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A Theragnostic HIFU Transducer and System for Inherently Registered Imaging and Therapy
A Theragnostic HIFU Transducer and System for Inherently Registered Imaging and Therapy
A Theragnostic HIFU Transducer and System for Inherently Registered Imaging and Therapy
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Evaluation of the HIFU-Converted VA Imaging System. To verify performance of the HIFU-converted imaging system, firstly an agar-based phantom (1% agar with deionized water) was designed for inspecting its point spread functions (PSF). Two nylon strings (diameter about 500 um) were embedded in the agar-based tissue mimicking material, acting as two points. Raster scanning of the two strings was conducted on a plane 10 cm away from the phantom surface (Fig. 3(a)). The ARF-induced dynamic vibration lasted about 20 ms at each scanning position and the robot arm would move to the next one. A 20 ms period was used to guarantee that the vibrating signals can be captured in the reception, due to the limited accuracy of the synchronization between the HIFU stimulation and the hydrophone reception. This stimulation time could be further reduced if necessary. Under this imaging mode, the transmitted acoustic power was about 5 W by the HIFU transducer, with 2.5Wfrom each group of the elements. For each spatial position, the 9.6 kHz low-frequency acoustic emission was acquired by the hydrophone, bandpass filtered (100 Hz ~ 99 kHz) and amplified by an analogue filter (SR650, Thinksrs, USA), and in the end transferred to a computer for post processing. In the data processing, the 20 ms acoustic emission signals were first transformed to its spectrum by the FFT algorithm. The spectral component at 9.6 kHz, which is the target low-frequency signal coming from the tissue vibration, was picked up as the interested signal. Amplitude at this specific frequency in the spectrum was used as the value for VA imaging at that corresponding spatial position. The phase information was discarded. With all the values at different positions, a 2D VA image was formed for display. Unless otherwise specified, all experiments in this study were conducted in the same manner under similar parameter settings, and imaging data collected were also processed in this manner. To make a comparison, this HIFU-converted imaging system was also tested on an agar-graphite phantom which was fabricated in-house, and compared with the conventional B-mode ultrasound. The phantom's base material was 1% agar with deionized water, within which two agar-graphite poles (1% agar mixed with 0.5% graphite powder in deionized water) with diameter of 4 mm were buried [34]. The distance between centroids of the two poles was about 5 mm (Fig. 3(b)). A raster scanning of the two poles from the transverse perspective was conducted, and the imaging depth was also about 10 cm. The same phantom objectwas submerged in awater tank and scanned by the conventional B-mode ultrasound using a C5-2v probe connected to a Vantage 256 system (Verasonics, Kirkland, WA, USA).
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1 Evaluation of the HIFU-Converted VA Imaging System. 2 To verify performance of the HIFU-converted imaging system, firstly an agar-based phantom (1% agar with deionized water) was designed for inspecting its point spread functions (PSF). 3 Two nylon strings (diameter about 500 um) were embedded in the agar-based tissue mimicking material, acting as two points. 4 Raster scanning of the two strings was conducted on a plane 10 cm away from the phantom surface (Fig. 3(a)). 5 The ARF-induced dynamic vibration lasted about 20 ms at each scanning position and the robot arm would move to the next one. 6 A 20 ms period was used to guarantee that the vibrating signals can be captured in the reception, due to the limited accuracy of the synchronization between the HIFU stimulation and the hydrophone reception. 7 This stimulation time could be further reduced if necessary. 8 Under this imaging mode, the transmitted acoustic power was about 5 W by the HIFU transducer, with 2.5Wfrom each group of the elements. 9 For each spatial position, the 9.6 kHz low-frequency acoustic emission was acquired by the hydrophone, bandpass filtered (100 Hz ~ 99 kHz) and amplified by an analogue filter (SR650, Thinksrs, USA), and in the end transferred to a computer for post processing. 10 In the data processing, the 20 ms acoustic emission signals were first transformed to its spectrum by the FFT algorithm. 11 The spectral component at 9.6 kHz, which is the target low-frequency signal coming from the tissue vibration, was picked up as the interested signal. 12 Amplitude at this specific frequency in the spectrum was used as the value for VA imaging at that corresponding spatial position. 13 The phase information was discarded. 14 With all the values at different positions, a 2D VA image was formed for display. 15 Unless otherwise specified, all experiments in this study were conducted in the same manner under similar parameter settings, and imaging data collected were also processed in this manner. 16 To make a comparison, this HIFU-converted imaging system was also tested on an agar-graphite phantom which was fabricated in-house, and compared with the conventional B-mode ultrasound. 17 The phantom's base material was 1% agar with deionized water, within which two agar-graphite poles (1% agar mixed with 0.5% graphite powder in deionized water) with diameter of 4 mm were buried [34]. 18 The distance between centroids of the two poles was about 5 mm (Fig. 3(b)). 19 A raster scanning of the two poles from the transverse perspective was conducted, and the imaging depth was also about 10 cm. 20 The same phantom objectwas submerged in awater tank and scanned by the conventional B-mode ultrasound using a C5-2v probe connected to a Vantage 256 system (Verasonics, Kirkland, WA, USA).