EP0170072A1 - Dispositif de groupement phasé - Google Patents

Dispositif de groupement phasé Download PDF

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Publication number
EP0170072A1
EP0170072A1 EP85108128A EP85108128A EP0170072A1 EP 0170072 A1 EP0170072 A1 EP 0170072A1 EP 85108128 A EP85108128 A EP 85108128A EP 85108128 A EP85108128 A EP 85108128A EP 0170072 A1 EP0170072 A1 EP 0170072A1
Authority
EP
European Patent Office
Prior art keywords
delay
phased array
array device
elements
analog
Prior art date
Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
Granted
Application number
EP85108128A
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German (de)
English (en)
Other versions
EP0170072B1 (fr
Inventor
Ulrich Saugeon
Gert Hetzel
Dietmar Dr. Hiller
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
Siemens AG
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Siemens AG
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Filing date
Publication date
Application filed by Siemens AG filed Critical Siemens AG
Priority to AT85108128T priority Critical patent/ATE46783T1/de
Publication of EP0170072A1 publication Critical patent/EP0170072A1/fr
Application granted granted Critical
Publication of EP0170072B1 publication Critical patent/EP0170072B1/fr
Expired legal-status Critical Current

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    • G—PHYSICS
    • G10—MUSICAL INSTRUMENTS; ACOUSTICS
    • G10K—SOUND-PRODUCING DEVICES; METHODS OR DEVICES FOR PROTECTING AGAINST, OR FOR DAMPING, NOISE OR OTHER ACOUSTIC WAVES IN GENERAL; ACOUSTICS NOT OTHERWISE PROVIDED FOR
    • G10K11/00—Methods or devices for transmitting, conducting or directing sound in general; Methods or devices for protecting against, or for damping, noise or other acoustic waves in general
    • G10K11/18—Methods or devices for transmitting, conducting or directing sound
    • G10K11/26—Sound-focusing or directing, e.g. scanning
    • G10K11/34—Sound-focusing or directing, e.g. scanning using electrical steering of transducer arrays, e.g. beam steering
    • G10K11/341—Circuits therefor
    • G10K11/346—Circuits therefor using phase variation

Definitions

  • the invention relates to a phased array device according to the preamble of claim 1.
  • SAW filter technology see e.g. Ultrasonics, Vol. 17, pp. 225 - 229, Sept. 1979.
  • SAW filter technology it is necessary to mix the received signal of the individual ultrasound transducer element upwards in order to get into the high frequency band of 20-50 MHz required in SAW technology. After the summation of the individual received signals of the phased array, it must then be mixed again.
  • Disadvantages of the SAW technology are the fact that up-mixers have to be used in each channel, which means a considerable outlay, and the difficulty in achieving a sufficiently fine gradation of the delay times for the SAW filters.
  • This phase or time accuracy requires a sampling frequency f a > 28 MHz if the signal is to be processed digitally (EU-PS 0.027.618).
  • This high sampling frequency nowadays requires the use of ECL devices and leads to a relatively expensive phased array device.
  • Verzögerungsbauglieder provide the received signals with a short and e, -.er long delay. Then it is possible to combine several adjacent channels, eg 4, for signal processing.
  • a second basic embodiment is characterized in that a TGC amplifier and an analog-digital converter module are connected downstream of the ultrasonic transducer elements.
  • the respective control angle can be set very precisely because of the use of components with fixed component-specific delay times (tolerances) and the digital memory, especially some shift registers.
  • the delay does not drift even after the phased array device has been used for a long time fear.
  • the high accuracy in the setting of the control angle there is also a high level of accuracy in the focusing and thus a high resolving power. This is of particular interest when using concurrent focusing in the case of reception.
  • the phased array device according to FIG. 1 which is used in particular for medical imaging, consists of a large number of individual ultrasound transducer elements E1, E2,... E64, which are used both for the emission and for the reception of ultrasound signals be used.
  • E1, E2,... E64 Only the receiving part of the phased array device is shown. In such a device, the received ultrasound signals must be delayed with the high accuracy described above.
  • the number of ultrasonic transducer elements should be large. As cheaper Compromise here is the number 64 with an element spacing of ⁇ / 2.
  • the received ultrasound signals are provided with a short and a long delay. This makes it possible to combine adjacent signal processing channels. As will become clear later, 4 channels are combined in FIG. 1.
  • the device contains a mixed delay technique, namely an analog pre-delay and a digital main delay. So it's a hybrid solution.
  • the analog pre-delay is a fine delay. It takes place in an area labeled X. A total of 64 channels are provided in this area X. The fine deceleration takes place between 0 and 2 ⁇ .
  • the area X is followed by an area Y which comprises only 16 channels. In this area Y there are amplifiers that can be controlled as a function of depth. Area Y is followed by area Z, which also comprises 16 channels. There is a long-term delay here.
  • each ultrasound transducer element E1 to E64 is followed by a preamplifier V1 to V64 with a fixed gain.
  • These preamplifiers V1 to V64 are each followed by a multiplexer M1 to M64.
  • the respective multiplexer M can be supplied with clock pulses by a control device C, which is indicated by an arrow on the respective block M1 to M64.
  • An analog pre-delay element T1 to T64 is assigned to the multiplexers M1 to M64. Its delay time, in particular in the range from 0 to 600 nsec, can be set using the associated multiplexer M1 to M64.
  • the delay elements T1 to T64 can in particular be LC lines with a number of taps, e.g. Trade 16 taps. With such LC lines there is a delay which is precise enough for the present purposes.
  • the combined received signal obtained in this way is amplified depending on the depth with the aid of controllable amplifiers TGC1 to TGC16, in order then to be able to use the A / D converter dynamics.
  • the received signal is sampled using the quadrature method, ie in complex form.
  • the phase accuracy of the entire delay unit remains constant, for example ⁇ / 12 if 1
  • the output signal of the amplifier TGC1 is fed to a delay element, which consists of a memory N1 and two analog-digital converters Wl-1 and Wl-2 connected upstream thereof.
  • the two converters break down the received signal into a real and an imaginary part.
  • the converter Wl-1 generates the in-phase term or cosine component, while the converter Wl-2 provides the quadrature term or sine component.
  • the downstream memory N 1 is preferably a shift register. This is scanned, for example, in ⁇ / 8 steps, for which purpose the control device C supplies appropriate control pulses.
  • the coarse delay elements which are connected downstream of the further amplifiers TGC2 to TGC16, are constructed accordingly.
  • the output signal of the adder A consists of an imaginary part i and a real part q, so it is complex. From these two parts i and q one can determine the relationship form the amount of signal that can be displayed on a screen.
  • each channel has a series connection of an analog-digital converter W1 to W16 with a memory N1 to N16 controlled by a control device C '.
  • the analog-to-digital converter W1 to W16 is each subjected to a sampling frequency f by the control device C '. This is preferably somewhat higher than the previously stated value of 10.5 MHz.
  • Theoretical studies have shown that the frequency f can be below 20 MHz.
  • the phase accuracy of the digital chain is determined by the sampling frequency certainly. At a sampling frequency
  • FIG. 3 shows a fully digitized implementation of a delay concept, the delay in a phased array device again being divided into a fine delay (see area X) and a coarse delay (see area Z).
  • 64 channels are again provided in the area X of the fine delay, while only 16 processing channels are provided in the subsequent coarse delay area Z.
  • the components should be designed using ECL technology. It is assumed in the present case that the A / D conversion is carried out with a relatively high sampling frequency, which can also be greater than 28 MHz. In deviation from this, it can also be carried out according to the quadrature method, which is not shown in FIG. 3.
  • each of the shift registers VL1 to VL64 can comprise a total of 16 stages, while each of the shift registers VR1 to VR16 contains four times these 16 stages.
  • the same basic building blocks can be used in both types of shift registers.
  • the function of the shift registers VL1 to VL64 corresponds to a combination of the multiplexers Ml to M64 and the time delay elements Tl to T64 from FIG. 1.
  • the output of four such shift registers, for example VL1 to V14, each of which leads to neighboring ultrasonic transducer elements, for example E1 to E4 belong, are each connected together to a summing element S1 to S16.
  • a summing element S1 to S16 instead of a combination of four channels each, another number can be used, for example a number of 8 channels.
  • the delay times of the individual shift registers VL1 to VL64 can be changed under computer control during the reception of an ultrasound line, in particular in order to achieve dynamic focusing. For this purpose, their control inputs are connected to a control device C ".
  • the outputs of the individual summing elements S1 to S16 are each connected to an addition element AGL via an assigned shift register VR1 to VR16, which bring about the longer of the two delays. This sums up the individual summarized and delayed signals.
  • an output signal s' which is high-frequency compared to that of FIGS. 1 and 2. This high-frequency output signal s' corresponds to the amount and can be used for the image display. However, the two signal components i and q could also be derived from this high-frequency output signal s'.

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  • Physics & Mathematics (AREA)
  • Engineering & Computer Science (AREA)
  • Acoustics & Sound (AREA)
  • Multimedia (AREA)
  • Investigating Or Analyzing Materials By The Use Of Ultrasonic Waves (AREA)
  • Ultra Sonic Daignosis Equipment (AREA)
  • Measurement Of Velocity Or Position Using Acoustic Or Ultrasonic Waves (AREA)
  • Variable-Direction Aerials And Aerial Arrays (AREA)
EP85108128A 1984-07-12 1985-07-01 Dispositif de groupement phasé Expired EP0170072B1 (fr)

Priority Applications (1)

Application Number Priority Date Filing Date Title
AT85108128T ATE46783T1 (de) 1984-07-12 1985-07-01 Phased-array-geraet.

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
DE3425705 1984-07-12
DE19843425705 DE3425705A1 (de) 1984-07-12 1984-07-12 Phased-array-geraet

Publications (2)

Publication Number Publication Date
EP0170072A1 true EP0170072A1 (fr) 1986-02-05
EP0170072B1 EP0170072B1 (fr) 1989-09-27

Family

ID=6240486

Family Applications (1)

Application Number Title Priority Date Filing Date
EP85108128A Expired EP0170072B1 (fr) 1984-07-12 1985-07-01 Dispositif de groupement phasé

Country Status (5)

Country Link
US (1) US4829491A (fr)
EP (1) EP0170072B1 (fr)
JP (1) JPH0778492B2 (fr)
AT (1) ATE46783T1 (fr)
DE (2) DE3425705A1 (fr)

Cited By (3)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US4975885A (en) * 1988-09-30 1990-12-04 Siemens Aktiengesellschaft Digital input stage for an ultrasound apparatus
EP0430450A2 (fr) * 1989-11-28 1991-06-05 Hewlett-Packard Company Système d'imagerie à ultrasons comprenant un réseau commandé en phase en deux dimensions, avec variation de phase distribuée
FR2721716A1 (fr) * 1994-06-27 1995-12-29 Westinghouse Electric Corp Procédé de mise en forme d'un faisceau et conformateur de faisceau combiné, déphaseur et retardateur, utilisé dans ce procédé.

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CA1232059A (fr) * 1985-03-21 1988-01-26 Donald C. Knudsen Controleur de retard numerique pour generateurs de signaux sonar et radar
DE3920705A1 (de) * 1989-06-24 1991-01-10 Honeywell Elac Nautik Gmbh Digitaler richtungsbildner
US5263004A (en) * 1990-04-11 1993-11-16 Hewlett-Packard Company Acoustic image acquisition using an acoustic receiving array with variable time delay
US5269307A (en) * 1992-01-31 1993-12-14 Tetrad Corporation Medical ultrasonic imaging system with dynamic focusing
DE4223676C2 (de) * 1992-07-17 1997-06-12 Siemens Ag Verfahren zur adaptiven räumlichen Ausfilterung eines gewünschten Signals und zur Unterdrückung von Störersignalen beim Funksignalempfang
US5685308A (en) * 1994-08-05 1997-11-11 Acuson Corporation Method and apparatus for receive beamformer system
US5793701A (en) * 1995-04-07 1998-08-11 Acuson Corporation Method and apparatus for coherent image formation
US5928152A (en) * 1994-08-05 1999-07-27 Acuson Corporation Method and apparatus for a baseband processor of a receive beamformer system
US6029116A (en) * 1994-08-05 2000-02-22 Acuson Corporation Method and apparatus for a baseband processor of a receive beamformer system
US5573001A (en) * 1995-09-08 1996-11-12 Acuson Corporation Ultrasonic receive beamformer with phased sub-arrays
US6128958A (en) * 1997-09-11 2000-10-10 The Regents Of The University Of Michigan Phased array system architecture
KR100264866B1 (ko) 1998-07-13 2000-09-01 윤종용 다수의 트렁크 기능을 지원하는 디지털 트렁크회로
US6166573A (en) * 1999-07-23 2000-12-26 Acoustic Technologies, Inc. High resolution delay line
US6421443B1 (en) 1999-07-23 2002-07-16 Acoustic Technologies, Inc. Acoustic and electronic echo cancellation
US8057408B2 (en) * 2005-09-22 2011-11-15 The Regents Of The University Of Michigan Pulsed cavitational ultrasound therapy
US10219815B2 (en) 2005-09-22 2019-03-05 The Regents Of The University Of Michigan Histotripsy for thrombolysis
US20070083120A1 (en) * 2005-09-22 2007-04-12 Cain Charles A Pulsed cavitational ultrasound therapy
US9061131B2 (en) 2009-08-17 2015-06-23 Histosonics, Inc. Disposable acoustic coupling medium container
CA2770706C (fr) * 2009-08-26 2017-06-20 Charles A. Cain Dispositifs et procedes d'utilisation de cavitation commandee a nuage de bulles dans le fractionnement de calculs urinaires
US9943708B2 (en) 2009-08-26 2018-04-17 Histosonics, Inc. Automated control of micromanipulator arm for histotripsy prostate therapy while imaging via ultrasound transducers in real time
US8539813B2 (en) 2009-09-22 2013-09-24 The Regents Of The University Of Michigan Gel phantoms for testing cavitational ultrasound (histotripsy) transducers
US9144694B2 (en) 2011-08-10 2015-09-29 The Regents Of The University Of Michigan Lesion generation through bone using histotripsy therapy without aberration correction
US9049783B2 (en) 2012-04-13 2015-06-02 Histosonics, Inc. Systems and methods for obtaining large creepage isolation on printed circuit boards
EP2844343B1 (fr) 2012-04-30 2018-11-21 The Regents Of The University Of Michigan Fabrication de transducteurs à ultrasons à l'aide d'un procédé de prototypage rapide
US20140100459A1 (en) 2012-10-05 2014-04-10 The Regents Of The University Of Michigan Bubble-induced color doppler feedback during histotripsy
US11432900B2 (en) 2013-07-03 2022-09-06 Histosonics, Inc. Articulating arm limiter for cavitational ultrasound therapy system
BR112015032926B1 (pt) 2013-07-03 2022-04-05 Histosonics, Inc. Sistema de terapia de ultrassom
US10780298B2 (en) 2013-08-22 2020-09-22 The Regents Of The University Of Michigan Histotripsy using very short monopolar ultrasound pulses
JP6979882B2 (ja) 2015-06-24 2021-12-15 ザ リージェンツ オブ ザ ユニヴァシティ オブ ミシガン 脳組織の治療のための組織破砕療法システムおよび方法
EP3389500A4 (fr) * 2015-12-18 2019-01-02 Ursus Medical LLC Système et procédé de formation de faisceau ultrasonore à ouverture reconfigurable
JP2018146520A (ja) * 2017-03-08 2018-09-20 三菱日立パワーシステムズ株式会社 超音波探傷の方法、システム、プログラム及び記憶媒体
CA3065214A1 (fr) 2017-06-20 2018-12-27 Butterfly Network, Inc. Conversion de signal analogique-numerique dans un dispositif a ultrasons
KR20200019210A (ko) 2017-06-20 2020-02-21 버터플라이 네트워크, 인크. 초음파 디바이스를 위한 단일-종단 트랜스-임피던스 증폭기(tia)
US11324484B2 (en) 2017-06-20 2022-05-10 Bfly Operations, Inc. Multi-stage trans-impedance amplifier (TIA) for an ultrasound device
WO2018236779A1 (fr) 2017-06-20 2018-12-27 Butterfly Network, Inc. Amplificateur doté d'une compensation de gain en temps intégrée destiné à des applications ultrasonores
JP6993847B2 (ja) * 2017-11-07 2022-01-14 富士フイルムヘルスケア株式会社 超音波撮像装置、超音波プローブ、および、送信装置
WO2020113083A1 (fr) 2018-11-28 2020-06-04 Histosonics, Inc. Systèmes et procédés d'histotrypsie
JP2023513012A (ja) 2020-01-28 2023-03-30 ザ リージェンツ オブ ザ ユニバーシティー オブ ミシガン ヒストトリプシー免疫感作のためのシステムおよび方法

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FR2399661A1 (fr) * 1977-08-05 1979-03-02 Anvar Perfectionnements aux dispositifs de formation d'images ultrasonores en echographie b
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Cited By (5)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US4975885A (en) * 1988-09-30 1990-12-04 Siemens Aktiengesellschaft Digital input stage for an ultrasound apparatus
EP0361264B1 (fr) * 1988-09-30 1994-08-10 Siemens Aktiengesellschaft Partie d'entreé numérique pour un appareil ultrasonique
EP0430450A2 (fr) * 1989-11-28 1991-06-05 Hewlett-Packard Company Système d'imagerie à ultrasons comprenant un réseau commandé en phase en deux dimensions, avec variation de phase distribuée
EP0430450A3 (en) * 1989-11-28 1991-12-11 Hewlett-Packard Company 2-d phased array ultrasound imaging system with distributed phasing
FR2721716A1 (fr) * 1994-06-27 1995-12-29 Westinghouse Electric Corp Procédé de mise en forme d'un faisceau et conformateur de faisceau combiné, déphaseur et retardateur, utilisé dans ce procédé.

Also Published As

Publication number Publication date
US4829491A (en) 1989-05-09
DE3425705A1 (de) 1986-01-16
ATE46783T1 (de) 1989-10-15
EP0170072B1 (fr) 1989-09-27
DE3573341D1 (en) 1989-11-02
JPS6151560A (ja) 1986-03-14
JPH0778492B2 (ja) 1995-08-23

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