Another method of focusing is using ultrasound arrays, as illustrated in Figure 2B: each element of the array radiates a wave with a pre-determined phase, so that waves from all elements interfere constructively only at a desired focal point. The size and shape of the focal region of most clinically available transducers is similar to a grain of rice: 2-3 mm in diameter and 8-10 mm in length. As mentioned above, diagnostic Inhibitors,research,lifescience,medical ultrasound and HIFU waves differ in amplitude. Typical diagnostic ultrasound transducers

operate at the pressures of 0.001 – 0.003 MPa which corresponds to SKI-606 datasheet time-averaged intensity of 0.1-100 mW/cm2. HIFU transducers produce much larger pressure amplitudes at the focus of the transducer: up to 60 MPa peak compressional pressures and up to 15 MPa peak rarefactional pressures, which corresponds to intensities of up to 20000 W/cm2. For comparison, one atmosphere is equal to 0.1 MPa. Ultrasound of such intensities is capable of producing both thermal and mechanical effects on tissue, which will be discussed below. Tissue heating The fundamental physical mechanism Inhibitors,research,lifescience,medical of HIFU, ultrasound absorption and conversion into heat, was Inhibitors,research,lifescience,medical first described in 1972 (15). Absorption of ultrasound, the mechanical

form of energy, in tissue is not as intuitive as absorption of electromagnetic radiation (e.g., light or RF radiation) and can be simplistically explained as follows. Tissue can be represented as viscous fluid contained by membranes. When a pressure wave propagates through the tissue, it produces relative displacement of tissue layers and causes directional motion or microstreaming of the fluid. Viscous friction of different layers of fluid then leads to heating (16). Both diagnostic ultrasound and HIFU heat tissue, Inhibitors,research,lifescience,medical however, since

Inhibitors,research,lifescience,medical the heating rate is proportional to the ultrasound intensity, the thermal effect produced by diagnostic ultrasound is negligible. In HIFU the majority of heat deposition occurs at the focal area, where the intensity is the highest. The focal temperature can be rapidly increased causing cell death at the focal region. A threshold for thermal necrosis, the denaturing of tissue protein, is calculated according to the thermal dose (TD) formulation: Levetiracetam (1) where t is treatment time, and R = 0.25 if T(t) < 43°C and 0.5 otherwise (17). The thermal dose required to create a thermal lesion is equivalent to the thermal dose of a 240-min exposure at 43°C, hence the common representation of thermal dose in “equivalent minutes”. This definition originated from the hyperthermia protocol, when the tissue was heated to a temperature of 43–45°C during a long exposure of several hours. However, it has been shown that this model gives good estimations of the thermal lesion dose for the higher temperatures caused by HIFU. For example, thermal lesion forms in 10 s at 53°C and 0.1 s at 60°C. In HIFU treatments, the temperature commonly exceeds 70°C in about 1–4 s.