CN100462735C - Ultrasound transceiver system for remote operation through minimal number of connecting wires - Google Patents
Ultrasound transceiver system for remote operation through minimal number of connecting wires Download PDFInfo
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- CN100462735C CN100462735C CNB028296885A CN02829688A CN100462735C CN 100462735 C CN100462735 C CN 100462735C CN B028296885 A CNB028296885 A CN B028296885A CN 02829688 A CN02829688 A CN 02829688A CN 100462735 C CN100462735 C CN 100462735C
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Images
Classifications
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- G—PHYSICS
- G01—MEASURING; TESTING
- G01S—RADIO DIRECTION-FINDING; RADIO NAVIGATION; DETERMINING DISTANCE OR VELOCITY BY USE OF RADIO WAVES; LOCATING OR PRESENCE-DETECTING BY USE OF THE REFLECTION OR RERADIATION OF RADIO WAVES; ANALOGOUS ARRANGEMENTS USING OTHER WAVES
- G01S7/00—Details of systems according to groups G01S13/00, G01S15/00, G01S17/00
- G01S7/52—Details of systems according to groups G01S13/00, G01S15/00, G01S17/00 of systems according to group G01S15/00
- G01S7/52017—Details of systems according to groups G01S13/00, G01S15/00, G01S17/00 of systems according to group G01S15/00 particularly adapted to short-range imaging
- G01S7/52079—Constructional features
-
- 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
- B06B1/0625—Annular array
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- G—PHYSICS
- G01—MEASURING; TESTING
- G01S—RADIO DIRECTION-FINDING; RADIO NAVIGATION; DETERMINING DISTANCE OR VELOCITY BY USE OF RADIO WAVES; LOCATING OR PRESENCE-DETECTING BY USE OF THE REFLECTION OR RERADIATION OF RADIO WAVES; ANALOGOUS ARRANGEMENTS USING OTHER WAVES
- G01S15/00—Systems using the reflection or reradiation of acoustic waves, e.g. sonar systems
- G01S15/88—Sonar systems specially adapted for specific applications
- G01S15/89—Sonar systems specially adapted for specific applications for mapping or imaging
- G01S15/8906—Short-range imaging systems; Acoustic microscope systems using pulse-echo techniques
- G01S15/8909—Short-range imaging systems; Acoustic microscope systems using pulse-echo techniques using a static transducer configuration
- G01S15/8915—Short-range imaging systems; Acoustic microscope systems using pulse-echo techniques using a static transducer configuration using a transducer array
- G01S15/8922—Short-range imaging systems; Acoustic microscope systems using pulse-echo techniques using a static transducer configuration using a transducer array the array being concentric or annular
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- G—PHYSICS
- G01—MEASURING; TESTING
- G01S—RADIO DIRECTION-FINDING; RADIO NAVIGATION; DETERMINING DISTANCE OR VELOCITY BY USE OF RADIO WAVES; LOCATING OR PRESENCE-DETECTING BY USE OF THE REFLECTION OR RERADIATION OF RADIO WAVES; ANALOGOUS ARRANGEMENTS USING OTHER WAVES
- G01S15/00—Systems using the reflection or reradiation of acoustic waves, e.g. sonar systems
- G01S15/88—Sonar systems specially adapted for specific applications
- G01S15/89—Sonar systems specially adapted for specific applications for mapping or imaging
- G01S15/8906—Short-range imaging systems; Acoustic microscope systems using pulse-echo techniques
- G01S15/895—Short-range imaging systems; Acoustic microscope systems using pulse-echo techniques characterised by the transmitted frequency spectrum
- G01S15/8956—Short-range imaging systems; Acoustic microscope systems using pulse-echo techniques characterised by the transmitted frequency spectrum using frequencies at or above 20 MHz
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- G—PHYSICS
- G01—MEASURING; TESTING
- G01S—RADIO DIRECTION-FINDING; RADIO NAVIGATION; DETERMINING DISTANCE OR VELOCITY BY USE OF RADIO WAVES; LOCATING OR PRESENCE-DETECTING BY USE OF THE REFLECTION OR RERADIATION OF RADIO WAVES; ANALOGOUS ARRANGEMENTS USING OTHER WAVES
- G01S7/00—Details of systems according to groups G01S13/00, G01S15/00, G01S17/00
- G01S7/52—Details of systems according to groups G01S13/00, G01S15/00, G01S17/00 of systems according to group G01S15/00
- G01S7/52017—Details of systems according to groups G01S13/00, G01S15/00, G01S17/00 of systems according to group G01S15/00 particularly adapted to short-range imaging
- G01S7/52079—Constructional features
- G01S7/5208—Constructional features with integration of processing functions inside probe or scanhead
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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
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- G—PHYSICS
- G01—MEASURING; TESTING
- G01S—RADIO DIRECTION-FINDING; RADIO NAVIGATION; DETERMINING DISTANCE OR VELOCITY BY USE OF RADIO WAVES; LOCATING OR PRESENCE-DETECTING BY USE OF THE REFLECTION OR RERADIATION OF RADIO WAVES; ANALOGOUS ARRANGEMENTS USING OTHER WAVES
- G01S7/00—Details of systems according to groups G01S13/00, G01S15/00, G01S17/00
- G01S7/52—Details of systems according to groups G01S13/00, G01S15/00, G01S17/00 of systems according to group G01S15/00
- G01S7/52017—Details of systems according to groups G01S13/00, G01S15/00, G01S17/00 of systems according to group G01S15/00 particularly adapted to short-range imaging
- G01S7/52046—Techniques for image enhancement involving transmitter or receiver
- G01S7/52047—Techniques for image enhancement involving transmitter or receiver for elimination of side lobes or of grating lobes; for increasing resolving power
Abstract
An ultrasound pulse echo transceiver system for operation at a distance from an ultrasound measurement or imaging system through a minimal set of wires, comprising at least one ultrasound transducer element and an electronic circuit being mounted close to the transducer element and containing at least a receiver amplifier and a transmit switch. DC bias voltage to the electronic circuit is provided from the ultrasound instrument via a bias wire, and the transducer element is electrically connected to the input of the receiver amplifier, the amplifier input being designed so that it tolerates large AC transmit pulse voltages at the transducer electrodes. The output of the receiver amplifier is fed to the ultrasound instrument through a receiver wire, possibly through other electronic circuits. A transmit switch on one terminal is connected to the hot electrode of the transducer element and on the other terminals is connected to a transmit wire that feeds high voltage AC pulses from the ultrasound instrument, possibly through a buffer amplifier that is part of the transceiver, for transmission of ultrasound pulses from the transducer.
Description
Technical field
The present invention relates to small structure be carried out the high resolution ultrasonic imaging with the high frequency more than the typical 5MHz, wherein ultrasonic transducer or transducer array are treated by the described structure of imaging by passage is approaching, and described passage has limited space and is used for cable circuit connection ultrasonic transducer and ultrasonic imaging or measuring equipment.The example of these application comprises transducer by end of conduit to the intravascular ultrasound imaging (IVUS) of vascular wall, prostatic urethra tube imaging or the mini-incision by slype penetrate or other intra-operatives to the high-resolution imaging of tumour and small vascular.The present invention has proposed to have the solution of the measured back-scattered signal of extra high signal to noise ratio (S/N ratio) in the case, and the electromagnetic interference (EMI) of external source is had very strong inertia.
More particularly, the present invention relates at by ultrasonic transducer, ultrasound transducer array and the two prime amplifier electronic equipment, the design of circuit in conjunction with formed acoustic beam, allow electronic equipment and transducer in the assembly of compactness, to carry out integrated with short distance, thereby can be, even fewly in ultrasonic imaging or measuring system, work to two cables with the electronics line of very few number.
The present invention can also be applied to obtain for the maximum signal to noise ratio of the high-frequency ultrasonic imaging of structure with to the inertia of electromagnetic interference (EMI), for example high resolving power skin or eyes imaging (f～20-100MHz) with simpler means.It further can also be applied to the transducer array of a few components with high impedance is carried out low frequency imaging and measurement, to improve signal to noise ratio (S/N ratio) in these cases and to the inertia of electromagnetic interference (EMI).Its lifting that can also be applied to the switch with linear array focuses on (elevation focusing), and to reduce the number of cables of connection device, it is easier to the manual operation of transducer array to make.
Background technology
The spatial resolution of ultrasonic echo imaging system and ultrasound wave wavelength are closely related.Ultrasound wave wavelength λ relates to ultrasonic frequency f, i.e. λ=c/f, and wherein c～1540 μ m/ μ s are the propagation rate of ultrasound wave in cell tissue.In order to obtain lower wavelength, just resolution more clearly must be used the praetersonic frequency.Yet the picture depth of ultrasonic echo imaging (image depth) is owing to the absorption of cell tissue to ultrasonic energy is restricted.Owing to this absorption along with frequency strengthens, this upper limit that has been the given operable frequency setting of picture depth.Therefore, image resolution ratio is subjected to the restriction of picture depth.
Therefore for for example imaging of vascular wall of micro-structure, perhaps other internals' micro-structure need make ultrasonic transducer near described structure, thereby picture depth and minimizing that ultrasound wave is absorbed are restricted.For picture depth less than 10mm, can use the ultrasonic frequency in 20-100MHz scope, wavelength coverage is 75 to 15 μ m.The spatial resolution that this has produced in about 150 μ m to 30 mu m ranges depends on transducer frequency, bandwidth and aperture.
Ultrasonic transducer can be by in the end of conduit or other elongation equipment transducer architecture being installed near the inner structure in the health, for example vascular wall or other organs, described conduit or other elongation equipment insert in the health by otch or body's natural opening.Utilize cable to connect the transducer that extends detector and ultrasonic imaging or measurement mechanism end then.Use such high frequency can bring practical problems to the transducer that has with a certain distance from imaging device like this, for example:
1. for the ultrasonic frequency that is higher than 30MHz, transducer and be connected to impedance between the cable of imaging device and do not match and brought loss, thus limited the maximum image degree of depth under signal to noise ratio (S/N ratio) and the given frequency.The limited thickness that inserts device has also limited the thickness that connects the line of transducer and imaging device, has brought additional absorption and has reduced imaging sensitivity.
2. for example at 35MHz, the electromagnetic wavelength in the cable is approximately 6m, and then quarter-wave is approximately 1.5m, and this approximately is the length of typical conduit.Therefore conduit becomes and is similar to the interior quarter-wave tuned antenna of ultrasonic receiver frequency range, and imaging system becomes very responsive to external electromagnetic interference (EMI) source in effective receiver frequency range.
3. the other problems of use thin cable relates to and obtains narrow ultrasonic beam between ultrasonic transducer and device.Influence in order in wave beam focuses on, to reduce ultrasonic wave diffraction, and reduce focus diameter thus, must have a large amount of wavelength and pass effective transducer aperture (typically approximately needing 50 kinds of wavelength to pass the aperture).Yet under so low diffraction focused on, the depth of focus had reduced, and has limited the scope and the spatial resolution of clear focusing.
For received beam, the usual method that addresses this problem is to use the transducer element array of dynamic focusing, and wherein received beam focuses on the degree of depth that whenever all is received the place immediately following echo.Be deferred to each array element signal and dynamic focusing that electron gain is controlled by increase, thereby should postpone to be close to identical to all elements with the summation of propagation delay from the focus to the element.The delay that increases can utilize sound lag or electric delay circuit or both combinations and obtain.Also wish simultaneously effective transducer is transmitted the aperture along with picture depth increases together, with of the expansion of restriction focal diameter along with the degree of depth.
4. transmit for pulse, must select the fixing beam focus that transmits, because after pulse is transmitted, promptly can not change to it.Thereby wishing so to select between the different transmission depths of focus to focus on most important image range with transmitting wave beam.A kind ofly can obtain in the following way at the dynamic focusing that transmits wave beam, be about to the entire image zone and regard as by subregion and constitute, wherein each subregion carries out imaging by the independent transmission pulse at this subregion inner focusing.Also wish simultaneously effective transducer is transmitted the aperture along with picture depth increases together, with of the expansion of restriction focal diameter along with the degree of depth.
Therefore, wish to have a kind of be positioned at insertion equipment end have high s/n ratio and to the transducer array of the high noise immunity of electromagnetic interference (EMI), this array has the receiving aperture of dynamic or switchable collectiong focusing and expansion, the transmission aperture that switchable transmission focuses on and expands, can operate from ultrasonic imaging or measurement mechanism by the line of minimum number, make the xsect of the equipment in the narrow structures that is inserted into minimize.
Summary of the invention
The present invention has designed a kind of solution at these problems by electronic circuit being installed near ultrasonic transducer or transducer array, and wherein said circuit can pass through small number of lines, even operates to two cables less.
According to an aspect of the present invention, a kind of ultrasonic pulse echo transceiver of operating apart from ultrasonic measurement or imaging device certain distance by line is provided, described transceiver comprises the ultrasound transducer array of a) being made up of at least one ultrasonic transducer element, and b) is installed to electronic circuit near described transducer array, wherein said electronic circuit comprises that at least one receiver amplifier and at least one transmit switch, described at least one element of transducer is electrically connected to described at least one receiver amplifier input terminal, described amp.in is designed so that its AC that allows described transducer electrode place transmits pulse voltage, signal from described receiver amplifier is presented to described ultrasonic unit by the receiver line, described at least one transmission switch is connected to described at least one element of transducer and is connected on the other end at one end presents the transmission line that transmits pulse from the AC of described ultrasonic unit, by buffer amplifier as a described transceiver part, be used to send ultrasonic pulse from described transducer array, the DC bias voltage offers described electronic circuit by the biasing line from described ultrasonic unit, and wherein said electronic circuit is selected the smooth or transmission aperture that focuses on of described transducer array.
According to a further aspect in the invention, provide a kind of ultrasonic image-forming system, having comprised: the transceiver that at least one is above-mentioned, and be connected to the ultrasonic pulse echo imaging device of described at least one transceiver.
In its reduced form, the invention provides prime amplifier, described prime amplifier can be operated by the two-wire cable of DC bias voltage is provided to this amplifier.When transmitting high-voltage pulse by line, the puncture circuit connects this and is wired to transducer to transmit ultrasonic pulse, in receiving mode, the low level signal on the transducer is exaggerated and is fed to imaging or measurement mechanism as high level signal and by same link.Because received signal level has raise on the cable, this system has reduced the susceptibility to line loss and external electromagnetic interference, therefore makes the sensitivity of imaging or measurement maximize.
Dynamic collectiong focusing for array, the present invention provides the integrated electronic circuit that is installed near transducer array in its common version, this circuit provides prime amplifier to each element and delay circuit, automatic switch in the time series of described prime amplifier after pulse transmits, thus the dynamic focusing of received beam obtained.In one embodiment of the invention, the sound lag circuit that is positioned at the element of transducer front is used to the delay completely or partially of element signal.This circuit can also be arranged so that thereby transmitting pulse selects different transmission focal lengths can obtain a plurality of transmission focal imagings in a sequence.The invention also discloses and before transmitting pulse, use the signaling of encoding to be provided with and dynamic collectiong focusing scope to select to transmit by single cable to focus on.
In simpler enforcement, amplifier and commutation circuit and with two-wire cable imaging device and transducer system between realized focal length and the aperture that can control of the present invention by using pre-programmed.Described commutation circuit optionally makes up one group of prefocusing array element and default the delay for each focusing range.The default focal length of described each element is selected as making the phase differential of crossing over each element and each effective aperture all less than a limit of the scope of carrying out beam shaping at element with postponing, and for example 90-120 spend.The element of accelerating is combined with the degree of depth, can obtain to limit the aperture of increase of beam diameter and the degree of depth of increase.
In the special enforcement of simplifying, the prefocus of each element and delay all provide by being positioned at each element sound lens material with suitable curvature and thickness before.Electronic circuit was provided possible amplification to this signal before optionally adding in the commutation circuit of controlling in the time from the signal of each element then, and described commutation circuit transmits to be carried out by pulse and resets.
Description of drawings
Fig. 1 a has shown an example embodiment according to the transceiver of being made up of single transducer element and electronic circuit that can operate from ultrasonic measurement or imaging device by many cables of the present invention;
Fig. 1 b has shown according to the receiver input switch and an example embodiment that transmits switch as a described electronic circuit part of the present invention;
Fig. 1 c has shown a simplified embodiment according to the transceiver of being made up of single transducer element and electronic circuit that can operate from ultrasonic measurement or imaging device by a two-wire cable of the present invention;
Fig. 1 d has shown the example embodiment according to the component-level of the transceiver circuit with single transducer element that can operate from ultrasonic unit by a two-wire cable of the present invention;
Fig. 2 a has shown an example embodiment of the annular array that the switching that is used for the effective aperture and the depth of focus according to the present invention is controlled;
Fig. 2 b and 2c have shown two other example embodiment of the annular array that the switching that is used for the effective aperture and the depth of focus according to the present invention is controlled;
Fig. 3 a shown according to of the present invention by electronic circuit and transducer array being used for of forming to effective reception with transmit the aperture and the depth of focus carries out selecting an example embodiment of the transceiver circuit that switches, this transceiver can be operated apart from ultrasonic measurement or imaging device certain distance by multi-thread cable; And
Fig. 3 b has shown that this transceiver can be operated apart from ultrasonic measurement or imaging device certain distance by a two-wire cable according to an example embodiment of the transceiver circuit of simplification of effective receiving aperture and the depth of focus dynamically being switched with fixing effective transmission aperture and the depth of focus by electronic circuit and transducer array being used for of forming of the present invention.
Embodiment
Provide some example embodiment of the present invention below with reference to accompanying drawing.Fig. 1 a has shown the ultrasonic pulse echo transceiver unit of being made up of electronic circuit 101 and ultrasonic transducer 102 100.Described transceiver unit is connected to ultrasonic measurement or imaging device 103 by a multi-thread cable 104.The DC bias voltage offers described electronic circuit from ultrasonic unit by biasing line 107, and described transceiver has the common ground that is connected to ultrasonic unit by ground wire 112.According to the known technology that protection low level received signal is not influenced by external electromagnetic interference, whole cable can be encapsulated in the conducting metal shielding, and described conducting metal shielding is described device place ground connection.
The thermode of element of transducer is connected to an end that transmits switch 109, and wherein the other end is connected to the output that transmits pulse buffer 110.High voltage AC transmits pulse and is fed by transmitting line 111 from ultrasonic unit, wherein during transmitting pulse persistance, transmits switch 109 and is switched to low AC voltage to send the ultrasonic pulse 113 from element of transducer 102.
After pulse transmits, transmit switch 109 and switch to high AC impedance, element of transducer 102 and transmission driving circuit 110 are isolated.Backscattering ultrasound wave 114 is converted into the low level electric signal by transducer, and offers prime amplifier 105 by receiver input switch 106.Described receiver input switch has low-down series impedance to low level signal in receiving cycle, and its series impedance is designed to meet the prime amplifier characteristic.High voltage AC for transducer transmits pulse, and receiver switch 106 plays the effect that restriction enters the maximum current of amp.in, and the protection that the receiver amp.in is transmitted pulse for high AC voltage is provided thus.
The output of receiver amplifier is provided for ultrasonic unit by receiving line 108, and the amplifying signal that the back-scattered signal on the element of transducer is provided thus is to ultrasonic measurement or imaging device.Be connected to the influence that the amplification level of the received signal on the cable of ultrasonic unit has reduced the circuit loss and disturbed from the external electric magnetic source, provide high s/n ratio for the received signal that is sent to described device thus.
Receive an example that transmits switch and in Fig. 1 b, be shown as 106.This switch is made up of two diodes 121 and 122 of reverse butt joint, has the forward bias current by biasing resistance 123,124,125. Electric capacity 126 and 127 provides switch to isolate to the DC of prime amplifier input end and transfer circuit biasing, wherein 109 examples that shown the transmission switch of being made up of two diodes 131 and 132.Transmitting switch provides for the high AC impedance isolation of the low level AC voltage on the switch input terminal with for the low AC impedance at the high level AC voltage that transmits switch input terminal.
The transceiver system that has shown the simplification that to present from ultrasonic unit by the two-wire cable among Fig. 1 c.In this embodiment of the present invention, DC setovers, transmits and receive to be connected and is integrated into single signal link 108, comprising ground wire 112, provides from the two-wire operation of ultrasonic unit to transceiver system.
In the example embodiment in Fig. 1 c, do not had the transmission impact damper on electronic circuit board, wherein transducer transmission drive signal directly offers by common signal line 108 from ultrasonic unit and transmits switch 109 and further offer element of transducer 102.For example, can provide DC to setover by public line 108 and not damage amplifier to amplifier output by the open transistor output of prime amplifier 105 or the resistance of connecting with amplifier output.Even have open transistor output, the resistance in series of using amplifier to export is carried out the impedance matching of the received signal of device cable still very convenient.Such resistance in series can further transmit impulse duration at high AC voltage and provide better protection for amplifier output.
Example among Fig. 1 b receives disconnector 106 and transmits the signal level of switch 109 by the switch input to be switched between the Low ESR in the high impedance in isolation mode and the connection pattern automatically.According to the conventional method of design of electronic circuits obviously, these switches can be made up of switching transistor or diode, and wherein hindrance is by control signal voltage or electric current decision.Therefore the present invention includes according to the modification of the electronic design technology of standard to the switch example in the accompanying drawing.
Fig. 1 d has shown the example of detailed circuit according to an embodiment of the invention among Fig. 1 c.In the figure, transistor 140 provides input protection switch 106 places that prime amplifier is provided at input protection switch 106 places by series capacitance 141 and limit transistor diode 142.Electric capacity 141 and amplifier input resistance are designed to together in the transmission cycle and by in the isolating diode 142 restriction loads, provide the high level transition function in actual ultrasonic frequency scope.It is that capacitor adds few noise to the signal that receives that series capacitance is compared with transistor in the advantage aspect the receiver input protection with diode.
The open output of amplifier transistor 140 offers signal wire 108 by resistance 143; resistor 143 is provided at and receives impedance matching interior at interval and the receiver cable, and provides the high voltage of amplifier transistor to transmit the pulse protection with transistors diodes 144.The resistance 145 that is connected to substrate allows to use the negative pulse that transmits in this design.
Transmitting switch 109 in this example is made up of one group of rightabout diode transistors 146 and 147.Four transistor diode 146 series connection are with the biasing/transmission/reception line of permission combination and the DC bias voltage between the transducer.The AC voltage amplitude of transfer circuit is assumed to the accumulation knee voltage (knee voltage) far above diode.
In order to control the focusing of ultrasonic beam, the invention provides the signal from selectable transducer group is carried out combined solution, wherein signal/the ripple of each element has fixed-focus and delay.Shown example annular array among Fig. 2 a according to principle of the invention work.The figure illustrates plane annular array with 3 elements 201,202 and 203.In described first example, element focuses on and delay line is realized by the acoustical material 204,205 and 206 that inserts previously at element of transducer on the acoustic path between cell tissue and the element of transducer.Shown the acoustical material (for the about 1540 μ m/ μ s of soft tissue object) with the acoustic propagation speed that is higher than the acoustic propagation speed for the treatment of imaging object in this particular example, it provides signal in advance more than signal delay in fact.Yet, such signal can be considered to negative in advance and postpone, and we can be called the acoustics delay line with the acoustical material setting of described transducer front for simplicity, and no matter the wave speed of this material is higher than or is lower than the wave speed of object/tissue.
The curvature of acoustical material provides the fixed-focus from the ripple of described element, and the interior thickness of described material provides the delay of element signal/ripple or (born delay) in advance.As general rule, the focusing of the signal/ripple of each element and delay be selected as making ripple from point source for the phase differential of being had a few in the effective aperture less than limit φ
m
In the specific example of Fig. 2 a, central member 201 participated in Fig. 2, being shown as 207 and 208 from z
nTo z
fScope R
1Interior beam shaping.In order to minimize the phase differential of this element in its gamut that participates in imaging, we select the fixed focal length F of element
1For:
Be shown 209 in the drawings.In order to minimize the phase differential in the gamut, scope z=z externally
nAnd z=z
fPhase differential on the central member at place is φ
m, this radius that provides inner member is
Beam diameter from described central member is given as in its imaging scope
Wave beam is subjected to expanding the restriction of circuit 210, and is in certain depth z
1=d
F1a
1/ λ is shown 211, crosses the restriction diameter d from the beam diameter expansion of element 201
F1, be shown the circuit 212 among Fig. 2 a.At a z
1Outside we by reducing beam angle to making up from the signal of element 201 with from the signal of second element 202.Like this beam angle is reduced to d
F1To be issued to 213 set-points of example circuit.
In this example embodiment, second element has participated in from z
1To z
fScope R
2Interior beam shaping.The fixed focal length of second element is selected as making the phase differential of whole element at R
2In minimize, this shows at z=z
1And z=z
fPlace's phase differential equals φ
m, this provides
In Fig. 2 a, be shown 214.Such focal length select to make element participate in wave beam from z
1To z
fGamut in phase differential minimize.The outer radius of second element is selected as making for z=z
1And z=z
fThe maximal phase potential difference of whole element is φ
mThis shows
The focal length of element is by the curvature decision of lens/lag line material.For very big F-number (=F/D, wherein D is an aperture diameter), can be with focal length F
kTo element #k approximate evaluation lens radius of curvature R
kFor
C wherein
1Propagation rate and c for lens material
tBe the object materials propagation rate of cell tissue for example.In order to make F-number near unified, lens curvature must change on whole lens, wherein can carry out detailed calculated by how much ray acoustics.
In order to obtain the optimum focusing of described new compound wave beam, thereby the thickness that can adjust the lens/lag line material of element of transducer front makes wave propagation phase place from two elements at focal length F
2In time, equate.This propagation phase by from element the average transmission time of the point of showing up a little (field point) determine.The F that has a few from No. 2 elements
2Travel-time equate because focal length is F
2Signal/ripple that the average thickness of the lens material of No. 2 element fronts has provided this element postpones, and therefore must be chosen as to make No. 2 elements to F
2Travel-time equal No. 1 element to F
2Average transmission time.The variation of the lens of each element front/lag line material thickness is as shown in Fig. 2 a, and the details of lens/lag line material thickness and curvature can be calculated by how much ray acoustics.
This process is carried out according to general principle then, supposes that wherein the signal from k element of transducer is combined to form the effective aperture.Along with increasing, z make focal diameter at z
kRestriction d is crossed in expansion
F1, we add element k+1 to the effective aperture.The fixed focal length of element k+1 and radius thereof are selected as making phase differential for z=z
kAnd z=z
fValue be φ
mObtain like this
As long as z
k＜z
fThen repeat this process.
Special in 3 element arrays among Fig. 2 a, we are at z
2Comprise three element 203, be shown 215 in the drawings, and three-element focal length is chosen as F according to formula (6)
3And be shown 216 in the drawings.The thickness of the lens of No. 3 element fronts/lag line material 206 and curvature are calculated according to how much ray acoustics, thereby: 1) from No. 3 elements to F
3Travel-time be invariable on whole element to obtain focal length F
3, and 2) from No. 3 elements to F
3Travel-time equal No. 1 and No. 2 elements on the F that has a few
3Average transmission time, thereby for No. 1 of combination and No. 2 element ripples and No. 3 element ripples at F
3The same propagation phase place is arranged.From the beam angle in aperture in full force and effect along with circuit 217 passes through depth z
2And expand.
The total quantity of required array element is by maximal phase potential difference φ
mWith select from z
nTo z
fThe imaging scope and the restriction beam angle d of selection
F1Determine.These parameters are given regularly, and the focal length of first element and diameter are promptly given, thereby the beam diameter in the most close zone that only has first element to participate in focusing on is also given.Must select z in pairs then
nAnd d
F1So that hithermost beam diameter is less than d
F1
Usually having need be with z
fThe darkest beam diameter at place is limited in d
F1Situation.This maximum diameter of hole radius that draws whole array is a
K=λ z
f/ d
F1For acceptable phase difference on the whole element
m, must select z
nFor
Therefore can utilize the general principle of summarizing above and use multiple design proposal.It should further be appreciated that in the effective aperture in depth range and can get rid of inner member.The secondary lobe (sidelobes) that this can increase in the wave beam of generation depends on to be excluded the relative diameter of element for whole effective aperture diameter.Such benefit is that the foreign range of inner member participation effective aperture has reduced, and allows the more approaching z of inner member
n, perhaps narrower wave beam in wideer diameter of inner member and the internal range.
From the focusing of the signal/ripple of each element with postpone and to obtain not having lens/delay material by shown in Fig. 2 b, forming array surface.In the figure, the focal length of each element is by its curvature decision, and the propagation delay of each element is by the determining positions of this element simultaneously.The position of components that indicates in Fig. 2 b can provide and the identical travel-time from new element to its focus of average transmission time to new element focus of element internally as discussed above.This has provided the complex form of array surface, and wherein Fig. 2 c has provided and made simpler array surface shape.Can use the additional electronic delay that some below will describe in this end in electronic circuit, guaranteeing the signal/ripple for element of making a fresh start and inner member, the phase place at the focus place of a new element is identical.Solution among Fig. 2 a provides simpler manufacturing technology like this, because net shape can be cast or cut into to lens/delay material at the top of planar array.The average thickness of the lens among Fig. 2 a/delay material also increases along with element width, and the absorption in lens/delay material provides the change mark (apodization) for the signal/ripple of whole array, to reduce beam side lobe.
Among Fig. 3 a 300 shown the example pulse echo transceiver circuit that has selectable transmission and collectiong focusing according to of the present invention.This transceiver is made up of example electronic circuit 301 with amplifier and the switch that is connected to three membrane transducer array elements 201,202 and 203.In receptive pattern; the thermode of element of transducer is connected to receiver amplifier 303,305 and 307 by receiver input switch 302,304,306, and described receiver input switch 302,304,306 is similar to the transceiver of discussing among Fig. 1 a-d and plays the receiver protective effect during transmitting.The output of receiver amplifier offers the signal summing circuit by focal length selector switch 309,311,313, also may pass through electronic signal lag line 308,310,312.Receive summing circuit and be output as the received signal that selectivity focuses on, offer ultrasonic unit by receiving lines 108.
In this example embodiment of the present invention, the collectiong focusing switch is by receive selecting circuit 315 controls, and described reception selects circuit 315 further to receive signaling line 316 by at least one and by the signal controlling from ultrasonic unit.By the signaling on this line, collectiong focusing switch 309,311 and 313 selected combination are closed so that the received signal from the selected combination of membrane transducer array elements 201,202,203 is sued for peace.With reference to discussion, can see that such selection provides selected effective receiving aperture and wave beam focal length in conjunction with Fig. 2.Delay line 308,311,312 postpones to provide for the required total element signal of the optimum focusing of received beam/ripple according to combining chosenly in conjunction with the description of Fig. 2 with the acoustics delay line of element of transducer front.In a lot of embodiment of the present invention, the acoustical material delay line that all signal delays may be added by formation array surface and array front obtains, thereby electronic delay circuit 308,310,312 can omit.Therefore, for given embodiment, can be by receiving signaling selective reception focal length and the aperture on the signaling line 316.
In order to transmit ultrasonic pulse, the embodiment among Fig. 3 a provides by transmitting cable 111 and has transmitted pulse to transceiver from ultrasonic unit.This signal offers the transmission buffer amplifier 317 that is connected to element of transducer 201,202,203 by transmitting switch 318,319,320.In this particular example, transmit switch 318 and be chosen to be diode switch 109 among Fig. 1 b, when input end has high AC potential pulse, automatically switch to low AC impedance, and when input end has low level AC signal, switch to high AC impedance.Therefore, in this embodiment, element 201 always participates in effectively transmitting the aperture.
By the composite signal on received signal line 316 and the transmission signal link 322, can obtain the minimum widith of the transmission/reception observation beam of combination in the certain depth scope.For continuous transmission pulse, this depth range can be from z
nTo z
fWhole measurement/imaging scope on order increase, thereby with the very narrow width of compound transmission/reception observation beam gamut is carried out imaging.
In order to reduce the wiring quantity that is connected to ultrasonic unit, receive and transmit signaling and all can utilize high AC voltage transmission pulse self to obtain by transmitting line 111.For example, reception and transmission select circuit all can to reset by the high voltage that cycle time goes up on the transmission line, thereby for first transmission pulse after resetting, have obtained to make up the short depth of focus of transmission/reception observation beam.Receive then and transmit and select circuit 315 and 321 to transmit pulse continuously by increment for each, thereby obtained to transmit the observation beam depth of focus of the increase of pulse, in the depth range that increases, measured and imaging thereby transmit pulse for each for each.This embodiment provides from z thus
nTo z
fWhole measurement/imaging scope on minimum beam angle.
Also note that by such operation collectiong focusing switch 309 can be hard-wired (hardwired) closure, allow to merge reception (315) and transmit (321) selection circuit.Yet in order to minimize the transmission number of pulses, when particularly having a large amount of array element, the depth range that generally can select more rough transmission to focus on dynamically switches collectiong focusing by in transmitting focusing range at each.Transmit then and select circuit 321 generally can directly select more rough element group for transfer port, select circuit generally can be transmitted pulsed reset by each and provide domino (domino) time of collectiong focusing switch to switch and receive, to provide after transmitting in pulse, be called dynamic collectiong focusing along with the stable aperture and the depth of focus that increases of time.Can cover whole imaging scope with transmission pulse (few) and fixing transmission aperture and focal length still less by this method to single transmission pulse.This provides the flank speed of measurement/imaging fully, though have than manying transmission focusing measurement and the littler compound transmission/reception observation beam width of imaging.
More simple embodiment according to the present invention is operated from ultrasonic unit by the two-wire cable, shown in Fig. 3 b.In receiving mode, element of transducer optionally is connected to summing amplifier 330 by receiving input switch 331, and described reception input switch 331 plays the effect that reception amplifier is protected during transmitting.In this embodiment, element 201 is fixedly coupled summing amplifier, element 202 and 203 is connected to summing amplifier by controllable collectiong focusing switch 332 and 333 simultaneously, and described controllable collectiong focusing switch 332 and 333 selects circuit 334 to control by receiving.This circuit resets by transmitting pulse, and transmits the back up to time t in pulse
1=2z
1/ c only has element 201 to be connected to summing amplifier.At this moment, collectiong focusing switch 332 is opened to increase the movable receiving aperture and the depth of focus according to the principle of describing in conjunction with Fig. 2.Time t after pulse transmits
2=2z
2/ c, collectiong focusing switch 333 are also opened with the effective receiving aperture of further increase and the depth of focus, focus on thereby obtained dynamic received beam effectively.The received signal of the dynamic focusing of summing circuit output place is sent to ultrasonic equipment by public biasing/reception/transmission line 107.
In order to transmit ultrasonic pulse, array element 201 and 202 is connected to common bias/reception/transmission line 107 by transmitting switch 335 and 336, described transmission switch 335 and 336 is low AC impedance by transmitting that high AC voltage on the line opens automatically, and turn-offs high AC impedance during the low level AC voltage on transmitting line.For the embodiment that is given, according to the top principle of describing in conjunction with Fig. 2, two array elements 201 with 202 in transfer mode parallel the connection, provide very large-scale transmission to focus on and appropriate transmission aperture and width.
Embodiment among Fig. 3 b provides the transceiver with fixing reception focal length that transmits focal length and dynamically switch, be used for the suitable narrow combination transmission/reception observation beam on whole measurement/imaging scope, gamut is had single transmission pulse, and therefore have higher image frame per second than the transmission focusing of describing in conjunction with Fig. 3 a of manying.
By the focusing technology of describing in conjunction with Fig. 2, the array element area can increase along with the depth of focus.In transfer mode, then should be with all active components of identical driven, and the physical property propagated of the ripple in the cell tissue depends on the element area and provides appropriate change to the element ripple.
In receiving mode, the point source on the beam axis can provide the open-circuit voltage from each element, the element area relationship in itself and the limit, and in those limits, the variation of element area can not influence the vibration mode (vibration pattern) of element.And the electrical impedance of element is as the inverse of element area and change.
Amplify by the open-circuit voltage of the high input impedance voltage reception amplifier in the electronic circuit element of transducer, must use the enlargement factor that is directly proportional with transducer area, to obtain beam configuration suitable in the summing circuit for each element receiver channel.For low input impedance electric current receiver amplifier, be inversely proportional to from the input current of each element of transducer and element electricity input/source impedance, so aforesaidly be directly proportional with the element area.The current gain that so can all element receiving cables equates and obtain thereby the suitable enlargement factor of each element signal is obtained suitable beam configuration.
The change mark of the element signal in whole aperture is used to reduce the secondary lobe in the wave beam.Yet, for large-scale element, annular array for example, the variation of the electronic receiver gain between the element passage has limited effect, because it can introduce very big step (step) in the apodizing function between element, this can increase secondary lobe.Therefore for large-scale element, providing more continuous change mark in the array front of the thickness with variation with the absorption acoustical material is of great use, for example shown in Fig. 2 a.
Example among Fig. 2 has been described the switching focusing by annular array, wherein it should be apparent that from above-mentioned discussion ultimate principle of the present invention can use linearity or two-dimensional array.The beam scanning of linear array can be according to principles well-known, by the horizontal switching that participates in element being realized the beam scanning of annular array simultaneously can realize by mechanical rotation or the whole transceiver devices of translation.
Therefore described transceiver is well suited for being installed to the end of imaging device of elongation to be inserted in for example lived subject of imageable target, so that transceiver is near treating imaging arrangement.Can allow like this to use the praetersonic frequency with the highest as far as possible resolution to structure imaging.The exemplary of these application comprises the imaging in the mini-incision operation, to imaging in the blood vessel of vascular wall, to the intrauterine imaging of uterine wall, perhaps to imaging in the prostatic urethra tube.In some applications, can use elongation equipment, described elongation equipment has and can treat on the imaging arrangement so that the imaging end is placed into from the end that this equipment end is controlled.In other were used, described elongation equipment can unmanaged flexibility, for example is inserted in the blood vessel.
Therefore, although show, describe and pointed out to be applied to the of the present invention basic innovation character of preferred embodiment at this, but should be appreciated that those skilled in the art can to institute's description equipment with and the form of making and details on various omissions, substitute and change and do not deviate from essence of the present invention.For example, clearly be intended that in basic identical mode and carry out basic identical function all within the scope of the present invention with all combinations of the element of realizing identical result and/or method step.And, will be appreciated that, in conjunction with any open form of the present invention or embodiment show and/or the structure described and/or element and/or method step can be used as the general essence of design alternative and be included in any other open describe or the form or embodiment of suggestion in.Therefore the present invention is only limited by the scope of appended claims.
Claims (16)
1. ultrasonic pulse echo transceiver of operating apart from ultrasonic measurement or imaging device certain distance by one group of line,
Described transceiver comprises the ultrasound transducer array of a) being made up of at least one ultrasonic transducer element, and b) be installed to electronic circuit near described transducer array, wherein
Described electronic circuit comprises that at least one receiver amplifier and at least one transmit switch,
Described at least one element of transducer is electrically connected to described at least one receiver amplifier input terminal, and described amp.in is designed so that its AC that allows described transducer electrode place transmits pulse voltage,
Signal from described receiver amplifier is presented to described ultrasonic unit by the receiver line,
Described at least one transmission switch is connected to described at least one element of transducer and is connected on the other end at one end presents the transmission line that transmits pulse from the AC of described ultrasonic unit, by buffer amplifier as a described transceiver part, be used to send ultrasonic pulse from described transducer array
The DC bias voltage offers described electronic circuit by the biasing line from described ultrasonic unit,
Wherein said electronic circuit is selected the smooth or transmission aperture that focuses on of described transducer array.
2. ultrasonic pulse echo transceiver according to claim 1, wherein said electronic circuit is from described transducer array selective reception aperture, with degree of depth inner focusing received beam, make that the signal from the reception of described received beam forms complete image or measures beam signal from given beam direction in imaging or measurement.
3. ultrasonic pulse echo transceiver according to claim 1, at least two in wherein said receiver line, biasing line and the transmission line are connected and are incorporated into the wall scroll line, and
Described receiver line, biasing line and transmission line are connected and are incorporated into the wall scroll line.
4. ultrasonic pulse echo transceiver according to claim 1, wherein said at least one receiver amplifier bear big AC and transmit the ability of voltage by obtaining with described amp.in series capacitors.
5. ultrasonic pulse echo transceiver according to claim 1, wherein said transducer array is made up of a single transducer element.
6. ultrasonic pulse echo transceiver according to claim 5, wherein said element of transducer is focused.
7. ultrasonic pulse echo transceiver according to claim 2, wherein
Described transducer array is composed of more than one element, and wherein each element has fixed focal length and is coupled to fixing signal delay line, and
Described electronic circuit comprises an element received signal summing circuit and at least one electronics collectiong focusing switch, and
Signal from least some array elements is coupled to described summing circuit through controlled electron collectiong focusing switch, and
The element focus of each element and element signal postpone to be made so that by closing the focusing switch that is used for an element group of selecting, obtain to have a reception effective aperture of selecting of given receiving aperture depth of focus.
8. ultrasonic pulse echo transceiver according to claim 7, wherein at least some described transmission switches can selectively cut out with control signal, can be selected electronically to select the focus of this transmission wave beam so that participate in a component number that transmits the aperture.
9. ultrasonic pulse echo transceiver according to claim 7, wherein said element signal postpone at least in part to obtain by one of following:
The acoustics lag line part of one lens combination of described element of transducer front, and
The relative mechanical positioning of these array elements.
10. ultrasonic pulse echo transceiver according to claim 7, comprise that a time sequence that is used for after pulse transmits closes these collectiong focusing switches so that be connected to the component number of this summing circuit and increase in time after pulse transmits, and after pulse transmits, produce the effective receiving aperture of increase in time and the depth of focus of increase, to produce the device that receives dynamic focus.
11. ultrasonic pulse echo transceiver according to claim 7, wherein
Total picture depth is divided into several subranges, and
Obtain to be used for the picture signal of each subrange from the signal of the reception of the transmission pulse of the separation that is used for each subrange, and
For the picture signal from each subrange, a receiving transducer element group is selected, and the focus of wherein said received beam is in this subrange to produce the received beam that focuses on, and wherein the signal of this reception is used to measurement/imaging.
12. ultrasonic pulse echo transceiver according to claim 8, wherein
Total picture depth is divided into several subranges, and
Obtain to be used for the picture signal of each subrange from the signal of the reception of the transmission pulse of the separation that is used for each subrange, and
For the picture signal from each subrange, one transmits the selected transmission wave beam that focuses on generation of element of transducer group, and the focus of wherein said transmission wave beam is in this subrange, and wherein the signal of this reception is used to measurement/imaging.
13. ultrasonic pulse echo transceiver according to claim 7, wherein said transducer array are to produce the annular array of this wave beam around the focusing of beam axis.
14. a ultrasonic image-forming system comprises:
At least one reaches according to the transceiver of claim 1
Be connected to the ultrasonic pulse echo imaging device of described at least one transceiver.
15. according to the ultrasonic image-forming system of claim 14, wherein said at least one transceiver is installed in the tip of an elongation equipment to insert in the body by otch or natural human body opening.
16. ultrasonic image-forming system according to claim 14, wherein this imaging system is used a transducer array, the two dimensional element that described transducer array has on the main line beam scanning direction distributes, wherein participate in the lifting focusing that element obtains to control, and obtain described linear beam scanning by these horizontal switchings that participate in elements by switching.
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| PCT/NO2002/000301 WO2004021044A1 (en) | 2002-08-29 | 2002-08-29 | An ultrasound transceiver system for remote operation through a minimal number of connecting wires |
Publications (2)
| Publication Number | Publication Date |
|---|---|
| CN1685246A CN1685246A (en) | 2005-10-19 |
| CN100462735C true CN100462735C (en) | 2009-02-18 |
Family
ID=31973750
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CNB028296885A Expired - Fee Related CN100462735C (en) | 2002-08-29 | 2002-08-29 | Ultrasound transceiver system for remote operation through minimal number of connecting wires |
Country Status (5)
| Country | Link |
|---|---|
| EP (1) | EP1540370A1 (en) |
| JP (1) | JP2005537081A (en) |
| CN (1) | CN100462735C (en) |
| AU (1) | AU2002313622A1 (en) |
| WO (1) | WO2004021044A1 (en) |
Families Citing this family (22)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| JP4795878B2 (en) * | 2006-07-13 | 2011-10-19 | 株式会社東芝 | Ultrasonic diagnostic apparatus, ultrasonic diagnostic apparatus and ultrasonic diagnostic system using ultrasonic probe |
| JP4991355B2 (en) * | 2007-03-14 | 2012-08-01 | 株式会社東芝 | Ultrasonic diagnostic apparatus and ultrasonic probe |
| US8197413B2 (en) | 2008-06-06 | 2012-06-12 | Boston Scientific Scimed, Inc. | Transducers, devices and systems containing the transducers, and methods of manufacture |
| WO2011024074A2 (en) | 2009-08-26 | 2011-03-03 | Insightec Ltd. | Asymmetric phased-array ultrasound transducer |
| EP2489034B1 (en) | 2009-10-14 | 2016-11-30 | Insightec Ltd. | Mapping ultrasound transducers |
| JP5558858B2 (en) * | 2010-02-15 | 2014-07-23 | 株式会社東芝 | Ultrasonic probe |
| US9852727B2 (en) | 2010-04-28 | 2017-12-26 | Insightec, Ltd. | Multi-segment ultrasound transducers |
| WO2014014958A1 (en) * | 2012-07-17 | 2014-01-23 | The Johns Hopkins University | High quality closed-loop ultrasound imaging system |
| CN105916599B (en) * | 2013-12-19 | 2019-03-26 | B-K医疗公司 | Ultrasonic imaging transducer array with integrated apodization |
| US9506741B2 (en) | 2014-06-09 | 2016-11-29 | The Johns Hopkins University | Optical coherence tomography systems and methods with magnitude and direction tracking of transverse motion |
| US20180317888A1 (en) * | 2015-11-24 | 2018-11-08 | Koninklijke Philips N.V. | Ultrasound systems with microbeamformers for different transducer arrays |
| KR101974484B1 (en) * | 2017-04-27 | 2019-09-05 | 서강대학교산학협력단 | Intravascular ultrasound transducer assembly for occlusion tunnelling |
| US11534761B2 (en) * | 2017-10-25 | 2022-12-27 | Universite De Lille | Acoustic tweezers |
| EP3485800A1 (en) | 2017-11-15 | 2019-05-22 | Koninklijke Philips N.V. | Sensing device and method for multiple remote sensors |
| CN109925004A (en) * | 2017-12-19 | 2019-06-25 | 苏州国科昂卓医疗科技有限公司 | Conduit and imaging device are peeped in snooping head and ultrasound with it in a kind of ultrasound |
| US11026662B2 (en) * | 2018-01-11 | 2021-06-08 | Siemens Medical Solutions Usa, Inc. | Ultrasound transmit/receive for pulse inversion |
| WO2019148478A1 (en) * | 2018-02-03 | 2019-08-08 | Shenzhen Genorivision Technology Co. Ltd. | An ultrasound apparatus |
| NL2020426B1 (en) | 2018-02-13 | 2019-08-20 | Univ Delft Tech | Data collection system, in particular suitable for imaging of a distant object |
| WO2020090787A1 (en) * | 2018-10-31 | 2020-05-07 | 京セラ株式会社 | Ultrasound detection device |
| CN112043310B (en) * | 2020-09-07 | 2021-12-03 | 电子科技大学 | Capacitive coupling type ultrasonic imaging front-end transmitting and receiving circuit |
| CN113180722A (en) * | 2021-04-20 | 2021-07-30 | 武汉大学 | Acoustic probe of electronic stethoscope |
| CN113848060A (en) * | 2021-09-27 | 2021-12-28 | 中国石油大学(华东) | Device and measurement system for dynamically measuring oil film cavitation area of sliding bearing |
Citations (5)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US4543828A (en) * | 1983-01-21 | 1985-10-01 | Siemens Ag | Ultrasonic imaging system |
| CN2068736U (en) * | 1990-04-05 | 1991-01-02 | 陈余品 | Passive numeric coding transmitter connected by double lead wire |
| US5186177A (en) * | 1991-12-05 | 1993-02-16 | General Electric Company | Method and apparatus for applying synthetic aperture focusing techniques to a catheter based system for high frequency ultrasound imaging of small vessels |
| US5226847A (en) * | 1989-12-15 | 1993-07-13 | General Electric Company | Apparatus and method for acquiring imaging signals with reduced number of interconnect wires |
| WO2002054379A2 (en) * | 2001-01-05 | 2002-07-11 | Angelsen Bjoern A J | Annular array |
Family Cites Families (2)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US4276779A (en) * | 1979-03-29 | 1981-07-07 | Raytheon Company | Dynamically focussed array |
| US6120454A (en) * | 1998-02-03 | 2000-09-19 | Boston Scientific Corporation | Annular array ultrasound catheter |
-
2002
- 2002-08-29 CN CNB028296885A patent/CN100462735C/en not_active Expired - Fee Related
- 2002-08-29 EP EP02753314A patent/EP1540370A1/en not_active Withdrawn
- 2002-08-29 AU AU2002313622A patent/AU2002313622A1/en not_active Abandoned
- 2002-08-29 JP JP2004532469A patent/JP2005537081A/en active Pending
- 2002-08-29 WO PCT/NO2002/000301 patent/WO2004021044A1/en active Application Filing
Patent Citations (5)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US4543828A (en) * | 1983-01-21 | 1985-10-01 | Siemens Ag | Ultrasonic imaging system |
| US5226847A (en) * | 1989-12-15 | 1993-07-13 | General Electric Company | Apparatus and method for acquiring imaging signals with reduced number of interconnect wires |
| CN2068736U (en) * | 1990-04-05 | 1991-01-02 | 陈余品 | Passive numeric coding transmitter connected by double lead wire |
| US5186177A (en) * | 1991-12-05 | 1993-02-16 | General Electric Company | Method and apparatus for applying synthetic aperture focusing techniques to a catheter based system for high frequency ultrasound imaging of small vessels |
| WO2002054379A2 (en) * | 2001-01-05 | 2002-07-11 | Angelsen Bjoern A J | Annular array |
Also Published As
| Publication number | Publication date |
|---|---|
| WO2004021044A1 (en) | 2004-03-11 |
| CN1685246A (en) | 2005-10-19 |
| EP1540370A1 (en) | 2005-06-15 |
| JP2005537081A (en) | 2005-12-08 |
| AU2002313622A1 (en) | 2004-03-19 |
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