Local critical stress correlates better than global maximum stress with plaque morphological features linked to atherosclerotic plaque vulnerability: an in vivo multi-patient study
© Tang et al; licensee BioMed Central Ltd. 2009
Received: 30 May 2009
Accepted: 3 August 2009
Published: 3 August 2009
It is believed that mechanical stresses play an important role in atherosclerotic plaque rupture process and may be used for better plaque vulnerability assessment and rupture risk predictions. Image-based plaque models have been introduced in recent years to perform mechanical stress analysis and identify critical stress indicators which may be linked to rupture risk. However, large-scale studies based on in vivo patient data combining mechanical stress analysis, plaque morphology and composition for carotid plaque vulnerability assessment are lacking in the current literature.
206 slices of in vivo magnetic resonance image (MRI) of carotid atherosclerotic plaques from 20 patients (age: 49–71, mean: 67.4; all male) were acquired for model construction. Modified Mooney-Rivlin models were used for vessel wall and all plaque components with parameter values chosen to match available data. A morphological plaque severity index (MPSI) was introduced based on in vivo plaque morphological characteristics known to correlate with plaque vulnerability. Critical stress, defined as the maximum of maximum- principal-stress (Stress-P1) values from all possible vulnerable sites, was determined for each slice for analysis. A computational plaque stress index (CPSI, with 5 grades 0–4, 4 being most vulnerable) was defined for each slice using its critical stress value and stress interval for each CPSI grade was optimized to reach best agreement with MPSI. Correlations between CPSI and MPSI, plaque cap thickness, and lipid core size were analyzed.
Critical stress values correlated positively with lipid core size (r = 0.3879) and negatively with cap thickness (r = -0.3953). CPSI classifications had 71.4% agreement with MPSI classifications. The Pearson correlation coefficient between CPSI and MPSI was 0.849 (p < 0.0001). Using global maximum Stress-P1 value for each slice to define a global maximum stress-based CPSI (G-CPSI), the agreement rate with MPSI was only 34.0%. The Pearson correlation coefficient between G-CPSI and MPSI was 0.209.
Results from this in vivo study demonstrated that localized critical stress values had much better correlation with plaque morphological features known to be linked to plaque rupture risk, compared to global maximum stress conditions. Critical stress indicators have the potential to improve image-based screening and plaque vulnerability assessment schemes.
Atherosclerotic plaques may rupture without warning and cause acute cardiovascular syndromes such as heart attack and stroke. Currently, screening and diagnosis of patients with atherosclerotic plaques are based on medical images such as magnetic resonance image (MRI), ultrasound, intravascular ultrasound (IVUS), or computerized tomography (CT). Increasing evidences showed that such image-only screening and diagnostic techniques are insufficient to identify those victims before the event occurs [1, 2]. It has been hypothesized that mechanical forces (rupture triggers) play an important role in plaque rupture process and should be considered in an integrated way with plaque morphology and composition for possible improvement of plaque assessment schemes . Large-scale studies based on in vivo patient data combining mechanical stress analysis, plaque morphology and compositions are needed to identify the critical stress indicators that are linked to plaque vulnerability.
In recent years, MRI techniques have shown their ability to non-invasively determine plaque size, shape and component [4–6]. Yuan et al. developed multi-contrast techniques to improve the quality of MR-images and to better differentiate various components of the plaque [4, 6]. Attempts of using ultrasound and IVUS techniques have been made to quantify vessel motion, mechanical properties and vessel wall structure, even to predict rupture locations [7, 8]. Using non-invasive MRI techniques, Cai et al. developed a classification system for carotid plaques based on in vivo MRI . MRI- and histology-based computational simulations for plaque rupture investigation and vulnerability assessment have been conducted by several groups and many interesting and significant results have been reported [10–24]. Holzapfel et al. introduced multi-layer 3D models for the simulation of balloon angioplasty using MRI and direct mechanical testing . Steinman studied influence of complex vessel geometry on flow behaviors using image-based realistic arterial geometries . Weinbaum et al. investigated critical stress behaviors at plaque cap with micro-calcification inclusions and elevated stress levels were observed . Bluestein et al. introduced fluid-structure interaction models to study influence of microcalcifications on vulnerable plaque mechanics . Li et al. showed that wall stress calculated based on in vivo MRI of carotid arteries was higher in symptomatic patients than in asymptomatic patients . Groen and Wentzel et al. reported a follow-up case study showing high flow shear stress region was associated with site of plaque rupture . Tang et al. introduced a "local maximum stress hypothesis" to identify the critical site and stress conditions in the plaque and proposed an ex vivo MRI-based computation plaque vulnerability index (CPVI) to access plaque vulnerability . Results from 34 2D ex vivo MRI slices from 14 human atherosclerotic coronary arteries indicated that CPVI has a good agreement (89%) with histology-based assessment.
Most of the current computational studies were at model development stage using one or a few samples. Large-scale in vivo MRI-based plaque mechanical analysis is lacking in the current literature. Due to the complexity of plaque architecture, analyzing the large amount of computational stress/strain data and identifying critical stress indicators which correlate closely with plaque vulnerability are time-consuming and challenging. A validated easy-to-use stress index would be more practical for potential patient screening and clinical applications.
In this paper, we extend our previous ex vivo study to an in vivo MRI-based multi-patient study to further validate that it is the localized critical stress conditions, not global maximum stress conditions, that have better correlations with plaque morphological features known to be linked to plaque vulnerability. A morphological plaque severity index (MPSI) and a computational plaque stress index (CPSI) were introduced for plaque classification and comparison. Correlations between CPSI and MPSI, plaque cap thickness, and lipid core size were quantified.
MRI data, method and model
MRI Data Acquisition
Assignment of Morphological Plaque Severity Index (MPSI)
Morphological plaque vulnerability index (MPSI) classifications and comparison with AHA classifications
Corresponding AHA lesion types (modified)
Level of vulnerability
I or II
Normal or nearly normal wall.
Moderate intimal thickening, no extracellular lipid, calcification or significant inflammation.
IV/V with less than 30% NC by area; or VII; or VIII
Advanced lesion with small necrotic core (<30% of plaque size), or can be fibrotic or calcified, thick fibrous cap (> 200 μm).
IV/V with 30–40% NC by area
Advanced lesion with Moderate lipid core (30–40% of plaque size) and fibrous cap (150–200 μm).
IV/V with > 40% NC by area; or VI
Advanced lesion with a very large necrotic core (>40%), thin fibrous cap (<150 μm), or with fibrous cap rupture, ulceration, or intraplaque hemorrhage.
Case distributions according to MPSI and agreement rate between CPSI and MPSI
Number of Slices
Agreement Rate (%)
A Pre-Shrink Process for In Vivo Data
The In vivo imaged arteries were under physiological pressure conditions. Therefore a pre-shrink process was necessary to obtain the zero-pressure geometry, which was used as the numerical starting geometry, and to recover the in vivo geometry when pressure was imposed in the lumen. In this study, for each patient, the shrinkage was determined by choosing the most circular (round) slice which would recover its in vivo shape best when lumen pressure was imposed. The shrinkage rates of contours of lumen (δin) and outer wall (δout) were numerically determined following an iterative procedure so that: 1) the vessel cross-section area was conserved (conservation of mass); and 2) the pressurized morphology and the original in vivo morphology had the best agreement. The determined shrinkage was applied to all the slices of this patient for consistency and uniformity and for future comparison with 3D models. This approach was chosen also because slice-specific shrinkage data would not be available in patient-screening practice. The average inner circumference shrinkage rate (δin) was 12% (SD ± 2.2%) for the 206 2D models.
Mesh Generation, Computational Models and Solution Methods
where σ is stress tensor (superscripts indicate different materials), ε is strain tensor, v is solid displacement vector, superscript letters "r" and "s" were used to indicate different materials. No-slip conditions and natural traction equilibrium conditions are assumed at all interfaces. For simplicity, all material densities were set to 1 g·cm-3 in this paper.
where I1 and I2 are the first and second invariants, C = [Cij] = XTX is the right Cauchy-Green deformation tensor, X = [Xij] = [∂xi/∂aj], (xi) is the current position, (ai) is the original position. Material parameters c i and D i (i = 1,2) were chosen to match available experimental measurement data [12, 14, 23]: vessel material/fibrous cap, c1 = 36.8 kPa, D1 = 14.4 kPa, D2 = 2; lipid core/hemorrhage, c1 = 2 kPa, D1 = 2 kPa, D2 = 1.5; calcification, c1 = 368 kPa, D1 = 144 kPa, D2 = 2.0; loose matrix, c1 = 18.4 kPa, D1 = 7.2 kPa; D2 = 1.5. c2 = 0 for all materials. A pulsating pressure was imposed in the lumen using the systolic/diastolic arm pressure data for each patient from their last hospital admission. Average systolic and diastolic pressures were 144.7 ± 21.5 and 75.6 ± 13.5 mmHg respectively, for the 20 patients studied. Pressure at the out-boundary of each vessel slice was set to zero.
The computational plaque models were solved using ADINA which uses unstructured finite element methods, nonlinear incremental iterative procedures and the Newton-Raphson iteration method to deal with complex geometries and nonlinear systems. Details of the models and methods are given in Tang et al.  and Bathe .
Definition and Calculation of Critical Stress
Critical stress was defined as the maximum of all local maximum Stress-P1 values from possible vulnerable sites. It is known that thin plaque cap is closely related to plaque rupture. Thus vulnerable sites include all locations where a thin region covers a plaque component and a local maximum Stress-P1 was found. It should be noted that our "thin region" includes fibrous cap over a lipid core, as well as "cap" over calcification and other plaque components. Healthy sites where no plaque components were present and rupture was unlikely were excluded from the "vulnerable site list", even if a local stress maximum occurred there. For each slice, Stress-P1 distribution corresponding to peak pressure condition was obtained from the 2D computational model. An automatic search was performed to find all local maximum Stress-P1 values from vulnerable sites. Then critical stress for that slice was determined using the definition given above. The site where critical stress was found was defined as the critical site. For slices without any components, critical stress was set to zero since these slices are assumed to be very stable.
CPSI Assignment, Quantitative Definition of Morphological Features and Data Analysis
Correlations between CPSI values and MPSI, plaque cap thickness, normalized lipid index and normalized wall index were analyzed. Global maximum Stress-P1values for each slice were also recorded for comparison and correlation analyses.
Correlations between Critical Stress and Cap Thickness, Normalized Lipid Index and Plaque Burden
Correlation between CPSI and MPSI
A simple numerical code was used to determine five equal stress intervals [0, a), [a, 2a), [2a, 3a), [3a, 4a), and [4a, +8) corresponding to CPSI values 0–4 to reach the best agreement between CPSI and MPSI. The five intervals (unit: KPa) [0, 35.5), [35.5, 71), [71, 106.5), [106.5, 142), and [142, +8) were used for CPSI values of 0, 1, 2, 3 and 4, respectively. The optimized agreement rate was 71.4% (147 matching cases out of 206). The Pearson correlation coefficient between CPSI and MPSI was 0.849 (p < 0.0001). Table 2 lists number of cases and agreement rate for each MPSI grade group. The agreement rate was 82.6% for the highly vulnerable group (MPSI = 4). According to the CPSI stress intervals, a plaque will be considered highly vulnerable (high risk) if its critical stress is higher than 142 kPa.
Correlation between an Index Based on Global Maximum Stress-P1 Values and MPSI
Purpose of Introducing Localized Critical Stress Indicator and CPSI
The purpose of introducing the localized critical stress indicator and CPSI index is to identify stress indicators which are more closely linked to plaque vulnerability, compared to global maximum stress conditions. The critical-stress based CPSI provides a plaque classification and assessment scheme which includes mechanical factors, plaque morphological features and tissue compositions for possible patient-screening applications. A 5-point scale (CPSI = 0, 1, 2, 3, and 4) was used so that the CPSI-based classifications would be comparable with AHA plaque classification scheme (Table 1). One main potential advantage for introducing CPSI is that it can provide quantitative assessment of plaques, compared to the current qualitative AHA scheme. More refined scales using decimals may be introduced to provide more quantitative assessment. Results from 206 slices suggested that CPSI and MPSI had a good agreement on plaque classification. Global maximum stress values showed much weaker correlation with MPSI, suggesting that localized critical stress may be a better indicator for plaque vulnerability.
The disagreement (28.6% overall, 17.4% for high risk plaques) suggested that CPSI scheme may complement image-only assessment schemes and lead to potential improvements. The present study is the first large-scale (n = 206) case study quantifying differences between mechanics-image combined and morphology-only assessment schemes. In Table 2, the worst match between CPSI and MPSI is in the scale of 1–3. This range of plaque represents the moderate stenosis, but with high risk for future plaque rupture. In fact, this class of plaque is the most interesting plaque that is often ignored in clinical practices. Developing some biomarker to identify the risk of these plaques would be great benefit for clinicians. CPSI could serve as such a biomarker providing additional mechanical stress information for image-based plaque assessment schemes.
It should be understood that plaque rupture is a multi-faceted process. CPSI covers only mechanical and morphological factors. We hope CPSI could provide complementing information for plaque assessment that image alone could not provide. Multiple biomarkers from different channels such as cell activity, lumen surface condition and inflammation should be jointly considered for more complete and accurate vulnerability assessment.
2D vs. 3D Models and Model limitation
Several other limitations exist in this study: a) Patient-specific material properties were not included because data was not available with current technology; b) some important factors such as lumen surface inflammation and erosion conditions were not taken into account since current in vivo MRI technology could not accurately provide these data; c) residual stress (opening angle) was not included in our model; d) the CPSI cannot well estimate the risk of cases with very narrow lumen and thick fibrous cap but having large lipid core and other components. Accuracy of CPSI could be improved with accurate cap thickness and material property measurements.
Results from this multi-patient in vivo study based on 206 slices demonstrated that localized critical stress values had much better correlation with plaque morphological features known to be linked to plaque rupture risk (r = 0.849 with MPSI), compared to global maximum stress conditions (r = 0.209 with MPSI). Critical stress values correlated positively with normalized lipid index (r = 0.3879) and negatively with cap thickness (r = -0.3953). Large scale and long-term patient studies using 3D models are needed to further validate our findings and identify potential stress risk indicators for patient screening plaque vulnerability assessment.
Tang's group has been publishing image-based modeling work in recent years. For more information, please visit Tang's website: http://users.wpi.edu/~dtang/. Dr. Yuan's group and their lab (Vascular Imaging Laboratory, University of Washington) have been developing MR imaging methods and have published extensively in this area. For more information, please visit their website: http://www.rad.washington.edu/research/our-research/groups/vil.
This research was supported in part by NSF grant DMS-0540684 and NIH grant R01 EB004759. Many helpful discussions with Dr. William Kerwin and Ms. Marina Ferguson are happily acknowledged.
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