cap thickness and necrotic core thickness, other geometric features play a role in plaque rupture. Structures behind the necrotic core, including intima, media and adventitia tissue, might influence cap stresses as well. These plaque components have diverse morphological structures. The thickness of the intima tissue can vary greatly. Some necrotic cores are separated from the media by a thick layer of tissue, while others almost touch the media (figure 1). The thickness of the media also shows great variation: at some locations, the media is severely compromised or even completely degraded (figure 1).
The material properties of plaque components are determined by their composition, which might vary greatly among different plaques. The intima tissue is especially heterogeneous: it consists of extracellular proteoglycan-rich matrix material, smooth muscle cells, inflammatory cells, collagen etc. . Since these components are present in different amounts in different plaques, the material properties of the intima tissue may vary greatly. Experimental studies on atherosclerotic plaque material properties have mostly reported high intima stiffness with the Young's moduli (E) between 500 kPa and 1000 kPa, even up to 2300 kPa [19, 21–26]; E = 1000 kPa has frequently been used in the numerical studies [7, 12, 18]. However, Lee et al. measured much lower E values: an average of 41 kPa for the nonfibrous and 82 kPa fibrous atherosclerotic intima tissues . This finding has been supported by a recent study that used an advanced testing method and reported a mean E value of 33 kPa.
The aim of our study was to investigate the influence of the variation of intima material properties and of geometric variations of different plaque components on cap stresses. A parametric study was carried out to explore the individual and combined effects of possible biomechanical determinants of plaque rupture.
Two dimensional (2D) idealized geometries of varying cap thickness, necrotic core thickness and angle, intima thickness behind the necrotic core, adventitia thickness, and local regression depth in the media tissue were generated to mimic the different geometric features of atherosclerotic plaque cross-sections. Different stiffness values for the intima were used in the models such that the stiffness range reported in literature [21, 22, 24–28] was covered to explore its influence on peak cap stress.
The symmetric idealized baseline geometry (figure 2.A) was constructed based on in vivo imaging studies [7, 18, 29–33] and morphometric analysis of histology images obtained from 10 atherosclerotic human coronaries. The structure comprises five different geometric components: cap, necrotic core, intima, media and adventitia. The cap was defined as the region of the intima separating the necrotic core and the lumen. By varying the geometric parameter values (Table 1), a large set of different 2D idealized plaque models was obtained. The lumen diameter was kept constant in all models. The thickness of each geometric component, except the media layer, was altered uniformly. The thickness of each geometric component, except the media layer, was altered uniformly. The media layer of an atherosclerotic plaque often shows local regression rather than uniform thinning. To model local media regression (figure 1, black arrows), the thickness of the media layer was reduced at the center or shoulder region (figure 2.B). The necrotic core angle was defined as given in figure 2.A.
Four different tissue types were used as plaque constituents: intima, necrotic core, media, and adventitia. Intima material properties were also applied to the cap. All tissue types were assumed to be incompressible and homogenous.
The neo-Hookean material model  was employed for the intima and necrotic core:
where W NH [N/m2] is the strain energy density function and I1 = λr 2+ λθ 2+ λz 2 is the first invariant with λr, λθ, and λz being the principal stretches in the radial, circumferential and axial directions. The only material constant in the model is C [N/m2]. For small deformations, C can be derived from the Young's modulus, E [N/m2], by
In the remainder of this paper, we will use Eqn. (2) and report E values to facilitate the comparison with E values in literature.
Since the intima can be relatively thick, the choice for its properties is especially important. To cover the wide intima stiffness range reported in literature, three different shear moduli for the intima were used in the current study: a high value (E = 1000 kPa)  to mimic stiff intima experimental results, a low value (E = 33 kPa)  for soft intima experimental results and an intermediate value (E = 500 kPa). The models generated using these three different intima stiffness values were labelled as stiff, intermediate and soft intima models. The isotropic neo-Hookean model was used for the intima since anisotropic, nonlinear material parameters for atherosclerotic human coronary intima are not available yet. The necrotic core was modelled as a very soft tissue (E = 1 kPa) .
For the media and adventitia, the anisotropic material model of Gasser et al. , which describes the strain energy density function for a composite material reinforced by two families of fibers, was used:
where μ, k1, k2 and κ Є [0,1/3] are the model parameters. The model parameter values were obtained by fitting the material model to the experimental human coronary data  with the help of MATLAB (R2006b, The Mathworks Inc.). I1 and I4 = λθ 2cos2φ+ λz 2sin2φ are invariants with φ being the angle between the fibers and circumferential direction in the individual layers. All material parameter values used in the present study are listed in Table 2.
The finite element analyses were performed with ABAQUS (Version 6.9.1, Dassault Systemes Simulia Corp., Providence, RI, USA). The models were meshed with three-node and four-node linear, hybrid elements. Element size was chosen such that at least 5 layers of elements were present in the cap layer. The models contained approximately 100k elements. Large deformation formulation and plane strain assumption, allowing for out of plane stress build up, were used for all computational models. Appropriate boundary conditions were used to suppress rigid body motion. Static intraluminal pressure of 15 kPa (~110 mmHg) was applied as the loading condition. Postprocessing of the simulations was performed with MATLAB. The peak von Mises stresses in the cap were computed for midcap and shoulder regions (figure 2.B) separately. The 99-percentile stress  was used as cap stress parameter and 1% of the highest stresses was excluded. Numerical simulations with finer meshes displayed negligible changes in the stress distribution.
An example of the numerical results is shown in figure 3 where the computed stress map of a plaque half cross-section is presented. The peak cap stresses in the models mainly occurred in the midcap region. However, the difference between the peak cap stresses in the shoulder region and the midcap was small and never exceeded 5%. Generally, the results for all simulations were identical when using maximum principal stresses instead of von Mises stresses. In the remaining part of the paper, only the peak stresses in the midcaps are presented. Overall, more than 1000 simulations were performed to evaluate single and combined effects of geometric plaque parameter variations for the three intima models. The geometric variation we investigated will be illustrated by discussing two relevant examples in detail (figure 4 and 5). The main findings are presented in Table 3 and will be summarized at the end of the section.
The influence of the cap thickness on peak cap stress for the three different intima models is shown in figure 4. For the baseline geometry, the peak cap stress for the soft intima changed non-linearly from 84 to 127 kPa (+50%) when the cap thickness decreased from 0.25 to 0.05 mm. The intermediate intima model showed the highest peak cap stress among the three intima models for all cap thickness values and the peak cap stress increased from 85 to 259 kPa (+205%) with decreasing cap thickness. For the stiff intima, the peak cap stress was slightly lower than the intermediate intima, increasing from 77 to 231 kPa (+200%). For the models with a thin cap, peak cap stress for the soft intima was lower than the stiff and intermediate intima models, while for the models with a thick cap, similar peak cap stresses were observed for all three intima models.
Thicker necrotic core elevated the peak cap stress as well (figure 5). For the soft intima, the peak cap stress was much lower than for the other two intima models irrespective of the necrotic core size. The stiff and intermediate models showed comparable results. For the soft intima, the peak cap stress increased almost linearly from 71 to 142 kPa (+100%), for the intermediate intima, from 156 to 296 kPa (+90%) and for the stiff intima, from 159 to 254 kPa (+60%) when the necrotic core thickness was varied from 0.6 to 1.4 mm in the baseline geometry.
The maximum effects of all varied geometric parameters on peak cap stress for different intima models are summarized in Table 3. Varying the necrotic core angle of the baseline geometry from 10° to 40°altered the peak cap stress by -6 for the stiff intima model and by -7% for the intermediate intima model. However, the change was -55% for the soft intima model. Due to change in the thickness of the intima layer behind the necrotic core from 0.3 to 0.7 mm, the peak cap stress decreased by 22% for the stiff intima model and 29% for the intermediate stiff model. By contrast, the peak cap stress was elevated by 27% for the soft intima model. For the stiff and intermediate intima models, change in the adventitia thickness from 0.1 to 0.2 mm had almost no effect on the peak cap stress (-1%) and for the soft intima model, the peak cap stress changed only by -5%. Local regression of the media layer did not change the peak cap stress more than 1% in any of the intima models studied (data not shown).
Insights into biomechanical factors that influence cap stresses of vulnerable plaques are important for rupture risk prediction. The morphology of an atherosclerotic plaque and the material properties of its components are important determinants of the stress distribution in the plaque cap. The present study showed that the stiffness of the intima of a plaque has a profound influence on the resulting cap stresses. It also revealed that, in addition to the thickness of the plaque cap and necrotic core, other morphological plaque features as necrotic core angle and intima thickness behind the necrotic core are of great importance for cap stresses.
The experimental studies reported stiffness values ranging from 30 kPa up to 2000 kPa for atherosclerotic intima [19, 21–26]. All previous computational studies used stiffness values in the upper range of the reported values for intima. In some studies [12, 13, 18] the impact of the material stiffness of intima on peak plaque stress has been investigated. However, even the lowest stiffness values in these papers were much higher than 30 kPa. Recent studies [28, 38] that focused on measuring the material properties of intima tissue have confirmed a previous study from Lee et al.  indicating that low stiffness values for the intima might be more appropriate. To the authors' knowledge, this is the first study that used intima stiffness values in the lower range of the reported experimental values [27, 28] and investigated how cap stresses are affected by intima stiffness.
For the stiff and intermediate intima models, the main load bearing plaque structure was the intima. Therefore, the stresses in the intima were higher than the stresses in the media and adventitia layers. For the soft intima models, the media and adventitia were relatively stiffer than the intima and contributed to supporting the overall load. Consequently, stresses in the media and adventitia increased while the ones in the intima and cap decreased. Hence, the soft intima models usually showed much lower peak cap stresses than the stiff and intermediate intima models.
Intima stiffness also altered the effects of geometric variations of the plaque morphology on peak cap stress. For the stiff and intermediate intima models, cap thickness was the most essential geometric plaque parameter within the investigated parameter range. A thinner cap elevated the peak cap stress dramatically, which is in line with the previous studies [8, 18, 39]. Necrotic core thickness was also an important geometrical feature, and an increase in the necrotic core thickness resulted in higher stresses, confirming the findings of Ohayon et al . Since the intima was the main load bearing structure, a thicker intima behind the necrotic core contained the deformation of the cap, thus the peak cap stress was reduced.
Since the media and adventitia were the load bearing structures for the soft intima models, the effect of reducing cap thickness was much less pronounced. The necrotic core thickness appeared to be the most influential morphological plaque parameter. A thicker intima layer increased the peak cap stress because deformations of the necrotic core and cap were much larger due to the larger soft intima behind the necrotic core. Furthermore, necrotic core angle emerged as an important geometric parameter in the soft intima models, being equally important as the cap thickness. This finding can be attributed to the difference of the circumferential length of the cap in the midcap region. We observed that the displacement of the central part of midcap region in radial direction was comparable for all the necrotic core angles. The length of the cap for smaller necrotic core angles was smaller than the length of the cap for the larger necrotic core angles. When subjected to comparable radial displacements, the smaller cap length for the smaller necrotic core angles induced higher strains and therefore higher stresses.
Plaque rupture is an interplay between the stress in the cap and local cap strength. To assess the risk of plaque rupture in clinical setting, both need to be determined. We showed that the stresses in the cap of a vulnerable plaque strongly depend on material properties of the intima and the geometric features of the individual plaque components. Currently, intima-media thickness (IMT) is used as a clinical measure to both detect and track the progression of atherosclerosis. IMT corresponds to the sum of the thickness values of the cap, necrotic core, intima behind the necrotic core, and media in the present study. IMT has been shown to correlate with the presence of coronary disease, and predict cardiovascular events , and a larger IMT was observed more in unstable angina patients than in the stable angina patients . However, we could not find any relation between IMT and peak cap stress in the current study (data not shown). The results of the current study support the need for more detailed quantitative imaging of the individual plaque components for stress assessment in coronary plaques. A combination of an intravascular ultrasound derived imaging technique  and optical coherence tomography (OCT)  could potentially provide the necessary quantitative geometric data for various plaque components, including cap thickness and necrotic core size. Rupture risk assessment also requires local information about cap strength. Several factors influence tissue strength, including local macrophage density . The presence of macrophages can be detected in vivo by means of OCT . Although further clinical validation of these advanced invasive imaging techniques is required, they might be combined in clinical imaging tools for rupture risk assessment.
One of the main limitations of the present study is the relatively simple material model that was used for the intima section. Anisotropic, nonlinear material properties found in literature were used for media and adventitia. However, intima tissue was assumed to be isotropic since no data is available for anisotropic material parameters for atherosclerotic human coronary intima. Atherosclerotic lesions are often highly complex structures with irregular geometries (figure 1). Due to the smooth tissue interfaces and component morphologies in the idealized geometries, no local stress concentrations were observed in this study. This explains the similar stress results in the shoulder and midcap region in contrast to some previous studies that used real plaque geometries [12, 13, 15]. However, the idealized geometries allowed isolating the effects of the investigated geometric features. In the current study, 2D models were used and stress results might be different than those of 3D models. However, Tang et al.  reported similar stress distribution maps for 2D and 3D finite elements models of atherosclerotic plaques. 2D models are easier to construct, require less computational effort, and are therefore effective for parametric analysis. Initial stresses were not incorporated in the computations. For the computations with realistic geometries, initial stresses should be taken into account since this leads to physiologically more realistic strains and stresses. It is likely that including initial stresses would not change the main findings of this study since idealized geometries were used and relative changes were evaluated. Residual stresses were not incorporated in the models either. Ohayon et al. showed that residual stresses in atherosclerotic plaques change stress values, but not the distribution within the structure . Thus, it is likely that incorporating residual stresses would not change the main findings of this study. Another limitation is that calcifications within atherosclerotic plaques were disregarded although they are present in atherosclerotic lesions . Although large calcifications might lower the plaque stresses , several studies have shown that microcalcification might induce local stress concentrations and elevations [48, 49]. If and how the impact of calcification on cap stresses is altered by intima stiffness and geometric features warrant further studies.
For the stiff and intermediate intima models, cap thickness was the most important morphological risk factor. For the soft intima models, necrotic core thickness and necrotic core angle had a bigger impact on peak cap stress. We therefore need to enhance our knowledge of intima material properties if we want to derive critical morphological plaque features for risk evaluation.
Schaar JA, Muller JE, Falk E, Virmani R, Fuster V, Serruys PW, Colombo A, Stefanadis C, Ward Casscells S, Moreno PR, et al.: Terminology for high-risk and vulnerable coronary artery plaques. Report of a meeting on the vulnerable plaque, June 17 and 18, 2003, Santorini, Greece. Eur Heart J 2004, 25: 1077–1082. 10.1016/j.ehj.2004.01.002
Falk E, Shah PK, Fuster V: Coronary plaque disruption. Circulation 1995, 92: 657–671.
Naghavi M, Libby P, Falk E, Casscells SW, Litovsky S, Rumberger J, Badimon JJ, Stefanadis C, Moreno P, Pasterkamp G, et al.: From vulnerable plaque to vulnerable patient: a call for new definitions and risk assessment strategies: Part I. Circulation 2003, 108: 1664–1672. 10.1161/01.CIR.0000087480.94275.97
Tang D, Teng Z, Canton G, Hatsukami TS, Dong L, Huang X, Yuan C: Local critical stress correlates better than global maximum stress with plaque morphological features linked to atherosclerotic plaque vulnerability: an in vivo multi-patient study. Biomed Eng Online 2009, 8: 15. 10.1186/1475-925X-8-15
Tang D, Teng Z, Canton G, Yang C, Ferguson M, Huang X, Zheng J, Woodard PK, Yuan C: Sites of rupture in human atherosclerotic carotid plaques are associated with high structural stresses: an in vivo MRI-based 3D fluid-structure interaction study. Stroke 2009, 40: 3258–3263. 10.1161/STROKEAHA.109.558676
Tang D, Yang C, Zheng J, Woodard PK, Saffitz JE, Petruccelli JD, Sicard GA, Yuan C: Local maximal stress hypothesis and computational plaque vulnerability index for atherosclerotic plaque assessment. Ann Biomed Eng 2005, 33: 1789–1801. 10.1007/s10439-005-8267-1
Ohayon J, Teppaz P, Finet G, Rioufol G: In-vivo prediction of human coronary plaque rupture location using intravascular ultrasound and the finite element method. Coron Artery Dis 2001, 12: 655–663. 10.1097/00019501-200112000-00009
Finet G, Ohayon J, Rioufol G: Biomechanical interaction between cap thickness, lipid core composition and blood pressure in vulnerable coronary plaque: impact on stability or instability. Coron Artery Dis 2004, 15: 13–20. 10.1097/00019501-200402000-00003
Tang D, Yang C, Zheng J, Woodard PK, Sicard GA, Saffitz JE, Yuan C: 3D MRI-based multicomponent FSI models for atherosclerotic plaques. Ann Biomed Eng 2004, 32: 947–960. 10.1023/B:ABME.0000032457.10191.e0
Kiousis D, Rubinigg S, Auer M, Holzapfel G: A methodology to analyze changes in lipid core and calcification onto fibrous cap vulnerability: The human atherosclerotic carotid bifurcation as an illustratory example. J Biomech Eng 2009, 131: 121002–121010. 10.1115/1.4000078
Lee RT, Schoen FJ, Loree HM, Lark MW, Libby P: Circumferential stress and matrix metalloproteinase 1 in human coronary atherosclerosis. Implications for plaque rupture. Arterioscler Thromb Vasc Biol 1996, 16: 1070–1073.
Cheng GC, Loree HM, Kamm RD, Fishbein MC, Lee RT: Distribution of circumferential stress in ruptured and stable atherosclerotic lesions. A structural analysis with histopathological correlation. Circulation 1993, 87: 1179–1187.
Williamson SD, Lam Y, Younis HF, Huang H, Patel S, Kaazempur-Mofrad MR, Kamm RD: On the sensitivity of wall stresses in diseased arteries to variable material properties. J Biomech Eng 2003, 125: 147–155. 10.1115/1.1537736
Huang H, Virmani R, Younis H, Burke AP, Kamm RD, Lee RT: The impact of calcification on the biomechanical stability of atherosclerotic plaques. Circulation 2001, 103: 1051–1056.
Richardson PD, Davies MJ, Born GV: Influence of plaque configuration and stress distribution on fissuring of coronary atherosclerotic plaques. Lancet 1989, 2: 941–944. 10.1016/S0140-6736(89)90953-7
Ohayon J, Finet G, Gharib AM, Herzka DA, Tracqui P, Heroux J, Rioufol G, Kotys MS, Elagha A, Pettigrew RI: Necrotic core thickness and positive arterial remodeling index: emergent biomechanical factors for evaluating the risk of plaque rupture. Am J Physiol Heart Circ Physiol 2008, 295: H717–727. 10.1152/ajpheart.00005.2008
Versluis A, Bank AJ, Douglas WH: Fatigue and plaque rupture in myocardial infarction. J Biomech 2006, 39: 339–347. 10.1016/j.jbiomech.2004.10.041
Loree HM, Kamm RD, Stringfellow RG, Lee RT: Effects of fibrous cap thickness on peak circumferential stress in model atherosclerotic vessels. Circ Res 1992, 71: 850–858.
Baldewsing RA, de Korte CL, Schaar JA, Mastik F, van der Steen AF: Finite element modeling and intravascular ultrasound elastography of vulnerable plaques: parameter variation. Ultrasonics 2004, 42: 723–729. 10.1016/j.ultras.2003.11.017
Virmani R, Kolodgie FD, Burke AP, Farb A, Schwartz SM: Lessons from sudden coronary death: a comprehensive morphological classification scheme for atherosclerotic lesions. Arterioscler Thromb Vasc Biol 2000, 20: 1262–1275.
Lee RT, Grodzinsky AJ, Frank EH, Kamm RD, Schoen FJ: Structure-dependent dynamic mechanical behavior of fibrous caps from human atherosclerotic plaques. Circulation 1991, 83: 1764–1770.
Loree HM, Grodzinsky AJ, Park SY, Gibson LJ, Lee RT: Static circumferential tangential modulus of human atherosclerotic tissue. J Biomech 1994, 27: 195–204. 10.1016/0021-9290(94)90209-7
Holzapfel GA, Sommer G, Regitnig P: Anisotropic mechanical properties of tissue components in human atherosclerotic plaques. J Biomech Eng 2004, 126: 657–665. 10.1115/1.1800557
Lendon CL, Davies MJ, Richardson PD, Born GV: Testing of small connective tissue specimens for the determination of the mechanical behaviour of atherosclerotic plaques. J Biomed Eng 1993, 15: 27–33. 10.1016/0141-5425(93)90089-H
Born GVR, Richardson PD: Mechanical properties of human atherosclerotic lesions. In Pathobiology of the Human Atherosclerotic Plaque. Edited by: Glagov S, Newman WP, Schaffa SA. New York: Springer Verlag New York, Inc; 1990:413–423.
Holzapfel GA, Sommer G, Gasser CT, Regitnig P: Determination of layer-specific mechanical properties of human coronary arteries with nonatherosclerotic intimal thickening and related constitutive modeling. Am J Physiol Heart Circ Physiol 2005, 289: H2048–2058. 10.1152/ajpheart.00934.2004
Lee RT, Richardson SG, Loree HM, Grodzinsky AJ, Gharib SA, Schoen FJ, Pandian N: Prediction of mechanical properties of human atherosclerotic tissue by high-frequency intravascular ultrasound imaging. An in vitro study. Arterioscler Thromb 1992, 12: 1–5.
Barrett SR, Sutcliffe MP, Howarth S, Li ZY, Gillard JH: Experimental measurement of the mechanical properties of carotid atherothrombotic plaque fibrous cap. J Biomech 2009, 42: 1650–1655. 10.1016/j.jbiomech.2009.04.025
Joshi AK, Leask RL, Myers JG, Ojha M, Butany J, Ethier CR: Intimal thickness is not associated with wall shear stress patterns in the human right coronary artery. Arterioscler Thromb Vasc Biol 2004, 24: 2408–2413. 10.1161/01.ATV.0000147118.97474.4b
Pessanha BS, Potter K, Kolodgie FD, Farb A, Kutys R, Mont EK, Burke AP, O'Leary TJ, Virmani R: Characterization of intimal changes in coronary artery specimens with MR microscopy. Radiology 2006, 241: 107–115. 10.1148/radiol.2411042201
Gradus-Pizlo I, Bigelow B, Mahomed Y, Sawada SG, Rieger K, Feigenbaum H: Left anterior descending coronary artery wall thickness measured by high-frequency transthoracic and epicardial echocardiography includes adventitia. Am J Cardiol 2003, 91: 27–32. 10.1016/S0002-9149(02)02993-4
von Birgelen C, Klinkhart W, Mintz GS, Papatheodorou A, Herrmann J, Baumgart D, Haude M, Wieneke H, Ge J, Erbel R: Plaque distribution and vascular remodeling of ruptured and nonruptured coronary plaques in the same vessel: an intravascular ultrasound study in vivo. J Am Coll Cardiol 2001, 37: 1864–1870. 10.1016/S0735-1097(01)01234-7
Virmani R, Burke AP, Farb A, Kolodgie FD: Pathology of the vulnerable plaque. J Am Coll Cardiol 2006, 47: C13–18. 10.1016/j.jacc.2005.10.065
Holzapfel GA: Nonlinear solid mechanics: a continuum approach for engineering. Chichester; New York: Wiley; 2000.
Loree HM, Tobias BJ, Gibson LJ, Kamm RD, Small DM, Lee RT: Mechanical properties of model atherosclerotic lesion lipid pools. Arterioscler Thromb 1994, 14: 230–234.
Gasser TC, Ogden RW, Holzapfel GA: Hyperelastic modelling of arterial layers with distributed collagen fibre orientations. J R Soc Interface 2006, 3: 15–35. 10.1098/rsif.2005.0073
Speelman L, Bosboom EM, Schurink GW, Hellenthal FA, Buth J, Breeuwer M, Jacobs MJ, van de Vosse FN: Patient-specific AAA wall stress analysis: 99-percentile versus peak stress. Eur J Vasc Endovasc Surg 2008, 36: 668–676. 10.1016/j.ejvs.2008.09.007
Tracqui P, Broisat A, Toczek J, Mesnier N, Ohayon J, Riou L: Mapping elasticity moduli of atherosclerotic plaque in situ via atomic force microscopy. J Struct Biol 2011, 174: 115–123. 10.1016/j.jsb.2011.01.010
Kumar RK, Balakrishnan KR: Influence of lumen shape and vessel geometry on plaque stresses: possible role in the increased vulnerability of a remodelled vessel and the "shoulder" of a plaque. Heart 2005, 91: 1459–1465. 10.1136/hrt.2004.049072
Corrado E, Rizzo M, Coppola G, Fattouch K, Novo G, Marturana I, Ferrara F, Novo S: An update on the role of markers of inflammation in atherosclerosis. J Atheroscler Thromb 17: 1–11.
Chen WQ, Zhang M, Ji XP, Ding SF, Zhao YX, Chen YG, Zhang C, Zhang Y: Usefulness of high-frequency vascular ultrasound imaging and serum inflammatory markers to predict plaque rupture in patients with stable and unstable angina pectoris. Am J Cardiol 2007, 100: 1341–1346. 10.1016/j.amjcard.2007.06.044
Nair A, Kuban BD, Tuzcu EM, Schoenhagen P, Nissen SE, Vince DG: Coronary plaque classification with intravascular ultrasound radiofrequency data analysis. Circulation 2002, 106: 2200–2206. 10.1161/01.CIR.0000035654.18341.5E
Jang IK, Tearney GJ, MacNeill B, Takano M, Moselewski F, Iftima N, Shishkov M, Houser S, Aretz HT, Halpern EF, Bouma BE: In vivo characterization of coronary atherosclerotic plaque by use of optical coherence tomography. Circulation 2005, 111: 1551–1555. 10.1161/01.CIR.0000159354.43778.69
Lendon CL, Davies MJ, Born GV, Richardson PD: Atherosclerotic plaque caps are locally weakened when macrophages density is increased. Atherosclerosis 1991, 87: 87–90. 10.1016/0021-9150(91)90235-U
Tearney GJ, Yabushita H, Houser SL, Aretz HT, Jang IK, Schlendorf KH, Kauffman CR, Shishkov M, Halpern EF, Bouma BE: Quantification of macrophage content in atherosclerotic plaques by optical coherence tomography. Circulation 2003, 107: 113–119. 10.1161/01.CIR.0000044384.41037.43
Tang D, Yang C, Mondal S, Liu F, Canton G, Hatsukami TS, Yuan C: A negative correlation between human carotid atherosclerotic plaque progression and plaque wall stress: in vivo MRI-based 2D/3D FSI models. J Biomech 2008, 41: 727–736. 10.1016/j.jbiomech.2007.11.026
Ohayon J, Dubreuil O, Tracqui P, Le Floc'h S, Rioufol G, Chalabreysse L, Thivolet F, Pettigrew RI, Finet G: Influence of residual stress/strain on the biomechanical stability of vulnerable coronary plaques: potential impact for evaluating the risk of plaque rupture. Am J Physiol Heart Circ Physiol 2007, 293: H1987–1996. 10.1152/ajpheart.00018.2007
Bluestein D, Alemu Y, Avrahami I, Gharib M, Dumont K, Ricotta JJ, Einav S: Influence of microcalcifications on vulnerable plaque mechanics using FSI modeling. J Biomech 2008, 41: 1111–1118. 10.1016/j.jbiomech.2007.11.029
Hoshino T, Chow LA, Hsu JJ, Perlowski AA, Abedin M, Tobis J, Tintut Y, Mal AK, Klug WS, Demer LL: Mechanical stress analysis of a rigid inclusion in distensible material: a model of atherosclerotic calcification and plaque vulnerability. Am J Physiol Heart Circ Physiol 2009, 297: H802–810. 10.1152/ajpheart.00318.2009
This project was funded by The Medical Delta grant HST Klein.
The authors declare that they have no competing interests.
Study design: ACA, LS, HB, MAG, RV, AL, AFWS, JJW, FHG
Computations: ACA, LS, FHG
Data analysis and interpretation: ACA, LS, JJW, FHG
Manuscript preparation: ACA, LS, JJW, FHG
Manuscript editing: ACA, LS, HB, MAG, RV, AL, AFWS, JJW, FHG
Manuscript revision: ACA, LS, HB, MAG, RV, AL, AFWS, JJW, FHG
All authors read and approved the final version of the manuscript.