MOJ ISSN: 2471-139X MOJAP

Anatomy & Physiology
Mini Review
Volume 1 Issue 1 - 2015
Optical Coherence Tomography in Coronary Atherosclerosis
Nikunj R Shah1,2*, Philippa J Howlett1, David S Fluck2, Mark Williams2, Adam Jacques2 and Michael Mahmoudi1,2
1Faculty of Health and Medical Sciences, University of Surrey, UK
2Ashford & St. Peter's Hospital NHS Foundation Trust, UK
Received:July 09, 2015 | Published: July 23, 2015
*Corresponding author: Nikunj R Shah, Faculty of Health and Medical Sciences, University of Surrey, UK, Tel: 07974 561197; Email:
Citation: Shah NR, Howlett PJ, Fluck DS, Williams M, Jacques A, et al. (2015) Optical Coherence Tomography in Coronary Atherosclerosis. MOJ Anat Physiol 1(1): 00003 DOI: 10.15406/mojap.2015.01.00003

Abstract

Despite developments in therapeutic and diagnostic technologies, the global burden of atherosclerotic coronary artery disease is increasing. Intravascular imaging has become an invaluable adjunct to percutaneous coronary intervention. Optical coherence tomography (OCT) is a catheter based invasive imaging system that uses light instead of ultrasound to produce high resolution in vivo images of coronary arteries and deployed stents. The technical aspects of intracoronary image acquisition, advantages, disadvantages of use and current applications of OCT in coronary atherosclerosis are discussed.

Keywords: Optical coherence tomography; Atherosclerosis; Coronary artery disease

Abbreviations

IVUS: Intravascular Ultrasound; OCT: Optical Coherence Tomography; FFR: Fractional Flow Reserve; TD-OCT: Tissue-Domain Optical Coherence Tomography; FD-OCT: Frequency-Domain Optical Coherence Tomography; PCI: Percutaneous Coronary Intervention; TCFA: Thin-Capped Fibroatheroma; MACE: Major Adverse Cardiovascular Event

Introduction

Despite advances in therapeutic and diagnostic technologies, ischaemic heart disease remains a global leading cause of death [1]. Most cases result from atherosclerosis, an inflammatory and fibro-proliferative process resulting in activation of growth factors, vasoregulatory mechanisms and cytokines resulting in intimal thickening and subsequent endoluminal obstruction [2]. More sophisticated interventional techniques have been adopted to combat the increasing burden of atherosclerosis, including intravascular ultrasound (IVUS), fractional flow reserve (FFR) and more recently, optical coherence tomography (OCT). This paper provides an overview of the principles and current uses of OCT in diagnosing and guiding the treatment of atherosclerotic coronary artery disease.

Principles of optical coherence tomography
Intravascular OCT provides a method of obtaining cross-sectional tomographic vascular imaging with definition that is superior to other currently available modalities. It acts as an optical analogue of IVUS, where ultrasound is replaced by light that is reflected or back-scattered from internal structures within tissue. This 'echo time delay' produces a measurable signal intensity or magnitude. As the speed of light does not allow direct measurement of the echo time delay, interferometric techniques are employed to analyse the reflected light signal. Two main technologies exist to create OCT images, time domain (TD-OCT) and Fourier or frequency domain (FD-OCT). While TD-OCT uses a moving mirror as its reference arm and a broadband light source, FD-OCT uses a fixed mirror with a variable frequency light source allowing simultaneous detection of reflections from all echo time delays [3]. This allows faster image acquisition rates, improved signal-to-noise ratio with subsequent higher quality imaging, making FD-OCT the imaging mode of preference [4]. By utilising this ultrafast frequency swept near-infrared light source to image the vessel, FD-OCT is able to gain axial resolutions in the region of 10 to 15µm and lateral resolutions of 20 to 90µm. The rotating fibre-optic system creates a detailed tissue image with a ten-fold greater resolution than that achieved with IVUS [5-7], due to the shorter wavelength (1280-1350nm range) of the imaging light compared with ultrasound. However, the shorter wavelength limits tissue penetration to 1 to 3mm as compared with 4 to 8mm achieved with IVUS, with the exception of calcified lesions in which ultrasound has a limited penetration [8].

Due to the high attenuation of light by red blood cells, effective OCT requires the clearing or flushing of blood from the lumen prior to imaging the desired segment of vessel. The slow acquisition speed of TD-OCT requires proximal balloon occlusion of the coronary of interest, with subsequent flushing of the artery to remove blood from the field of view. This limits its widespread adoption because of prolonged intravascular occlusion potentiating the risk of coronary damage and myocardial ischaemia. In FD-OCT, a greater frame rate is achieved because the swept source laser can be focussed quicker than the reference mirror can be moved in TD-OCT. Therefore, comprehensive volumetric microscopy of the vessel can be safely performed with the intra-arterial flushing of blood with a 10-15ml bolus of crystalloid solution, usually radio contrast, obviating the need for balloon occlusion of the vessel [9].

OCT in coronary atherosclerosis, percutaneous coronary intervention and plaque characterisation
Both TD and FD-OCT are deemed safe in assessing atherosclerotic plaque characteristics, as well as guiding percutaneous coronary intervention (PCI) [10-13]. The high definition of OCT imaging allows all aspects of plaque morphology to be accurately delineated including fibrous tissue, lipid accumulation and calcific deposition [6,14].

A large proportion of acute coronary events arise from sudden luminal obstruction caused by thrombosis as a result of plaque rupture or erosion. Our current understanding of vulnerable plaque biology suggests that approximately 80% of significant plaque rupture occurs within inflamed thin-capped fibroatheromas (TCFA) [15]. It is accepted that TCFA comprise of a thin fibrous cap less than 65µm in diameter, overlying a large necrotic lipid pool (>2 quadrants of the cross-sectional image), with associated inflammatory cell cap infiltration [16]. Studies using virtual histology IVUS have previously determined TCFA as a predictor of major adverse cardiovascular events (MACE) [17,18]. As OCT provides superior in vivo characterisation of plaque morphology, identifying TCFA may prospectively identify the most vulnerable lesions and therefore influence prognosis. This has been validated in clinical studies comparing OCT with IVUS in acute coronary cohorts [16,19], particularly as a rupture-prone fibrous cap less than 65 microns is well under the resolution capacity of IVUS. In vivo and post mortem studies have also corroborated the ability of OCT to accurately detect TCFA, especially in identifying its increased incidence in myocardial infarction [20-22]. Furthermore, OCT has been successfully used to examine the role of pharmacological interventions on plaque anatomy and stability [23-25].

Figure 1: Frequency domain-optical coherence tomography imaging of atherosclerotic arteries showing A) fibrotic plaque, B) fibrocalcific plaque, C) lipid-rich fibroatheroma and D) a thin-cap (arrow) fibroatheroma. Lipid/calcification arcs and fibrous cap thickness are marked

In normal vessels, the coronary artery appears as a three layered structure with OCT. A dark band denotes the low signal muscular media layer between the internal elastic lamina and external elastic lamina. Due to its limited tissue penetration, however, OCT is not well suited to assess significant vascular remodelling and total plaque volume. Fibrous plaques tend to appear as high signal homogenous regions with high levels of back-scatter. Calcifications within plaques are identified by the presence of well circumscribed, low back-scattering heterogenous areas [6,8,14,19]. Lipid pools, in contrast, are less well delineated than calcification and appear as diffusely bordered, low signal areas with more heterogenous back-scattering than fibrous plaques [6,8,14,19]. In reality, an overlying signal-rich band usually corresponds to a fibrous cap of varying thickness (See Figure 1). Thrombi are identified by the protrusion of a mass into the vessel lumen discontinuous from the arterial wall and may be found in culprit lesions of patients with acute coronary syndromes [6,8,14,19,26,27]. In the early stages of thrombogenesis, a rapidly organising thrombus traps blood cell constituents and on maturation, it becomes more fibrous and less cellular, turning from 'red' to 'white'. OCT has been shown to accurately distinguish between red and white thrombi, and may therefore aid in determining optimal therapeutic strategy [26]. Red thrombi, consisting mainly of signal attenuating red cells, are characterised by high back-scattering protrusions with signal-free shadowing. White thrombi, comprising predominantly of platelets and white cells, appear as signal-rich, low back-scattering projections into the vessel lumen 26. Plaque ulceration or rupture can be detected by OCT as a ruptured fibrous cap that connects the lumen with the lipid pool. These may or may not be associated with superimposed thrombus. (See Table)

Tissue Characteristics

OCT characteristics

Fibrous

Homogenous

High reflectivity

Low attenuation

Lipid

Diffuse edges

High reflectivity

High attenuation

Calcific

Sharp well defined edges

Low reflectivity (compared to IVUS)

Low attenuation

Red thrombus

Mass protruding into vessel lumen

Medium reflectivity

High attenuation

White thrombus

Luminal protrusion

Medium reflectivity

Low attenuation

Stents: Metallic

High reflectivity

High attenuation

Bioresorbable

Low reflectivity (if residual polymer present)

Low attenuation

Table 1: Image characteristics of optical coherence tomography with different plaque morphologies.

                                                      (IVUS - intravascular ultrasound)

In addition to plaque characterisation, OCT has been used to optimise and guide PCI by providing a clear depiction of the boundaries between vessel, lumen and metallic stent struts. The near infra-red OCT light does not penetrate metal, hence stent struts are visualized as linear structures with strong surface reflection and typical dorsal shadowing [28]. Earlier papers allude to OCT outperforming IVUS in detecting spontaneous and PCI-induced dissection, tissue prolapse and incomplete stent apposition, all of which have been implicated in acute as well as late stent thrombosis [12,29,30]. Limited outcome data also exists to show OCT-guided PCI as superior to angiography alone [31]. This unrivalled endovascular resolution has allowed assessment of the vascular response at individual stent strut level following device deployment. Hence, numerous in-vivo OCT studies have exploited its capability to study factors related to the prognosis of stent-implanted lesions, including neointimal hyperplasia, stent strut coverage, stent malapposition and in-stent neoatherosclerosis [32-34].

Technical drawbacks to OCT, in addition to limited tissue depth penetration, include inability to image plaques located at the very ostium of the coronaries, particularly with TD-OCT where balloon occlusion is required. Moreover, distinguishing different plaque morphology relies on operator experience and is subject to an element of inter-observer variability, analogous to grey-scale with IVUS [35].

Conclusion

Intracoronary OCT currently provides unparalleled high resolution anatomical data which the interventional cardiologist can use to optimise treatment. It allows detailed structural analysis of atherosclerotic plaques and helps characterise the vascular healing process post PCI. However, there are still limitations with this technique and alternative imaging modalities such as IVUS still have a role in plaque delineation and PCI optimisation. Future developments such as micro-OCT will offer spatial resolution that is ten times that of FD-OCT, permitting sub-cellular analysis of the atherosclerotic process and improved diagnostic capabilities for the prospective prevention of coronary artery disease. Potential research combining doppler-like signal detection with OCT will allow integration of physiological and anatomical assessment using a single device.

Acknowledgement

NS is the primary author. PH contributed to the manuscript and MM proof-read the manuscript and is the guarantor.

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