Brief Review
Intravascular Modalities for Detection of Vulnerable Plaque
Current Status
Briain D. MacNeill, Harry C. Lowe, Masamichi Takano,
Valentin Fuster, Ik-Kyung Jang
Abstract—Progress in the diagnosis, treatment, and prevention of atherosclerotic coronary artery disease is dependent on
a greater understanding of the mechanisms of coronary plaque progression. Autopsy studies have characterized a
subgroup of high-risk, or vulnerable, plaques that result in acute coronary syndromes or sudden cardiac death. These
angiographically modest plaques share certain pathologic characteristics: a thin, fibrous cap, lipid-rich core, and
macrophage activity. Diagnostic techniques for vulnerable-plaque detection, including serologic markers and noninvasive and invasive techniques, are needed. Recent advances in intravascular imaging have significantly improved the
ability to detect high-risk, or vulnerable, plaque in vivo by using various features of plaque vulnerability as methods of
identification. The characteristic anatomy of a thin, fibrous cap overlying a lipid pool has promoted high-resolution
imaging, such as intravascular ultrasound, optical coherence tomography, and intracoronary magnetic resonance. The
lipid-rich core is identifiable by angioscopically detected color changes on the plaque surface or by its unique absorption
of energy, or “Raman shift,” of its cholesterol core, driving coronary spectroscopy. Finally, temperature heterogeneity
arising at foci of plaque inflammation has prompted the development of intracoronary thermography. In this review, we
will discuss these techniques, their relative advantages and limitations, and their potential clinical application.
(Arterioscler Thromb Vasc Biol. 2003;23:1333-1342.)
Key Words: atherosclerosis 䡲 acute coronary syndrome 䡲 coronary imaging
A
therosclerosis and its thrombotic complications are the
leading cause of morbidity and mortality in industrialized countries. Progress in the diagnosis, treatment, and
prevention is dependent on a greater understanding of the
mechanisms of atherosclerotic plaque progression. Lack of a
suitable large-animal model for atherosclerotic plaque rupture
has concentrated research efforts on pathologic studies and
imaging modalities to advance our understanding of the
pathogenesis of vulnerable plaque.
Historically, revascularization techniques of coronary artery bypass surgery and percutaneous coronary intervention
(PCI) have targeted flow-limiting, hemodynamically significant stenoses, which are readily detected by coronary angiography. However, it is now accepted that acute coronary
syndromes most commonly result from disruption of atherosclerotic plaques that are angiographically modest in severity.1–3 This concept is echoed in studies of plaque regression
that demonstrate significant reductions in acute coronary
events despite disappointing regression of angiographically
detected stenoses, suggesting that strategies of revascularization, although effective in reducing symptoms, do little to
prevent acute coronary events.4
In recent years, cardiovascular research has sought potential strategies for detecting high-risk plaques before their
disruption. These potentially powerful techniques are aimed
at identification of populations at risk and plaque monitoring
and might eventually guide targeted therapy. Proposed diagnostic tools include serologic techniques and noninvasive and
invasive imaging. This review focuses on invasive modalities, summarizes the recently developed invasive techniques,
and compares their advantages and limitations.
Definition of Vulnerable Plaque
Although progression of atheromatous plaque has been well
described and atherosclerotic lesion types characterized, the
concept of the vulnerable plaque is a novel one.1,5 The term
“vulnerable plaque” refers to a subgroup of often modestly
stenotic plaques that are prone to rupture or erosion, often
resulting in acute coronary syndromes and sudden cardiac
death.5 Postmortem evaluation has shown that rupture-prone
plaques have certain characteristics: a thin, fibrous cap (⬍65
m); a large, lipid-rich pool; and increased macrophage
activity (Figure 1).6 – 8 Cellular mechanisms thought to predispose to plaque vulnerability include reduced collagen
synthesis, local overexpression of collagenase, and smooth
muscle cell apoptosis.4 These molecular changes appear most
prominent at the plaque shoulder, where mechanical strain is
Received March 28, 2003; revision accepted May 20, 2003.
From the Division of Cardiology (B.D.M., H.C.L., M.T., I.-K.J.), Massachusetts General Hospital and Harvard Medical School, Boston, Mass, and the
Zena and Michael A. Wiener Cardiovascular Institute (V.F.), Mount Sinai Medical Center, New York, NY.
Correspondence to Ik-Kyung Jang, MD, PhD, Cardiology Division, Bigelow/Gray 800, Massachusetts General Hospital, 55 Fruit St, Boston, MA
02114. E-mail Jang.ik@mgh.harvard.edu
© 2003 American Heart Association, Inc.
Arterioscler Thromb Vasc Biol. is available at http://www.atvbaha.org
DOI: 10.1161/01.ATV.0000080948.08888.BF
1333
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Arterioscler Thromb Vasc Biol.
August 2003
not provide direct information on the changes within the
vessel wall necessary to detect vulnerable plaque.2 This
limitation has promoted interest in alternative invasive or
catheter-based techniques to directly visualize the arterial
wall and to characterize plaque composition. Invasive techniques are, by definition, associated with procedural risk,
limited to a specific region of the coronary arterial tree, and
inappropriate for screening large populations.
Various plaque components have been targeted to determine potential vulnerability of individual plaques (Table 1).
The characteristic architecture of a thin, fibrous cap overlying
a lipid pool has prompted further development of highresolution imaging modalities, including intravascular ultrasound (IVUS), optical coherence tomography (OCT), and
intracoronary magnetic resonance. The cholesterol-rich, lipid
core underlying the fibrous cap is also identifiable by both
angioscopically detected color changes reflected on the
plaque surface and its unique absorption of energy, or
“Raman shift,” of its cholesterol crystals, thus driving the
development of coronary spectroscopy. Finally, temperature
heterogeneity arising at foci of plaque inflammation has
promoted the development of intracoronary thermography.
Figure 1. Histology of a lipid-rich, or vulnerable, coronary
plaque. The thin fibrous cap (arrows) and lipid core (LC) are features of vulnerable coronary plaque. Of note, the preserved
luminal area renders coronary angiography or other forms of
luminography obsolete in vulnerable-plaque detection.
Intravascular Ultrasound
IVUS has provided insight into the extent and distribution of
atherosclerotic plaque, allowing characterization of vessel
wall and plaque morphology.15 IVUS is capable of characterizing the plaque core, although with less sensitivity for
lipid-rich than calcified lesions. Plaque morphology can be
described by ultrasound as echoreflective, corresponding to
calcified plaque; hyperechoic, representing fibrous plaque;
and hypoechoic, indicating a lipid-rich core.16 Plaque characterization is reliable in distinguishing fibrous and calcified
plaque but not soft or lipid-rich plaque, owing in part to
variable concentrations of cholesterol crystals and calcospherites that form the heterogeneous components of the
cholesterol core.17 In terms of macrocalcification, IVUS
yields a 3-fold higher detection rate compared with angiography, with a sensitivity and specificity of 89% and 97%,
respectively. However, the echo-reflective properties of calcium result in acoustic shadows that preclude accurate quantification and obscure imaging of adjacent structures.18,19
With regard to the IVUS detection of microcalcification,
defined as flecks of calcium ⬍0.05 mm, a sensitivity as low
maximized.
It has been suggested that disruption in cap
integrity releases procoagulant factors, particularly tissue
factor, creating a nidus for thrombus formation and the
potential for an acute coronary event.11 Although vulnerable
plaques continuously rupture throughout the vasculature, only
certain plaques form an occlusive thrombus, causing clinical
syndromes.12 Factors that determine the fate of a plaque
rupture are unknown.
The terms “vulnerable plaque” and “high-risk plaque” are
imperfect, in that they are predictive, prophetic, or prospective in nature. A more descriptive term, such as “thin-capped
fibroatheroma,” is often favored; however, for the purpose of
this review, these terms will be used synonymously.
9,10
Invasive Imaging Techniques
Coronary plaque begins eccentrically and induces a process
of remodeling, resulting in arterial dilatation and preservation
of the luminal area.2,13,14 Coronary angiography, historically
the “gold standard,” illustrates luminal narrowing but does
Comparison of Noninvasive and Invasive Imaging Modalities for Detection of Individual Characteristics of
Vulnerable Plaque
Imaging Modality
IVUS
Angioscopy
Resolution
Penetration
Fibrous Cap
Lipid Core
Inflammation
Calcium
Thrombus
Current Status
100 m
Good
⫹
⫹⫹
–
⫹⫹⫹
⫹
CS/CA
UK
Poor
⫹
⫹⫹
–
–
⫹⫹⫹
CS/CA*
OCT
10 m
Poor
⫹⫹⫹
⫹⫹⫹
⫹
⫹⫹⫹
⫹
CS
Thermography
0.5 mm
Poor
–
–
⫹⫹⫹
–
–
CS
Spectroscopy
NA
Poor
⫹
⫹⫹
⫹⫹
⫹⫹
–
PCS
160 m
Good
⫹
⫹⫹
⫹⫹
⫹⫹
⫹
PCS
Intravascular MRI
NA indicates not applicable; CS, clinical studies; CA, clinically approved for commercial use; CA*, clinically approved commercial
use in Japan; PCS, preclinical studies; UK, unknown.
⫹⫹⫹⫽sensitivity⬎90%; ⫹⫹⫽sensitivity 80% to 90%; ⫹⫽sensitivity 50% to 80%; [en]⫽sensitivity ⬍50%.
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MacNeill et al
as 17% was found.20 The importance of calcium in plaque
vulnerability remains an issue of ongoing debate.21,22
The 2-dimensional IVUS image, derived from ultrasound
frequencies in the range of 20 to 40 MHz, results in an axial
resolution of 100 to 200 m and a lateral resolution of 250
m.16 These properties, though beneficial for visualizing
deep structures, limit imaging of microstructure, yielding a
sensitivity of only 37% for the detection of plaque rupture
with IVUS.23 Although 3-dimensional image reconstruction
improves border definition, it has not yet been tested for
detection of vulnerable plaque or plaque disruption.
Several techniques have been developed to improve the
IVUS detection of plaque vulnerability. To maximize the
differentiation of a lipid-rich or sonolucent plaque, integrated
backscatter (IB) and assessment of the radiofrequency envelope within the plaque have been analyzed. Correlation of the
parameters of the radiofrequency envelope generated from ex
vivo plaque with histologic markers of plaque vulnerability
have yielded modified algorithms that augment the detection
of the lipid-rich core associated with plaque vulnerability.24
In vivo application of IB IVUS has recently been shown to
enhance visualization of plaque characteristics and improve
the resolution to ⬇40 m.25 Two important limitations of IB
IVUS include the analogous signal obtained from intimal
hyperplasia and lipid-rich plaque, necessitating complex
methodology for adequate differentiation, and second, a
significant reduction in the sensitivity of plaque characterization as imaging moves off axis.25
The intracoronary pressure changes of the cardiac cycle
exert forces resulting in conformational change in coronary
plaque that have been proposed as predictors of plaque
vulnerability. IVUS elastography combines ultrasound images with radiofrequency measurements to detect regions of
increased strain that are prone to rupture, thus improving the
discrimination between lipid-rich and fibrous plaque, traditionally a limitation of standard IVUS.26,27 Furthermore, ex
vivo IVUS elastography has demonstrated a positive correlation between strain measurements and the presence of
macrophages and an inverse relation with the quantity of
smooth muscle cells within coronary plaque, supporting the
role of macrophage-derived matrix metalloproteinases in the
development of thin-capped, vulnerable plaque.28 Recently,
an in vivo animal study validated IVUS elastographic criteria
for identifying lipid-rich plaque and demonstrated a sensitivity and specificity of 92% in identifying the presence of
macrophages at foci of increased strain within the plaque.29
Although beneficial in segregating plaque types, IVUS elastography has been criticized for its inability to differentiate
normal artery from early and advanced fibrous plaques.30
Related structural properties that have been studied as
markers of vulnerability include plaque distensibility and
remodeling. Plaque disruption is ultimately triggered by
intrinsic changes and/or extrinsic forces, including shear
stress and wall stress. Plaque distensibility provides a measure of wall stiffness, a marker of the dynamics of intrinsic
changes and extrinsic forces, and has been related to plaque
distribution31 and thickness.32 Distensibility, calculated with
gated IVUS images and intracoronary pressures, is correlated
with the angioscopic categorization of vulnerable plaque and
Vulnerable-Plaque Detection
1335
Figure 2. Stationary IVUS images during diastole (A) and systole
(B) demonstrate the distensibility of coronary plaque during the
cardiac cycle, which can be quantified by the distensibility
index. Vulnerable plaques, identified by angioscopy, have been
shown to display greater distensibility.33 Tick marks⫽0.5 mm
OCT features of lipid-rich plaque (Figure 2).33,34 Distensibility measurements can, however, be confounded by axial
motion of the IVUS catheter during the cardiac cycle,
resulting in systolic and diastolic images of different sites.
Observations of focal arterial dilatation at the site of aortic
and coronary plaque have led to theories of arterial remodeling in response to plaque development.13,15,35 Subsequently,
coronary luminal area was shown to be preserved during
early plaque progression owing to a process of internal elastic
lamina dilatation, termed “positive remodeling.” Similarly,
“negative remodeling” describes shrinkage of the external
elastic membrane in response to plaque development. Although initially thought of as a protective or beneficial
process in reducing effective percent stenosis, positive remodeling has been associated with acute coronary syndromes
and angioscopically complex lesions.36 Negative remodeling,
on the other hand, is seen more frequently in stable coronary
artery disease.37 The pathophysiology of vascular remodeling
and the mechanisms that link plaque vulnerability to remodeling are unclear. Hemodynamic and humoral effects are
thought to result in secretion of factors that influence cell
proliferation, apoptosis, and the composition of extracellular
matrix.38 Histologic studies of remodeled arteries demonstrate an inflammatory process similar to that seen in vulnerable plaque.39,40 Limited clinical studies have shown positive
remodeling associated with high lipid levels41 and negative
remodeling associated with lipid-lowering therapy, suggesting that remodeling is significant in plaque vulnerability and
stabilization.42
Potential artifacts that arise with IVUS include “ringdown” artifacts produced by acoustic oscillations in the
piezoelectric transducer that obscure near-field images and
“nonuniform rotational distortion,” arising from uneven drag
on the cable, causing cyclic oscillations of the ultrasound
probe.16 Specific limitations to the IVUS identification of
vulnerable plaque remain the issues of resolution and inability to adequately discriminate between fibrous and lipid-rich
plaques. The combination of new, high-frequency catheters
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Figure 3. Angioscopic color grading of atherosclerotic coronary
plaque, with white plaque representing fibrous plaque (A). Yellow plaque signifies a lipid-rich core seen through a thin, fibrous
cap. The intensity of the image increases as the fibrous cap
thins and becomes increasingly transparent (B, C, and D). An
irregular or complex lipid-rich plaque is seen in E, and a lipidrich plaque with associated thrombus is shown in F. A 0.014-in.
wire in D provides a reference of scale.
integrated with the techniques of IVUS signal modification
will certainly enhance the role of IVUS in vulnerable-plaque
detection. Balancing these limitations is the significant experience that exists in the clinical application and interpretation
of this modality and the capability to image long arterial
segments safely.
Angioscopy
Although historically attempts have been made to visualize
intracardiac structures,43 it was not until the development and
application of fiberoptics that direct visualization of coronary
arteries could be achieved. Coronary angioscopy complements angiography by characterizing plaque composition and
illuminating the presence of thrombus or endoluminal irregularities, such as ulcerations, fissures, or tears.
The normal artery appears angioscopically as glistening
white, whereas atherosclerotic plaque can be categorized on
the basis of its angioscopic color as yellow or white (Figure
3).44,45 Histologic correlation has demonstrated high concentrations of cholesterol-laden crystals seen through a thin,
fibrous cap in yellow plaque and a thick, fibrous cap in
smooth white plaques.44 Platelet-rich thrombus at the site of
plaque rupture is characterized as white granular material,
and fibrin/erythrocyte-rich thrombus, as an irregular, red
structure protruding into the lumen.45 Furthermore, yellow
plaques are seen more commonly at the site of culprit lesions,
increase the likelihood of a subsequent coronary event, and
demonstrate increased susceptibility to rupture and thrombosis with increased intensity of yellow color, all supporting the
concept that yellow lesions correspond to vulnerable
plaque.44,46,47 Indeed, angioscopic studies have shown multiple sites of vulnerable-plaque rupture throughout the coronary circulation at the time of myocardial infarction, supporting the hypothesis of a systemic trigger for plaque rupture.12
Despite the equal prevalence of vulnerable plaque in infarctrelated and non–infarct-related arteries, only culprit segments
have demonstrated angioscopically evident thrombus.12 Such
infarct-related segments demonstrate red and white thrombus
overlying yellow plaque in the early phase, with the persistence of white thrombus for the first month after infarction.
Both culprit and nonculprit, infarct-related, vulnerable, yellow plaques followed up angioscopically for 6 months have
demonstrated a significant reduction in maximum intensity of
yellow color and associated thrombus, albeit less completely
in diabetes and hyperlipidemia.48 Changes in plaque color
have also been recorded with lipid-lowering interventions.49
Rupture of vulnerable, yellow plaque has also been demonstrated in asymptomatic stable angina, in which the prevalence of “silent” plaque rupture diagnosed angioscopically
was 29.3% and was significantly more prevalent in diabetes
and hypertension.50 Furthermore, the presence of yellow
plaque at the time of PCI has been shown to be an independent risk for future ischemic events in a prospective, 5-year
angioscopic study.51 The mechanical features of vulnerable
plaque have been studied with a combination of angioscopy
and IVUS in which yellow and white plaques were compared
in terms of stiffness, distensibility, and remodeling. Yellow
plaques demonstrated increased distensibility and compensatory remodeling, thought to predispose to mechanical fatigue
from repetitive strain at the shoulder regions of coronary
plaque.33
The most significant limitation of current angioscopic
systems is the need to create a blood-free field. This is
achieved with a proximal occluding balloon, which itself can
create complications, the most devastating of which include
coronary rupture, dissection, thrombosis, or arrhythmia. The
alternative system uses a smaller catheter to continuously
flush saline in front of the angioscope to transiently displace
blood, but this technique requires removal of the guidewire
before acquisition of each image. The catheter design (3.0 to
5.0F) of both systems precludes angioscopic evaluation of
small vessels (⬍2 mm) and renders assessment of cross-stenotic lesions difficult (please see http://www.ahajournals.
org). Moreover, the subjectivity of color interpretation has
been criticized, resulting in efforts to develop an automated
analysis system of angioscopic images. Finally, angioscopy
images only the luminal surface, and although changes in the
vessel wall are reflected on the surface, this might not be
sufficiently sensitive to detect subtle alterations in plaque
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MacNeill et al
Vulnerable-Plaque Detection
1337
Figure 4. In vivo intracoronary imaging
of lipid-rich plaque with OCT (A) and
IVUS (B). The OCT image demonstrates
the superiority of resolution, whereas the
IVUS image highlights greater image
penetration. A thin, fibrous cap, marked
with an arrow, is seen to overlie a lipidrich core (LC). GW indicates guidewire
artifact.
composition, a feature that has been raised in recent comparisons of imaging modalities.25
Optical Coherence Tomography
OCT measures backscattered light, or optical echoes, derived
from an infrared light source directed at the arterial wall, and
as such, it can be regarded as an analogue of IVUS.52
Resolution capabilities of 2 to 10 m, validated ex vivo,
allow superior definition of the order necessary to resolve
thin, fibrous caps that are responsible for plaque vulnerability, whereas the heterogeneous morphologies of coronary
plaque are readily discernible into calcified, fibrous, and lipid
rich (Figure 4).53,54 OCT characteristics of various plaque
components have been established by ex vivo histologic
correlation, highlighting a sensitivity and specificity of 92%
and 94%, respectively, for lipid-rich plaque; 95% and 100%
for fibrocalcific plaque; and 87% and 97% for fibrous
plaque.55
In a comparison with high-resolution IVUS, OCT has
proved equivalent in detecting plaque and discerning fibrous
and calcified plaque morphologies. In terms of resolution,
OCT was found to be superior, allowing identification of
intimal hyperplasia, internal and external elastic laminas, and
regions of lipid-rich plaque not detected by IVUS.53 Importantly, this study demonstrated the clinical application of
OCT and its superiority to IVUS in detecting characteristics
of vulnerable plaque.53 Recently, the ability of OCT to detect
and quantify macrophage infiltration was demonstrated in an
autopsy study. The presence of macrophages within the
fibrous cap, identified by immunoperoxidase staining for
CD68, was correlated with the optical signal, such that a
sensitivity and specificity of 100% was achieved for the
detection of an arbitrary quantity of ⬎10% CD68-positive
macrophages within that imaged region.56
Newer platforms that are being applied to coronary OCT
include polarization imaging, spectroscopy, Doppler, and
elastography. OCT is extremely sensitive to changes in light
polarization; the major source of polarization contrast, or
birefringence, originates from fibrous plaque or cholesterol
crystals, thus potentially advancing plaque discrimination.
The addition of spectroscopic analysis supplements the structural detail of OCT with biochemical analysis of the plaque
core, providing synergism in plaque imaging. OCT elastography, as with its IVUS counterpart, applies high-resolution
imaging with radiofrequency measurements to detect foci of
increased strain that are prone to plaque rupture. New
wire-based systems with a diameter of 0.014 in. facilitate
imaging of the smallest coronary arteries.
Current limitations of OCT remain significant and are
related predominantly to the features of a light-based energy
source, including poor tissue penetration and interference
from blood. The latter necessitates techniques similar to
angioscopy that displace blood, such as saline injection with
or without a proximal occlusion balloon. These maneuvers
limit prolonged image acquisition and preclude screening
long arterial segments. A penetration of 2 mm, though
considerably less than that with IVUS, is probably sufficient
to detect the features of plaque vulnerability that are predominantly superficial in location.
Thermography
In union with the structural changes described earlier are the
biologic processes that characterize the pathophysiology of
vulnerable plaque. One such process is an intense inflammatory reaction, manifested by the local invasion of macrophages and lymphocytes, and the deposition of matrix metalloproteinases that degrade the supporting collagen and
promote plaque fragility.2 This inflammatory activity creates
local elevations in temperature that can be detected with a
catheter-based thermistor with a temperature differentiation
of 0.05°C and a spatial resolution of 0.5 mm.57,58 Ex vivo
carotid plaque has demonstrated temperature heterogeneity
directly proportional to the degree of histologically detected
inflammation, confirming its ability to quantify the pathophysiologic process within plaque.57 Clinically, coronary
arterial temperature differentials are greater in patients who
present with acute coronary events and are associated with a
higher adverse event rate after successful PCI, both suggesting a predictive role for thermography.59,60 Similarly, cell
adhesion molecules, which mark the inflammatory process
central to the pathogenesis of coronary artery disease, have
been correlated with temperature differentials at culprit lesions in acute coronary syndromes.61 Finally, plaque stabilization with lipid-lowering therapy reportedly reduces temperature heterogeneity, supporting an anti-inflammatory effect of
statin therapy.58
There appears to be a significant overlap between temperature differentials in stable and unstable presentations of
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August 2003
coronary artery disease, and there is no clear evidence that
temperature differentials are related to a specific plaque
vulnerability rather than a generalized marker of inflammation, in which case, a serologic marker might be more
appropriate.58 – 62 Similarly, individual variations in temperature heterogeneity have been documented, suggested to arise
from altered blood flow through a stenotic lesion or as a result
of systemic inflammation or medication, all features that
question its capacity to assess individual plaque vulnerability.58 Although several catheter designs are currently available, all require contact with the arterial wall, and their use
can therefore be complicated by vessel injury (please see
⬍http://www.ahajournals.org). Without the structural definition obtained from high-resolution imaging modalities, the
independent role of thermography seems limited. Furthermore, the immediate evaluation of local mechanical therapy
and the selection of an appropriate site for background
measurement are confounded.58 However, combining thermography with the structural detail of other imaging modalities theoretically produces an attractive synergy of anatomic
and physiologic predictors of plaque vulnerability.
core and thin fibrous plaque but also as a result of physiologic
variables such as pH.69 In human atherosclerotic plaque,
NIRS achieved a sensitivity of 90% and a specificity of 93%
for detection of the lipid core.64 The sensitivity and specificity
for features of plaque vulnerability ranged from 77% to 93%
for the fibrous cap and inflammation.64 It remains unclear
whether combining the predictive value of each component
might result in an even greater sensitivity and specificity for
vulnerable-plaque detection. Incorporating measurements of
temperature and pH into the spectroscopic system has been
proposed to further improve high-risk-plaque detection.70
Transferring ex vivo spectroscopy to in vivo coronary
imaging raises several hurdles, not the least of which is
noncontact spectroscopic evaluation through flowing blood,
although in theory and initial practice, this seems feasible.64,71
As with thermography, lack of structural definition hinders all
methods of spectroscopy, limiting their independent application in vulnerable-plaque detection; however combined with
an imaging technique such as IVUS, OCT, or angioscopy, it
might provide a valuable additional dimension.
Intravascular Magnetic Resonance Imaging
Spectroscopy
Spectroscopy, the study of energy wavelengths, has been
investigated as a method of detecting vulnerable plaque by
using different energy sources, including infrared or laser.63– 65 To date, the most validated methods are Raman
spectroscopy (RS) and near-infrared spectroscopy (NIRS).
Raman spectra are created by processing the collected light
scattered from an artery that is emitted during laser illumination. The Raman spectrum of a given molecule is unique,
allowing analysis of chemical composition from the patterns
of reflected light, known as diffuse reflectance spectroscopy.
The molecular characteristics of lipid and calcium salts
render RS highly sensitive for plaque detection, as demonstrated both in vivo and in vitro.63,66 By combining the
independent spectra of the various chemical constituents of
atherosclerotic plaque, a diagnostic algorithm has been validated to classify coronary artery plaques with a specificity of
94%.67
Combining IVUS and RS in an ex vivo study demonstrated
synergism between the structural definition of IVUS and the
chemical quantification of RS, in which spectroscopy accurately identified and quantified calcium salts and cholesterol.66 Limitations of RS lie in the small number of photons
recruited into the Raman shift, resulting in poor tissue
penetration, low signal-to-noise ratio, and background noise
from backscattered light within the optical fibers of the
catheter-based system.
NIRS measures diffuse reflectance signals by using infrared light as an energy source. Infrared light results in greater
tissue penetration than RS (2 mm compared with 0.3 mm) but
a lower capability to identify individual components of
plaque, resolved in part by the use of pattern recognition for
plaque typing. Quantification of cholesterol within atherosclerotic plaque by NIRS correlates well with more destructive, traditional techniques of chromatography (correlation
coefficient⫽0.926) in aortic plaque.68 Vulnerable plaque is
thought to emit a unique spectrum, in part because of its lipid
In superficial large arteries such as the carotid, standard
magnetic resonance imaging (MRI) is capable of discriminating plaque components, including lipid, collagen, thrombus,
and calcium on the basis of biochemical properties.72 As the
distance from the external coil and the artery increases,
however, a significant fall-off in signal to noise occurs,
resulting in reduced resolution. A practical solution to improve imaging in deeper arteries is to insert intravascular
coils in the artery or the adjacent vein.73 Several intravascular
coil designs have been developed, each demonstrating superior resolution than standard MRI for vessel wall imaging
(160 m compared with 300 m). Ex vivo aortic imaging
with a 5F intravascular MRI probe and a 1.5-T scanner
yielded sufficient resolution to discern the adventitial, medial,
and intimal layers and to allow plaque characterization with a
sensitivity of 83% and 100% for detection of fibrous cap and
necrotic core, respectively.74 Furthermore, basic grading of
plaque characteristics as mild, moderate, or severe displayed
a correlation between histology and intravascular MRI of
75% and 74% for cap thickness and extent of necrotic core,
respectively.74 With use of a standard 0.5-T MRI combined
with a 5F intravascular MRI coil, the signal properties of
fibrous cap, lipid core, calcium, thrombus, and edema were
characterized within carotid plaque, demonstrating that
through a variety of imaging approaches, standard magnets
could achieve a sufficient degree of resolution, thus expanding their availability (Figure 5).75 In this study, in which a
variety of imaging protocols were assessed, the discrimination between T1- and T2-weighted images proved time
consuming and less informative than the use of various pulse
sequences (inversion recovery, magnetization transfer contrast, and gradient echo sequences) that capitalized on the
differences in biochemical composition of various plaque
components.75 Limited in vivo studies suggest that intravascular MRI is effective through flowing blood, although the
applicability of plaque characterization validated ex vivo
remains unknown.76
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MacNeill et al
Figure 5. Intravascular MRI of a carotid artery with corresponding histology (A) demonstrates a modestly elevated signal intensity in lower half of a T1 sequence. B, The same region during
water signal suppression in the inversion recovery sequence,
demonstrating persistent signal in the lower half of the artery,
thus differentiating this region as high in lipid content and
improving the differentiation of lipid plaque from the external
fibrous intima in the upper half of the image. C, Corresponding
hematoxylin-and-eosin–stained slide with high magnification of
the selected region, confirming the presence of lipids and cholesterol crystals. D, Trichome stained slide, with high magnification of the selected region displayed in F illustrates the fibrous
cap above lipid pool that is seen in the intravascular MRI (B).75
Current intravascular MRI coil designs are hampered, to
varying degrees, by common themes that limit their clinical
application. Catheters are typically 5F in outer diameter and
require a close match between coil and arterial diameter to
prevent fall-off in radial resolution. Furthermore, axial resolution is limited, necessitating multiple catheter manipulations and repeated imaging. Finally, image quality is reduced
significantly as the intravascular coil moves off axis from the
external magnet field, a significant limitation for imaging
tortuous coronary arteries. Despite these considerable difficulties, the image quality and the recent development of
MRI-compatible catheters make intravascular MRI an area of
intense research.
Emerging Technologies
Several new developments, including pharmacologic and
mechanical interventions, might augment vulnerable-plaque
detection in the future. Such pharmacologic interventions
target specific receptor activation, cell metabolism, or biologic pathways to enable a holistic evaluation by marrying
Vulnerable-Plaque Detection
1339
structural morphology with biologic activity. Although nuclear imaging has achieved many of these goals, including
receptor activation, metabolism, and apoptosis, the image
resolution is limited by the distance from the tracer to the
detector.77–79 Improvements in signal-to-noise ratio have been
achieved with the application of intravascular catheter–
mounted detectors, allowing enhanced sensitivity for detecting changes within atherosclerotic plaque (please see http://
www.ahajournals.org).80 Recently, metal nanoparticles have
been explored as contrast agents to enhance various imaging
techniques.81 The nanoparticle’s ability to enhance both linear
and nonlinear optical processes at low energy result in high
resonant scattering to which optical imaging is particularly
sensitive.82 Their high biocompatibility and small diameter (5
to 10 m) allow easy diffusion through cellular junctions and
phagocytosis by macrophages, enhancing detection of inflammatory processes. Newer generations of molecular probes
demonstrate enzyme-specific fluorescence that is detectable
by diffuse optical or fluorescence-mediated tomography.83
These probes are quenched in the inactive state but fluoresce
brightly when activated on cleavage by specifically targeted
enzymes. In a similar manner, quantum dots or nanocrystals,
which emit photonic energy, can be tagged with specific
antibodies to function as cellular beacons that are visible to
optical modalities.84
Interest in the development of microelectromechanical
systems (MEMS) for medical applications has exploded in
recent years. In the most general sense, this technology
attempts to exploit and extend the fabrication techniques used
in the microelectronics industry to medicine. The most
immediate potential of MEMS in intravascular imaging
includes the development of smaller catheter systems with a
higher sensitivity and signal amplification. MEMS will also
facilitate the development of multimodality sensors to combine the discriminatory power of 2 or more modalities to
resolve the remaining challenges within invasive imaging.
Application of Novel Technologies
The value of any diagnostic procedure is dependent on the
availability of effective treatment options. Concerning vulnerable plaque, the arsenal of potential therapies is sadly
lacking. Plaque stabilization holds promise but is only partially effective, evidenced by the 50% to 70% of acute
coronary events that it fails to prevent.85 Other pharmacologic
solutions have been suggested and await further studies.85 In
the era of drug-eluting stents, local mechanical treatment
might hold promise, including local genetic or photodynamic
therapies for plaque stabilization. The development of these
novel imaging modalities opens new avenues of research that
will likely define the future treatment of vulnerable plaque.
The relative merits of invasive, noninvasive, and serologic
markers will ultimately be decided on the basis of the
optimum treatment strategies. If plaque stabilization remains
the domain of pharmacologic therapy, then risk factor assessment in union with a serologic marker is sufficient to
determine treatment. If, however, localized or targeted intraarterial therapy proves successful, then the need for structural
definition and precise localization will drive imaging
modalities.
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Arterioscler Thromb Vasc Biol.
August 2003
Beyond research, however, do these novel technologies
serve a role within current clinical practice, and if so how,
will they be optimally employed? The answer is unknown
and is likely to remain so until natural history studies are
complete for clarification of the determinants of plaque
vulnerability and specifically, the features that result in
symptomatic plaque rupture. One can speculate that these
novel tools are best adopted as a continuum of currently
available diagnostic tools in which high-risk populations
would be identified through application of currently recommended risk factor assessment, in addition to inflammatory
markers or genetic analysis.86 In addition to instigating
aggressive risk factor modification, a proportion of these
patients might warrant further evaluation, in which, for
instance, a noninvasive imaging modality might provide a
better risk assessment and highlight regions within the arterial
tree that were of particular concern.87– 89 Targeted intravascular imaging at these sites would definitively characterize
the plaque site and ideally provide a measure of the risk of
plaque disruption. Such a vulnerability index would allow a
clear decision analysis toward appropriate therapy.
The optimum modality for intravascular imaging remains
undefined. Each modality possesses unique advantages that
might be synergistic. For example, combination of a highresolution imaging modality with a biologic measurement
from spectroscopy or thermography augments structural detail with functional assessment of metabolic or molecular
changes. Similarly, with OCT and IVUS, the potential for
synergism exists, as their relative advantages and limitations
are complementary: OCT provides high resolution but poor
penetration, whereas IVUS yields superior penetration but
poor resolution.
Conclusions
Greater understanding of the biology of atherothrombotic
disease drives interest in detection of vulnerable plaque. The
ability to detect and monitor vulnerable plaque is keenly
sought to define its natural history and support studies of
progression and regression. A number of novel imaging
modalities have recently been proposed to identify specific
areas of plaque vulnerability. Defining the optimal imaging
modality of vulnerable-plaque detection will depend on
whether treatment continues to be pharmacologic plaque
stabilization, in which case an overall risk of vulnerable
plaque would suffice, or locally directed therapy, requiring
precise anatomic definition.
Ultimately, population screening with traditional risk factors, newer serum markers, and possibly gene chips will
define a group of high-risk patients in whom noninvasive
imaging is appropriate. Features of plaque vulnerability
detected noninvasively might justify invasive modalities.
Currently, however, the optimum approach to vulnerableplaque detection incorporates structural definition of a highresolution modality, such as OCT or intravascular MRI, with
biologic processes detected by spectroscopy or
thermography.
Acknowledgments
The authors would like to acknowledge Drs Tearney and Bouma
from the Wellman Laboratory of Photomedicine, Massachusetts
General Hospital, for the OCT images. We are grateful to Magna
Laboratory (Syosset, NY) and Atheron (Los Angeles, Calif) for
images of intravascular catheters.
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Intravascular Modalities for Detection of Vulnerable Plaque: Current Status
Briain D. MacNeill, Harry C. Lowe, Masamichi Takano, Valentin Fuster and Ik-Kyung Jang
Arterioscler Thromb Vasc Biol. 2003;23:1333-1342; originally published online June 12, 2003;
doi: 10.1161/01.ATV.0000080948.08888.BF
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