Abstract
Background:
To explore the potential of synchrotron radiation (SR) phase contrast imaging (PCI) for real-time microbubble formation monitoring during radiofrequency ablation (RFA).
Methods:
RFA was performed on ex vivo porcine muscle tissue using unipolar and multi-tined expandable electrodes. Images of microbubble formation in the samples were captured by both SR PCI and absorption contrast imaging. The synchronous ablation temperature was recorded. Each RFA electrode type group contained 6 samples. Ablation size was assessed by histologic examination.
Results:
Microbubble formation during RFA could be visualized by SR PCI. The diameter of the microbubbles revealed on the image ranged from tens of microns to several millimeters, and these microbubbles first appeared at the edge of the RFA electrode when the target region temperature reached approximately 60°C and rapidly extended outwards. The average microbubble range measured on PCI was 17.66 ± 0.74 mm. The average range of coagulation necrosis measured by histological examination was 17.22 ± 0.38 mm. There was no significant difference between them (P > 0.05). The range of microbubbles corresponded to the ablation zone.
Conclusion:
PCI enabled real-time high-resolution visualization of microbubble formation during RFA, indicating a potential for its use in ablation monitoring.
Background
Radiofrequency ablation (RFA) has gained widespread acceptance in the local therapy of various benign and malignant solid lesions, particularly those involving the liver, lung, kidney and musculoskeletal system (–). It is usually performed percutaneously under image guidance and is appropriate for inoperable patients with comorbidities.
In clinical practice, it is difficult to predict the RFA zone. The size and shape of the RFA zone can vary according to many factors, including the location of the lesion, the histological characteristics of the lesion and adjacent tissues, the type of electrode, duration of ablation and the heat sink phenomenon (–). This disadvantage may explain why the local recurrence rate after RFA is higher than that after surgery, especially for voluminous lesions (–). Some studies show a sharp rise in the rate of local recurrences and a decline of overall survival for tumors over 3–5 cm (–). And nowadays, the indication of RFA is usually limited to the lesions less than 5 cm. If the RFA zone can be monitored accurately during the procedure, the relatively high local residue and recurrence rate could be overcome.
Currently, RFA procedures are generally performed under ultrasound (US), computed tomography (CT), or magnetic resonance imaging (MRI) guidance (–). These traditional image guidance methods can help to localize the RFA electrode to the lesion site but do not serve as a real-time monitoring tool to evaluate the ablation zone during the procedure due to their physical limitations. To overcome these disadvantages, a new monitoring method should be employed. Synchrotron radiation (SR) phase contrast imaging (PCI) is more functional than conditional absorption contrast imaging (ACI) and is characterized by its high spatial resolution of sub-micron level and high temporal resolution of milliseconds (–). Moreover, according to the phase shift caused by variations in the refractive index and thickness of materials (), PCI is effective at the border of two different structures and can provide significant edge enhancement for low-density materials, including gas, organic materials, and soft tissues (, –).
In previous studies, the range of microbubbles formed during RFA corresponded to the RFA zone (, ). Therefore, in this study, we planned to use PCI to reveal microbubble formation during RFA using two different types of frequently used RFA electrodes and evaluate the potential for real-time monitoring of RFA.
Materials and Methods
All experiments were conducted in accordance with the guidelines established and approved by Shanghai Jiao Tong University’s Institutional Animal Care and Use Committee (Approval number: B-2015-011).
Sample Preparation
Porcine muscle (Lingchang Biotech, Shanghai, China) was used and cut into appropriately sized samples (3 × 3 × 3 cm for the multi-tined electrode, 2.5 × 2.5 × 2.5 cm for the uni-polar electrode).
In clinical practice, RFA is most frequently applied to liver and muscular like tissue. Porcine liver was excluded at this study, because ex vivo hepatic vessels contain gas, which can be revealed by PCI and hamper the observation of micro-bubble formation during RFA.
SR Parameters
The study was performed in the BL13W1 beamline at the Shanghai Synchrotron Radiation Facility (SSRF, China). A 3.5 GeV electron storage ring generated X-rays with an energy range of 8–72.5 keV and an average beam current of 180 mA. X-rays were then monochromatized by a double-crystal monochromator with Si (111) and Si (311) crystals at an energy level of 22 KeV. Energy resolution was ΔE/E<5 × 103. Incoming X-rays were converted into visible light using a 100 μm thick CdWO4 cleaved single crystal scintillator and consecutively captured by a CCD camera (Photonic Science, Britain) with pixel size of 9 μm. The sample was placed 34 m downstream of the SR source. The distance between the sample and the CCD camera had a changeable range of 8 m.
ACI and PCI Parameters
A total of 0.2 ml of gas was injected into the central of one 2.5 × 2.5 × 2.5 cm sample by a 17G needle, in order to identify the different presentation of bubbles on SR ACI and PCI.
Synchrotron radiation images of this sample were obtained at 22 KeV with two different object-to-detector distances of 10 and 600 mm. At an object-to-detector distance of 10 mm, detector was placed immediately behind the sample, the phase contrast effect is minimal, ACI was obtained (Figure 1A). The phase contrast effect increases with the augmentation of object-to-detector distance. At an object-to-detector distance of 600 mm, PCI can be captured (Figure 1B). As the quality of visible bubbles using PCI was greater than that using ACI. PCI was then used to monitor the following RFA procedure.
FIGURE 1
RFA Parameters
Radiofrequency ablation was performed with a RITA Model 1500X radiofrequency generator, 250 W, 460 Hz frequency (RITA Medical Systems, Mountain View, CA, United States). The RFA electrodes included a unipolar electrode and multi-tined expandable electrodes. The RFA time was 7 min for the unipolar electrode and 5 min for the multi-tined expandable electrodes with a 1 cm expandable range. The energy level was 90 W. The target goal temperature was set to 105°C, and the real-time actual temperature was measured by thermodetectors in the electrodes. The RFA electrodes were localized to the center of the sample, which was placed on a translation stage. The electrode axis was perpendicular to the synchrotron source and confirmed by SR fluoroscopy. The loop electrode was adhered to the underside of the sample. Each RFA electrode type group contained six samples, and there were 12 RFA ablations performed during the course of this study.
Image Acquisition
Images were captured with an exposure time of 40 ms at 98 frames per minute. Background noise was eliminated using Image-Pro Plus 6.0 (Media Cybernetics Inc., United States), and image quality was compared. The microbubble formation process was pseudo-colored using a normalization algorithm via MATLAB 7.0 (MathWorks, United States). The range of microbubbles, RFA temperature and RFA time were synchronously recorded.
Pathological Analysis
Samples were bisected across the long axe of the electrode track for immediate gross examination. The width of the RFA ablation zone was measured by calipers. The sample was then fixed in 10% formalin and later stained with hematoxylin and eosin (H&E) for histomorphological analysis.
Statistical Analysis
The data are presented as the means ± standard error. Using SPSS 19.0 software, the range of microbubble measured on the PCI and the range of RFA zone showed on gross examination and histomorphological analysis were compared using the paired t-test. A P-value of less than 0.05 was defined as statistically significant.
Results
Comparison of Bubble Morphology Between PCI and ACI
The PCI and ACI characteristics of bubbles are displayed in Figure 1 after an injection of gas in the same sample. The contrast between bubbles and surrounding tissue was not clear in ACI (Figure 1a). After adjusting the sample-to-detector distance to 600 mm, bubbles with sharp edges could be clearly visualized by PCI (Figure 1b). The quality of visible bubbles using PCI was greater than that using ACI.
PCI of Microbubble Formation During RFA
Images were obtained 20 s after RFA began. For the unipolar electrode, 40 s after RFA began, when the local temperature reached approximately 60°C, microbubbles began to appear at the electrode edge. For the multi-tined expandable electrodes, 60 s after RFA began, microbubbles began to appear at the same temperature of 60°C. During RFA, from the electrode surface outward, the newly generated microbubbles were irregular and cleft-like in shape. As the temperature rose, microbubbles continued to increase and expand rapidly outward. The density and range of microbubbles increased with the rise in temperature and RFA duration. The complete microbubble diffusion process was revealed and pseudo-colored (Figures 2, 3).
FIGURE 2
FIGURE 3
The RFA temperature-time curve and microbubble range-time curve of the unipolar electrode were recorded (Figure 4).
FIGURE 4
PCI of Microbubble Transformation After RFA
Images were captured from 10 to 30 min after RFA. Microbubbles remained in the tissue. Gradually, the microbubbles became regular circle- or oval-shaped and displayed a tendency to fuse together. The diameter of the microbubbles ranged from tens of microns to several millimeters (Figure 5).
FIGURE 5
Tissue Section Images After RFA
Sectional images of the sample and pathological sections (Figure 6) were obtained after RFA.
FIGURE 6
Radiofrequency ablation was performed on six samples using a unipolar electrode. The average microbubble range measured on PCI was 17.66 ± 0.74 mm. The average range of coagulation necrosis (including complete and partial coagulation necrotic areas) measured by histological examination was 17.22 ± 0.38 mm. There was no significant difference between them (P > 0.05).
The diameter of the ablation zone of the multi-tined expandable electrodes was more than 20 mm. The final microbubble range could not be measured because the field of our CCD vision was limited to 20 mm.
Discussion
Radiofrequency ablation electrodes can deliver a high-frequency sinusoidal electromagnetic current that induces agitation of tissue ions, after which energy dissipates as heat through ionic friction (). If the tissue temperature reaches approximately 60°C and this temperature is maintained for a few seconds, irreversible damage can occur due to DNA denaturation, manifesting as coagulation necrosis ().
The key point of real-time monitoring of RFA is to identify coagulation necrosis from the adjacent tissue. However, the problem in exact quantification of the coagulation necrotic zone still prevails and hinders the treatment effect of RFA therapy (). The imaging techniques used during the RFA procedure include US, CT, and MRI, which serve as ideal guidance tools. However, they have some limitations in the real-time monitoring of the ablation area. Hypersonic microbubble formation during the ablation and acoustic shadow of the RFA electrode shield the lesion and impair the quality of US images (, 39). CT cannot clearly delineate the boundary between the coagulation zone and the area of peripheral edema because of their similar densities. Frequency interference between the RF generator and the MR imager is difficult to avoid. Most current MRI and RFA devices do not allow for simultaneous MRI and the application of RFA energy ().
Previous studies have used US and US Nakagami imaging to monitor RFA microbubble formation, the range of which corresponded with the ablation zone (, ). However, microbubbles of tens of microns in diameter cannot be directly visualized using US imaging, as it has limited spatial resolution. Moreover, the posterior margin of the ablation zone is difficult to observe due to electrode acoustic shadow and irregular reflections of ultrasound by microbubbles ().
Variations in the refractive index between gas and soft tissue are evident and can cause an edge enhancement effect on PCI. This effect is a significant advantage of PCI and is the result of the high spatial coherence of inline PCI achievable with a large object-to-detector distance (). PCI is more suitable for microbubble observation than ACI and can reveal microbubbles of tens of microns in size. With the characteristic of high temporal resolution, PCI can even detect microbubbles newly formed on the surface of RFA electrodes. In our study, microbubble formation during the entire RFA procedure and the transformation after RFA could be directly visualized by PCI.
The hypothesis of microbubble formation during RFA is as follows. First, when the temperature of the tissue reaches the boiling point, vapor is generated in the form of microbubbles. Second, microbubbles in the blood within microvessels flow out because of the hyperemia induced by ablation (40). As the samples used in this study were ex vivo, the potential interference of microvessels could be excluded, and the first hypothesis might be more reasonable.
Microbubbles appeared when the temperature increased and diffused outward from the surface of RFA electrodes. We observed a phenomenon during this procedure: the temperature threshold of microbubble formation was 60°C, which is much lower than the boiling point of water. There are two possible explanations: First, because of the relatively low heat conductivity of the tissue, vapor could be generated at 60°C and manifest as microbubbles. Second, local temperature may have reached the boiling point, but the area may be limited and could not be accurately measured by thermodetectors in the electrodes. The relationship between microbubble formation and the exact local temperature should be explored in future studies.
Nevertheless, microbubble formation indicates that the local tissue temperature has reached at least 60°C. At this temperature, coagulation necrosis in tissues is irreversible (). According to this phenomenon, the microbubble range revealed by PCI may reflect the coagulation necrotic area.
After RFA, microbubbles remained in the ablation zone on PCI. Some fused together and formed bubbles of several millimeters in diameter. This phenomenon can explain the origin of bubbles observed on CT images in some clinical cases after RFA ().
In previous studies, SR PCI has showed some advantages in the clinical imaging diagnostic domain. Compared to the traditional mammography, the image quality was improved by using PCI (41, 42). A significant reduction of radiation dose was obtained by SR high resolution CT (43). According to our study, with its high resolution of low-density materials and high temporal resolution, SR PCI has the potential to be used in real-time monitoring of the RFA zone via microbubble imaging.
There are some limitations to our study. First, an ex vivo study might not reflect actual microbubble transformation in vivo, and the influence of microvessel perfusion and the heat sink phenomenon should be considered. Second, the RFA zone of multi-tined expandable electrodes was larger than the field of the CCD, and its range could not be measured by PCI. Third, although in our study, the range of microbubbles after RFA using unipolar electrodes was close to that measured on histological cross-sections, which contained complete and partial coagulation necrotic areas; additionally, the transition between complete coagulation necrosis and partial coagulation necrosis was gradual, and the boundary was indistinct. Further quantitative studies should be carried out to analyze the relationship between the density of microbubbles and the degree of coagulation necrosis.
Conclusion
Synchrotron radiation PCI enabled real-time high-resolution visualization of microbubble formation during RFA. The temperature threshold of micro-bubble appearance was about 60°C. At this temperature level, protein denaturation and cellular damage is irreversible, meaning that the range of micro-bubbles corresponds with cell necrosis area, which was confirmed by pathological examinations in our study. In summary, SR PCI has a potential for real-time monitoring of RFA zone.
Statements
Data availability statement
The datasets generated for this study are available on request to the corresponding author.
Ethics statement
The animal study was reviewed and approved by the Shanghai Jiao Tong University School of Medicine Institutional Animal Care & Use Committee.
Author contributions
WH, JL, and ZWa designed the research and supervised the report. ZWu and RT performed the research. WH and JL wrote the manuscript. XD, KC, and ZWa supervised the report. KC, ZWu, and QW analyzed the data. All authors contributed to the article and approved the submitted version.
Funding
This work was supported by the National Science Foundation of China (Nos. 81471808 and 81771949), Shanghai Municipal Commission of Health and Family Planning (No. 201640087), Clinical Key Specialist Construction Project of Shanghai Municipal Health Commission [Interventional Radiology (No. shslczdzk06002) & 3D Printing (No. shslczdzk07002)], and Shanghai Municipal Key Clinical Specialty (No. ZK2019A02). The above foundations are all related to the content of the article.
Conflict of interest
The authors declare that the research was conducted in the absence of any commercial or financial relationships that could be construed as a potential conflict of interest.
Abbreviations
- ACI
absorption contrast imaging
- CT
computed tomography
- MRI
magnetic resonance imaging
- PCI
phase contrast imaging
- RFA
radiofrequency ablation
- SR
synchrotron radiation
- US
ultrasound.
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Summary
Keywords
radiofrequency ablation, synchrotron, microbubbles, radiation, phase contrast imaging
Citation
Huang W, Lu J, Tang R, Wu Z, Wang Q, Ding X, Wang Z and Chen K (2020) Phase Contrast Imaging Based Microbubble Monitoring of Radiofrequency Ablation: An ex vivo Study. Front. Oncol. 10:1709. doi: 10.3389/fonc.2020.01709
Received
25 December 2019
Accepted
30 July 2020
Published
25 August 2020
Volume
10 - 2020
Edited by
Po-Hsiang Tsui, Chang Gung University, Taiwan
Reviewed by
Xiaoming Yang, University of Washington, United States; Ji Hoon Shin, University of Ulsan, South Korea
Updates
Copyright
© 2020 Huang, Lu, Tang, Wu, Wang, Ding, Wang and Chen.
This is an open-access article distributed under the terms of the Creative Commons Attribution License (CC BY). The use, distribution or reproduction in other forums is permitted, provided the original author(s) and the copyright owner(s) are credited and that the original publication in this journal is cited, in accordance with accepted academic practice. No use, distribution or reproduction is permitted which does not comply with these terms.
*Correspondence: Zhongmin Wang, wzm0722@hotmail.com
†These authors have contributed equally to this work
This article was submitted to Cancer Imaging and Image-directed Interventions, a section of the journal Frontiers in Oncology
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