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Journal articles on the topic 'Ultrasound beam'

Author: Grafiati

Published: 28 June 2021

Last updated: 18 February 2022

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1

Lu, Jian-Yu, Hehong Zou, and James F. Greenleaf. "Biomedical ultrasound beam forming." Ultrasound in Medicine & Biology 20, no. 5 (January 1994): 403–28. http://dx.doi.org/10.1016/0301-5629(94)90097-3.

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2

Ter Haar, G. "Ultrasound focal beam surgery." Ultrasound in Medicine & Biology 21, no. 9 (January 1995): 1089–100. http://dx.doi.org/10.1016/0301-5629(95)02010-1.

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3

Chatzifotis, Panagiotis I. "Non-Destructive Testing with Ultrasound in Rails and Ship Plates." Key Engineering Materials 605 (April 2014): 613–16. http://dx.doi.org/10.4028/www.scientific.net/kem.605.613.

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This paper deals with finding of defects, such as cracks, breakdowns and inclusions in rails and in ship plates, by ultrasound technique. Pulse echo method and twin beams technique is some of the ultrasonic inspection methods we have used for thickness measurements and for inspection of the welds. Initially, the thickness of rails and ship plates was measured by ultrasound devices using straight beam transducers and then the weldings of these samples were checked by using angle beam transducers.

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4

Dolazza, Enrico. "Ultrasound beam softening compensation system." Journal of the Acoustical Society of America 104, no. 5 (November 1998): 2560. http://dx.doi.org/10.1121/1.423824.

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5

Preston, R. C. "The NPL ultrasound beam calibrator." IEEE Transactions on Ultrasonics, Ferroelectrics and Frequency Control 35, no. 2 (March 1988): 122–39. http://dx.doi.org/10.1109/58.4162.

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6

Martin, K. "A thermal beam shape phantom for physiotherapy ultrasound beams." European Journal of Ultrasound 6 (October 1997): S29. http://dx.doi.org/10.1016/s0929-8266(97)90341-4.

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7

Bae, Sua, and Tai-Kyong Song. "Methods for Grating Lobe Suppression in Ultrasound Plane Wave Imaging." Applied Sciences 8, no. 10 (October 11, 2018): 1881. http://dx.doi.org/10.3390/app8101881.

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Plane wave imaging has been proven to provide transmit beams with a narrow and uniform beam width throughout the imaging depth. The transmit beam pattern, however, exhibits strong grating lobes that have to be suppressed by a tightly focused receive beam pattern. In this paper, we present the conditions of grating lobe occurrence by analyzing the synthetic transmit beam pattern. Based on the analysis, the threshold of the angle interval is presented to completely eliminate grating lobe problems when using uniformly distributed plane wave angles. However, this threshold requires a very small angle interval (or, equivalently, too many angles). We propose the use of non-uniform plane wave angles to disperse the grating lobes in the spatial domain. In this paper, we present an approach using two uniform angle sets with different intervals to generate a non-uniform angle set. The proposed methods were verified by continuous-wave transmit beam patterns and broad-band 2D point spread functions obtained by computer simulations.

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8

Zhou, Jingcheng, Xu Guo, Cong Du, and Xingwei Wang. "Ultrasound beam steering using a fiber optic ultrasound phased array." Optics Letters 44, no. 21 (November 1, 2019): 5390. http://dx.doi.org/10.1364/ol.44.005390.

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9

Fischetti, Anthony J., and Richard C. Scott. "Basic Ultrasound Beam Formation and Instrumentation." Clinical Techniques in Small Animal Practice 22, no. 3 (August 2007): 90–92. http://dx.doi.org/10.1053/j.ctsap.2007.05.002.

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10

Alles, Erwin J., Sacha Noimark, Edward Zhang, Paul C. Beard, and Adrien E. Desjardins. "Pencil beam all-optical ultrasound imaging." Biomedical Optics Express 7, no. 9 (August 26, 2016): 3696. http://dx.doi.org/10.1364/boe.7.003696.

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11

Kremkau, Frederick W. "The New Paradigm for Understanding, Teaching, and Testing Sonographic Principles." Journal for Vascular Ultrasound 42, no. 4 (September 12, 2018): 198–202. http://dx.doi.org/10.1177/1544316718799238.

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Two alternative fundamental principles of operation are present in the array of sonographic equipment commercially available currently. Principle 1 has been the operating principle for over 50 years. Recently, Principle 2 has appeared. In Principle 1, there is a one-to-one correspondence between the echo stream from an emitted ultrasound pulse and its displayed scan line, ie, physical beam-forming is directly coupled with displayed scan lines. In Principle 2, fewer pulses are required and focusing is not necessary, and yet the entire image is in focus (ie, excellent detail resolution) and with higher frame rates (improved temporal resolution). This “virtual beam-forming” is accomplished through massive, parallel, high-speed computational postprocessing. The resulting images are similar to what extremely thin, laser-like physical ultrasound beams would produce. However, such beams cannot be physically produced in the frequency range required for imaging depths appropriate for human anatomic imaging. Virtual beam-forming significantly improves nearly every aspect of sonographic, anatomic imaging and Doppler motion detection and presentation.

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12

Demi, Libertario. "Practical Guide to Ultrasound Beam Forming: Beam Pattern and Image Reconstruction Analysis." Applied Sciences 8, no. 9 (September 3, 2018): 1544. http://dx.doi.org/10.3390/app8091544.

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Starting from key ultrasound imaging features such as spatial and temporal resolution, contrast, penetration depth, array aperture, and field-of-view (FOV) size, the reader will be guided through the pros and cons of the main ultrasound beam-forming techniques. The technicalities and the rationality behind the different driving schemes and reconstruction modalities will be reviewed, highlighting the requirements for their implementation and their suitability for specific applications. Techniques such as multi-line acquisition (MLA), multi-line transmission (MLT), plane and diverging wave imaging, and synthetic aperture will be discussed, as well as more recent beam-forming modalities.

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13

Straube, William L., Eduardo G. Moros, Daniel A. Low, Eric E. Klein, Virgil M. Willcut, and Robert J. Myerson. "An ultrasound system for simultaneous ultrasound hyperthermia and photon beam irradiation." International Journal of Radiation Oncology*Biology*Physics 36, no. 5 (December 1996): 1189–200. http://dx.doi.org/10.1016/s0360-3016(96)00369-0.

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14

Gao, Jing, Sandy Cochran, and Zhihong Huang. "Ultrasound beam distortion and pressure reduction in transcostal focused ultrasound surgery." Applied Acoustics 76 (February 2014): 337–45. http://dx.doi.org/10.1016/j.apacoust.2013.06.003.

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15

Buck, Tahisha M., Dylan C. Sieck, and John R. Halliwill. "Thin-beam ultrasound overestimation of blood flow: how wide is your beam?" Journal of Applied Physiology 116, no. 8 (April 15, 2014): 1096–104. http://dx.doi.org/10.1152/japplphysiol.00027.2014.

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It has been predicted that the development of thin-beam ultrasound could lead to an overestimation of mean blood velocity by up to 33% as beam width approaches 0% of vessel diameter. If both beam and vessel widths are known, in theory, this overestimation may be correctable. Therefore, we updated a method for determining the beam width of a Doppler ultrasound system, tested the utility of this technique and the information it provides to reliably correct for the error in velocity measurements, and explored how error-corrected velocity estimates impact the interpretation of in vivo data. Using a string phantom, we found the average beam width of four different probes varied across probes from 2.93 ± 0.05 to 4.41 ± 0.06 mm (mean ± SD) and with depth of insonation. Using this information, we tested the validity of a calculated correction factor to minimize the thin-beam error in mean velocity observed in a flow phantom with known diameter. Use of a correction factor reduced the overestimation from 39 ± 11 to 7 ± 9% ( P < 0.05). Lastly, in vivo we explored how knowledge of beam width improves understanding of physiological flow conditions. In vivo, use of a correction factor reduced the overestimation of mean velocity from 23 ± 11 to −4 ± 9% ( P < 0.05). Thus this large source of error is real, has been largely ignored by the early adaptors of Doppler ultrasound for vascular physiology studies in humans, and is correctable by the described techniques.

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16

SONGKAITIWONG, KITTIPHOT, and KITSAKORN LOCHAROENRAT. "COMPUTATIONAL ALGORITHM OF TWO PARALLEL ULTRASOUND BEAMS OF 1D CANCER TISSUE MODEL FOR SAFE AND EFFECTIVE HYPERTHERMIA TREATMENT." Journal of Mechanics in Medicine and Biology 19, no. 03 (May 2019): 1950012. http://dx.doi.org/10.1142/s021951941950012x.

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The mathematical algorithm of two parallel ultrasound beams on a one-dimensional (1D) cancer tissue model for hyperthermia treatment was created using Matlab software. Physically, the model incorporated two beams; the first beam was permanently placed at the center of the tumor, whereas the other was set between the first beam and the tumor. The computational implementation of this technique relies on the Crank–Nicolson method. This technique is a finite different method that offers an exact heat transfer calculation based on the heat analysis of the heat node structure from a 1D biological tissue model. The Matlab software implementation was composed of two stages: tissue temperature profile calculation and optimization computation. To obtain the tissue temperature profile, the beam heat was varied from 45∘C to 75∘C (seven different levels of heat from the same source), while the second beam was allowed to move between the first beam and the tumor to locations at distances of 1 to 9[Formula: see text]mm (nine positions). The obtained tissue temperature profiles were subsequently analyzed to achieve the optimal time, beam position, and beam heat of the treatment. As a result of the optimization, the best position for the second beam was determined to be 5[Formula: see text]mm from the center of the tumor. Further, all tumor cells were observed to have died, whereas all normal tissues were safe. The optimal time, beam position, and beam heat of the treatment were finally collected to create and fit a mathematical function for further hyperthermia treatment.

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17

Daniel, Timothy D., Fred Gittes, Ivars P. Kirsteins, and Philip L. Marston. "Bessel beam expansion of linear focused ultrasound." Journal of the Acoustical Society of America 144, no. 6 (December 2018): 3076–83. http://dx.doi.org/10.1121/1.5080602.

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18

Prall, M., R. Kaderka, N. Saito, C. Graeff, C. Bert, M. Durante, K. Parodi, J. Schwaab, C. Sarti, and J. Jenne. "Ion beam tracking using ultrasound motion detection." Medical Physics 41, no. 4 (March 20, 2014): 041708. http://dx.doi.org/10.1118/1.4868459.

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19

Von Behren, Patrick L., and Paul D. Freiburger. "Elevation beam pattern variation for ultrasound imaging." Journal of the Acoustical Society of America 121, no. 2 (2007): 694. http://dx.doi.org/10.1121/1.2640222.

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20

Denisov, E. S., B. K. Temyanov, R. K. Sagdiev, and M. G. Fazlyyyakhmatov. "Beam Control System for Ultrasound Scanning Device." IOP Conference Series: Materials Science and Engineering 69 (December 11, 2014): 012014. http://dx.doi.org/10.1088/1757-899x/69/1/012014.

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21

Giammalva, Giuseppe Roberto, Cesare Gagliardo, Salvatore Marrone, Federica Paolini, Rosa Maria Gerardi, Giuseppe Emmanuele Umana, Kaan Yağmurlu, et al. "Focused Ultrasound in Neuroscience. State of the Art and Future Perspectives." Brain Sciences 11, no. 1 (January 10, 2021): 84. http://dx.doi.org/10.3390/brainsci11010084.

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Transcranial MR-guided Focused ultrasound (tcMRgFUS) is a surgical procedure that adopts focused ultrasounds beam towards a specific therapeutic target through the intact skull. The convergence of focused ultrasound beams onto the target produces tissue effects through released energy. Regarding neurosurgical applications, tcMRgFUS has been successfully adopted as a non-invasive procedure for ablative purposes such as thalamotomy, pallidotomy, and subthalamotomy for movement disorders. Several studies confirmed the effectiveness of tcMRgFUS in the treatment of several neurological conditions, ranging from motor disorders to psychiatric disorders. Moreover, using low-frequencies tcMRgFUS systems temporarily disrupts the blood–brain barrier, making this procedure suitable in neuro-oncology and neurodegenerative disease for controlled drug delivery. Nowadays, tcMRgFUS represents one of the most promising and fascinating technologies in neuroscience. Since it is an emerging technology, tcMRgFUS is still the subject of countless disparate studies, even if its effectiveness has been already proven in many experimental and therapeutic fields. Therefore, although many studies have been carried out, many others are still needed to increase the degree of knowledge of the innumerable potentials of tcMRgFUS and thus expand the future fields of application of this technology.

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22

Giammalva, Giuseppe Roberto, Cesare Gagliardo, Salvatore Marrone, Federica Paolini, Rosa Maria Gerardi, Giuseppe Emmanuele Umana, Kaan Yağmurlu, et al. "Focused Ultrasound in Neuroscience. State of the Art and Future Perspectives." Brain Sciences 11, no. 1 (January 10, 2021): 84. http://dx.doi.org/10.3390/brainsci11010084.

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Transcranial MR-guided Focused ultrasound (tcMRgFUS) is a surgical procedure that adopts focused ultrasounds beam towards a specific therapeutic target through the intact skull. The convergence of focused ultrasound beams onto the target produces tissue effects through released energy. Regarding neurosurgical applications, tcMRgFUS has been successfully adopted as a non-invasive procedure for ablative purposes such as thalamotomy, pallidotomy, and subthalamotomy for movement disorders. Several studies confirmed the effectiveness of tcMRgFUS in the treatment of several neurological conditions, ranging from motor disorders to psychiatric disorders. Moreover, using low-frequencies tcMRgFUS systems temporarily disrupts the blood–brain barrier, making this procedure suitable in neuro-oncology and neurodegenerative disease for controlled drug delivery. Nowadays, tcMRgFUS represents one of the most promising and fascinating technologies in neuroscience. Since it is an emerging technology, tcMRgFUS is still the subject of countless disparate studies, even if its effectiveness has been already proven in many experimental and therapeutic fields. Therefore, although many studies have been carried out, many others are still needed to increase the degree of knowledge of the innumerable potentials of tcMRgFUS and thus expand the future fields of application of this technology.

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23

Konečný, Petr, Václav Veselý, Petr Lehner, Daniel Pieszka, and Libor Žídek. "Investigation of Selected Physical Parameters of Cementitious Composite during Sequential Fracture Test." Advanced Materials Research 969 (June 2014): 228–33. http://dx.doi.org/10.4028/www.scientific.net/amr.969.228.

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The paper is focusing on the investigation of the effective crack length obtained from bending test on concrete notched beams with the complementary measurements of ultrasound passing time through the tested concrete specimen. The ultrasound passing time measurements are performed on several stages of the fracture process along the specimen ligament for each tested notched beam. Gained results of the time of ultrasound pulse needed to pass through specimens' failure zone, i.e. its dependence on the crack length or opening, provide information which may help to identify the process of crack formation without the visible indications. The fracture tests are conducted for a set of specimens differing in the notch length. Changes of the ultrasound passing times with increasing effective crack length are observed and discussed.

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24

Lu, Jian-yu, and James F. Greenleaf. "Producing Deep Depth of Field and Depth-Independent Resolution in Nde with Limited Diffraction Beams." Ultrasonic Imaging 15, no. 2 (April 1993): 134–49. http://dx.doi.org/10.1177/016173469301500205.

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Limited diffraction beams, such as Durnin's J0 Bessel beam, are a class of nonspreading solutions to the isotropic/homogeneous scalar wave equation. These beams can be approximately produced with finite aperture and energy over a deep depth of field. In this paper, we report the application of a broadband J0 Bessel beam to nondestructive evaluation (NDE) of materials. Pulse-echo images of a stainless steel block phantom were obtained with both the Jo Bessel beam and a conventional focused Gaussian beam. Results show that uniformly high resolutions were obtained with the J0 Bessel beam over a large distance. In addition, the lateral resolution of the J0 Bessel beam is almost independent of the speed of sound of the materials inspected. In contrast, the lateral resolution of images obtained with the conventional focused Gaussian beam changes dramatically with the distance and the focal length of the beam in water is greatly reduced by the steel block. Therefore, limited diffraction beams could be useful for nondestructive evaluation of materials of different speeds of sound. Restoration of pulse-echo images obtained with these beams could be simplified.

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25

Ghanem, Mohamed A., Adam D. Maxwell, Yak-Nam Wang, Bryan W. Cunitz, Vera A. Khokhlova, Oleg A. Sapozhnikov, and Michael R. Bailey. "Noninvasive acoustic manipulation of objects in a living body." Proceedings of the National Academy of Sciences 117, no. 29 (July 6, 2020): 16848–55. http://dx.doi.org/10.1073/pnas.2001779117.

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In certain medical applications, transmitting an ultrasound beam through the skin to manipulate a solid object within the human body would be beneficial. Such applications include, for example, controlling an ingestible camera or expelling a kidney stone. In this paper, ultrasound beams of specific shapes were designed by numerical modeling and produced using a phased array. These beams were shown to levitate and electronically steer solid objects (3-mm-diameter glass spheres), along preprogrammed paths, in a water bath, and in the urinary bladders of live pigs. Deviation from the intended path was on average <10%. No injury was found on the bladder wall or intervening tissue.

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26

Li, Meng-Lin, and Pai-Chi Li. "Improved Fourier-Transform-Based Parallel Receive Beam Formation." Ultrasonic Imaging 25, no. 2 (April 2003): 73–84. http://dx.doi.org/10.1177/016173460302500201.

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A Fourier transform (FT)-based technique for forming parallel receive beams has been previously employed to increase the imaging frame rate in ultrasonic imaging. However, the image quality in FT-based parallel reconstruction is degraded because differences in range focusing delays are ignored and a wide transmit beam needs to be used. In this paper, an adaptive weighting technique based on a focusing-quality index is used to reduce the sidelobes of the FT-derived parallel receive beams. The focusing-quality index is derived from the spatial spectrum of the received aperture data after the receive delays have been applied. Since the spatial spectrum of the baseband aperture data is also used to approximate receive beams in FT-based parallel reconstruction, the adaptive weighting technique can be directly combined with the FT-based technique for forming parallel receive beams with only a slight increase in system complexity. Real ultrasound data are used to demonstrate the efficacy of the proposed technique on both wire targets and speckle-generating objects. The results clearly demonstrate the effectiveness in reducing the sidelobes. In addition, the image background noise is suppressed. The principles, experimental results, and the extension of the proposed technique to 3D ultrasound imaging are described in this paper.

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27

Sikora, Marjan, Ivo Mateljan, and Nikola Bogunović. "Beam Tracing with Refraction." Archives of Acoustics 37, no. 3 (November 1, 2012): 301–16. http://dx.doi.org/10.2478/v10168-012-0039-y.

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Abstract This paper presents the beam tracing with refraction method, developed to examine the possibility of creating the beam tracing simulation of sound propagation in environments with piecewise non- homogenous media. The beam tracing with refraction method (BTR) is developed as an adaptive beam tracing method that simulates not only the reflection but also the refraction of sound. The scattering and the diffraction of sound are not simulated. The BTR employs 2D and 3D topology in order to efficiently simulate scenes containing non-convex media. After the beam tracing is done all beams are stored in a beam tree and kept in the computer memory. The level of sound intensity at the beginning of each beam is also memorized. This beam data structure enables fast recalculation of results for stationary source and geometry. The BTR was compared with two commercial ray tracing simulations, to check the speed of BTR algorithms. This comparison demonstrated that the BTR has a performance similar to state-of- the-art room-acoustics simulations. To check the ability to simulate refraction, the BTR was compared with a commercial Finite Elements Method (FEM) simulation. In this comparison the BTR simulated the focusing of the ultrasound with an acoustic lens, with good accuracy and excellent performance.

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28

Gudra, Tadeusz, and Sylwia Muc. "A Study of Interaction of Ultrasonic and Optical Wave in Optical Fiber Using the Air Gap." Archives of Acoustics 36, no. 3 (September 1, 2011): 613–28. http://dx.doi.org/10.2478/v10168-011-0043-7.

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AbstractThere exist some possibilities for simultaneous delivery of laser radiation and ultrasounds of low frequency and high intensity: introducing ultrasound oscillations in the optical fiber by the rigid connection of the fiber to the vibrating element and non-contact influence of the ultrasonic wave on the laser beam. The article presents the results of Matlab simulations and experimental studies of influence of the ultrasonic wave on the laser beam. A role of the air gap, and its influence on laser-ultrasonic transmission in optical fiber was examined. Advantages and disadvantages of both solutions of interaction of ultrasonic and optical waves in, e.g., surgical applications are discussed.

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29

Guracar, Ismayil M., and Patrick J. Phillips. "Contrast Imaging Beam Sequences for Medical Diagnostic Ultrasound." Journal of the Acoustical Society of America 129, no. 2 (2011): 1142. http://dx.doi.org/10.1121/1.3561619.

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30

David, Guillaume, Jean-luc Robert, Bo Zhang, and Andrew F. Laine. "Time domain compressive beam forming of ultrasound signals." Journal of the Acoustical Society of America 137, no. 5 (May 2015): 2773–84. http://dx.doi.org/10.1121/1.4919302.

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31

Wooh, Shi-Chang, and Yijun Shi. "Three-dimensional beam directivity of phase-steered ultrasound." Journal of the Acoustical Society of America 105, no. 6 (June 1999): 3275–82. http://dx.doi.org/10.1121/1.424655.

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32

Huang, S. "Transverse blood flow measurement using dual beam ultrasound." Ultrasonic Imaging 13, no. 2 (April 1991): 210. http://dx.doi.org/10.1016/0161-7346(91)90136-6.

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33

Hedberg, Claes M., Sara A. K. Andersson, and Kristian C. E. Haller. "Deflection dynamics of rock beam caused by ultrasound." Mechanics of Time-Dependent Materials 17, no. 4 (January 12, 2013): 597–604. http://dx.doi.org/10.1007/s11043-012-9207-8.

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34

Lu, M. H., Y. P. Zheng, and Q. H. Huang. "Ultrasound elastomicroscopy using water beam indentation: preliminary study." International Congress Series 1274 (October 2004): 87–96. http://dx.doi.org/10.1016/j.ics.2004.07.019.

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35

Takeuchi, Shinichi, Keisuke Kurita, Chouyuu Uehara, and Seiya Ozeki. "Micro ultrasound motor with coiled stator for rotationally driving of ultrasound beam of Intravascular ultrasound imaging system." Journal of the Acoustical Society of America 140, no. 4 (October 2016): 3371. http://dx.doi.org/10.1121/1.4970770.

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36

Ledoux, Léon A. F., Jean M. Willigers, Peter J. Brands, and Arnold P. G. Hoeks. "Modeling of the Correlation of Analytic Ultrasound Radiofrequency Signals for Angle-Independent Motion Detection." Ultrasonic Imaging 20, no. 4 (October 1998): 223–42. http://dx.doi.org/10.1177/016173469802000401.

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Conventional pulsed ultrasound systems are able to assess motion of scatterers in the direction of the ultrasound beam, i.e., axial motion, by determining the lag at which the maximum correlation occurs between consecutively-received radiofrequency (rf) signals. The accuracy, resolution, and processing time of this technique is improved by making use of a model for the correlation of rf signals. All previously-described correlation models only include axial motion, but it is common knowledge that lateral motion, i.e., motion in the plane perpendicular to the beam axis, reduces the correlation of rf signals in time. In the present paper, a model for the correlation of analytic rf signals in depth and time is derived and verified. It also includes, aside of some signal and transducer parameters, both axial and lateral motion. The influence of lateral motion on the correlation of (analytic) rf signals is strongly related to local phase and amplitude characteristics of the ultrasound beam. It is shown how the correlation model, making use of an ultrasound transducer with a circular beam shape, can be applied to estimate, independent of angle, the magnitude of the actual motion. Furthermore, it is shown that the model can be applied to estimate the local signal-to-noise ratio and rf bandwidth.

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37

Andreae, Michael H. "In Line with the Ultrasound Beam, the Third Dimension to Ultrasound-guided Nerve Blocks." Anesthesiology 105, no. 4 (October 1, 2006): 856–57. http://dx.doi.org/10.1097/00000542-200610000-00041.

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38

Gray, Andrew T. "In Line with the Ultrasound Beam, the Third Dimension to Ultrasound-guided Nerve Blocks." Anesthesiology 105, no. 4 (October 1, 2006): 857. http://dx.doi.org/10.1097/00000542-200610000-00042.

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39

Shipley, J. A., M. Halliwell, and P. N. T. Wells. "Localising an ultrasound beam travelling within the scan plane of a diagnostic ultrasound imager." Ultrasonics 37, no. 2 (February 1999): 123–31. http://dx.doi.org/10.1016/s0041-624x(98)00062-6.

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40

Van der Merwe, M. G., N. Bhagwandin, J. E. Van der Spuy, and P. E. Le Roux. "Characterization of the acoustic output of therapeutic ultrasound equipment." South African Journal of Physiotherapy 48, no. 1 (February 29, 1992): 4–8. http://dx.doi.org/10.4102/sajp.v48i1.727.

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The safety and efficacy of ultrasound therapy may be compromised if the output from therapy transducers differs considerably from the indicated value. Although the total power output of a transducer can be easily measured using a pressure balance, it is also important to know how this energy is distributed through space. By using a hydrophone scanning technique, beam profiles of the energy distribution can be obtained. From the beam profiles various parameters such as the effective radiating area (ERA) and the beam non-uniformity ratio (BNR) can be determined. Since the spatial-average intensity selected for treatment is a ratio of the emitted ultrasound power and the effective radiating area, it is essential to be able to measure parameters like the effective radiating area. In this study ERA and BNR measurements for commercially available devices were performed with a hydrophone scanning technique.

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41

Gane, Andrea. "Constructing a Homemade Ultrasound Phantom -The Problems Encountered." BMUS Bulletin 10, no. 3 (August 2002): 33–36. http://dx.doi.org/10.1177/1742271x0201000307.

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The task of designing, manufacturing and testing a homemade ultrasound phantom was an academic exercise towards a Postgraduate Diploma in Medical Ultrasound. The aim was not to produce a highly accurate device suitable for a quality assurance programme but to provide the opportunity to understand many aspects of the ultrasound beam and to demonstrate the principles of physics involved.

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42

Kim, Joo Han, Tae Kyong Song, and Song Bai Park. "Pipelined Sampled-Delay Focusing in Ultrasound Imaging Systems." Ultrasonic Imaging 9, no. 2 (April 1987): 75–91. http://dx.doi.org/10.1177/016173468700900201.

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A sampled-delay focusing technique was recently proposed by the authors which completely eliminates the use of analog L-C delay lines for beam focusing in ultrasound B-mode imaging systems. With this approach, the product of sampling rate and maximum time delay is required to be less than unity. To remove this constraint, we propose in this paper a first-in-first-out pipelining technique. This allows one to perform beam steering and dynamic focusing simultaneously on a resolution-cell basis and in a completely digital fashion without the use Of analog L-C delay lines.

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43

Seo, Jongbum. "1443: Advanced Beam Control for Focused Ultrasound: Anti-Focus." Ultrasound in Medicine & Biology 35, no. 8 (August 2009): S219. http://dx.doi.org/10.1016/j.ultrasmedbio.2009.06.829.

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Beklemysheva, Katerina, Alexey Vasyukov, Alexey Ermakov, and Alena Favorskaya. "Numerical modeling of ultrasound beam forming in elastic medium." Procedia Computer Science 112 (2017): 1488–96. http://dx.doi.org/10.1016/j.procs.2017.08.034.

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Saito, Shigemi, and Tetsuya Kawagishi. "Modified Ultrasound Source for Long Focused Second Harmonic Beam." Japanese Journal of Applied Physics 43, no. 5B (May 28, 2004): 3231–36. http://dx.doi.org/10.1143/jjap.43.3231.

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Raeymaekers, Bart, Cristian Pantea, and Dipen N. Sinha. "Creating a collimated ultrasound beam in highly attenuating fluids." Ultrasonics 52, no. 4 (April 2012): 564–70. http://dx.doi.org/10.1016/j.ultras.2011.12.001.

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Moshfeghi, M. "Ultrasound Reflection-Mode Tomography Using Fan-Shaped-Beam Insonification." IEEE Transactions on Ultrasonics, Ferroelectrics and Frequency Control 33, no. 3 (May 1986): 299–314. http://dx.doi.org/10.1109/t-uffc.1986.26833.

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Deng, Cheri. "Local tissue displacements induced by a focused ultrasound beam." Journal of the Acoustical Society of America 112, no. 5 (November 2002): 2404. http://dx.doi.org/10.1121/1.4779814.

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Willink, Robin, and David H. Evans. "Volumetric blood flow calculation using a narrow ultrasound beam." Ultrasound in Medicine & Biology 21, no. 2 (January 1995): 203–16. http://dx.doi.org/10.1016/s0301-5629(94)00107-3.

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Martin, Kevin, and Richard Fernandez. "A thermal beam-shape phantom for ultrasound physiotherapy transducers." Ultrasound in Medicine & Biology 23, no. 8 (January 1997): 1267–74. http://dx.doi.org/10.1016/s0301-5629(97)00109-9.

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