US3587561A - Ultrasonic transducer assembly for biological monitoring - Google Patents

Ultrasonic transducer assembly for biological monitoring Download PDF

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Publication number
US3587561A
US3587561A US830750A US3587561DA US3587561A US 3587561 A US3587561 A US 3587561A US 830750 A US830750 A US 830750A US 3587561D A US3587561D A US 3587561DA US 3587561 A US3587561 A US 3587561A
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United States
Prior art keywords
ultrasonic
transducer assembly
transducer
printed circuit
ultrasonic transducer
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Expired - Lifetime
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US830750A
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English (en)
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Janis Gunars Ziedonis
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F Hoffmann La Roche AG
Kontron Inc
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F Hoffmann La Roche AG
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Assigned to KONTRON INCORPORATED reassignment KONTRON INCORPORATED ASSIGNMENT OF ASSIGNORS INTEREST. Assignors: ROCHE MEDICAL ELECTRONICS INC. A CORP. OF NJ.
Assigned to ROCHE MEDICAL ELECTRONICS INC., A CORP. OF NJ reassignment ROCHE MEDICAL ELECTRONICS INC., A CORP. OF NJ ASSIGNMENT OF ASSIGNORS INTEREST. Assignors: HOFFMANN-LA ROCHE INC.
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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
    • A61B8/04—Measuring blood pressure
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
    • A61B8/42—Details of probe positioning or probe attachment to the patient
    • A61B8/4209—Details of probe positioning or probe attachment to the patient by using holders, e.g. positioning frames
    • A61B8/4227—Details of probe positioning or probe attachment to the patient by using holders, e.g. positioning frames characterised by straps, belts, cuffs or braces
    • B—PERFORMING OPERATIONS; TRANSPORTING
    • B06—GENERATING OR TRANSMITTING MECHANICAL VIBRATIONS IN GENERAL
    • B06B—METHODS OR APPARATUS FOR GENERATING OR TRANSMITTING MECHANICAL VIBRATIONS OF INFRASONIC, SONIC, OR ULTRASONIC FREQUENCY, e.g. FOR PERFORMING MECHANICAL WORK IN GENERAL
    • B06B1/00—Methods or apparatus for generating mechanical vibrations of infrasonic, sonic, or ultrasonic frequency
    • B06B1/02—Methods or apparatus for generating mechanical vibrations of infrasonic, sonic, or ultrasonic frequency making use of electrical energy
    • B06B1/06—Methods or apparatus for generating mechanical vibrations of infrasonic, sonic, or ultrasonic frequency making use of electrical energy operating with piezoelectric effect or with electrostriction
    • B06B1/0607—Methods or apparatus for generating mechanical vibrations of infrasonic, sonic, or ultrasonic frequency making use of electrical energy operating with piezoelectric effect or with electrostriction using multiple elements
    • B06B1/0622—Methods or apparatus for generating mechanical vibrations of infrasonic, sonic, or ultrasonic frequency making use of electrical energy operating with piezoelectric effect or with electrostriction using multiple elements on one surface

Definitions

  • the transducer assembly is usable for blood [56] Reiereum Cited pressure monitoring by placement with an inflatable cuff UNITED STATES PATENTS about a body limb for detection of arterial wall motion in- 2,763,l53 9/1956 Simjian 128/24A cuted by cuff pressure variations.
  • systolic blood pressure can be observed from the external cuff or bladder pressure at the moment that the initially occluded artery first begins to mementarily change its shape from a closed to open configuration, and the diastolic pressure can be observed from the cuff or bladder pressure at the moment the artery ceases to be occluded during any part of the cardiac cycle.
  • Such changes in arterial wall position are determined preferably by use of a Doppler ultrasonic technique, where the frequency of the reflected sound wave will deviate from the fixed frequency of the transmitted wave in proportion to the velocity of a movable surface which in the instant case is the arterial wall.
  • the reflected sound wave thus, is a wave frequency modulated in accordance with the velocity of the arterial wall.
  • the purpose of the present invention is to provide an ultrasonic transducer assembly for assuring reliable measurement of blood pressure values over a wide range of bodily variations, such as arm diameter.
  • the present invention contemplates an ultrasonic assembly including a flexible printed circuit board having a preset curved configuration and which board simultaneously serves to support on and provide an electrical connection with an array of transducer elements.
  • the entire assembly, including lenses for the transducer elements, is electrically insulated to prevent any transfer of current to a patient.
  • Other provisions of the present invention call for a recessed lens arrangement and a ceramic lens material which has physical characteristics similar to those ofthe transducer elements.
  • FIG. I is a perspective view of the transducer assembly.
  • FIG. 2 is a cross-sectional view of the transducer assembly taken along line 2-2 of FIG. 1.
  • FIG. 3 is a cross-sectional view of the transducer assembly taken along line 3-3 of FIG. I.
  • FIG. 4 is a schematic wiring diagram disclosing electrical hookup of the printed circuit board.
  • FIG. 5 is a top plan view of the transducer assembly with the potting compound removed.
  • FIG. 6 is a cross-sectional view of the transducer assembly taken along line 6-6 of FIG. 5.
  • FIG. 7 illustrates an alternate design for thelens portion of a transducer unit.
  • FIG. 7a shows a cross-sectional view of the alternate design taken along line 70-71: of FIG. 7.
  • FIG. 8 depicts a perspective view of another form of transducer unit construction.
  • FIG. 9 is of cross-sectional view taken along line 9-9 of FIG. 8.
  • FIG. 10 is a schematic plan view of the transducer assembly and an occlusive cuff applied to an arm of a human subject.
  • FIG. II is a schematic cross-sectional view taken along line 11-11 of FIG. 10.
  • FIG. 12 is a schematic longitudinal cross-sectional view of a artery subjected to external occlusive pressure.
  • FIGS. 1, 2 and 3 DESCRIPTION There is illustrated in FIGS. 1, 2 and 3 a preferred embodiment of the present invention concerning an ultrasonic transducer assembly 21 having a surface defining a cavity 22 containing a plurality of exposed lenses representative of transducer units 25-29 arranged at equally spaced intervals between one another and adapted for dispersing a guided beam of ultrasonic energy and receiving reflected ultrasonic energy, as will be more fully described hereinafter.
  • the transducer assembly basically includes a flexible printed circuit board 24 to the plurality of ultrasonic units 25-29 each comprising a transducer element 31, such as a piezoelectric crystal, by way of individual transducer support boards 32.
  • the lens 30 of each transducer unit is secured to the crystal 31.
  • a flexible or semiflexible potting compound 33 serves to cover or encapsulate the printed circuit board and ultrasonic transducer units, as shown, except for leaving lenses 30 exposed.
  • the top planar surface defined by he potting compound lays flush with the uppermost surfaces of lenses 30.
  • a cable 34 is electrically connected to the transducer assembly for delivering electrical energy to and/or deriving electrical energy from crystals 31.
  • FIG. 3 depicts the normal preset curved configuration given to the transducer assembly, prior to crystal mounting, to assure minimum flexing of the assembly for utilization with a curved portion of a body surface.
  • the absence of such a preset curved configuration would, upon application to the body with pressure, require the assembly to change from a flat to curved shape to conform with the curvature of the body area to which the assembly is applied, thereby materially changing the positioning of transducer units 25-29 to alter the effective energy transfer pattern thus reducing the reliability of the assembly as an input device to any particular system.
  • FIG. 3 Also illustrated in FIG. 3 are a series of opening or recesses 35 in the potting compound between adjacent transducer units.
  • a physical arrangement serves a threefold purpose including: reduction of ultrasonic cross-coupling; minimizing stress on bonding between lenses 30 and the potting compound; and enabling space 35 as well as cavity 22 to retain an ultrasonic coupling paste, which pastes are normally used as an intermediate medium when ultrasonic energy is applied to or derived from a patient.
  • FIG. 4 A schematic circuit diagram of the transducer assembly is depicted in FIG. 4, wherein a cable 34, including a pair of individually shielded wires 36, 37, or a single coaxial cable (common ground) are electrically connected to printed circuit board 24 having a subdivided circuit pattern on each the front and back portions 24' and 24" respectively.
  • a cable 34 including a pair of individually shielded wires 36, 37, or a single coaxial cable (common ground) are electrically connected to printed circuit board 24 having a subdivided circuit pattern on each the front and back portions 24' and 24" respectively.
  • R and T On the positioning of the receiver and transmitter crystals are respectively denoted as R and T for convenience.
  • hot potential signal lines 38 and 39 are respectively connected in series the receiver (R) crystals of transducer units 25, 27, 29 and the transmitter (T) crystals of transducer units 26, 28.
  • the subdivided pattern is such that the receiving and transmitting crystals are separated, having ground return signal lines 41 and 43, respectively or common ground, located at each side of the circuit board.
  • the ground signal lines 41 at each side are connected via lead 42 whereas the ground signal lines 43 at each side are connected via lead 44.
  • Cable wire 36 is tied to the receiver hot line 38 while its shield is connected to the associated ground line 41, whereby in similar fashion, cable wire 37 is tied to transmitter hot line 39 while its shield is connected to the associated ground line 43.
  • FIGS. 5 and 6 represent views of the transducer assembly less the encapsulating potting compound 33, wherein the receiver and transmitter hot lines 38 and 39, are shielded by RF shielding members 45 and 46 respectively each including a layer of insulation 47, such as fiberglass, clad with a copper coating 48.
  • the RF shielding members are secured, by bonding agent 49, to the printed circuit board and are shown to overlap the adjacent ground lines 41, 43.
  • the RF shield 45 is grounded to ground line 41 by way of a conductive band 51, whereas in a similar manner RF shield 46 is grounded to ground line 43 via a conductive band 52.
  • the printed circuit board basically, is a nonconductive flexible member 53 fabricated of fiberglass or other suitable material, and clad at each side with a thin layer of conductive material such as copper. As may be observed, the printed circuit board enables good electrical contact to be made with the crystal even with substantial flexing of the board enhancing its reliability. Prior to mounting the transducers, predetermined mechanical stresses are applied to shape the printed circuit board for altering the copper bonded at each side thereof, enabling the circuit board to normally present a precurved configuration. Potting compound 33 when applied aids to maintain said configuration. 7
  • Each of the transducer units as previously discussed, is similarly constructed with a piezoelectric crystal such as of lead zirconate titanate having the desired frequency resonance.
  • the crystal is plated at each side (not shown) with a fine deposite of silver for purposes of making electrical contact to the transducers and electrical grounding.
  • the underside of crystal 3] is bonded to a backing or transducer support board 32 to assure that the crystal is protected from any possibility of electrical shorting.
  • the transducer support board is made ofa nonconductive material like fiberglass, with a thin layer metallized surface at its underside enabling the support board to readily be soldered to the printed circuit board.
  • the type of lens selected for use with the crystal has been found to play an important role in the overall operation of the transducer assembly.
  • the lens material selected must be such to: have similar physical characteristics to that of the crystal (piezoelectric materials) to reduce the effects of external stress and strain including thermal expansion; have a high ultrasonic velocity to maintain proper beam deflection from the crystal; and act as a good electrical insulator.
  • the need for a relatively similar thermal expansion is necessary to prevent excessive strain on the crystal with varying temperatures, so that a good bond may be maintained intermediate the two members.
  • a high ultrasonic velocity in the lens with respect to body tissue enables achievement of the desired maximum beam spread at the lens interface with body tissue.
  • alumina A1 0,
  • Advantages of the alumina type lenses include such features as being mechanically strong, capable of being metallized, and being chemically inert so as not to be susceptible to ultrasonic coupling gels and alcohol or similar cleaning agents.
  • the overall transducer assembly when applied about an arm and energized, will spread a pie-shaped like beam of ultrasonic energy as will be explained in greater detail hereinafter.
  • a lens configuration selected to accomplish this end may be best observed with respect to FIGS. 1, 3 and 5, wherein there is depicted a convex curvature across the lens 30 width for dispersing ultrasonic energy generated from the' crystal by refraction at the lens-skin interface.
  • the convex curvature focuses reflections of the dispersed energy for reception purposes.
  • FIGS. 7 and 7a Another lens configuration especially conceived for this purpose is shown in FIGS. 7 and 7a where both convex and concave curvatures are designed within a depressed face 54 of the lens.
  • An advantage of the latter embodiment is to narrow down the ultrasonic energy in the length dimension even more, so that the width of the ultrasonic beam falling on the artery would be reduced with an enchanced energy concentration allowing for a more accurate reading of artery motion.
  • FIGS. 8 and 9 An alternate approach in mounting the crystal with the lens is illustrated in FIGS. 8 and 9 where the electrically nonconductive lens 55 is provided with a rectangular cavity 56 at its backside.
  • the lens 55 serves as a housing for the crystal 57 which is recessed within the housing allowing it to be spaced from the circuit board by an insulating member 58 such as silicone, epoxy or other suitable material.
  • the peripheral surface about the bottom edge 59 of the housing is soldered to the printed circuit board 24. Electrical contact of crystal 57 with the board wiring is achieved by conductive straps 61 extending through apertures 62 in the printed circuit board and connected to the positive potential of the circuit.
  • the transducer assembly 21 is employed in combination with a conventional inflatable pneumatic cuff 63 (shown in phantom) placed about an arm 64 for utilizing an ultrasonic technique to measure blood pressure values.
  • this technique involves use of the Doppler effect for detection of wall motion of an artery, such as the brachial artery, constrictable under external occlusive pressure during the phase of rapid transition of the arterial wall between open and closed configurations. The opening and closing arterial wall motion made mention to, will occur within that portion of the arm subject to the pneumatic cuff.
  • the preset curved transducer assembly 21 is positioned between the cuff and arm, so that its lengthwise dimension is wrapped about the arm to partially environ its outer circumference.
  • the transducer assembly will, with minimum flexing, readily conform with the arcuate surface of the arm about which it is placed with minimum strain between the printed circuit board and the transducer units or the bonded encapsulating insulation material, thus enhancing the reliability of the unit as a whole.
  • the flexibility of the printed circuit boards allows for changes in its curvature when it is used on different arm diameter sizes.
  • the occlusive properties of the cuff will not be materially affected.
  • the pocket will retain an ultrasonic coupling gel inserted therein to maintain good contact with the arm, thus obviating any concern over the gel being squeezed out with the application ofcuff pressure.
  • the crystal upperside is insulated from the patient by the ceramic lens which may comprise of the special housing configuration shown in FIGS. 8 and 9, whereas the remainder of the transducer assembly is potted in the non conductive potting compound, assuring that no electrical components will come in contact with a patient. Also, the support board protects the crystal underside from electrical shorting.
  • the transducer assembly is applied about an arm under a pneumatic cuff 63 as depicted in FIGS. and 11.
  • a pneumatic cuff 63 As pressure within the cuff is increased only a minimum flexing of the transducer assembly will occur in use with any one of a large range of arm sizes due to the initial preset curved configuration of the assembly.
  • Excitation of crystals 31 of transmitting units 26 and 28 by a suitable oscillating source via cable 34 will cause a generation of ultrasonic energy which, by way of lenses 30, is guided to irradiate across the arm of beam of predetermined design, as illustrated in FIGS. 10 and 11, that is narrow 65 along a first plane and spread 66 along a second plane perpendicular to the first.
  • the beam coverage will easily include the artery, thereby minimizing critical transducer placement.
  • Spacing between the individual transducer units 25-29 is selected on the bases of available beam spread to assure proper beam overlap near the surface of the lenses. Reflections of the ultrasonic energy illuminating the artery will then be detected by the receiving units 25, 27 and 29.
  • the advantage of the narrow beam configuration may be readily realized with reference to FIG. 12, wherein it is shown that the arrangement reduces the error in sensing the motion of the artery from the partly occluded wall 67 as opposed to the occluded portion 68 which moves with a relatively faster velocity, thus, enabling more distinct Doppler signals to be detected.
  • transducer units employed, it should be understood that the number of units to be used depends on the relative size of the crystals and the area of the arm to be covered. For the particular embodiment discussed above, it was found that a minimum coverage of three-quarters of the internal area of an average arm to be quite satisfactory.
  • An ultrasonic transducer assembly for use on a human or animal body comprising:
  • printed circuit means resilient about a transverse axis and extending longitudinally to define a longitudinal axis perpendicular to said transverse axis
  • said printed circuit means shaped to normally present a curved configuration to minimize flexing of the transducer assembly with varying shaped body surfaces
  • each of said ultrasonic transducer means includes:
  • said ultrasonic element is of piezoelectric material; and said lens means lS of ceramic having a similar thermal expansion as its related ultrasonic element and a relatively high ultrasonic velocity with respect to body tissue.
  • said ceramic lens is fabricated of alumina (A1 0 ).
  • said ceramic lens means defines a housing having an aperture in which said ultrasonic element is contained.
  • said lens means has a convex shape about an axis parallel with said transverse axis and a concave shape about an axis parallel with said longitudinal axis.

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  • Health & Medical Sciences (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Engineering & Computer Science (AREA)
  • Heart & Thoracic Surgery (AREA)
  • Molecular Biology (AREA)
  • Nuclear Medicine, Radiotherapy & Molecular Imaging (AREA)
  • Pathology (AREA)
  • Radiology & Medical Imaging (AREA)
  • Physics & Mathematics (AREA)
  • Biomedical Technology (AREA)
  • Veterinary Medicine (AREA)
  • Medical Informatics (AREA)
  • Biophysics (AREA)
  • Surgery (AREA)
  • Animal Behavior & Ethology (AREA)
  • General Health & Medical Sciences (AREA)
  • Public Health (AREA)
  • Hematology (AREA)
  • Mechanical Engineering (AREA)
  • Ultra Sonic Daignosis Equipment (AREA)
  • Investigating Or Analyzing Materials By The Use Of Ultrasonic Waves (AREA)
US830750A 1969-06-05 1969-06-05 Ultrasonic transducer assembly for biological monitoring Expired - Lifetime US3587561A (en)

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JP (1) JPS4911189B1 (fr)
CH (1) CH510432A (fr)
DE (1) DE2025794A1 (fr)
FR (1) FR2045853B1 (fr)
GB (1) GB1269869A (fr)
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Cited By (50)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US3780725A (en) * 1971-03-04 1973-12-25 Smith Kline Instr Fetal heartbeat monitoring system with plural transducers in one plane and at different angles thereto
DE2345088A1 (de) * 1972-09-21 1974-03-28 Stanford Research Inst Lineare wandleranordnung fuer die ultraschall-bildwandlung
US3847016A (en) * 1971-12-08 1974-11-12 Hoffmann La Roche Ultrasonic transducer assembly
US3847141A (en) * 1973-08-08 1974-11-12 Nasa Ultrasonic bone densitometer
US3859984A (en) * 1972-08-14 1975-01-14 Corometrics Medical Systems In Ultrasonic transducer for fetal monitoring
US3958559A (en) * 1974-10-16 1976-05-25 New York Institute Of Technology Ultrasonic transducer
US4086916A (en) * 1975-09-19 1978-05-02 Joseph J. Cayre Cardiac monitor wristwatch
US4103677A (en) * 1975-11-24 1978-08-01 Commissariat A L'energie Atomique Ultrasonic camera
JPS54162591A (en) * 1978-06-13 1979-12-24 Japan Radio Co Ltd Method of making semicylindrical ultrasonic vibrator
US4216403A (en) * 1977-07-27 1980-08-05 Hans List Monoaxially oriented piezoelectric polymer transducer for measurement of mechanical values on bodies
US4252026A (en) * 1979-01-15 1981-02-24 The Commonwealth Of Australia, C/-The Department Of Health Multiple line of sight ultrasonic apparatus
US4276779A (en) * 1979-03-29 1981-07-07 Raytheon Company Dynamically focussed array
DE3124979A1 (de) * 1980-06-27 1982-03-11 Matsushita Electric Industrial Co., Ltd., Kadoma, Osaka "ultraschallwandler-anordnung fuer bogenabtastung"
US4459850A (en) * 1978-11-29 1984-07-17 Ckd Praha, Oborovy Podnik Apparatus for picking-up and analyzing emitted accoustic and ultrasonic signals in hollow bodies
EP0145429A2 (fr) * 1983-12-08 1985-06-19 Kabushiki Kaisha Toshiba Ensemble linéaire courbé de transducteurs ultrasonores
US4656384A (en) * 1984-10-25 1987-04-07 Siemens Aktiengesellschaft Ultrasonic detection sensor in hybrid structure with appertaining electronic circuit
US4690144A (en) * 1982-04-02 1987-09-01 Medtronic, Inc. Wireless transcutaneous electrical tissue stimulator
US4747192A (en) * 1983-12-28 1988-05-31 Kabushiki Kaisha Toshiba Method of manufacturing an ultrasonic transducer
US4860761A (en) * 1985-04-12 1989-08-29 Omron Tateisi Electronics Co. Pulse wave detecting apparatus for blood pressure measurement
US4862895A (en) * 1985-04-12 1989-09-05 Omron Tateisi Electronics Co. Electronic blood pressure meter
US4930511A (en) * 1988-05-11 1990-06-05 Lunar Radiation, Inc. Ultrasonic densitometer device and method
US4966152A (en) * 1987-07-21 1990-10-30 Hewlett-Packard Company Transducer
WO1991011960A1 (fr) * 1990-02-08 1991-08-22 Credo Group, Inc. Lentille ultrasonique de haute energie a facettes de montage
US5042489A (en) * 1988-05-11 1991-08-27 Lunar Corporation Ultrasonic densitometer device and method
US5054490A (en) * 1988-05-11 1991-10-08 Lunar Corporation Ultrasonic densitometer device and method
US5099849A (en) * 1988-05-11 1992-03-31 Lunar Corporation Ultrasonic densitometer device and method
US5218963A (en) * 1991-10-15 1993-06-15 Lunar Corporation Ultrasonic bone analysis device and method
US5343863A (en) * 1988-05-11 1994-09-06 Lunar Corporation Ultrasonic densitometer device and method
US5349959A (en) * 1988-05-11 1994-09-27 Lunar Corporation Ultrasonic densitometer device and method
US5483965A (en) * 1988-05-11 1996-01-16 Lunar Corporation Ultrasonic densitometer device and method
US5603325A (en) * 1988-05-11 1997-02-18 Lunar Corporation Ultrasonic densitometer with width compensation
US5615681A (en) * 1994-12-22 1997-04-01 Aloka Co., Ltd Method for measuring speed of sound in tissue and tissue assessment apparatus
US5840029A (en) * 1988-05-11 1998-11-24 Lunar Corporation Imaging ultrasonic densitometer
US5931684A (en) * 1997-09-19 1999-08-03 Hewlett-Packard Company Compact electrical connections for ultrasonic transducers
US5977691A (en) * 1998-02-10 1999-11-02 Hewlett-Packard Company Element interconnections for multiple aperture transducers
US5990598A (en) * 1997-09-23 1999-11-23 Hewlett-Packard Company Segment connections for multiple elevation transducers
US6027449A (en) * 1988-05-11 2000-02-22 Lunar Corporation Ultrasonometer employing distensible membranes
US6155982A (en) * 1999-04-09 2000-12-05 Hunt; Thomas J Multiple sub-array transducer for improved data acquisition in ultrasonic imaging systems
US6277076B1 (en) 1988-05-11 2001-08-21 Lunar Corporation Ultrasonic densitometer with pre-inflated fluid coupling membranes
EP1266622A1 (fr) * 2001-05-30 2002-12-18 friendly sensors AG Capteur de déformation et/ou mouvement
CN101632986B (zh) * 2009-08-18 2011-02-02 长沙山河超声波技术有限公司 一种超声波换能器装置及其制造方法
US20130188446A1 (en) * 2012-01-24 2013-07-25 Toshiba Medical Systems Corporation Ultrasound probe and ultrasound diagnosis apparatus
US20130267853A1 (en) * 2010-12-03 2013-10-10 Research Triangle Institute Ultrasound device, and associated cable assembly
US20150343492A1 (en) * 2014-05-30 2015-12-03 Arman HAJATI Piezoelectric transducer device with lens structures
CN105396824A (zh) * 2015-11-20 2016-03-16 无锡南方声学工程有限公司 一种超声波清洗机振盒
US10022751B2 (en) 2014-05-30 2018-07-17 Fujifilm Dimatix, Inc. Piezoelectric transducer device for configuring a sequence of operational modes
US10107645B2 (en) 2014-05-30 2018-10-23 Fujifilm Dimatix, Inc. Piezoelectric transducer device with flexible substrate
WO2019169406A1 (fr) * 2018-03-02 2019-09-06 Rowe Technologies, Inc. Appareil transducteur hybride et procédés de fabrication et d'utilisation
US10698107B2 (en) 2010-11-01 2020-06-30 Rowe Technologies, Inc. Multi frequency 2D phased array transducer
US11090027B2 (en) 2015-06-30 2021-08-17 Koninklijke Philips N.V. Methods, apparatuses, and systems for coupling a flexible transducer to a surface

Families Citing this family (5)

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US4232555A (en) * 1979-04-18 1980-11-11 Eastman Kodak Company Ultrasonographic exposure apparatus
JPS56161799A (en) * 1980-05-15 1981-12-12 Matsushita Electric Ind Co Ltd Ultrasonic wave probe
DE3033598A1 (de) * 1980-09-06 1982-04-15 Robert Bosch Gmbh, 7000 Stuttgart Verfahren zur ultraschalltherapie
FR2617394B1 (fr) * 1987-07-03 1994-07-29 Boutin Gerard Dispositif de mesure de la pression sanguine dans une artere superficielle
EP2419023A4 (fr) * 2009-04-14 2013-01-16 Maui Imaging Inc Sonde à ultrasons médicale multi-ouvertures universelle

Cited By (64)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US3780725A (en) * 1971-03-04 1973-12-25 Smith Kline Instr Fetal heartbeat monitoring system with plural transducers in one plane and at different angles thereto
US3847016A (en) * 1971-12-08 1974-11-12 Hoffmann La Roche Ultrasonic transducer assembly
US3859984A (en) * 1972-08-14 1975-01-14 Corometrics Medical Systems In Ultrasonic transducer for fetal monitoring
JPS6121659B2 (fr) * 1972-09-21 1986-05-28 Stanford Res Inst Int
DE2345088A1 (de) * 1972-09-21 1974-03-28 Stanford Research Inst Lineare wandleranordnung fuer die ultraschall-bildwandlung
JPS4971902A (fr) * 1972-09-21 1974-07-11
US3971962A (en) * 1972-09-21 1976-07-27 Stanford Research Institute Linear transducer array for ultrasonic image conversion
US3847141A (en) * 1973-08-08 1974-11-12 Nasa Ultrasonic bone densitometer
US3958559A (en) * 1974-10-16 1976-05-25 New York Institute Of Technology Ultrasonic transducer
US4086916A (en) * 1975-09-19 1978-05-02 Joseph J. Cayre Cardiac monitor wristwatch
US4103677A (en) * 1975-11-24 1978-08-01 Commissariat A L'energie Atomique Ultrasonic camera
US4216403A (en) * 1977-07-27 1980-08-05 Hans List Monoaxially oriented piezoelectric polymer transducer for measurement of mechanical values on bodies
JPS54162591A (en) * 1978-06-13 1979-12-24 Japan Radio Co Ltd Method of making semicylindrical ultrasonic vibrator
US4459850A (en) * 1978-11-29 1984-07-17 Ckd Praha, Oborovy Podnik Apparatus for picking-up and analyzing emitted accoustic and ultrasonic signals in hollow bodies
US4252026A (en) * 1979-01-15 1981-02-24 The Commonwealth Of Australia, C/-The Department Of Health Multiple line of sight ultrasonic apparatus
US4276779A (en) * 1979-03-29 1981-07-07 Raytheon Company Dynamically focussed array
DE3124979A1 (de) * 1980-06-27 1982-03-11 Matsushita Electric Industrial Co., Ltd., Kadoma, Osaka "ultraschallwandler-anordnung fuer bogenabtastung"
US4440025A (en) * 1980-06-27 1984-04-03 Matsushita Electric Industrial Company, Limited Arc scan transducer array having a diverging lens
US4690144A (en) * 1982-04-02 1987-09-01 Medtronic, Inc. Wireless transcutaneous electrical tissue stimulator
EP0145429A2 (fr) * 1983-12-08 1985-06-19 Kabushiki Kaisha Toshiba Ensemble linéaire courbé de transducteurs ultrasonores
US4686408A (en) * 1983-12-08 1987-08-11 Kabushiki Kaisha Toshiba Curvilinear array of ultrasonic transducers
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Also Published As

Publication number Publication date
CH510432A (de) 1971-07-31
JPS4911189B1 (fr) 1974-03-15
GB1269869A (en) 1972-04-06
FR2045853B1 (fr) 1973-12-21
NL7008063A (fr) 1970-12-08
DE2025794A1 (de) 1970-12-10
FR2045853A1 (fr) 1971-03-05
SE354179B (fr) 1973-03-05

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