WO2017029599A1 - Scanner à ultrasons avec une pluralité de transducteurs et procédé d'utilisation associé - Google Patents

Scanner à ultrasons avec une pluralité de transducteurs et procédé d'utilisation associé Download PDF

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Publication number
WO2017029599A1
WO2017029599A1 PCT/IB2016/054878 IB2016054878W WO2017029599A1 WO 2017029599 A1 WO2017029599 A1 WO 2017029599A1 IB 2016054878 W IB2016054878 W IB 2016054878W WO 2017029599 A1 WO2017029599 A1 WO 2017029599A1
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WIPO (PCT)
Prior art keywords
ultrasonic
mirror
pulses
transducer
transducers
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PCT/IB2016/054878
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English (en)
Inventor
Dr. Trygve BURCHARDT
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Eyelife As
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Publication of WO2017029599A1 publication Critical patent/WO2017029599A1/fr

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    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
    • A61B8/44—Constructional features of the ultrasonic, sonic or infrasonic diagnostic device
    • A61B8/4444—Constructional features of the ultrasonic, sonic or infrasonic diagnostic device related to the probe
    • A61B8/4461—Features of the scanning mechanism, e.g. for moving the transducer within the housing of the probe
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
    • A61B8/44—Constructional features of the ultrasonic, sonic or infrasonic diagnostic device
    • A61B8/4477—Constructional features of the ultrasonic, sonic or infrasonic diagnostic device using several separate ultrasound transducers or probes
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
    • A61B8/52—Devices using data or image processing specially adapted for diagnosis using ultrasonic, sonic or infrasonic waves
    • A61B8/5207—Devices using data or image processing specially adapted for diagnosis using ultrasonic, sonic or infrasonic waves involving processing of raw data to produce diagnostic data, e.g. for generating an image

Definitions

  • This disclosure relates to methods and apparatuses for imaging sections of a body, (e.g., a human body) by transmitting ultrasonic energy into the body and determining the characteristics of the ultrasonic energy reflected therefrom. More particularly, this disclosure relates to an improved ultrasonic scanning technique and system with an acoustic mirror and a plurality of transducers.
  • Some ultrasonic imaging devices include a transducer and a rotating acoustic mirror.
  • An illustrative device for creating images based on ultrasonic pulses comprises a first ultrasonic transducer and a second ultrasonic transducer, each configured to transmit and receive ultrasonic pulses; and a mirror configured to reflect the ultrasonic pulses, wherein the mirror is configured to rotate.
  • the first ultrasonic transducer, the second ultrasonic transducer, and the mirror are positioned in a probe head.
  • the mirror is configured to reflect the ultrasonic pulses while rotating, and wherein received ultrasonic pulses are used to determine an ultrasonic scan of material adjacent to the lens.
  • the mirror is configured to reflect the ultrasonic pulses from the first ultrasonic transducer during a first range of rotation of the mirror and is configured to reflect the ultrasonic pulses from the second ultrasonic transducer during a second range of rotation of the mirror, wherein the first and second ranges of rotation make up a single rotation of the mirror.
  • the device is configured such that the ultrasonic pulses received at the first or the second transducer reflected from the mirror during the first range of rotation are used to determine a first ultrasonic scan of material adjacent to the lens, and wherein the device is configured such that the ultrasonic pulses received at the first or the second transducer reflected from the mirror during the second range of rotation are used to determine a second ultrasonic scan of material adjacent to the lens.
  • the device is configured such that the first and the second ultrasonic transducers transmit and receive ultrasonic pulses that are used to determine two ultrasonic scans of the material adjacent to the lens per rotation of the mirror. In some embodiments, the device is configured such that the two ultrasonic scans per rotation increase a frame rate of a resultant ultrasonic image without diminishing quality of the resultant ultrasonic image. In some embodiments, the device is configured such that the two ultrasonic scans per rotation increase the image quality of a resultant ultrasonic image without diminishing a frame rate of the resultant ultrasonic image.
  • the first ultrasonic transducer is configured to transmit ultrasonic pulses at a first frequency and the second ultrasonic transducer is configured to transmit ultrasonic pulses at a second frequency that is different than the first frequency.
  • the device is configured such that the ultrasonic pulses received at the first or the second transducer from the transmission of pulses at a first frequency are combined with the ultrasonic pulses received at the first or second transducer from the transmission of pulses at a second frequency to determine an ultrasonic scan of material adjacent to the lens.
  • the first frequency is in the range of 1 to 5 MHz and the second frequency is in the range of 8 to 20 MHz.
  • the device further includes at least one additional ultrasonic transducer.
  • the probe head further comprises a lens configured to direct the ultrasonic pulses.
  • the mirror is configured to rotate at a rotational speed of the motor.
  • the first ultrasonic transducer and the second ultrasonic transducer are circular transducers with rings for beam forming.
  • the device further comprises an electronics chamber that comprises a battery and electrical circuitry, wherein the electrical circuitry is electrically connected to the ultrasonic transducer.
  • the electrical circuitry is configured to control an operational parameter of the device. Controlling the operational parameter of the device may comprise controlling at least one operational parameter selected from the group consisting of: (a) the frequency of pulses generated by the transducers, (b) the pulse length of pulses generated by the transducers, (c) the timing of pulses generated by the transducers, and (d) the number of pulses generated by the transducers.
  • the electrical circuitry is configured to perform a function on the received ultrasonic pulses selected from the group consisting of: (a) registering the voltage variations on the transducer, (b) converting the signal to digital, (c) performing beam forming upon reception of the signals, (d) performing scan conversion, (e) performing demodulation, (f) performing variable gain compensation, and other typical ultrasound pre- and post-processing techniques.
  • An illustrative method for increasing the image quality, frame rate, or both of images created based on ultrasonic pulses comprises: using a device for creating images based on ultrasonic pulses, the device comprising a first ultrasonic transducer and a second ultrasonic transducer, each configured to transmit and receive ultrasonic pulses, and a mirror configured to reflect the ultrasonic pulses, wherein the mirror is configured to rotate; and reflecting a first ultrasonic pulse, transmitted from the first transducer, off the mirror to an area of tissue to be scanned, when the mirror is in a first position.
  • the method further comprises reflecting a second ultrasonic pulse, transmitted from the second transducer, off the mirror to the area of tissue to be scanned, when the mirror is in a second position; and receiving, at the first and second transducers, ultrasonic pulses reflected back from the area of tissue.
  • the method further comprises converting the reflected pulses into electrical signals to generate a scan using the pulses received at each of the first and second transducers. A first scan is generated using pulses received at the first transducer and a second scan is generated using pulses received at the second transducer such that two scans are generated for each rotation of the mirror.
  • the generation of two scans with each rotation of the mirror allows for an increase in a frame rate of a resultant ultrasonic image without diminishing quality of the resultant ultrasonic image, an increase the image quality of the resultant ultrasonic image without diminishing the frame rate of the resultant ultrasonic image, or both.
  • An illustrative method for generating an image based on ultrasonic pulses comprises using a device for creating images based on ultrasonic pulses, the device comprising a first ultrasonic transducer and a second ultrasonic transducer, each configured to transmit and receive ultrasonic pulses, and a mirror configured to reflect the ultrasonic pulses, wherein the mirror is configured to rotate; and reflecting a first ultrasonic pulse, transmitted from the first transducer at a first frequency, off the mirror to an area of tissue to be scanned, when the mirror is in a first position.
  • the method further comprises reflecting a second ultrasonic pulse, transmitted from the second transducer at a second frequency, off the mirror to the area of tissue to be scanned, when the mirror is in a second position; and receiving, at the first and second transducers, ultrasonic pulses reflected back from the area of tissue.
  • the method further comprises converting the reflected pulses into electrical signals to generate a single scan using the pulses received at each of the first and second transducers.
  • the single scan includes a representation of deep tissue, obtained by the ultrasonic pulses transmitted at the first frequency, and a representation of superficial tissue, obtained by the ultrasonic pulses transmitted at the second frequency.
  • Fig. 1A is a top view of an ultrasound probe with an acoustic mirror in accordance with an illustrative embodiment.
  • Fig. IB is a side view of an ultrasound probe with an acoustic mirror in accordance with an illustrative embodiment.
  • FIG. 1C is a front end view of an ultrasound probe with an acoustic mirror in accordance with an illustrative embodiment.
  • FIG. 2A is a top view of an ultrasound probe with more than one transducer in accordance with an illustrative embodiment.
  • FIG. 2B is a side view of an ultrasound probe with more than one transducer in accordance with an illustrative embodiment.
  • Fig. 2C is a front end view of an ultrasound probe with more than one transducer in accordance with an illustrative embodiment.
  • FIG. 3 illustrates a circular transducer with rings for beam forming in accordance with an illustrative embodiment.
  • Ultrasound differs from other forms of radiation used for imaging in its interaction with living systems in that ultrasound is a mechanical wave. Accordingly, the information provided by the use of ultrasonic waves is of a different nature than that obtained by other methods and is found to be complementary to other diagnostic methods, such as those employing X-rays. Also, the risk of tissue damage using ultrasound appears to be much less than the apparent risk associated with ionizing radiations such as X-rays.
  • Ultrasound imaging devices can be used in settings other than a medical setting. For example, ultrasound imaging devices can be used for finding cracks in materials (e.g., metals, steel, etc.), diagnosing machinery malfunctions, etc.
  • Many diagnostic techniques using ultrasound are based on a pulse-echo method, wherein pulses of ultrasonic energy are periodically generated by a suitable piezoelectric transducer. Each short pulse of ultrasonic energy is focused to a narrow beam, which is transmitted into the patient's body in which the energy eventually encounters interfaces. Once the energy encounters interference, a portion of the ultrasonic energy is reflected at the boundary back to the transducer. After generation of the pulse, the transducer operates in a "listening" mode in which the device converts received reflected energy, or "echoes," from the body into electrical signals. The time of arrival of the echoes depends on the distance of the interfaces from the device and the propagation velocity of the ultrasonic energy. The amplitude of the echoes is indicative of the reflection properties of the interphase and, accordingly, of the nature of the characteristic structure forming the interphase. In alternative embodiments, any suitable method of transmitting and/or receiving ultrasonic energy may be used.
  • B-scan the echo information is of a form similar to a conventional television display. That is, the received echo signals are utilized to modulate the brightness of the display at each point scanned.
  • This type of display is useful, for example, when the ultrasonic energy is scanned transverse to the body so that individual "ranging" information yields individual scan lines on the display, and successive transverse positions are utilized to obtain successive scan lines on the display.
  • the two-dimensional B-scan technique yields a cross-sectional picture in the plane of the scan, and the resultant display can be viewed directly and/or be recorded. In most instances, ultrasonic energy is almost totally reflective at interfaces with gas.
  • coupling fluid such as water or oil, or a direct-contact type transducer can be used to limit the amount of gas through which the ultrasonic energy passes.
  • An illustrative type of apparatus having a console includes a timing signal generator, energizing and receiving circuitry, and a display/recorder for displaying and/or recording image-representative electronic signals, such as those described in U.S. Pat. No. 4,084,582 and U.S. Pat. No. 6,712,765.
  • a portable scanning head or module suitable for being hand held, can have a fluid-tight enclosure having a scanning window formed of a flexible material.
  • a transducer in the portable scanning module converts energy and also converts received ultrasound echoes into electrical signals, which are coupled to the receiver circuitry.
  • a focusing lens is coupled to the transducer, and a fluid, such as water or oil, fills the portable scanning module in the region between the focusing lens and the scanning window.
  • a reflective scanning mirror is disposed in the fluid, and a driving motor, energized in synchronism with the timing signals, drives the scanning mirror in a periodic fashion.
  • the ultrasonic beam is reflected off of the scanning mirror and into the body being examined via a scanning window formed of a rigid material.
  • the dimensions scanned are: (1) depth into the body, which varies during each display scan line by virtue of the ultrasonic beam travelling deeper into the body as time passes; and (2) a slower transverse scan caused by the scanning mirror.
  • the display is typically in a rectangular format (for example, the familiar television type of display with linear sweeps in both directions).
  • the transverse scan of the ultrasonic beam itself, as implemented by the scanning mirror results in a sector scan. For distances deeper in the body, the fanning out of the sectors results in geometrical distortion when displayed on a linear rectangular display.
  • the azimuth dimension in the extreme far field may be, for example, 2.5 times larger than the azimuth dimension in the extreme near field.
  • the density of information on the far field side of the display is much higher than the density of information on the near field side of the display. In other words, what appears to be equal distance in the body on the far field side and the near field side of the display are actually different distances.
  • the scanning window is in the form of an acoustic lens for converging the scan of the ultrasonic beam incident thereon that forms within the enclosure, as in U.S. Pat. No. 4,325,381.
  • the acoustic lens reduces geometric distortion of the scan of the ultrasonic beam.
  • the window/lens is formed of a rigid plastic material in a substantially plano-concave shape, with the concave surface facing the outside of the enclosure.
  • the window/lens is provided with a focal length of about 1.5 times the distance between the reflective scanning means and the windows/lens and may be particularly suitable for a functioning embodiment. In alternative embodiments, any suitable lens, window, focal length, etc. may be used.
  • Figs. 1A-1C depict an ultrasound probe 100 using a circular transducer 130 and a rotating acoustic mirror 145 to position the ultrasound beam and enable scanning functions. Compared to the more traditional linear phase array transducers, improved focus of the ultrasound pulse can be obtained from this configuration.
  • Fig. 1 A is a diagram of an ultrasound probe from a top view in accordance with an illustrative embodiment.
  • Fig. IB is a diagram of an ultrasound probe from a side view in accordance with an illustrative embodiment.
  • Fig. 1C is diagram of a front end view of an ultrasound probe in accordance with an illustrative embodiment. In alternative embodiments, additional, fewer, and/or different elements may be used.
  • An ultrasound probe 100 includes an electronics chamber 105 which may contain circuitry and a battery, a wall 110, a motor 115, a motor shaft 120, a transducer 130, a lens 135, a cavity 140, a mirror 145, and a probe head 150.
  • the electronics chamber 105 houses electronics and possibly batteries and is attached to the probe head 150.
  • the chamber 105 is removably attached to the probe head 150.
  • the probe head 150 includes the motor 115 that is attached to the mirror 145.
  • the angle of the mirror 145 and the location of the transducer 130 are arranged such that the propagation pathway of the ultrasonic pulses is through the lens 135, is reflected by the mirror 145, and is received by the transducer 130, or vice versa after the pulse is transmitted by the transducer 130.
  • the plane of the lens 135 is substantially perpendicular to the transducer 130 and the angle of the mirror is 45°.
  • alternative configurations for the plan of the lens 135 and the angle of the mirror 145 may be used.
  • the output shaft of the motor is mechanically coupled to the mirror.
  • the mirror may be indirectly coupled to the motor.
  • the probe head 150 (including cavity 140) can be liquid filled.
  • the liquid can be any suitable liquid such as water or oil.
  • the cavity 140 is positioned on the opposite side of the mirror 145 from the transducer 130.
  • the motor 115 is connected to the mirror 145 via a shaft and when the motor is running, the mirror 145 rotates at a rotational speed of the motor.
  • the rotating mirror is in the correct positioning to the transducer 130 to reflect the pulses about 1/6 of its rotation time.
  • ultrasound pulses will be reflected from the mirror and out of the probe head through the lens 135.
  • the beam forming electronics controls this, which can be programmed to give the correct focus depth for the ultrasound pulse in the body.
  • the ultrasound pulses travels through the probe chamber, which may be liquid filled, is reflected by the mirror and travels out through the probe head.
  • the probe chamber which may be liquid filled
  • the mirror When a lens is placed at the probe head 150, a linear image is produced.
  • the rotation of the mirror results in each pulse to be reflected at a different angle. This creates the scanning function.
  • the pulse duration is typically only a few bits
  • the transducer After a pulse has been fired, the transducer goes into "listening" mode, at which time it then acts as a receiver for the echo ultrasound signals. The time from sending a pulse to receiving an echo back is typically a few hundred microseconds.
  • the rotational speed of the motor determines how many pulses can be fired with each rotation, as the mirror is in position only part of the time. [0034] As the motor 115 spins, the mirror 145 spins, thereby altering the path of the ultrasonic pulses emitted by the transducer 130 and transmitted through the lens 135. The altered path allows the ultrasound probe 100 to scan the medium at the end of the ultrasound probe 100 (e.g., a human body) without moving the transducer.
  • the frame rate for ultrasound in video mode is, thereby, determined by the rotational speed. With increased rotational speed of the motor, the frame rate increases for the imaging, giving better video functionality. However, with a faster rotation of the motor fewer pulses can be fired as the mirror face passes the transducer, reducing the resolution of the picture captured.
  • rotating the mirror at 600 rpm gives a frame rate of 10 pictures per second. If the distance to and from the transducer and into the body is 6 cm, the speed of the ultrasound wave on average is 1540 m/sec, and the mirror is 3 cm wide., the number of 0.75 ms pulses is calculated to be 120 per rotation. If the rotation speed is increased to 1200 rpm (giving video of 20 frames/second) on the same configuration, the number of pulses is reduced to 60, thereby lowering the quality while increasing the frame rate. It is preferred to have as high frame rate and as many lines (pulses) on the image as possible. Typically, the difference in the image quality is minor with increased pulses above 120. Therefore, it would be desirable to maintain this image quality (120 pulses per rotation) at a faster frame rate. Generally, ultrasound equipment runs at 10 to 40 frames per second.
  • Fig. 2A is a diagram of an ultrasound probe with more than one transducer, such as a first and second transducer 230 and 231 shown in accordance with an illustrative embodiment of Fig. 2A.
  • Fig. 2B is a diagram of an ultrasound probe with more than one transducer from a side view in accordance with an illustrative embodiment.
  • Fig. 2C is diagram an ultrasound probe with more than one transducer from a front end view in accordance with an illustrative embodiment.
  • additional, fewer, and/or different elements may be used.
  • An ultrasound probe 200 includes an electronics chamber 205, preferably containing electronics and a battery, a wall 210, a motor 215, a motor shaft 220, a first transducer 230, a second transducer 231, a lens 235, a mirror 245, and a probe head 250.
  • the various elements of ultrasound probe 200 are similar to the elements of the ultrasound probe 100 of Figs. 1A-1C, and may be similarly configured, except that the ultrasound probe has more than one transducer.
  • the motor 215 spins
  • the mirror 245 spins, thereby altering the path of the ultrasonic pulses emitted by the transducers 230, 231 and transmitted through the lens 235.
  • the altered path allows the ultrasound probe 200 to scan the medium at the end of the ultrasound probe 200 (e.g., a human body) without moving the transducer(s).
  • the time in which the mirror is in the correct position for the transducer to transmit a pulse is doubled and, thereby, the image quality can be improved at a given frame rate or, alternatively, the frame rate can be improved while maintaining the same image quality.
  • the electronics for beam forming may be programmed to give different focus points within the body for each of the transducers.
  • the azimuth resolution of the ultrasound image is related to the focus of the ultrasound pulse, and the further away the image is from the focal point of the ultrasound pulse the lower the resolution of the image is. Therefore, for many ultrasound investigations using a single transducer, beam forming with several focal points are used. By overlaying images with different focal points, a larger zone of focus can be obtained.
  • the disadvantage is that more pulses are required to generate the picture. If the rotational speed is constant, there will be a compromise between area of focus and pickle resolution, due to the number of pulses that can be fired.
  • the rotational speed can be lowered, however, that will reduce the frame rate and reduce the quality of the video recording.
  • the ultrasound probe according to the present disclosure which uses two or more transducers in the probe head as shown in Figure 2, overcomes this constraint.
  • Several focal points can be programmed for both transducers, and the same frame rate or similar pixel resolution can be obtained with better focus over a larger depth profile.
  • the two (or more) transducers each have a different frequency range.
  • Conventional transducers are built with a specific frequency range.
  • the frequency is in the 1 to 20 MHz range.
  • the frequency of the ultrasound pulse from the transducer is set according to the depth of penetration required.
  • For imaging of organs deep into the body a low frequency is used.
  • For imaging close to the skin a high frequency is used. The higher the frequency, the lower the wavelength so better resolution.
  • high frequency attenuates more easily than low frequency, thus for deeper imaging the echo becomes weak making it difficult to distinguish it from noise. Therefore, lower image quality is obtained when using high frequency for deep imaging.
  • transducer in the ultrasound probe with different frequency range allow for both shallow, or superficial, and deep penetration imaging. It is possible to set, for instance, one transducer in the 1 to 5 MHz range and a second one in the 8 to 20 MHz range. This may allow users to do more investigations without requiring a variety of probes. It can reduce cost and improving quality and flexibility. Other frequency ranges can be used depending on the depth range and image quality that the user is targeting
  • more than two transducers may be used, if desired.
  • the type and number of transducers is determined by evaluating the needs and recognizing the trade-offs between number of pulses needed with each pass of the mirror, the frame rate required for video display, the number of focus points on the image, and the depth profile required.
  • the electronics chamber 205 houses electronics and may also house one or more batteries, and is attached to the probe head 250. In some embodiments, the chamber 205 is removably attached to the probe head 250.
  • the electronics incorporates standard ultrasound processors. On the transmit side, the electronics controls the frequency, the pulse length, the timing and the number of pulses generated by the two or more transducers. In particular, as described above, the electronics may set the transducers to different frequencies or having different focal points. The electronics also control the beam forming during transmission by setting the timing for the various rings on the one or more transducers.
  • the electronics On the receive side of the electronics, the electronics register the voltage variations on the transducer, converts the signal to digital, performs beam forming upon reception of the signals, scan conversion, demodulation, variable gain compensation and other classical ultrasound signal processing methods. The data may then be sent to an external devices, such as via wifi to a tablet for further post processing and image display. [0044]
  • the electronics also controls the rotation of the mirror and the timing for positioning of the mirror so that the mirror, transducer(s) and lens alignment is optimal for the sending and receiving of the ultrasound signals. Battery control and monitoring may also be controlled by the electronics.
  • the probe head 250 includes the motor 215 that is attached to the mirror 245.
  • the angle of the mirror 245 and the location of the transducers 230, 231 are arranged such that the propagation pathway of the ultrasonic pulses is through the lens 235, is reflected by the mirror 245, and is received by the transducer 230, or vice versa after the pulse is transmitted by the transducer 230.
  • the plane of the lens 235 is substantially perpendicular to the transducer 230 and the angle of the mirror is 45°. In other embodiments, alternative
  • the probe head 250 (including cavity 240) can be liquid filled.
  • the liquid can be any suitable liquid such as water or oil.
  • the cavity 240 is positioned on the opposite side of the mirror 245 from the transducer 230.
  • the motor 215 is connected to the mirror 245 via a shaft and when the motor is running, the mirror 245 rotates.
  • the mirror shaft, or axis of rotation is not centered with the transducer 230. In this way, the beam formed by the transducer is correctly aligned with the facets of the mirror 245 as the mirror rotates.
  • ultrasound pulses will be reflected from the mirror facet and out of the probe head through the lens 235.
  • the beam forming electronics controls this, which can be programmed to give the correct focus depth for the ultrasound pulse in the body.
  • microseconds such as between 0.5ms and 10ms.
  • the transducer After a pulse has been fired, the transducer goes into "listening" mode, at which time it then acts as a receiver for the echo ultrasound signals.
  • the time from sending a pulse to receiving an echo back is typically a few hundred microseconds.
  • the rotational speed of the motor determines how many pulses can be fired with each rotation, as the mirror is in position only part of the time.
  • FIG. 3 is an illustration of a circular transducer 300 with rings 301-308 for beam forming in accordance with an illustrative embodiment.
  • This figure depicts the type of transducer used in an ultrasound probe according to the embodiments described herein.
  • a circular transducer array with several conductive rings is used. The area between each ring may equal to keep the ultrasound intensity constant.
  • the transducer 300 shown has eight rings, though any appropriate number of rings may be used for beam forming. Beam forming of the ultrasound pulse is possible by varying the timing of the voltage signal over the rings.
  • any of the operations described herein can be implemented at least in part as computer-readable instructions stored on a computer- readable memory. Upon execution of the computer-readable instructions by a processor, the computer-readable instructions can cause a node to perform the operations.
  • any two components so associated can also be viewed as being “operably connected”, or “operably coupled”, to each other to achieve the desired functionality, and any two components capable of being so associated can also be viewed as being “operably couplable”, to each other to achieve the desired functionality.
  • operably couplable include but are not limited to physically mateable and/or physically interacting components and/or wirelessly interactable and/or wirelessly interacting components and/or logically interacting and/or logically interactable components.

Abstract

Un dispositif donné à titre d'exemple pour créer des images sur la base d'impulsions à ultrasons comprend un premier transducteur à ultrasons et un deuxième transducteur à ultrasons, chacun configuré pour émettre et recevoir des impulsions à ultrasons. Le dispositif comprend en outre un miroir configuré pour réfléchir les impulsions à ultrasons. Le premier miroir est conçu pour pivoter. Le premier transducteur à ultrasons, le deuxième transducteur à ultrasons, et le miroir sont positionnés dans une tête de sonde. Le dispositif peut comprendre en outre au moins un transducteur à ultrasons additionnel.
PCT/IB2016/054878 2015-08-14 2016-08-12 Scanner à ultrasons avec une pluralité de transducteurs et procédé d'utilisation associé WO2017029599A1 (fr)

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Cited By (3)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
WO2018203142A3 (fr) * 2017-05-05 2019-02-14 Biim Ultrasound As Sonde ultrasonore portative
CN112515631A (zh) * 2020-10-22 2021-03-19 中国科学院深圳先进技术研究院 血管内窥成像装置
CN113866271A (zh) * 2021-09-18 2021-12-31 中航复合材料有限责任公司 用于复合材料叶片检测的超声双反射法自动扫描系统

Citations (8)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US4084582A (en) 1976-03-11 1978-04-18 New York Institute Of Technology Ultrasonic imaging system
US4325381A (en) 1979-11-21 1982-04-20 New York Institute Of Technology Ultrasonic scanning head with reduced geometrical distortion
JPH0556974A (ja) * 1991-09-04 1993-03-09 Toshiba Corp 超音波診断装置
US5651366A (en) * 1994-09-19 1997-07-29 Board Of Trustees Of The Leland Stanford Junior University Forward viewing ultrasonic imaging catheter
US6712765B2 (en) 2000-12-28 2004-03-30 Florida Atlantic University Ultrasonic scanning method and apparatus
US20100249603A1 (en) * 2009-03-31 2010-09-30 Boston Scientific Scimed, Inc. Systems and methods for making and using a motor distally-positioned within a catheter of an intravascular ultrasound imaging system
US20120172698A1 (en) * 2010-12-30 2012-07-05 Boston Scientific Scimed, Inc. Imaging system
US20120197113A1 (en) * 2011-01-31 2012-08-02 Sunnybrook Health Sciences Centre Ultasonic probe with ultrasonic transducers addressable on common electrical channel

Patent Citations (8)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US4084582A (en) 1976-03-11 1978-04-18 New York Institute Of Technology Ultrasonic imaging system
US4325381A (en) 1979-11-21 1982-04-20 New York Institute Of Technology Ultrasonic scanning head with reduced geometrical distortion
JPH0556974A (ja) * 1991-09-04 1993-03-09 Toshiba Corp 超音波診断装置
US5651366A (en) * 1994-09-19 1997-07-29 Board Of Trustees Of The Leland Stanford Junior University Forward viewing ultrasonic imaging catheter
US6712765B2 (en) 2000-12-28 2004-03-30 Florida Atlantic University Ultrasonic scanning method and apparatus
US20100249603A1 (en) * 2009-03-31 2010-09-30 Boston Scientific Scimed, Inc. Systems and methods for making and using a motor distally-positioned within a catheter of an intravascular ultrasound imaging system
US20120172698A1 (en) * 2010-12-30 2012-07-05 Boston Scientific Scimed, Inc. Imaging system
US20120197113A1 (en) * 2011-01-31 2012-08-02 Sunnybrook Health Sciences Centre Ultasonic probe with ultrasonic transducers addressable on common electrical channel

Cited By (5)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
WO2018203142A3 (fr) * 2017-05-05 2019-02-14 Biim Ultrasound As Sonde ultrasonore portative
US10945706B2 (en) 2017-05-05 2021-03-16 Biim Ultrasound As Hand held ultrasound probe
US11744551B2 (en) 2017-05-05 2023-09-05 Biim Ultrasound As Hand held ultrasound probe
CN112515631A (zh) * 2020-10-22 2021-03-19 中国科学院深圳先进技术研究院 血管内窥成像装置
CN113866271A (zh) * 2021-09-18 2021-12-31 中航复合材料有限责任公司 用于复合材料叶片检测的超声双反射法自动扫描系统

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