From Wikipedia, the free encyclopedia
This article contains content that is written like . Please help
by removing
and inappropriate , and by adding encyclopedic content written from a . (January 2015) ()
High intensity focused ultrasound (HIFU) is an early stage medical technology that is in various stages of development worldwide to treat a range of disorders.
The mechanism is similar to using a magnifying glass to focus sunlight. Focused ultrasound uses an acoustic lens to concentrate multiple intersecting beams of ultrasound on a target. Each individual beam passes through tissue with little effect but at the focal point where the beams converge, the energy can have useful thermal or mechanical effects. HIFU is typically performed with real-time imaging via ultrasound or MRI to enable treatment targeting and monitoring (including thermal tracking with MRI).
This section needs more
or relies too heavily on primary sources. Please review the contents of the section and
if you can. Unsourced or poorly sourced material may be challenged and . (April 2016)
Therapeutic applications use ultrasound to deliver heat or agi much higher energies are used than in . In many cases the frequencies used are different. Specific therapeutic applications of ultrasound include this non-exhaustive list:
Ultrasound sources may be used to generate regional heating and mechanical changes in biological tissue, e.g. in ,
and . However the use of ultrasound in the treatment of musculoskeletal conditions has fallen out of favor.
Focused ultrasound may be used to generate highly localized heating to treat cysts and tumors (benign or malignant), This is known as Magnetic Resonance guided Focused Ultrasound (MRgFUS) or High Intensity Focused Ultrasound (HIFU). These procedures generally use lower frequencies than medical diagnostic ultrasound (from 0.250 to 2 MHz), but significantly higher energies. HIFU treatment is often guided by .
Focused ultrasound may be used to break up
Ultrasound may be used for
treatment by .
has been found to have physiological effects such as ability to stimulate bone-growth, and potential to temporarily disrupt the
for drug delivery.[]
HIFU is being studied in men with .
In 2015 the FDA authorized two HIFU devices for the ablation of prostate tissue.
Treatment for symptomatic
became the first approved application of HIFU by the
(FDA) in October 2004. Studies have shown that HIFU is safe and effective, and that patients have sustained symptomatic relief is sustained for at least two years without the risk of complications involved in surgery or other more invasive approaches. Up to 16-20% of patients will require additional treatment.
A focused ultrasound system is approved in Israel, Europe, Korea and Russia to treat , , and . This approach enables treatment of the brain without incisions and without radiation. In 2016, the US Food and Drug Administration () approved Insightec’s Exablate Neuro system to treat essential tremor.
HIFU has been successfully applied in
to destroy solid tumors of the bone, brain, breast, liver, pancreas, rectum, kidney, testes, prostate.
HIFU has been found to have palliative effects. CE approval has been given for palliative treatment of . Experimentally, a palliative effect was found in cases of advanced .
HIFU may also be used to produce heating for other purposes than cell destruction. For example, HIFU and other devices may be used to activate temperature-sensitive liposomes filled with cancer drug "cargo", to release the drug in high concentrations only at focused tumor sites and when triggered to do so by the hyperthermia device (See ).
HIFU devices have been cleared to treat subcutaneous adipose tissue for the purposes of body contouring (known colloquially, and incorrectly since there is no suction involved, as "non-invasive liposuction"). These devices are available in the US, Canada, the EU, Australia, and certain countries in Asia. HIFU is also cleared, with lower energy levels, for eyebrow lifts.[]
An ultrasound-guided device received CE approval for
treatment in 2007, and in 2011 received CE approval for treatment of .[]
Another device that is guided by optical cameras received CE approval for the treatment of
This section needs more
or relies too heavily on primary sources. Please review the contents of the section and
if you can. Unsourced or poorly sourced material may be challenged and . (April 2016)
HIFU beams are precisely focused on a small region of diseased tissue to locally deposit high levels of energy. The temperature of tissue at the focus will rise to between 65 and 85 °C, destroying the diseased tissue by . Higher temperatures are usually avoided to prevent boiling of liquids inside the tissue. Each
(individual ultrasound energy deposition) treats a precisely defined portion of the targeted tissue. The entire therapeutic target is treated by using multiple sonications to create a volume of treated tissue, according to a protocol developed by the physician. Anesthesia is not required, but sedation is generally recommended.
There are many direct mechanical and thermal mechanisms of focused ultrasound that can be utilized to treat many diseases, as well as methods to augment and/or optimize other treatment approaches.
Thermal ablation is the primary mechanism utilized by the currently approved HIFU devices. As an acoustic wave propagates through the tissue, part of it is absorbed and converted to heat. With focused beams, a very small region of heating can be achieved deep in tissues (usually on the order of millimeters). Tissue damage occurs as a function of both the temperature to which the tissue is heated and how long the tissue is exposed to this heat level in a metric referred to as "thermal dose". By focusing at more than one place or by scanning the focus, a volume can be thermally ablated.
Focused ultrasound using lower intensities, producing low temperature rise () and/or mechanical agitation, can also be utilized to deliver drugs to the brain and other areas of the body. For example, focused ultrasound beams are being studied to temporarily open up the blood-brain barrier to enable delivery of drugs to diseased brain tissue. This technique involves infusing a therapeutic agent along with gas-filled
into the bloodstream. The ultrasound is then applied to target areas in brain, causing the bubbles to vibrate, loosening the
lining the blood vessels and allowing high concentrations of the drug to enter targeted tissues.
At high enough acoustic intensities,
(microbubbles forming and interacting with the ultrasound field) can occur. Microbubbles produced in the field oscillate and grow (due to factors including rectified ), and can eventually implode (inertial or transient cavitation). During inertial cavitation, very high temperatures occur inside the bubbles, and the collapse is associated with a
and jets that can mechanically damage tissue.
Because the onset of cavitation and the resulting tissue damage can be unpredictable, it has generally been avoided in clinical applications thus far. However, researchers have been working on a method of controlling this cavitation, called Histotripsy. This technique can be very precise, causing minimal damage to surrounding tissue, and the bubbles used in cavitation are easily visible with ultrasound imaging, enabling accurate targeting and monitoring. Clinically, histotripsy has a wide range of possible uses from cardiovascular disease to various types of cancer. For very sensitive regions such as the brain, more research is needed to confirm the safety profile of treatment with histotripsy. Using injected microbubbles, to lower the threshold for inertial cavitation only at the target, may help reduce damage to adjacent tissues.
HIFU can be applied to cancers to disrupt the
and trigger an immune response, as well as possibly enhance the efficacy of immunotherapy. Focused ultrasound, either alone or enhanced by microbubbles and/or thrombolytic agents, can also dissolve blood clots. Ultrasound energy causes vibrations that can either break the clot apart directly — via disruption of the fibrin matrix — or make it more susceptible to the effects of thrombolytic agents.
There are several ways to
ultrasound—via a lens (for example, a
lens), a curved , a , or any combination of the three. This concentrates it int it is similar in concept to focusing light through a . This can be determined using an exponential model of . The ultrasound intensity profile is bounded by an exponentially decreasing function where the decrease in ultrasound is a function of distance traveled through tissue:
{\displaystyle I=I_{o}{e}^{-2\alpha \mathrm {z} }}
{\displaystyle I_{o}}
is the initial intensity of the beam,
{\displaystyle \alpha }
(in units of inverse length), and z is distance traveled through the attenuating medium (e.g. tissue).
In this model,
{\displaystyle {\frac {-\partial I}{\partial \mathrm {z} }}=2\alpha I=Q}
is a measure of the
of the heat absorbed from the ultrasound field. Sometimes, SAR is also used to express the amount of heat absorbed by a specific medium, and is obtained by dividing Q by the tissue density. This demonstrates that tissue heating is proportional to intensity, and that intensity is inversely proportional to the area over which an ultrasound beam is spread—therefore, focusing the beam into a sharp point (i.e. increasing the beam intensity) creates a rapid temperature rise at the focus.[]
The amount of damage caused in the tissue can be modeled using Cumulative Equivalent Minutes (CEM). Several formulations of the CEM equation have been suggested over the years, but the equation currently in use for most research done in HIFU therapy comes from a 1984 paper by Dewey and Sapareto:
{\displaystyle {\mathit {CEM}}=\int _{t_{o}}^{t_{f}}R^{T_{\mathrm {reference} }-T}dt}
with the integral being over the treatment time, R=0.5 for temperatures over 43 °C and 0.25 for temperatures between 43 °C and 37 °C, a reference temperature of 43 °C, and time in minutes. This formula is an empirical formula derived from experiments performed by Dewey and Sapareto by measuring the survival of cell cultures after exposure to heat.[]
The ultrasound beam can be focused in these ways:
Geometrically, for example with a
or with a spherically curved .
Electronically, by adjusting the relative phases of elements in an array of transducers (a ""). By dynamically adjusting the electronic signals to the elements of a phased array, the beam can be steered to different locations, and aberrations in the ultrasound beam due to tissue structures can be corrected.[]
High Intensity Focused Ultrasound requires a location tracking position to ensure safety and to verify that currents are going to the proper place. This allows lesion formation to be controlled where tissues are destroyed. Examples of this include x-ray, MRI, and Diagnostic Ultrasound. The most basic method of this is Visual monitoring. X-rays were the earliest form of guidance. MRI allows tissue contrast for localization of target volume, characterization of diffusion, perfusion, flow, and temperature, enabling detection of tissue damage. Diagnostic Ultrasound can indicate treatment progress by showing the area as hyper echoic images in real time during the scan.
This section needs additional citations for . Please help
by . Unsourced material may be challenged and removed. (April 2016) ()
The first investigations of HIFU for non-invasive ablation were reported by Lynn et al. in the early 1940s. Extensive important early work was performed in the 1950s and 1960s by William Fry and Francis Fry at the University of Illinois and Carl Townsend, Howard White and George Gardner at the Interscience Research Institute of Champaign, Ill., culminating in clinical treatments of neurological disorders. In particular High Intensity ultrasound and ultrasound visualization was accomplished stereotaxically with a Cincinnati precision milling machine to perform accurate ablation of brain tumors. Until recently, clinical trials of HIFU for ablation were few (although significant work in hyperthermia was performed with ultrasonic heating), perhaps due to the complexity of the treatments and the difficulty of targeting the beam noninvasively. With recent advances in medical imaging and ultrasound technology, interest in HIFU ablation of tumors has increased.
The first commercial HIFU machine, called the Sonablate 200, was developed by the American company Focus Surgery, Inc. (Milipitas, CA) and launched in Europe in 1994 after receiving CE approval, bringing a first medical validation of the technology for benign prostatic hyperplasia (BPH). Comprehensive studies by practitioners at more than one site using the device demonstrated clinical efficacy for the destruction of prostatic tissue without loss of blood or long term side effects. Later studies on localized prostate cancer by Murat and colleagues at the Edouard Herriot Hospital in Lyon in 2006 showed that after treatment with the Ablatherm (EDAP TMS, Lyon, France), progression-free survival rates are very high for low- and intermediate- risk patients with recurrent prostate cancer (70% and 50% respectively) HIFU treatment of prostate cancer is currently[] an approved therapy in Europe[], Canada, South Korea, Australia, and elsewhere.[] As of 2012, clinical trials for the Sonablate 500 in the United States are ongoing for prostate cancer patients and those who have experienced radiation failure.
Use of magnetic resonance-guided focused ultrasound was first cited and patented in 1992. The technology was later transferred to InsighTec in Haifa Israel in 1998. The InsighTec ExAblate 2000 was the first MRgFUS system to obtain FDA market approval in the United States.
Currently, there are HIFU systems approved to treat , pain from bone metastases and the prostate in Asia, Canada, Europe, Israel, Latin America and the United States. There is regulatory approval to treat a range of cancers, including breast, kidney, liver, the pancreas and soft tissue sarcoma in Europe and Asia. There is a brain system approved in Europe, Korea and Russia to treat essential tremor, Parkinsonian tremor and neuropathic pain. Non-image guided HIFU devices may be marketed for cosmetic purposes (typically for body fat reduction) in some jurisdictions.
Robertson, VJ; Baker, KG (2001). "A review of therapeutic ultrasound: Effectiveness studies". Physical therapy. 81 (7): 1339–50.  .
Baker, KG; Robertson, VJ; Duck, FA (2001). "A review of therapeutic ultrasound: Biophysical effects". Physical therapy. 81 (7): 1351–8.  .
Hynynen, K McDannold, N Sheikov, Nickolai A.; Jolesz, Ferenc A.; Vykhodtseva, Natalia (2005). "Local and reversible blood–brain barrier disruption by noninvasive focused ultrasound at frequencies suitable for trans-skull sonications". NeuroImage. 24 (1): 12–20. :.  .
Jácome-Pita, F; Sánchez-Salas, R; Barret, E; Amaruch, N; Gonzalez-Enguita, C; Cathelineau, X (2014). . Ecancermedicalscience. 8: 435. :.   .  .
Fennessy, F Fischer, K McDannold, N Jolesz, F Tempany, Clare (2015). . International Journal of Women's Health. 7: 901–12. :.   .  .
Stewart, Elizabeth A.; Gostout, B Rabinovici, J Kim, Hyun S.; Regan, L Tempany, Clare M. C. (2007). "Sustained Relief of Leiomyoma Symptoms by Using Focused Ultrasound Surgery". Obstetrics & Gynecology. 110 (2, Part 1): 279–87. :.  .
Elias, W. J Huss, D Voss, T Loomba, J Khaled, M Zadicario, E Frysinger, Robert C.; Sperling, Scott A.; Wylie, S Monteith, Stephen J.; Druzgal, J Shah, Binit B.; Harrison, M Wintermark, Max (2013). "A Pilot Study of Focused Ultrasound Thalamotomy for Essential Tremor". New England Journal of Medicine. 369 (7): 640–8. :.  .
Jeanmonod, D Werner, B Morel, A Michels, L Zadicario, E Schiff, G Martin, Ernst (2012). "Transcranial magnetic resonance imaging–guided focused ultrasound: noninvasive central lateral thalamotomy for chronic neuropathic pain". Neurosurgical Focus. 32 (1): E1. :.  .
Magara, A Bühler, R Moser, D Kowalski, M Pourtehrani, P Jeanmonod, Daniel (2014). . Journal of Therapeutic Ultrasound. 2: 11. :.   .  .
FDA News Release. , , July 11, 2016
Aubry, Jean-F Pauly, K Moonen, C ter Haar, G Ries, M Salomir, R Sokka, S Sekins, K Shapira, Y Ye, F Huff-Simonin, H Eames, M Hananel, A Kassel, N Napoli, A Hwang, J Wu, F Zhang, L Melzer, A Kim, Young- Gedroyc, Wladyslaw (2013). "The road to clinical use of high-intensity focused ultrasound for liver cancer: technical and clinical consensus". Journal of Therapeutic Ultrasound. 1 (1): 1–13. :.
. New York: Springer. 2016.  .
(Press release). Philips Healthcare. April 20, 2011. Archived from
on October 5, .
Wu, F.; Wang, Z.-B.; Zhu, H.; Chen, W.-Z.; Zou, J.-Z.; Bai, J.; Li, K.-Q.; Jin, C.-B.; Xie, F.-L.; Su, H.-B. (2005). "Feasibility of US-guided High-Intensity Focused Ultrasound Treatment in Patients with Advanced Pancreatic Cancer: Initial Experience". Radiology. 236 (3): 1034–40. :.  .
. 510(k) Premarket Notification Database.
2015. Premarket notification, device in classification "focused ultrasound for tissue heat or mechanical cellular disruption", classification description "Focused ultrasound stimulator system for aesthetic use"
. New York: Springer. 2016. pp. 3–20.  .
Huisman, M Lam, Mie K; Bartels, Lambertus W; Nijenhuis, Robbert J; Moonen, Chrit T; Knuttel, Floor M; Verkooijen, Helena M; van Vulpen, M van den Bosch, Maurice A (2014). . Journal of Therapeutic Ultrasound. 2: 16. :.   .  .
K?hler, Max O.; Mougenot, C Quesson, B Enholm, J Le Bail, B Laurent, C Moonen, Chrit T. W.; Ehnholm, G?sta J. (2009). "Volumetric HIFU ablation under 3D guidance of rapid MRI thermometry". Medical Physics. 36 (8): 3521–35. :. :.  .
Park, J Zhang, Y Vykhodtseva, N Jolesz, Ferenc A.; McDannold, Nathan J. (2012). . Journal of Controlled Release. 162 (1): 134–42. :.   .  .
Tung, Yao-S Vlachos, F Feshitan, Jameel A.; Borden, Mark A.; Konofagou, Elisa E. (2011). . The Journal of the Acoustical Society of America. 130 (5): 3059–67. :. :.   .  .
Leighton, T.G. (1997). Ultrasound in food processing. Chapter 9: The principles of cavitation: Thomson Science, London, Blackie Academic and Professional. pp. 151–182.
Roberts, William W.; Hall, Timothy L.; Ives, K Wolf, J. S Fowlkes, J. B Cain, Charles A. (2006). "Pulsed Cavitational Ultrasound: A Noninvasive Technology for Controlled Tissue Ablation (Histotripsy) in the Rabbit Kidney". The Journal of Urology. 175 (2): 734–8. :.  .
Xu, Z Fowlkes, J. B Rothman, Edward D.; Levin, Albert M.; Cain, Charles A. (2005). . The Journal of the Acoustical Society of America. 117 (1): 424–35. :. :.   .  .
Zhou, Yu-Feng (2011). . World Journal of Clinical Oncology. 2 (1): 8–27. :.   .  .
Kwan, James J.; Graham, S Coussios, Constantin C. (2013). "Inertial cavitation at the nanoscale". Proceedings of Meetings on Acoustics. 19 (1): 075031. :. :.
Wrenn, Steven P.; Dicker, Stephen M.; Small, Eleanor F.; Dan, Nily R.; Mleczko, Micha?; Schmitz, G Lewin, Peter A. (2012). . Theranostics. 2 (12): 1140–59. :.   .  .
Haen, Sebastian P.; Pereira, Philippe L.; Salih, Helmut R.; Rammensee, Hans-G Gouttefangeas, Cécile (2011). . Clinical and Developmental Immunology. 2011: 160250. :.   .  .
Wu, Feng (2013). "High intensity focused ultrasound ablation and antitumor immune response". The Journal of the Acoustical Society of America. 134 (2): . :. :.  .
Wright, C Hynynen, K Goertz, David (2012). . Investigative Radiology. 47 (4): 217–25. :.   .  .
Monteith, Stephen J.; Kassell, Neal F.; Goren, O Harnof, Sagi (2013). "Transcranial MR-guided focused ultrasound sonothrombolysis in the treatment of intracerebral hemorrhage". Neurosurgical Focus. 34 (5): E14. :.  .
Abi-Jaoudeh, N Pritchard, William F.; Amalou, H Linguraru, M Chiesa, Oscar A.; Adams, Joshua D.; Gacchina, C Wesley, R Maruvada, S McDowell, B Frenkel, V Karanian, John W.; Wood, Bradford J. (2012). . Journal of Vascular and Interventional Radiology. 23 (7): 953–961.e2. :.   .  .
P Hariharan et al. (2007)[]
Sapareto, Stephen A.; Dewey, William C. (1984). "Thermal dose determination in cancer therapy". International Journal of Radiation Oncology, Biology, Physics. 10 (6): 787–800. :.  .
Chan, Arthur H.; Vaezy, S Crum, Lawrence A. (2003). "High-intensity Focused Ultrasound". AccessScience. McGraw-Hill Education. :.
Gelet, A; Murat, Fran?ois-J Poissonier, L (2007). . European Oncological Disease. 1 (1): 60–2.
USHIFU (2012).
Archived from
on August 7, 2009.
Hynynen, K.; Damianou, C.; Darkazanli, A.; Unger, E.; Levy, M.; Schenck, J. F. (1992). "On-line MRI monitored noninvasive ultrasound surgery". Proceedings of the Annual International Conference of the IEEE Engineering in Medicine and Biology Society. :.  .
, "Magnetic resonance guided focussed ultrasound surgery", issued March 19, 1992
at Curlie (based on )
Software for performing various ultrasound simulations with MATLAB
from The New York Times on 18
- Using HIFU to treat pain related to bones metastases by UCSF Radiology and Biomedical Imaging
- Using HIFU to treat uterine fibroids by UCSF Radiology and Biomedical Imaging
: Hidden categories: