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DEPENDENCE OF BOILING HISTOTRIPSY TREATMENT EFFICIENCY ON HIFU FREQUENCY AND FOCAL PRESSURE LEVELS
DEPENDENCE OF BOILING HISTOTRIPSY TREATMENT EFFICIENCY ON HIFU FREQUENCY AND FOCAL PRESSURE LEVELS
DEPENDENCE OF BOILING HISTOTRIPSY TREATMENT EFFICIENCY ON HIFU FREQUENCY AND FOCAL PRESSURE LEVELS
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This minimal output amplitude was then used to deliver 30 pulses of 10ms duration at PRF of 1 Hz per single focal spot. The focus was then moved laterally by 5-10 mm and the process repeated, with 5-10 focal spots treated per frequency. In the second case, the HIFU frequency was fixed at either 1.5 MHz, 1.2 MHz or 1.0 MHz. Isolated pulses with a set duration shorter than 10 ms (in particular, 5 ms, 2 ms and 1 ms) were delivered with gradually increasing amplitude until the hyperechoic region was observed. Then 30 pulses of a set dura- tion and PRF resulting in 1% duty factor (2, 5 and 10 Hz, correspondingly) were delivered (Fig 3a). After all the exposures were performed, the tissue sample was imaged with a higher frequency probe (L7-4), bisected and photographed. The shape, color (whitened or reddened vs same color as surrounding tissue) and consistency (liquid vs cohesive soft tissue) of the lesion and its maximum axial and longitudinal dimensions were the outcome measures. The time to reach boiling temperature in both PA gel and ex vivo tissue samples was predicted according to weak shock theory as follows (Canney et al. 2010; Hamilton and Blackstock 1998): where T is the change from ambient temperature to 100C, cv is the volumetric heat capacity of tissue, A1 is the shock amplitude, beta is the coefficient of non-linearity in tissue or gel, fo is the fundamental HIFU frequency, rho is the gel/tissue density and c is the sound speed in gel or tissue. The physical parameters of PA gel and tissue used to calculate the time to reach boiling are listed in Table 1. The in situ pressures in PA gel were considered the same as in water. In tissue, we used a modified derating procedure developed in previous work (Khokhlova et al. 2011), which accounts for both tissue attenuation, alpha, and coefficient of non-linearity. In that method, the focal HIFU waveforms are first measured in water at each output electric voltage setting. The in situ focal waveform at a depth l in tissue, corresponding to a voltage level V is then calculated as follows: (i) Take the focal waveform measured in water at the voltage setting, V': (ii) Multiply the corresponding waveform by the ratio betawater/beta Here betawater = 3.5 and the values for attenuation in heart and liver tissues were taken from the literature (Duck 1990; Khokhlova et al. 2011; Lafon et al. 2005) and are summarized in Table 1.
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1 This minimal output amplitude was then used to deliver 30 pulses of 10ms duration at PRF of 1 Hz per single focal spot. 2 The focus was then moved laterally by 5-10 mm and the process repeated, with 5-10 focal spots treated per frequency. 3 In the second case, the HIFU frequency was fixed at either 1.5 MHz, 1.2 MHz or 1.0 MHz. 4 Isolated pulses with a set duration shorter than 10 ms (in particular, 5 ms, 2 ms and 1 ms) were delivered with gradually increasing amplitude until the hyperechoic region was observed. 5 Then 30 pulses of a set dura- tion and PRF resulting in 1% duty factor (2, 5 and 10 Hz, correspondingly) were delivered (Fig 3a). 6 After all the exposures were performed, the tissue sample was imaged with a higher frequency probe (L7-4), bisected and photographed. 7 The shape, color (whitened or reddened vs same color as surrounding tissue) and consistency (liquid vs cohesive soft tissue) of the lesion and its maximum axial and longitudinal dimensions were the outcome measures. 8 The time to reach boiling temperature in both PA gel and ex vivo tissue samples was predicted according to weak shock theory as follows (Canney et al. 2010; Hamilton and Blackstock 1998): where T is the change from ambient temperature to 100C, cv is the volumetric heat capacity of tissue, A1 is the shock amplitude, beta is the coefficient of non-linearity in tissue or gel, fo is the fundamental HIFU frequency, rho is the gel/tissue density and c is the sound speed in gel or tissue. 9 The physical parameters of PA gel and tissue used to calculate the time to reach boiling are listed in Table 1. 10 The in situ pressures in PA gel were considered the same as in water. 11 In tissue, we used a modified derating procedure developed in previous work (Khokhlova et al. 2011), which accounts for both tissue attenuation, alpha, and coefficient of non-linearity. 12 In that method, the focal HIFU waveforms are first measured in water at each output electric voltage setting. 13 The in situ focal waveform at a depth l in tissue, corresponding to a voltage level V is then calculated as follows: (i) Take the focal waveform measured in water at the voltage setting, V': (ii) Multiply the corresponding waveform by the ratio betawater/beta Here betawater = 3.5 and the values for attenuation in heart and liver tissues were taken from the literature (Duck 1990; Khokhlova et al. 2011; Lafon et al. 2005) and are summarized in Table 1.