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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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However, the sonication field for imaging needs to be uniform in its intensity to guarantee high quality echoes from different spatial locations. In this sense, the concaved transducer is not optimal for conventional ultrasound imaging. Several improved beamforming methods were studied to mitigate the above effect, showing that it was possible to integrate imaging and therapy with this dual-mode device. One of the main conflicts in this dual-mode paradigm is that it requires a rather wide bandwidth for the transducer because the typical frequency (< 3 MHz) for HIFU ablation is quite different from the frequency (2-10 MHz) for a fairly good ultrasound imaging. Although piezo-composite-based transducer was adopted to broaden the bandwidth, this problem has not been fully tackled. In addition, some compromises always had to be made to balance the performances between imaging and therapy. For example, transmitting elements with high acoustic transmission rate are important for therapeutic efficiency, but it cannot avoid deteriorating the pulse shape in the imaging mode. Also, a large number of transmitting and sensing elements with small size on the concave array are important for the imaging quality, which inevitably affects the therapeutic efficiency in many ways. By contrast, the strategy in this study for achieving an inherent spatial registration between imaging and therapy is to introduce a relatively unique imaging modality called vibro-acoustography (VA). The VA method was first proposed by Fatemi in 1998 [16]. Although it is still an acoustic imaging technique, the principle behind VA is no longer based on pulse-echo imaging, but rather on tissue vibrations being stimulated by modulated oscillating acoustic radiation force (ARF) [17], [18], [19]. The tissue vibrating takes place at low frequency (normally less than 100 kHz) and a highly sensitive hydrophone is used to receive the acoustic signals. The ARF-induced vibration can be realized in different means, and the most common one is to generate two intersecting beams at slightly different frequencies (f1 and f2), resulting in the vibration at a frequency equal to |f1 − f2 | [18]. It is thought that the acoustic emissions carry unique information reflecting mechanical and acoustic properties of the vibrating tissue, such as its stiffness, scattering and absorption within the intersected region [19]. In the past two decades, the VA imaging has been explored in vivo in a range of clinical applications, including calcification detection [20], [21], [22], breast imaging [23], [24], thyroid imaging [25], and brain injury detection [26]. In addition to its applications in diagnosis, the VA method has also been studied in the HIFU-based therapy. In a series of studies, Hynynen et al.
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1 However, the sonication field for imaging needs to be uniform in its intensity to guarantee high quality echoes from different spatial locations. 2 In this sense, the concaved transducer is not optimal for conventional ultrasound imaging. 3 Several improved beamforming methods were studied to mitigate the above effect, showing that it was possible to integrate imaging and therapy with this dual-mode device. 4 One of the main conflicts in this dual-mode paradigm is that it requires a rather wide bandwidth for the transducer because the typical frequency (< 3 MHz) for HIFU ablation is quite different from the frequency (2-10 MHz) for a fairly good ultrasound imaging. 5 Although piezo-composite-based transducer was adopted to broaden the bandwidth, this problem has not been fully tackled. 6 In addition, some compromises always had to be made to balance the performances between imaging and therapy. 7 For example, transmitting elements with high acoustic transmission rate are important for therapeutic efficiency, but it cannot avoid deteriorating the pulse shape in the imaging mode. 8 Also, a large number of transmitting and sensing elements with small size on the concave array are important for the imaging quality, which inevitably affects the therapeutic efficiency in many ways. 9 By contrast, the strategy in this study for achieving an inherent spatial registration between imaging and therapy is to introduce a relatively unique imaging modality called vibro-acoustography (VA). 10 The VA method was first proposed by Fatemi in 1998 [16]. 11 Although it is still an acoustic imaging technique, the principle behind VA is no longer based on pulse-echo imaging, but rather on tissue vibrations being stimulated by modulated oscillating acoustic radiation force (ARF) [17], [18], [19]. 12 The tissue vibrating takes place at low frequency (normally less than 100 kHz) and a highly sensitive hydrophone is used to receive the acoustic signals. 13 The ARF-induced vibration can be realized in different means, and the most common one is to generate two intersecting beams at slightly different frequencies (f1 and f2), resulting in the vibration at a frequency equal to |f1 − f2 | [18]. 14 It is thought that the acoustic emissions carry unique information reflecting mechanical and acoustic properties of the vibrating tissue, such as its stiffness, scattering and absorption within the intersected region [19]. 15 In the past two decades, the VA imaging has been explored in vivo in a range of clinical applications, including calcification detection [20], [21], [22], breast imaging [23], [24], thyroid imaging [25], and brain injury detection [26]. 16 In addition to its applications in diagnosis, the VA method has also been studied in the HIFU-based therapy. 17 In a series of studies, Hynynen et al.