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Eur Heart J. Nov 2009; 30(21): 2566–2574.
PMCID: PMC2771148

Imaging of the unstable plaque: how far have we got?

Abstract

Rupture of unstable plaques may lead to myocardial infarction or stroke and is the leading cause of morbidity and mortality in western countries. Thus, there is a clear need for identifying these vulnerable plaques before the rupture occurs. Atherosclerotic plaques are a challenging imaging target as they are small and move rapidly, especially in the coronary tree. Many of the currently available imaging tools for clinical use still provide minimal information about the biological characteristics of plaques, because they are limited with respect to spatial and temporal resolution. Moreover, many of these imaging tools are invasive. The new generation of imaging modalities such as magnetic resonance imaging, nuclear imaging such as positron emission tomography and single photon emission computed tomography, computed tomography, fluorescence imaging, intravascular ultrasound, and optical coherence tomography offer opportunities to overcome some of these limitations. This review discusses the potential of these techniques for imaging the unstable plaque.

Keywords: Atherosclerosis, Molecular imaging, Vulnerable plaque

Need for high resolution imaging of plaque biology

Acute coronary syndromes (ACS) are the most frequent cause of hospitalization in western countries and may be complicated by acute heart failure or sudden cardiac death. The underlying mechanism of ACS is plaque rupture, endothelial erosion, and/or intraplaque haemorrhage with partial or complete occlusion of an epicardial coronary artery.

Mortality of the sequelae of ACS remains high. Instead of preventing ACS, we are frequently limited to diagnose evolving ACS by relying on electrocardiogram changes, chest pain, and markers of cardiomyocyte necrosis. In order to limit the damage, this leaves us with ‘late’ measures such as percutaneous interventions. Nevertheless, in the best case scenario, we fix the problem (thrombotic coronary artery occlusion) after the event (plaque rupture or erosion) occurred. Instead, prevention of this event with the identification of patients at risk for plaque rupture would be desirable.

Vulnerable plaques are characterized by increased inflammatory infiltrates (i.e. mainly monocytes/macrophages, some T-cells, and neutrophils). Upon ingestion of modified LDL, macrophages become foam cells and release inflammatory cytokines and proteases that induce fibrous cap thinning.1,2 Lipid-loaded foam cells eventually die, thereby leading to growth of the necrotic core.

Relying on inflammation as a central pathogenic aspect of plaque vulnerability, circulating inflammatory biomarkers of vulnerable plaques have been identified. They provide valuable diagnostic and prognostic information.3 However, they do not provide insight in the anatomic localization of vulnerable plaques. Thus, timely and anatomically precise imaging of vulnerable plaques is a medical need, since angiographic and pathological studies demonstrate that coronaries frequently occlude acutely without flow-limiting stenoses.4,5 These findings suggest that the biological characteristics of plaques rather than the degree of luminal narrowing determine the risk for coronary occlusion. X-ray coronary angiography only visualizes the coronary lumen and provides minimal structural or biological information about the vessel wall. Thus, high resolution imaging of plaques reporting on critical lesion biology may identify patients at risk for ACS. Although a number of recent reviews have summarized novel imaging approaches aimed at achieving these goals,68 we here focus on novel imaging techniques that come close to fulfilling this promise in the near future (Table 1).

Table 1
Tools for imaging the unstable plaque

Targeted fluorescence imaging

Fluorescence imaging has revolutionized preclinical research because it is sensitive, cost-effective and can be used over a wide range from microscopic to macroscopic and ex vivo to in vivo applications. Currently, the main impact of optical imaging of inflamed atherosclerotic plaques is preclinical. Intravital microscopy9 and whole mouse tomographic imaging10 have targeted the key aspects of lesion biology. In addition, preclinical tools such as ex vivo immunofluorescence microscopy and flow cytometry are frequently used to validate novel imaging agents in rodent models. In particular, fluorescence molecular tomography holds promise for non-invasive imaging of murine models of atherosclerosis, because it allows quantification of tracer fluorochrome concentrations.11 Comparable to positron emission tomography (PET)–computed tomography (CT), recent addition of hybrid anatomical imaging, for instance fluorescence-mediated tomography–CT, allows to exactly identify the anatomic source of molecular signals (Figure 1A).

Figure 1
Fluorescence imaging of protease activity. (A) In vivo fluorescence molecular tomography (FMT) of an atherosclerotic mouse after injection of a cathepsin-targeted protease reporter. Hybrid FMT–CT imaging shows activation of the sensor in the aortic ...

Clinical translation of optical imaging has been hampered by physical hurdles, as light does not penetrate more than 8 cm of tissue. Although the use of fluorochromes in the near-infrared spectrum optimizes tissue penetrance and minimizes autofluorescence,12 the coronary artery tree is out of reach for non-invasive fluorescent sensing. However, carotid arteries should be accessible for non-invasive fluorescent imaging as they are closer to the body surface.

Recent advances in catheter-based technology allow to probe fluorescence in the vascular wall from inside the vessel (Figure 1BE).13 For situations in which invasive angiography is needed, fluorescent sampling of the vascular wall may develop into a valuable add-on as fluorescent probes can identify several hallmarks of lesion inflammation. Among these, activatable protease reporters are particularly promising.14 These probes are injected in a quenched, inactive state. Fluorochromes are attached to a polypeptide backbone, which is targeted by the protease of interest. Upon cleavage of the backbone by the enzyme, fluorochromes are liberated and gain a higher distance to each other, which renders them excitable with a laser in the appropriate wavelength.11 After excitation, they emit light at a higher wavelength, detectable with appropriate charge-coupled device cameras or catheter sensors. In a hypothetical clinical scenario, pull-back scans of the coronary tree after systemic injection of an activatable fluorescent protease sensor may locate inflamed, vulnerable lesions in proximal coronary segments that have a high probability of causing ischaemic complications and therefore may warrant therapeutic intervention.

Nuclear imaging

The foremost advantage of nuclear imaging is its excellent sensitivity, which translates into the detection of sparse targets in the nanomolar range with low tracer doses. Until recently, single photon emission computed tomography (SPECT) and PET imaging of vascular biology were hampered by the low spatial resolution (4–10 mm) and limited ability to visualize anatomical detail. However, hybrid imaging of CT and magnetic resonance imaging (MRI) in dual modality systems exactly attribute the molecular signal to the anatomic source (Figure 2AC). This progress has led to increased interest in the development of nuclear tracers for vascular applications.

Figure 2
Nuclear imaging of plaque biology. (AC) Clinical 18FDG PET–CT imaging in a patient with coronary artery disease shows uptake of the tracer in a stenotic segment (confirmed by angiography).19 (DG) In vivo PET–CT imaging ...

18FDG (fluorodeoxyglucose) is a glucose analogon that enriches in metabolically active cells. It is clinically approved for cancer imaging and has been explored for imaging inflamed plaques with enhanced metabolism. Experimental and clinical studies suggest that 18FDG enriches in plaque macrophages and correlates with neovessel content.1517 A limitation of 18FDG relates to its moderate specificity18 and the high background uptake in the myocardium, although some dietary measures may reduce cardiomyocyte uptake (Figure 2A and B).19 18FDG is currently the only readily available PET tracer for atherosclerotic studies and provides the possibility to explore PET–CT imaging for vascular targets in patients. Therefore, the number of clinical studies using 18FDG is on the rise.20,21

Several tracers that target specific aspects of lesion biology are currently tested. Vascular cell adhesion molecule-1 (VCAM-1) is expressed early in the course of atherosclerotic disease, is favourably positioned on endothelial cells lining the inflamed plaque and therefore provides unhindered access for probes from the blood. Most importantly, VCAM-1 is central to both development and complications of atherosclerotic plaques. Monocytes/macrophages that are recruited into the subendothelial layer of the arterial wall bind to VCAM-1 via the integrin VLA-4, a decisive step for cell extravasation. Vascular cell adhesion molecule-1 had been targeted with a variety of probes with magnetic, optical, and ultrasound reporters.2224 More recently, a PET tracer has been developed25, termed 18F-4V. Its good affinity, favourable pharmacokinetics and the choice of target make 18F-4V a promising candidate for translation (Figure 2DG).

The trimodal nanoparticulate PET/MRI/optical agent 64Cu-TNP was used to image a target downstream of VCAM-1, the presence of lesional macrophages.26 The fluorescent properties of 64Cu-TNP have been exploited to quantify the target cells by flow cytometric profiling of digested aortic plaques. Interestingly, this tracer is primarily taken up into macrophages. In a direct comparison with high-field T2*-weighted MRI, the detection threshold was 50 times lower for PET detection.26

Plaque foam cells eventually undergo apoptosis and form a necrotic core. Probes have been explored that target apoptosis using annexin-V as affinity ligand. Annexin-V binds to phosphatidylserine that is normally hidden on the inside of the cell membrane. In one small clinical study, increased uptake of 99mTc-labelled annexin-V in the carotid artery correlated with histological signs of apoptosis after endarterectomy.27

Much of the mayhem caused by macrophages inside lesions is inflicted through protease activity. Released by monocytes/macrophages, these enzymes digest extracellular matrix and weaken the fibrous cap that protects the plaque against rupture. Several groups have developed small molecule inhibitors of matrix metalloproteinases and labelled these with radiotracers for SPECT imaging.2830 Other matrix proteins such as the extradomain B of fibronectin31 and the C domain of tenascin-C32 are also increased in advanced plaques. Because these agents can visualize inflamed atherosclerotic plaques in mice, they may provide attractive opportunities for imaging advanced plaques in patients.

Macrophages deliver high payloads of vascular endothelial growth factor and may therefore stimulate growth of blood vessels. The leaky character of plaque neovessels has been inferred to promote intraplaque haemorrhage, further exacerbating inflammation.33 Upon formation of these new microvessels, involved endothelial cells express a variety of integrins on their surface, which have been targeted using nuclear probes.34 Frequently, affinity ligands binding to integrins incorporate the amino acid sequence Arg-Gly-Asp (RGD), which binds to alphavbeta3.35 This integrin is also expressed by leucocytes, smooth muscle cells, and platelets. Some of these tracers have already been used in clinical studies.36

Taken together, nuclear imaging techniques hold great promise for non-invasive detection of inflamed, rupture-prone atherosclerotic lesions. Their limited ability to provide anatomical detail has been overcome by hybrid CT or MRI. Although we are seeing the first PET images of coronary arteries in patients, the rapid motion and small size of these vascular territories still pose greater challenges than imaging of the carotid arteries.

Magnetic resonance imaging

Magnetic resonance imaging is a safe and non-invasive technique that operates without X-rays. Using MRI, contrast between different tissues can easily be obtained and amplified using contrast agents. These characteristics render MRI well positioned for monitoring atherosclerotic disease progression or to guide therapy. Since MRI is a relatively signal-insensitive technique when compared with CT or PET, long scanning times are required for improving spatial resolution.

The current gold standard for the identification of coronary artery stenoses is X-ray coronary angiography. However, it is invasive and associated with significant costs and radiation exposure. Magnetic resonance imaging has the potential to overcome some of these limitations. However, the technical challenges related to spatial resolution, contrast generation, and motion artefact suppression are significant. To date, results from the only multicenter trial37 suggest that MRI can reliably identify significant proximal luminal disease and rule out patients without significant proximal or three-vessel disease. However, the specificity of MRI is still relatively low. More advanced and promising approaches include whole heart coronary MR angiography38 (Figure 3AC), as well as the use of both high magnetic field strength39 and molecular imaging agents.40

Figure 3
Visualization of a coronary atherosclerosis by MRI. (A) Curved multiplanar reconstruction of a whole-heart coronary MRA data acquisition shows a stenosis in the left anterior descending (LAD) artery (arrow). (B) Volume-rendering method in the same patient ...

On conventional coronary MRI, there is little contrast between the luminal blood and the coronary vessel wall. Using sophisticated magnetization preparation schemes,41 a high ‘dark-blood’ contrast between the coronary blood pool and the coronary vessel wall can be obtained.42 Building on this technique, positive coronary arterial remodelling was successfully quantified in patients with mild coronary artery disease.43 Furthermore, this technique visualized differences in coronary vessel wall remodelling in high-risk diabetic patients with and without nephropathy (Figure 3D and E).44

Magnetic resonance imaging was further refined for resolving plaque structure: multisequence MRI was able to detect unstable fibrous caps in advanced human carotid plaques.45 In addition, after selecting patients with carotid artery stenosis via ultrasound, bilateral carotid MRI scans at 1.5 T identified complex lesions in a substantial number of arteries in the absence of high-grade narrowing.46 Moreover, tools have been developed for MRI of coronary plaque components. Gadolinium (Gd) clearance is delayed in regions of carotid atherosclerotic plaques with thin fibrous caps (<60 µm)47 which was attributed to both inflammation and endothelial dysfunction. Later on, delayed signal enhancement in the coronary vessel wall after Gd identified patients with established coronary artery disease (Figure 3F).48,49 Similarly, enhanced contrast uptake was found in the coronary vessel wall of patients 6 days after AMI50 and decreased 3 months later parallel to the declines in C-reactive protein. Thus, delayed Gd enhancement of the coronary vessel wall may be useful for visualization of inflammatory activity in patients with ACS. The question remains whether delayed Gd enhancement identifies plaques at risk for rupture. Of note, for some of these applications, the association between Gd exposure during MRI and the rare development of nephrogenic systemic fibrosis has to be considered when using Gd for plaque characterization.51,52

A number of MRI-based strategies have been proposed for detecting inflammation in atherosclerotic plaques using targeted gadolinium agents53 and superparamagnetic nanoparticles which are taken up by macrophages.54 This notion was extended recently using a positive contrast off-resonance imaging sequence (inversion recovery with ON-resonant water suppression-MRI).55 In combination with intravenously injected superparamagnetic nanoparticles (monocrystalline iron-oxide nanoparticles—MION-47), this technique generated positive contrast in areas of plaque macrophages56 in an animal model. Currently, the development of contrast agents that ‘highlight’ specific plaque components for MRI seems promising. So far, molecular agents targeted to adhesion molecules,23 or high-density lipoprotein,57 matrix metalloproteinases,58 and macrophage scavenger receptors59 have been tested at the preclinical level, and agents targeted to fibrin60 and macrophages61 have already been used in patients.

In summary, translation of molecular MRI to clinical applications appears particularly promising in combination with above-mentioned MRI techniques for coronary vessel wall imaging.

Computed tomography

Recent technological advances including multi-detector CT, dual-source CT, and ECG-gated CT led to a growing interest in CT as a tool for non-invasive characterization of coronary artery disease. When compared with MRI, CT is more signal-efficient and high-spatial resolution images of the entire coronary arterial tree can be obtained in a short period of sustained respiration, thereby markedly reducing scanning time. However, exposure to X-ray remains a concern and iodinated contrast agents are needed. Thus, imaging of low-risk subjects and repeated studies should not be performed.62 There has been a large number of recent single centre trials that examined the sensitivity and specificity of coronary CT angiography (CTA) in comparison to X-ray angiography. Consistent with the results from these studies, findings from a recent international multicenter trial63 suggest that coronary 64-row multi-detector CTA is accurate in identifying coronary stenoses and characterizing disease severity in symptomatic patients who have coronary calcium scores of 600 or less. However, multi-detector CTA cannot currently be used as a substitute of conventional coronary angiography given its negative predictive value of 83% and positive predictive value of 91%.

With iodinated contrast agents, Hounsfield units can be measured directly and the expectation was that plaques or their components can be characterized based on X-ray attenuation. Due to considerable overlap in the attenuation spectrum of lipid and fibrous tissue,64 most of the contemporary CT methods unfortunately cannot identify unstable plaques. However, an iodinated contrast agent with specificity for plaque macrophages recently improved visualization of plaque macrophages in an atherosclerotic rabbit model.65

Intravascular ultrasound

Intravascular ultrasound (IVUS) is an invasive, catheter-based imaging technique that provides two-dimensional cross-sectional images of the whole arterial wall. The high accuracy of IVUS to measure lumen, plaque, and vessel area as well as morphological features is established. Given its axial resolution ~100 µm using 40 MHz detectors, IVUS has the ability to localize plaques and quantify plaque burden. Moreover, IVUS is able to identify echolucent areas that represent lipid-rich plaques and may thus have the potential to identify unstable plaques by quantifying necrotic cores in coronary arteries.66 However, given the limited specificity of echolucency, the restricted access to proximal coronary segments, its moderate sensitivity to detect lipid-rich lesions and fibrous cap thickness, this technique has not yet reached clinical routine.

Advances in IVUS technology, i.e. spectral analysis of the IVUS backscatter radiofrequency signal have further improved the tissue characterization of plaques to a degree that it is referred to as virtual histology (VH-IVUS); the raw signals from reflection of ultrasound waves are transduced into a colour-coded representation of plaque characteristics.67 During recent years, VH-IVUS has been extensively validated. Ex vivo analyses of human plaque specimens showed that VH-IVUS could identify plaque components such as lipids, fibrous tissue, calcifications, and the necrotic core.68 Some limitations were reported in a porcine model of complex coronary lesions in which VH-IVUS was not accurate in detecting the relative amount of specific plaque components within each corresponding histological specimen.69 In patients with ACS or stable coronary artery disease, VH-IVUS detected thin-cap fibroatheroma as a morphological plaque feature associated with high-risk ACS presentation.70 On the basis of these findings, VH-IVUS emerges as a promising tool for further characterization of vulnerable plaques.

Optical coherence tomography

Optical coherence tomography (OCT) represents a new optical analogue of ultrasound imaging and has been introduced as an intravascular imaging modality with excellent spatial resolution (10–15 µm) that provides cross-sectional images of the coronary arteries. When compared with IVUS, OCT facilitates the identification of intimal hyperplasia, the internal and external elastic laminae as well as echolucent regions. Optical coherence tomography can also detect and quantify the key pathological features of vulnerable plaques such as a thin fibrous cap (<65 µm) and a large lipid pool.71 The safety and feasibility of using an intravascular OCT image wire system has been demonstrated in ACS patients as well as in patients with acute myocardial infarction.72 Furthermore, OCT has been used successfully to assess culprit lesion morphology in vivo73 and restenosis after stenting.74

A very attractive upgrade of OCT has recently been introduced: Fourier-domain-OCT, also called optical frequency domain imaging (OFDI) works at much higher frame rates (>100 frames/s). This technique enables rapid, three-dimensional imaging of long coronary segments from 3 to 7 cm at pullback rates >20 mm/s after a brief, non-occlusive saline purge,75 therefore eliminating the necessity to use a closure balloon.

Imaging the unstable plaque—present and future

How can aforementioned imaging modalities be used for imaging the unstable plaque?

Among the anatomical imaging tools (Figure 4, right), CT and MRI hold promise given their non-invasive character. Whereas MRI provides excellent soft tissue contrast and a better contrast resolution, CT allows much shorter scanning times. However, the hazard of exposing patients to radiation is a concern. The invasive approaches IVUS-VH and OCT/OFDI offer high-excellent spatial resolution. The combination of anatomical with biological imaging using hybrid techniques, i.e. PET–CT or PET–MRI, appears to be particularly attractive. Among those, targeted imaging that measures inflammation holds the greatest promise to identify unstable plaques by reporting on macrophages and other mechanisms involved in plaque vulnerability (Figure 4, left) such as adhesion molecules, proteases, and matrix components.

Figure 4
Techniques for imaging the unstable plaque. This scheme illustrates morphological and biological tools for visualizing vulnerable plaques. Modalities with clinical applications are given in bold.

How should the patients be selected for plaque imaging and how should we manage these unstable plaques?

Optimal patient selection may be reached by integrating individual risk factors, clinical data, and key plasma biomarkers. Once critical lesions are identified, tailored interventions may reduce the risk of complications caused by the prospective culprit lesion. However, optimal management of unstable plaques remains to be defined and tested prospectively. Preventive or therapeutic options may include minimizing risk factors using life style changes, systemic drug therapy such as statins that reduce inflammation, and mechanical ‘plaque sealing’ using PCI. Currently, it is unclear if invasive ‘cool down’ of inflamed atherosclerotic lesions has a favourable risk–benefit ratio. Thus, the appropriate use of any plaque imaging modality and consecutive interventions need to be investigated in prospective clinical trials, ultimately leading to guidelines for identification, risk stratification, and therapy of patients with unstable plaques.

Funding

This work was supported by grants from the Swiss National Science Foundation 31-114094/1 (C.M.M.), the URPP ‘Integrative Human Physiology’ at the University of Zurich (C.M.M.), AHA SDG 0835623D (M.N.), and in part by the NIH grants R01HL095629-01 (M.N.), R01HL096576-01 (M.N.), R01-HL084186 (M.S.), R01-HL61912 (M.S.), and the Donald W. Reynolds Foundation (M.S.). Further support was provided by unrestricted grants from the MERCATOR Foundation Switzerland and a strategic alliance with Pfizer, Inc. New York. Funding to pay the Open Access publication charges for this article was provided by Cardiovascular Research Foundation Zurich.

Conflict of interest: none declared.

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