Open access peer-reviewed chapter

Designating Vulnerability of Atherosclerotic Plaques

By Bukem Tanoren Bilen

Submitted: March 18th 2019Reviewed: November 27th 2019Published: December 4th 2019

DOI: 10.5772/intechopen.90664

Downloaded: 48

Abstract

Microcalcification is an indication of vulnerability of plaques in humans. With conventional imaging modalities, screening of micrometer-sized structures in vivo with high spatial resolution has not been achieved. The goal of this study is to evaluate the potentials of micro-computed tomography (micro-CT), scanning electron microscopy (SEM), energy dispersive X-ray spectroscopy (EDS), time-resolved fluorescence spectroscopy (TRFS), scanning acoustic microscopy (SAM), and photo-acoustic microscopy (PAM) in the determination of atherosclerotic plaques with microcalcifications and, therefore, the prospect of constructing a modality on a catheter system. The discrimination of microcalcifications within the fibrocalcific plaques and, therefore, the effectivity of these imaging techniques are discussed. The potential of quantum dots (QDs) in biological imaging is also elucidated since they attract great attention as contrast and therapeutic agents, owing unique properties including good light stability, low toxicity, strong fluorescence intensity, and changing emission wavelength with QD size, ranging from 10 to 100 Å in radius.

Keywords

  • atherosclerosis
  • vulnerable plaques
  • computed tomography
  • time-resolved fluorescence spectroscopy
  • scanning electron microscopy
  • scanning acoustic microscopy
  • photoacoustic microscopy
  • microcalcification
  • quantum dots

1. Introduction

Thin-cap fibroatheromas (TCFAs), which have fibrous caps of thickness of <65 μm [1], are found to be at high risk for rupture. TCFAs have necrotic cores and also calcium depositions [2, 3]. Indicators of plaque vulnerability are microcalcifications or spotty calcifications within the plaques [4, 5], not larger calcifications, which are found to be stable and no longer threatening [6, 7]. Methods such as computed tomography (CT) and echocardiography, which are conventional noninvasive imaging modalities, can detect advanced calcifications. On the other hand, magnetic resonance imaging (MRI), micro-optical coherence tomography (micro-OCT) or positron emission tomography (PET) can identify early calcifications with limitations [6, 8]. However, these modalities are either very expensive or involve ionizing radiation. Therefore, seeking an alternative technique, which can give both morphological and chemical information about tissues at subcellular level, is inevitable.

Micro-CT is an accurate imaging modality for the observation of micrometer-sized structures, which can provide much higher resolution than cone beam computed tomography (CBCT) can. Quantitatively, micro-CT generally has a resolution of less than 10 μm voxel size, while CBCT has a resolution ranging between 76 and 400 μm [9, 10, 11]. Using X-rays, micro-CT can perform in vitro processing of the structure of materials such as composites, polymers, and biological materials (bone, teeth, cartilage tissue) and imaging of up to four different substances in a material [12] by a simple sample preparation and positioning procedure and without a requirement of high vacuum or low temperatures that may adversely affect the structure. However, micro-CT is an expensive diagnostic imaging technique requiring an ionizing radiation.

Scanning electron microscopy (SEM) can obtain images with a resolution in the order of a nanometer, by scanning the surface of the specimen with a focused beam of electrons. Energy dispersive X-ray spectroscopy (EDS), which can be implemented in electron microscope systems, is a chemical characterization technique detecting all elements ranging from beryllium (Be) to uranium (U) and their distributions within samples, also by the bombardment of the specimen surface with a focused electron beam. Consequently, both morphological and chemical information about the sample can be obtained by SEM-EDS. Microcalcifications can easily be observed with SEM-EDS; however, this would again be a very expensive method.

Time-resolved fluorescence spectroscopy (TRFS) measures the average fluorescence lifetime that a fluorophore spends in a biological tissue in the excited state, when it is excited by a source from its ground state, and the lifetime of the fluorophore changes as a result of interaction with its molecular environment. Various parameters regarding the molecular environment such as binding, temperature, or concentration can be analyzed by the change in the lifetime. TRFS has not been implemented in clinics yet, however, it has been investigated widely as a new tool for the characterization of atherosclerotic plaques. The success of TRFS in obtaining compositional information about the plaques [13, 14, 15] inspired scientists to combine fluorescence lifetime imaging with other modalities such as IVUS [16], second harmonic generation (SHG) microscopy [17], OCT [18], and Raman spectroscopy [19]. Intravascular catheters using TRFS technique have also been built [20, 21], since TRFS catheters can obtain good signals even within the artery, where blood does not affect lifetime properties but fluorescence intensity.

High axial and lateral resolutions of around 20–100 μm, a good penetration depth of around 5 mm, and low cost makes ultrasound imaging very popular for the observation of soft tissue; however, it can only provide morphological information. Besides, the signal detection capability of conventional ultrasonography has to be increased for the detection of microcalcifications, since high echo signals from such small surfaces are not available [22]. These disabilities have been overcome by combining ultrasound with photoacoustic imaging, and the detection of lipid-laden plaque was achieved by providing both morphological and lipid-specific chemical information about the human coronary artery [23]. Photoacoustic microscopy (PAM) is a well-known imaging modality that combines optical and ultrasound imaging. In this technique, typically, nanosecond lasers excite the tissue, and absorbed photons lead to pressure waves via thermoelastic expansion [24]. Ultrasonic transducers capture the emerged pressure waves and produce the map of optical absorbers located within the tissue. Since ultrasonic waves scatter less in biological tissue as opposed to visible portion of electromagnetic spectrum, whole body imaging is possible with a tomographic approach [25]. To increase the penetration even further, lasers operating in the near-infrared region are preferred for excitation where tissue is relatively transparent.

Scanning acoustic microscopy (SAM) is an imaging modality which gives information about the morphology and the mechanical properties of the specimen simultaneously at microscopic levels. High-frequency ultrasound signals are focused to identify the elastic properties of biological tissues. Major advantages of SAM over other imaging techniques are no requirement of special staining and capture of an image of an area of around 5 mm x 5 mm in a couple of minutes. The speed of sound (SOS) through tissues [26, 27, 28, 29, 30, 31, 32, 33, 34, 35] or acoustic impedance of samples [36, 37] can be calculated by SAM, and two-dimensional distributions are mapped. Similarly, cells and organelles can be resolved by acoustic microscopy using higher frequencies of 100–1200 MHz [38, 39, 40, 41, 42, 43, 44, 45].

Quantum dots (QDs) are used as contrast and therapeutic agents since they have unique properties including strong fluorescence intensity with excellent light stability, low toxicity, and changing emission wavelength with QD size, ranging from 10 to 100 Å in radius [46]. Therefore, they possess great potential in the fields of biological imaging, molecular markers [47, 48, 49], and drug delivery [50, 51, 52]. QDs are useful in tumor detection [53], cardiovascular imaging [54], and cancer targeting [55]. Their high optical absorption and biocompatibility made noble metal nanoparticles to be widely used as biomarkers [56, 57]. On the other hand, graphene quantum dots (GQDs) are extensively used in biomedical applications [58, 59] since they exhibit lower cytotoxicity than cadmium (Cd), selenium (Se)-, and lead (Pb)-based quantum dots do [60]. The use of QDs as contrast agents in magnetic resonance imaging (MRI) [61], optical coherence tomography (OCT) [54], positron emission tomography (PET), single-photon emission computed tomography (SPECT), optical imaging such as fluorescence spectroscopy and Raman spectroscopy, and photoacoustic imaging (PAI) [62, 63, 64] proved their potential as diagnostic agents.

Here, we discuss the ability of these modalities in discriminating the collagen-rich areas from calcified regions within human carotid plaques. Micro-CT and SEM monitors microcalcifications, while EDS provides elemental distribution within plaques. TRFS provides information about the molecular environment of the plaques with the help of QDs. PAM is successful in imaging the fibrocalcific plaques with micrometer resolution. SAM provides micrometer resolution in morphology and also mechanical information about the samples, and therefore, differentiation of the collagen-rich areas from calcified regions is achieved.

2. Imaging of human fibrocalcific plaques

2.1 Micro-computed tomography (micro-CT)

Plaques fixed within 2% formaldehyde can be monitored with micro-CT, after obtaining micro-focal spot and arranging high-resolution detectors for X-rays. With full-scan mode 360° for each plaque, calcifications spread through are observed as can be seen in Figure 1.

Figure 1.

Micro-CT image of a fibrocalcific plaque sample in which the calcifications can be monitored clearly in three dimensions.

2.2 Scanning electron microscopy and energy dispersive X-ray spectroscopy (SEM-EDS)

SEM images of the collagen-rich and calcified regions of the plaques can be obtained as shown in Figure 2 and in Figure 3, respectively. EDS analyses of representative regions 2 and 3 are shown in Figure 4 and in Figure 5, respectively. SEM images can be used to differentiate collagen-rich and calcific regions in fibrocalcific plaques, and EDS analyses are performed for determining the compositional differences between two regions of interest. In Figure 2, collagen-rich region in one plaque sample is observed and one region is chosen for EDS analysis. Similarly, in Figure 3, calcification-rich region is visualized in one sample and one region is chosen for EDS analysis. As can be seen in Figure 4, in collagen-rich regions, calcium deposition is insignificant, while in calcified regions, as shown in Figure 5, calcium peak is pronounced.

Figure 2.

Scanning electron microscopy image of the collagen-rich region of the plaque. Energy dispersive X-ray spectroscopy is performed on the designated region 2.

Figure 3.

Scanning electron microscopy image of the calcific region of the plaque. Energy dispersive X-ray spectroscopy is performed on the designated region 3.

Figure 4.

Energy dispersive X-ray spectroscopy result of the highly calcified region 2, shown in Figure 2.

Figure 5.

Energy dispersive X-ray spectroscopy result of the highly calcified region 3, shown in Figure 3.

2.3 Time-resolved fluorescence spectroscopy (TRFS)

For TRFS experiments, cadmium-telluride/cadmium sulfide (CdTe/CdS) QDs are sprayed on plaque samples and fluorescence lifetimes of the QDs are determined.

The decay of the fluorescence intensity I(t) at time t is given as

It=i=1nAiexptτiE1

where τirepresents the fluorescence lifetime of the ith component and Aiis its corresponding decay amplitude. The fractional impact of the components to the total intensity is given by

fi=AiτiiAiτiE2

The intensity decay is evaluated using the average intensity lifetime or the average amplitude lifetime. The amplitude average lifetime is obtained from

<τ>=ifiτiE3

The intensity average lifetime is obtained from

τ=iAiτiiAiE4

The fluorescence lifetime of QDs is measured on a microscope slide prior to the experiment for the comparison of the lifetime value with those measured on the plaque samples. The lifetime of the QDs on the microscope slide is measured to be 9.24 ns. As seen in Table 1, the fluorescence lifetime values of the QDs on a plaque sample are different on various regions.

Regionτ1 (ns)τ2 (ns)<τ > (ns)<τ > (ns)χ2
12.900.611.312.170.82
23.350.721.362.300.87
34.301.001.903.030.86
44.731.092.303.601.03
54.541.011.913.151.03
64.871.062.093.500.93
73.700.831.442.410.97

Table 1.

Fluorescence decay parameters of CdTe/CdS QDs on different regions of the plaque.

Figure 6 shows the fluorescence lifetime decay curves acquired from the excitation of the CdTe/CdS QDs on the plaque sample for regions 1, 3, and 4. For the different regions of the sample, the parameters of the decay populations of the QDs confined on the plaque are determined by the two exponential decay fit, minimizing the χ2 parameter. A significant change is noticeably seen in the characteristics of these three curves for various regions of the sample. These results clearly show that there is an obvious and efficient electron transfer between the QDs and the regions of the plaque, and therefore, there are noticeably different decay parameters at collagen-rich and calcified regions. TRFS is successful in providing information about the molecular environment of the plaque.

Figure 6.

Fluorescence decay curves of the CdTe/CdS QDs on regions of 1, 3, and 4 on a plaque sample.

2.4 Scanning acoustic microscopy (SAM)

SAM images of the atherosclerotic plaques are received using acoustic impedance mode of SAM as can be seen in Figure 7. This image is constructed using the acoustic reflections from both surfaces of the reference (water) and the plaque cross section on the polystyrene substrate. The acoustic impedance distribution indicates different acoustic properties due to the variation of elasticity within the atherosclerotic plaques. The acoustic impedance is determined to be less than 2 MRayl for the collagen-rich areas and greater than 2 MRayl for the calcified areas.

Figure 7.

Acoustic impedance map of a severely calcific plaque sample obtained with acoustic impedance mode of SAM. The scanning area is 4.8 mm x 4.8 mm.

SAM in acoustic impedance mode measures the acoustic impedance of the target by comparing the reflected signal from the tissue with the one from the reference. The reflected signal from the reference is

Sref=ZrefZsubZref+ZsubS0E5

where S0is the signal generated by the transducer of SAM, Zrefis the reference’s acoustic impedance (1.50 MRayl), and Zsubis the substrate’s acoustic impedance (2.37 MRayl). The signal reflected by the target is

Starget=ZtargetZsubZtarget+ZsubS0E6

Consequently, the target’s acoustic impedance is calculated as

Ztarget=1+StargetS01StargetS0ZsubE7

2.5 Photoacoustic microscopy (PAM)

An optically resolved setting (OR-PAM), where focused spot-size on the sample determines the resolution of the system, is successful in imaging the atherosclerotic plaques, as can be seen in Figure 8. Calcific regions with greater acoustic impedance values (Figure 8b) can also be discriminated by PAM (Figure 8c).

Figure 8.

(a) Digital image, (b) normalized acoustic impedance map, and (c) photoacoustic image of the sample.

3. Quantum dots (QDs)

Photostable QDs are widely used in imaging systems. The photoluminescence image of CdTe/CdS QD aggregates excited with 430 nm is obtained by an inverted fluorescence microscope, as shown in Figure 9. The excellent fluorescence intensity with light stability of QDs makes them favorable as diagnostic agents. Use of CdTe/CdS QDs in TRFS experiments of this study reveals their potential in biomedical applications.

Figure 9.

Photoluminescence image of CdTe/CdS QDs excited with 430 nm. Scale bar is 200 = μm.

4. Conclusion

Here, we discuss the abilities of the imaging modalities on the determination of plaque components of atherosclerotic fibrocalcific plaques. The determination of collagen and calcification within the plaques is done successfully. Micro-CT, SEM, and PAM monitors the microcalcifications. EDS provides elemental distribution within plaques, while TRFS provides information about the molecular environment of the plaques by measuring the lifetime values of CdTe/CdS QDs. SAM provides micrometer resolution in morphology and also mechanical information about the samples. Acoustic impedance maps of the samples show clearly different values in collagen-rich and calcified regions. Consequently, SAM seems predominant over other modalities since SAM is capable of acquiring morphological and chemical information about the plaques simultaneously and usable in clinics. However, for in vivo studies, first, an intravascular SAM probe, similar to intravascular ultrasound (IVUS) probe, has to be developed.

Acknowledgments

Micro-CT experiments were performed in 3D Medical and Industrial Design Laboratory in Istanbul University. SEM-EDS experiments were performed in Nanotechnology Research and Application Center in Sabancı University. TRFS experiments were performed in Photonics Laboratory in Bogazici University. SAM and PAM experiments were performed in Biological and Medical Laboratory in Bogazici University.

Conflict of interest

The author declares no conflict of interest.

NotationDefinitionLocation first used
IFluorescence intensityEq. (1)
ADecay amplitudeEq. (1)
τFluorescence lifetimeEq. (1)
fFractional impactEq. (2)
ZrefReference’s acoustic impedanceEq. (5)
ZsubSubstrate’s acoustic impedanceEq. (5)
SrefReflected signal from the referenceEq. (5)
S0Signal generated by the transducerEq. (5)

Notes/thanks/other declaration

I want to thank all the colleagues who helped me to discuss the characterization techniques mentioned here. Thanks to Leyla Sener Turker for micro-CT experiments. Thanks to Meltem Sezen for SEM-EDS experiments. Thanks to M. Naci Inci for TRFS experiments. Many thanks to M. Burcin Unlu for allowing me to use all of the facilities of Biological and Medical Laboratory not only for SAM and PAM experiments but also for many other research topics.

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Bukem Tanoren Bilen (December 4th 2019). Designating Vulnerability of Atherosclerotic Plaques, Lipid Peroxidation Research, Mahmoud Ahmed Mansour, IntechOpen, DOI: 10.5772/intechopen.90664. Available from:

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