Quantitative Intracranial Atherosclerotic Plaque Characterization at 7T MRI: An Ex Vivo Study with Histologic Validation

Abstract

BACKGROUND AND PURPOSE:

In recent years, several high-resolution vessel wall MR imaging techniques have emerged for the characterization of intracranial atherosclerotic vessel wall lesions in vivo. However, a thorough validation of MR imaging results of intracranial plaques with histopathology is still lacking. The aim of this study was to characterize atherosclerotic plaque components in a quantitative manner by obtaining the MR signal characteristics (T1, T2, T2*, and proton density) at 7T in ex vivo circle of Willis specimens and using histopathology for validation.

MATERIALS AND METHODS:

A multiparametric ultra-high-resolution quantitative MR imaging protocol was performed at 7T to identify the MR signal characteristics of different intracranial atherosclerotic plaque components, and using histopathology for validation. In total, 38 advanced plaques were matched between MR imaging and histology, and ROI analysis was performed on the identified tissue components.

RESULTS:

Mean T1, T2, and T2* relaxation times and proton density values were significantly different between different tissue components. The quantitative T1 map showed the most differences among individual tissue components of intracranial plaques with significant differences in T1 values between lipid accumulation (T1 = 838 ± 167 ms), fibrous tissue (T1 = 583 ± 161 ms), fibrous cap (T1 = 481 ± 98 ms), calcifications (T1 = 314 ± 39 ms), and the intracranial arterial vessel wall (T1 = 436 ± 122 ms).

CONCLUSIONS:

Different tissue components of advanced intracranial plaques have distinguishable imaging characteristics with ultra-high-resolution quantitative MR imaging at 7T. Based on this study, the most promising method for distinguishing intracranial plaque components is T1-weighted imaging.

Ischemic stroke is one of the major diseases in the Western world, associated with high morbidity and mortality.^1,2 Identifying the cause of ischemic stroke is of great clinical importance, not only for deciding the best treatment options for the individual patient but also for possibly preventing future ischemic events, both recurrent and new.

Intracranial atherosclerosis is one of the main causes of ischemic stroke and TIA worldwide, accounting for approximately 9%–33% of all ischemic strokes and TIAs (depending on race-ethnicity) and is the major cause of cerebral ischemic events in the Asian population. Additionally, the risk of recurrent ischemic stroke is increased in patients with underlying intracranial atherosclerosis.^3–8 Similar to extracranial atherosclerosis, for intracranial atherosclerosis, the degree of luminal stenosis is currently the main factor determining whether an atherosclerotic plaque is symptomatic and/or treatment is necessary. In the past decade, plaque composition has become an additional important feature in extracranial atherosclerosis management, enabling identification of specific culprit lesions requiring treatment, even when not causing significant stenosis.^9–12 However, for intracranial atherosclerosis, this is not yet common practice, even though the literature suggests that also intracranially, stenosis grade is not always associated with a risk of ischemic events: In patients with a high-grade stenosis, only 1 in every 5–10 patients will have a recurrent ischemic stroke.^5,6,13,14 This implies that like in extracranial atherosclerosis, luminal information is not the only important marker for future cerebrovascular events.

In recent years, several high-resolution intracranial vessel wall imaging techniques using 3T and 7T MR imaging have emerged for the evaluation and characterization of atherosclerotic vessel wall lesions in vivo.¹⁵ However, these in vivo techniques so far have not been validated with histopathology, due to poor accessibility of the intracranial arteries. Therefore, the question arises if these techniques are truly able—ie, have enough image contrast—to distinguish different atherosclerotic plaque components. In the past 2 years, 2 ex vivo correlation studies have been performed at 7T MR imaging to assess its ability to visualize different intracranial atherosclerotic plaque components.^16,17 These ex vivo studies showed that 7T MR imaging is capable of identifying focal thickening of the intracranial arterial vessel wall and distinguishing different plaque components within advanced intracranial atherosclerotic plaques with different image contrast weightings. Recently, a first case report was published demonstrating the correlation between certain intracranial atherosclerotic plaque components visualized in vivo at 3T and histologic validation of the plaque postmortem.¹⁸ Those studies used qualitative MR images to score the atherosclerotic plaque signal heterogeneities. As a next step toward validation, quantitative assessment of MR signal characteristics of specific plaque components might enable more firm conclusions regarding the ability of T1-, T2-, T2*-, and proton density (PD)-weighted sequences in characterizing intracranial atherosclerotic plaques. Once it is known which plaque components can be identified with ex vivo MR imaging sequences, a translation can be made to in vivo intracranial vessel wall MR imaging, by developing sequences based on the nuclear magnetic resonance tissue properties of the identified atherosclerotic plaque components. In the current study, a multiparametric ultra-high-resolution quantitative MR imaging protocol was performed to identify the MR signal characteristics of different intracranial atherosclerotic plaque components, and using histopathology for validation.

Materials and Methods

Specimens

Human circle of Willis (CoW) specimens with a macroscopic presence of high atherosclerotic plaque burden were selected by an experienced pathologist (A.V.) from >100 postmortem examinations that were performed in our institution. Material was handled in a coded manner that met the criteria of the Code of Conduct used in the Netherlands for the responsible use of human tissue in medical research (www.federa.org/codes-conduct), and institutional review board approval for this retrospective study was obtained.

Specimen Preparation

All specimens had been stored in buffered formalin (4%). Preparation of the specimens for MR imaging and histologic sampling was performed according to the method previously described by van der Kolk et al.¹⁶ Cactus spines were used as fiducials and placed at 15 locations in the agarose gel adjacent to an artery for histologic sampling, to enable spatial correlation with histology. The 15 locations were chosen to sample all major vessels of the CoW, including their branches (eg, A2 segment of the anterior cerebral artery), and the fiducials were placed at the location of a visible vessel wall abnormality (if present). The locations included the following: the anterior cerebral (A1 and A2 segments), middle cerebral (M1 segment), intracranial internal carotid (C7 segment), posterior cerebral (P2 segment), basilar (upper, middle, and lower part), and vertebral arteries (left and right if applicable).

Imaging

The embedded specimens were scanned in a 7T whole-body system (Achieva; Philips Healthcare, Best, the Netherlands). A custom-made high density receive coil (16 channels per 70 cm²; High density surface array; MR Coils BV, Drunen, the Netherlands) was used for signal reception,¹⁹ and a volume transmit/receive coil, for transmission (Quad TR; Nova Medical, Wilmington, Massachusetts). Each embedded specimen was imaged individually. The petri dish containing the embedded specimen was placed in the middle of the transmit coil on top of the receive coil; plastic filling was used to stabilize and secure the petri dish.

Protocol

Imaging was performed at room temperature. The scan protocol had 3 sequences with different contrast weightings to image the specimens, from which quantitative MR parameter maps were calculated. For T1, T2, and PD mapping, the driven equilibrium single pulse observation of T1 (DESPOT1) and T2 (DESPOT2) sequences were used.²⁰ TR was chosen as short as allowed by the desired spatial resolution and FOV. We calculated optimal flip angle pairs for the DESPOT1 and DESPOT2 scans, assuming a range of T1 and T2 values of 150–650 ms and 10–30 ms, respectively. T2* maps were obtained by using a dual-echo 3D T2*-weighted scan. The applied scan parameters are presented in Table 1. A 3D B₁ map was acquired by using the actual flip angle method to correct for B₁ inhomogeneity during postprocessing of the MR images.²¹ Total scan time was approximately 19.5 hours per specimen. All MR images were acquired with an isotropic resolution. This allowed reconstructions along arbitrary planes, which enabled accurate matching of the MR images to the sectioning plane of the histologic sections.

Table 1:

Scan parameters of the 7T MRI protocol

Pulse Sequence	DESPOT1	DESPOT2	T2* Map
TR/TE1/TE2 (ms)	16/4.3/–	36/18/–	53/6/26
Flip angle	11°/44°	12°/62°	29°
No. of sections	153	153	153
FOV (mm)	150 × 150 × 20	150 × 150 × 20	150 × 150 × 20
Acquisition matrix	1152 × 1154	1152 × 1152	1152 × 1154
Acquired voxel size (mm)	0.13 × 0.13 × 0.13	0.13 × 0.13 × 0.13	0.13 × 0.13 × 0.13
Bandwidth (Hz/pixel)	165	41	101
TFE factor	1154	1152	1154
Repeated scans	4	3	1
Acquisition time	06 hr 21 min 28 sec	11 hr 07 min 34 sec	02 hr 00 min 53 sec

Note:—TFE indicates turbo field echo.

MR Image Processing

The MR images were processed by using Matlab, Version R2014b (MathWorks, Natick, Massachusetts). First, the DESPOT1 and DESPOT2 dynamic scans were coregistered to correct for small shifts between the matching images. Next, the parametric images (T1, T2, T2* relaxation times and PD values) were calculated from the original MR imaging datasets according to the method previously described by Deoni et al.²⁰ B₁ correction was performed during calculation of the parametric T1 and T2 maps, to correct for B₁ inhomogeneity within the specimen.

Histopathology

After MR imaging, 0.5-mm-thick tissue samples were taken from the 15 marked locations of each CoW specimen for histologic processing, which was performed by using an in-house-developed protocol, as previously described.¹⁶ Classification of the histologic sections was performed according to the modified American Heart Association classification by Virmani et al,²² a well-established method that is based on atherosclerotic characteristics as follows: 1) no anomaly; 2) early lesion, including intimal thickening (<50% smooth-muscle cells, no lipids, inflammatory cells), fatty streak, and pathologic intimal thickening (>50% smooth-muscle cells, rich in proteoglycans, foamy macrophages); and 3) advanced lesion, including fibrolipid plaque (>40% lipid), thin cap atheroma (<65-μm thickness), fibrous plaque (<40% lipid), fibrocalcified plaque (>40% calcified), and calcified nodule (calcified element protruding the intima). When applicable, plaque complications (rupture, hemorrhage, or erosion) were also assessed. The histologic classification was performed by 1 experienced observer (N.P.D.), blinded to the MR imaging results.

Matching of MR and Histology Images

Image reconstructions were made perpendicular to the relevant arteries (section thickness, 0.13 mm) at the locations of the fiducials seen on the MR images, by using the software program VesselMASS (Leiden University Medical Center, Leiden, the Netherlands). The MR images and the histologic sections were manually matched by 1 observer (A.A.H.) by using the marked locations with the fiducials in the MR images, the ink markings in the histologic sections, and gross morphologic features. Samples were excluded when no match was found or when air bubbles were present in the MR images.

Plaque Component Analysis

To analyze different plaque components, we used only plaques histologically scored as advanced, therefore including several components, because a previous study showed no heterogeneity in qualitative signal intensity in early lesions.¹⁶ The identified plaque components included fibrous tissue, fibrous cap, lipid accumulation (increasing mass of lipids [lipid retention] within the intimal area, which is defined as the “plaque”), intraplaque hemorrhage, and calcifications (deposition of extracellular calcium within the plaque). On the basis of the identified plaque components in a histologic section, ROIs were drawn manually within the corresponding regions on T1-weighted MR images (DESPOT1 acquired with a flip angle of 44°, used for calculation of the quantitative maps) by 1 observer (A.A.H.). The ROIs were used to calculate the mean T1, T2, and T2* relaxation times and PD values for those regions in the MR parameter maps, by using the dedicated vessel wall analysis software VesselMASS.

Statistical Analysis

All statistical analyses were performed by using SPSS statistics (Version 20.0; IBM, Armonk, New York). Because the data were normally distributed but the assumption of homogeneity of variance was not met, the Welch test was conducted to compare the mean ROI values of the different tissue components. Games-Howell post hoc tests were performed for pair-wise comparisons. A P value < .05 was statistically significant.

Results

Fifteen CoW specimens were selected for this study (9 men; mean age, 68.7 ± 13.3 years). In total, 213 samples of CoW arteries were obtained (in 8 specimens, ≥1 vessel segment was absent; n = 12 vessel segments); 8 of the 213 samples (3.8%) were excluded because they were not assessable for histologic classification (the samples could not be sliced properly), resulting in 205 samples available for histologic classification.

Histologic Classification

Six samples (2.9%) were scored as nondiseased; 143 samples (69.8%) showed early lesions (intimal thickening, n = 97, pathologic intimal thickening, n = 19, and fatty streak, n = 27); and 56 samples (27.3%) showed advanced plaques (fibrous plaque, n = 28, fibrolipid plaque, n = 25, and fibrocalcified plaque, n = 3). No calcified nodules or thin cap atheromas were seen. Of the 56 advanced plaques, 18 (32%) were excluded due to lack of a match (n = 3) or an air bubble present in the MR images (n = 15), resulting in 38 MR imaging–matched advanced atherosclerotic plaques (20 fibrous plaques, 16 fibrolipid plaques, and 2 fibrocalcified plaques) that could be used for the ROI analysis. ROIs were drawn in the matched MR images of the advanced atherosclerotic plaques within the corresponding regions of the tissue components identified in the histologic sections: lipid accumulation (n = 17), fibrous tissue (n = 24), fibrous cap (n = 12), calcifications (n = 5), and vessel wall (n = 37).

Quantitative MR Parameter Maps

Figures 1–3 show examples of histologic sections with the matched MR parameter maps (T1, T2, T2*, and PD) of advanced plaques from the CoW specimens. Figure 4 and Table 2 show the results of the ROI analysis. For each quantitative MR parameter map, a significant difference was found among certain identified tissue components. In Fig 3B, the single sample containing intraplaque hemorrhage is shown. The hemorrhage can be distinguished from the surrounding fibrous tissue in the T1 and PD maps. This sample was not included in the statistical analysis because only 1 sample contained an intraplaque hemorrhage in this study.

Fig 1.

Histologic sections (Van Gieson elastic stain) of 2 different samples from the CoW specimens classified as fibrolipid plaques: (A) left vertebral artery and (B) left middle cerebral artery (arrow indicates lipid accumulation; arrowhead, fibrous cap). The corresponding T1-weighted image (T1w; DESPOT1 acquired with a flip angle of 44°) and the calculated parametric maps (T1, T2, T2*, and PD) are shown. ROIs were drawn at the location of tissue components identified in the histologic section (yellow ROI indicates lipid accumulation; blue ROI, fibrous cap; green + red ROI, vessel wall) to calculate the mean T1, T2, T2*, and PD values for those regions. Lipid accumulation can be distinguished from the fibrous cap and the vessel wall in the T1, PD, and T2 maps. A, The lipid accumulation area has already developed into the beginning of a lipid core.

Fig 2.

Histologic sections (Van Gieson elastic stain) of 2 different samples from the CoW specimens classified as fibrous plaques: (A) right middle cerebral artery and (B) left intracranial internal carotid artery (arrowhead indicates fibrous tissue). The corresponding T1-weighted image (DESPOT1 acquired with a flip angle of 44°) and the calculated parametric maps (T1, T2, T2*, and PD) are shown. ROIs were drawn at the location of tissue components identified in the histologic section (blue ROI indicates fibrous tissue; green + red ROI, vessel wall) to calculate the mean T1, T2, T2*, and PD values for these regions. Here, fibrous tissue can be distinguished from the vessel wall in the T1 and T2 maps (partly) and, to a lesser extent, in the T2* map.

Fig 3.

Histologic sections (H&E stain) of 2 different samples from the CoW specimens containing calcifications (A) and an intraplaque hemorrhage (B): right intracranial internal carotid artery (A), classified as fibrocalcified plaque, and middle part of the basilar artery (B), classified as fibrous plaque with an old hemorrhage (arrow indicates fibrous tissue, arrowhead: calcification, A, and hemorrhage, B). The corresponding T1-weighted image (DESPOT1 acquired with a flip angle of 44°) and the calculated parametric maps (T1, T2, T2*, and PD) are shown. ROIs were drawn at the location of tissue components identified in the histologic section (yellow ROI indicates calcification, A, or intraplaque hemorrhage, B; blue ROI, fibrous tissue; green + red ROI, vessel wall) to calculate the mean T1, T2, T2*, and PD values for those regions. Here, the tissue area containing calcifications can be well distinguished in both the PD and T1 maps and, to a lesser extent, in the T2 and T2* maps. The intraplaque hemorrhage can be distinguished from the surrounding fibrous tissue in the T1 and PD maps.

Fig 4.

Boxplots showing the distribution of the mean ROI values of each identified tissue component determined in the quantitative T1 (A), PD (B), T2 (C), and T2* (D) maps of each advanced plaque sample. The asterisk indicates post hoc pair-wise comparison (P < .05).

Table 2:

NMR characteristics of different intracranial plaque tissue components^a

	Lipid Accumulation (n = 17)	Fibrous Tissue (n = 24)	Fibrous Cap (n = 12)	Calcifications (n = 5)	Vessel Wall (n = 37)
T1 (ms)	838 ± 167	583 ± 161	481 ± 98	314 ± 39	436 ± 122
PDb	0.94 ± 0.10	1.10 ± 0.26	1.13 ± 0.21	0.15 ± 0.03	1.0 ± 0
T2 (ms)	22 ± 6.8	18 ± 10	15 ± 9.2	9.4 ± 2.8	10 ± 4.4
T2* (ms)	18 ± 6.2	25 ± 11	21 ± 8.4	8.9 ± 3.0	18 ± 6.5

Note:—NMR indicates nuclear magnetic resonance.

^aFor each identified plaque component the mean ± SD of the mean ROI values for all parameters (T1, PD, T2, T2*) are given. Group differences between tissue components were tested with the Welch test; all maps showed a significant difference (P < .001) between tissue components.

^bNormalized to vessel wall.

Post Hoc Analysis

The On-line Table gives an overview of the post hoc tests performed for pair-wise comparisons of mean ROI values of the identified tissue components, with the resulting P values.

Discussion

The current study focused on obtaining ex vivo quantitative T1, T2, and T2* relaxation times and PD values for different intracranial atherosclerotic plaque components. Its goal was to provide detailed insight into the ability of MR imaging to characterize intracranial atherosclerotic plaque components. Our main results show that primarily, T1 relaxation times were significantly different between different plaque components; the other quantitative maps (PD, T2, and T2*) showed mostly nonsignificant differences between the individual tissue components present in the advanced intracranial plaques.

Thus far, atherosclerotic plaques have been extensively studied in extracranial carotid arteries with both in vivo^23–25 and ex vivo^26–29 MR imaging. These studies showed good correlation between MR imaging plaque characteristics and histologic findings. The advantage of extracranial carotid artery plaques is that in vivo MR imaging can be performed before a carotid endarterectomy procedure, allowing direct correlation with histopathology. However, extrapolation of MR signal characteristics of extracranial plaques to intracranial plaques may not be directly applicable because the intracranial arteries are smaller and have some unique histologic features.^18,30–32 Even so, several studies have recently reported visualization of different intracranial plaque components in vivo by using MR imaging, such as lipids,³³ fibrous cap,^33–35 and intraplaque hemorrhage.^34,36–38 These in vivo techniques, however, have not been validated thoroughly with histopathology, due to the poor accessibility of the intracranial arteries. Recently, Turan et al¹⁸ published a first case report demonstrating the correlation between certain intracranial atherosclerotic plaque components visualized in vivo at 3T with histologic validation of the plaque postmortem. However, further correlations are needed to define additional plaque components and to increase the number of cases. As a first step toward MR imaging validation, 2 ex vivo correlation studies^16,17 assessed the ability of 7T MR imaging to image plaque components. These qualitative studies showed 7T to have sufficient image contrast to distinguish different plaque components within advanced plaques. As a second step toward validation, the current study quantitatively assessed intracranial atherosclerotic plaques to enable more firm conclusions regarding the ability of T1-, T2-, T2*-, and PD-weighted sequences to characterize intracranial atherosclerotic plaques.

Our results showed that the T1 relaxation times gave the most differences between individual tissue components of advanced intracranial plaques. Tissue components identified in the histologic sections as lipid accumulation, fibrous tissue, fibrous cap, calcifications, and vessel wall showed significant differences in T1 relaxation times, indicating that they can be distinguished from each other in a T1-weighted sequence. Lipid accumulation showed the longest mean T1 relaxation time, indicating that this may appear as a hypo-isointense region in a T1-weighted sequence. van der Kolk et al¹⁶ also showed the lipid-rich core to be hypointense on T1-weighted imaging of ex vivo CoW specimens at 7T, while Turan et al¹⁸ demonstrated in vivo lipid and loose matrix to have an isointense signal intensity compared with the surrounding tissue on a T1-weighted image at 3T. However, both studies were based on a limited number of observations. Previous studies on carotid atherosclerotic plaques^11,27,39 have shown the lipid-rich core to be hyperintense on T1-weighted imaging. An explanation for this difference could be that the stage of development of the lipid-rich core in the current study might be earlier compared with the extracranial carotid artery studies. In the current study, only 1 sample was identified showing the beginning of a lipid core (Fig 1A); all other samples that were classified as a fibrolipid plaque were still at the stage of lipid accumulation. Intracranial arteries showed more stable lesions and develop mainly as fibrous plaques.³⁰ Another explanation could be that lipids in an atherosclerotic plaque undergo a partially irreversible phase transition when cooled⁴⁰; however, it is not clear whether this transition affects the MR imaging properties of the lipids.²⁷

The other quantitative maps (PD, T2, and T2*) showed less significant differences among the mean ROI values of the individual tissue components present in the advanced intracranial plaques. The fibrous cap and fibrous tissue showed a larger mean PD value compared with lipid accumulation; however, these differences did not reach statistical significance. Chung et al³⁴ also found the fibrous cap to be hyperintense in PD-weighted imaging of intracranial plaques in vivo. Based on the T2 relaxation time, a distinction can be made between lipids/fibrous tissue on the one hand and vessel wall/calcifications on the other. However, for each analyzed tissue component, the T2 relaxation times showed a large relative SD. In addition, the T2 relaxation times were not consistently larger than the T2* relaxation times; this finding is in contrast to what is known from nuclear magnetic resonance theory. The DESPOT2 method for estimating the T2 relaxation times might be more sensitive to noise than the DESPOT1 method and might, thus, have been negatively affected by the limited SNR resulting from the high resolution used in the current study. Future studies specifically focused on plaque T2 relaxation times may show more significant results. For carotid plaque characterization, it has been shown that reviewing multiple contrast-weighted images provided the most comprehensive evaluation for certain plaque components (eg, intraplaque hemorrhage and lipid-rich necrotic core).^27,41

Only at a few locations were intracranial calcified plaques detected. This finding is in agreement with the low prevalence of intracranial calcified plaques beyond the proximal segments of the ICA and vertebral artery.^30,42 The calcifications that were detected showed low values in all quantitative maps. The PD map showed the largest differences between calcifications and other plaque components and the intracranial vessel wall. It would be expected that this large difference would also be present on the T2* maps, due to the increased susceptibility effects; however, this difference was not seen in our small sample. This outcome could be due to the relatively lower SNR for the T2* maps (only 1 signal average was used for the T2*-weighted sequence). Also, the T2* of calcifications is known to be very short relative to the shortest TE of the current T2*-weighted sequence.⁴³ These factors can potentially impede accurate fitting of the T2* relaxation times. A sequence can be used that measures at even shorter TEs to overcome this impediment; however, this result would come at a price of attainable spatial resolution.

Plaque complications were very rare in this study: Only 1 sample with an intraplaque hemorrhage was found. Previous studies have shown a lower prevalence of intraplaque hemorrhage in intracranial compared with extracranial atherosclerosis, and the prevalence of intraplaque hemorrhage is higher in plaques of symptomatic patients (who experienced a cerebral infarct) compared with asymptomatic patients.^30,31,38 In the current study, the CoW specimens were selected on the basis of the macroscopic presence of a high atherosclerotic plaque burden, without knowledge of the clinical background of the patients. In addition, samples were taken at 15 marked locations per CoW specimen only. Increasing the number of samples per specimen and selecting specimens from symptomatic patients might increase the number of plaque complications found.

This study has several limitations. First, fixation effects of formalin have been shown to change relaxation parameters with time.^44,45 Compared with relaxation times in vivo for the vessel wall of the extracranial carotid arteries,⁴⁶ the relaxation times in the current ex vivo study are considerably shorter. Similar shortening was found in a previous postmortem study, in which the relaxation times for gray and white matter were measured in formalin-fixed human brains.⁴⁷ With an understanding of the effects of sample preparation, the MR imaging data can be correctly related to in vivo data.⁴⁴ Second, the MR imaging experiments were performed at room temperature instead of body temperature, which will have influenced the quantitative measurements in the postmortem specimens.⁴⁴ The 7T MR imaging platform does not provide the possibility of performing temperature-controlled imaging. For now, this is the first study trying to identify specific intracranial plaque components in a quantitative manner to measure whether individual tissue components can be distinguished from each other on the basis of their nuclear magnetic resonance tissue properties. This might suggest which contrast weightings need further consideration, to offer the greatest potential to really discriminate different plaque components in vivo. A next step for future studies would be to validate the current findings in a new set of intracranial plaques with optimized MR imaging sequences, preferably of patients with cerebrovascular disease, by characterizing the plaque components on the basis of the MR images alone (with histologic validation afterward) and assessing the reliability of the measurements.

This study was performed to investigate which MR imaging relaxation times discriminate best among the different plaque components and, thereby, in essence, to predict which image contrast weighting would work best in vivo in characterizing atherosclerotic plaques. On the basis of this study, the T1 relaxation time seems to be the most promising parameter. For now, a direct translation of the quantitative sequences used in the current ex vivo setting to in vivo will be difficult due to the long scan times necessary to achieve the ultra-high resolution required to identify different plaque components. However, this study shows that T1-weighted imaging is probably the best method for distinguishing intracranial plaque components ex vivo and therefore might be most promising for in vivo application. Now that it is known which plaque components can be identified with ex vivo MR imaging sequences, a translation can be made to in vivo intracranial vessel wall MR imaging by fine-tuning the current in vivo sequences on the basis of the nuclear magnetic resonance tissue properties of the identified atherosclerotic plaque components to obtain optimal image contrast between the different tissue components. Also, future developments in receive coil technology (increasing the number of receive elements) may provide significant improvement in SNR to make quantitative assessment of the intracranial arterial vessel wall possible in vivo. Furthermore, in vivo, we expect that quantitative assessment will first become feasible for the thicker arterial vessel wall of the more proximal intracranial arteries, including the distal carotid artery and the vertebrobasilar arterial vessel walls.

Conclusions

We showed that different tissue components of advanced intracranial plaques have distinguishable imaging characteristics by using ultra-high-resolution quantitative MR imaging at 7T. Now that it is known which plaque components can be identified with ex vivo MR imaging sequences, a translation may be made to in vivo intracranial vessel wall MR imaging to obtain optimal image contrast between the different plaque components. Based on this study, the most promising method for distinguishing these plaque components is T1-weighted imaging.

ABBREVIATIONS:

CoW

circle of Willis

DESPOT1

driven equilibrium single pulse observation of T1

DESPOT2

driven equilibrium single pulse observation of T2

PD

proton density