High intensity focused ultrasound (HIFU) is gaining rapid clinical acceptance as a treatment modality enabling non-invasive tissue heating and ablation for numerous applications. HIFU treatments are usually carried out in a single session, often as a day case procedure, with the patient either fully conscious, lightly sedated or under light general anaesthesia. A major advantage of HIFU over other thermal ablation techniques is that there is no necessity for the transcutaneous insertion of probes into the target tissue. The high powered focused beams employed are generated from sources placed either outside the body (for treatment of tumours of the liver, kidney, breast, uterus, pancreas and bone) or in the rectum (for treatment of the prostate), and are designed to enable rapid heating of a target tissue volume, while leaving tissue in the ultrasound propagation path relatively unaffected. Given the wide-ranging applicability of HIFU, numerous extra-corporeal, transrectal and interstitial devices have been designed to optimise application-specific treatment delivery. Their principle of operation is described here, alongside an overview of the physical mechanisms governing HIFU propagation and HIFU-induced heating. Present methods of characterising HIFU fields and of quantifying HIFU exposure and its associated effects are also addressed.

https://www.tandfonline.com/doi/pdf/10.1080/02656730601186138

High intensity focused ultrasound: physical principles and devices.

Ultrasonic biophysics is the study of mechanisms responsible for how ultrasound and biological materials interact. Ultrasound-induced bioeffect or risk studies focus on issues related to the effects of ultrasound on biological materials. On the other hand, when biological materials affect the ultrasonic wave, this can be viewed as the basis for diagnostic ultrasound. Thus, an understanding of the interaction of ultrasound with tissue provides the scientific basis for image production and risk assessment. Relative to the bioeffect or risk studies, that is, the biophysical mechanisms by which ultrasound affects biological materials, ultrasound-induced bioeffects are generally separated into thermal and non-thermal mechanisms. Ultrasonic dosimetry is concerned with the quantitative determination of ultrasonic energy interaction with biological materials. Whenever ultrasonic energy is propagated into an attenuating material such as tissue, the amplitude of the wave decreases with distance. This attenuation is due to either absorption or scattering. Absorption is a mechanism that represents that portion of ultrasonic wave that is converted into heat, and scattering can be thought of as that portion of the wave, which changes direction. Because the medium can absorb energy to produce heat, a temperature rise may occur as long as the rate of heat production is greater than the rate of heat removal. Current interest with thermally mediated ultrasound-induced bioeffects has focused on the thermal isoeffect concept. The non-thermal mechanism that has received the most attention is acoustically generated cavitation wherein ultrasonic energy by cavitation bubbles is concentrated. Acoustic cavitation, in a broad sense, refers to ultrasonically induced bubble activity occurring in a biological material that contains pre-existing gaseous inclusions. Cavitation-related mechanisms include radiation force, microstreaming, shock waves, free radicals, microjets and strain. It is more challenging to deduce the causes of mechanical effects in tissues that do not contain gas bodies. These ultrasonic biophysics mechanisms will be discussed in the context of diagnostic ultrasound exposure risk concerns.

Ultrasound—biophysics mechanisms

High intensity beams of ultrasound may be focused at depth within the body, thereby producing selective damage within the focal volume, with no harm to overlying or surrounding tissues. The technique is thus noninvasive, insofar as the source of ultrasound energy is situated outside the body. The mechanism for cell killing is predominantly thermal, although acoustic cavitation may also occur. Ultrasound focal surgery was first conceived in the 1940s as a possible tool for creating selective damage in the brain for neurosurgical research; its potential for more widespread clinical use was not exploited at that time, probably because of the lack of facilities for providing precise visualisation and localisation of the damage. The availability of modern imaging techniques has encouraged a revival of clinical interest, and applications in ophthalmology, urology and oncology are currently being developed.

Ultrasound focal beam surgery.

Deep lying soft tissue tumors may be treated by a nonincisional surgical procedure executed inside an MR imaging system using a thermal effect delivered by a focused ultrasound transducer. A prototype system is constructed to assess MRI thermal monitoring and the localization of the heat zone in muscle. The temperature distribution of the focal spot is imaged with MRI while mechanically moving the transducer with an hydraulic 3-axis positioner. Acoustic power is applied with a spherical shell transducer using 1- to 10-s duration pulses at frequencies of 1.5 MHz to selectively coagulate tissue at 60-70 degrees C. The procedure is monitored with a series of fast second gradient echo, T1-weighted, temperature sensitive MR sequences. Acquisitions are optimized for high temperature sensitive images that yield the thermal diffusivity, heat flow time constant and the focal spot size in muscle. MR temperature maps of muscle provide localization and dosimetry both in the focal region and near field.

MR temperature mapping of focused ultrasound surgery.

Transpupillary thermotherapy of occult subfoveal choroidal neovascularization in patients with age-related macular degeneration

Absfrucct-A theoretical model was developed to compute the spatiotemporal features of temperature rises induced in ocular tissue during exposure to high-intensity focused ultrasound The model incorporates damage integral evaluation to predict the Occurrence and dimensions of thermally induced lesions Experimental data confirmed the accuracy of computed lesion dimensions for scleral and chorioretinal lesions Computed results also are in agreement with measured threshold exposure levels needed to produce minimal chorioretinal lesions The model is being improved to account for blood-flow cooling effects during longterm hyperthermia Data were collected using this long-term mode on Greene’s melanoma implanted in the rabbit choroid, and these data indicate that tumor regression can be achieved at levels that are consistent with damage integral predictions

http://ieeexplore.ieee.org/iel5/10326/32869/01539608.pdf

D.J. Coleman

Papers

Ultrasonic Hyperthermia for Ophthalmic Therapy