CN102215755A - Ultrasound 3d imaging system - Google Patents

Ultrasound 3d imaging system Download PDF

Info

Publication number
CN102215755A
CN102215755A CN2009801454367A CN200980145436A CN102215755A CN 102215755 A CN102215755 A CN 102215755A CN 2009801454367 A CN2009801454367 A CN 2009801454367A CN 200980145436 A CN200980145436 A CN 200980145436A CN 102215755 A CN102215755 A CN 102215755A
Authority
CN
China
Prior art keywords
beamformer
array
submatrix
numerous
wave beam
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.)
Pending
Application number
CN2009801454367A
Other languages
Chinese (zh)
Inventor
A·羌
贺兴柏
W·翁
N·伯杰
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.)
TeraTech Corp
Original Assignee
TeraTech Corp
Priority date (The priority date 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 date listed.)
Filing date
Publication date
Priority claimed from US12/286,555 external-priority patent/US8551000B2/en
Application filed by TeraTech Corp filed Critical TeraTech Corp
Publication of CN102215755A publication Critical patent/CN102215755A/en
Pending legal-status Critical Current

Links

Images

Classifications

    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
    • A61B8/44—Constructional features of the ultrasonic, sonic or infrasonic diagnostic device
    • A61B8/4444—Constructional features of the ultrasonic, sonic or infrasonic diagnostic device related to the probe
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
    • A61B8/44—Constructional features of the ultrasonic, sonic or infrasonic diagnostic device
    • A61B8/4483—Constructional features of the ultrasonic, sonic or infrasonic diagnostic device characterised by features of the ultrasound transducer
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
    • A61B8/48—Diagnostic techniques
    • A61B8/483—Diagnostic techniques involving the acquisition of a 3D volume of data
    • 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
    • G01S15/8925—Short-range imaging systems; Acoustic microscope systems using pulse-echo techniques using a static transducer configuration using a transducer array the array being a two-dimensional transducer configuration, i.e. matrix or orthogonal linear arrays
    • 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
    • G01S15/8927—Short-range imaging systems; Acoustic microscope systems using pulse-echo techniques using a static transducer configuration using a transducer array using simultaneously or sequentially two or more subarrays or subapertures
    • 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
    • G01S7/52082—Constructional features involving a modular construction, e.g. a computer with short range imaging equipment
    • 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
    • G01S7/52085—Details related to the ultrasound signal acquisition, e.g. scan sequences
    • G01S7/52095—Details related to the ultrasound signal acquisition, e.g. scan sequences using multiline receive beamforming
    • 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
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
    • A61B8/44—Constructional features of the ultrasonic, sonic or infrasonic diagnostic device
    • A61B8/4444—Constructional features of the ultrasonic, sonic or infrasonic diagnostic device related to the probe
    • A61B8/4472—Wireless probes
    • 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
    • G01S15/8959—Short-range imaging systems; Acoustic microscope systems using pulse-echo techniques using coded signals for correlation purposes
    • 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
    • G01S15/8993—Three dimensional imaging systems

Abstract

The present invention relates to an ultrasound imaging system in which the scan head either includes a beamformer circuit that performs far field subarray beamforming or includes a sparse array selecting circuit that actuates selected elements. When used with second stage beamforming system, three dimensional ultrasound images can be generated.

Description

The ultrasound wave 3-D imaging system
Related application
This part application is the U.S. Patent application the 12/286th of JIUYUE in 2008 application on the 30th, it is the priority of No. the 61/192nd, 063, the U.S. Patent application of topic application with " Ultrasound 3D Imaging System (ultrasound wave 3-D imaging system) " that No. 555 part continuation application and requirement give JIUYUE in 2008 people such as Chiang on the 15th.This part application also requires to give No. the 11/474th, 098, the U.S. Patent application of application on June 23rd, 2006 and the priority of the international patent application applied on June 22nd, 2007 PCT/US2007/014526 number.The full content of above-mentioned application is incorporated this paper at this into by quoting as proof.
Background technology
The medical ultrasonic imaging has become the industrial standard of many medical imaging applications.Technology is for using two dimension (2D) transducer array to provide three-dimensional (3D) image of internal organs and tumor to research and develop.These systems need thousands of wave beams to generate channel.Operating such system's desired power has caused the simulation phase-shifting technique to use the compromise that causes picture quality with digital delay beamformer.
In the ultrasound imaging techniques of facilitating improved real-time three-dimensional imaging capability, exist to further improved demand.In addition, this improved ability should be supported the successive real-time demonstration to fourth dimension 4D function.
Summary of the invention
The present invention relates to be used for the system of medical ultrasound imaging, this system uses two dimension (2D) array of the element of transducer in the probing shell that three-dimensional (3D) imaging is provided.Embodiment of the present invention are provided for the system and method that high-resolution and a lot of imaging patterns are arranged of medical imaging.
In preferred embodiments, probing shell comprises the first wave beam generative circuit, and this circuit generates second housing that data send the second wave beam generative circuit to wave beam.The first wave beam generative circuit provides far field submatrix wave beam generating run.Consequent wave beam generates second housing that the data from scan head is sent to the second wave beam generative circuit, and wherein the second wave beam generative circuit provides the wave beam control and the wave beam near field to focus on.
Embodiment preferred provides the probe that can be connected with traditional ultrasonic system, and wherein probe offers traditional wave beam to input and generates processing capacity.The probe beamformer can utilize the low-power charge-domain processor that has at least 32 wave beams to generate channel.
The preferred embodiments of the invention are used thinned array in the place of having only the sub-fraction element of transducer to be activated.Provide suitable average lobe bandwidth by four corner element selecting array, average side-lobe energy and clutter are minimized, eliminate periodically and maximizing, produce high quality image peak sidelobe ratio.Pass through interested volume or zone in order to control wave beam, different element of transducers must start to keep this peak sidelobe ratio by suitable order.System processor can provide needed transducer activation sequence so that the angle that beam position is different by programming.As an alternative, discrete controller can be used for controlling the thinned array activation.Embodiment preferred provides the probe of band integrated switching circuit, and wherein integrated switching circuit is used for selecting the thinned array active element continuously for successive multiple wave beam generates.Probe can be connected with traditional ultrasonic system, and wherein probe provides and inputs to traditional wave beam generation processing capacity.In another embodiment, emission array element and receiving array element can be operated independently, and wherein conveying element comprises thinned array, and receiving element is the array that almost fills up.In preferred embodiments, multiplex adapter and beamformer circuit can be integrated among the interface system, or as an alternative, are integrated among the host processing system, stay the 2D transducer array and are installed in the probing shell.
The present invention utilizes that every grade non-destructive of delay element predicts in the beamformer.So, under the situation of 65 grades of delay lines, for instance, 64 spendable outputs are arranged, one every grade.Temporal resolution may be at 1/8 λ in the scope of 1/16 λ.
Use high pressure multiplex adapter and non-destructive in the probe to predict the continuous wave beam generation that allows time-sharing multiplex.The a plurality of wave beams of tap selection formation that change every delay line continuously are possible now.
Except three-dimensional (3D) display capabilities, for instance, fourth dimension or time resolution pictorial display can be used for writing down and show image sequence with the speed record more than per second 10 frames.This allows to observe the feature that changes fast with the television frame speed of per second 30 frames, for example, blood or fluidicly flow, the motion of heart wall, or the like.
Another preferred embodiment of the present invention is utilized three grades of beamformer systems, wherein the first order is finished the first wave beam generating run to the data of receiving from transducer array, wherein transducer array produces first wave beam and generates data, follow is the second level in first order back, the second wave beam generating run is finished in the second level provides second level wave beam to generate data, and these data are delivered to the 3rd wave beam of finishing the 3rd wave beam generating run subsequently and generate level.
The charge-domain processors that can both use at different levels are realized.Data also can be before the first order or the second level, the third level or be transformed into digital form from analog form thereafter.A level can be utilized parallel wave beam generating run, and the second level provides successive wave beam to generate.
Description of drawings
Fig. 1 illustrates the use of the two-dimentional tiled arrays that is used for ultrasonic imaging according to the present invention.
Fig. 2 illustrates steerable two-dimensional array according to the present invention.
Fig. 3 A illustrates the use that is used for far field wave beam control and the first beamformer device that focuses on and is used for the second time delay beamformer of near field wave beam generation.
Fig. 3 B illustrates the first analog submodule array beam maker that data is transmitted to digital beamformer.
Fig. 3 C illustrates the probe that is used for the two-dimensional transducer probe.
Fig. 3 D illustrates the preferred embodiment of utilizing flexible PCB and cable assembly.
Fig. 4 illustrates the preferred embodiment of 3-D imaging system according to integrated submatrix probe invention.
Fig. 5 illustrates the preferred embodiment that the charge-domain processor is used for the integrated submatrix probe invention of second time delay wave beam generation.
Fig. 6 A illustrates the use that band of the present invention second level wave beam generates the integrated submatrix probe probe of processor for ultrasonic wave.
Fig. 6 B is the use of the integrated submatrix probe of the digital wave beam generation of oolemma processor for example.
Fig. 7 illustrates according to ultrasonic system of the present invention.
Fig. 8 A illustrates the thinned array of using according to the present invention.
Illustrate to Fig. 8 B graphic formula the thinned array performance.
Fig. 9 A illustrates the use of the of the present invention integrated thinned array probe probe that is connected with the main system of electrically charged territory wave beam generation processing.
Fig. 9 B illustrates the use of the of the present invention integrated thinned array probe probe that connects with traditional digital type ultrasound wave system with the parallel wave beam generator device of m.
Figure 10 illustrates the probe that is connected with portable computer according to the preferred embodiments of the invention.
Figure 11 illustrates the receiving array that almost fills up, and wherein receiving element is independently and not to overlap with emission array.
Illustrate to Figure 12 graphic formula the orientation and the elevation angle cross section of receiving array beam pattern.
Figure 13 is the amplifier section of azimuth beam directional diagram shown in Figure 12, shows main lobe and sidelobe structure.
Figure 14 illustrates almost by the receiving array beam pattern of complete filling.
Figure 15 shows that according to the present invention be the transmitting site that thinned array is selected.
Figure 16 illustrates the sectional view of the emission thinned array beam pattern of embodiment shown in Figure 15.
Figure 17 illustrates sparse emission array beam pattern.
It is possible to the central peak value with respect to beam pattern less than-35 decibels that Figure 18 illustrates the average side-lobe energy of restriction.
Figure 19 illustrates 2D and postpones the differential equation.
Figure 20 illustrates differential and shows profile.
Figure 21 illustrates the differential delay error.
Figure 22 A-22C illustrates the embodiment of the system processor of tetrad wave beam generation system.
Figure 23 A and Figure 23 B illustrate the transmitted waveform that is used for the noncoding of spread spectrum ultrasonic transmission and coding.
Figure 24 A-24C illustrates the program that is used for forming the transmission signal.
Figure 25 A-25D illustrates the preferred embodiment that comprises matched filter.
Specific implementation method
The purpose of wave beam generation system is that the signal focus that will receive from picture point lists to transducer array.By in beamformer suitable delay being inserted into the wavefront of propagating along specific direction, the signal that arrives from interested direction is by addition coherently, and from those irrelevant ground additions or deleted of other direction.For real-time three-dimensional applications, independently electronic circuit all is essential for each element of transducer.Therefore, use traditional embodiment, electronic devices and components become not only huge but also expensive apace along with component number increases gradually.Traditionally, the expense of high-resolution beamformer, size, complexity and power demand are avoided by " workaround " system approach.Use for real-time three-dimensional high definition rate ultrasonic imaging, select two-dimentional wave beam generation processor based on the available electron method control of delay and read group total machine algorithm.
The notion of the acoustics conformal lens of available electron method control is the plane " brick and tile " that the surface of 2D transducer array is divided into less relatively submatrix.As at this by quoting the United States Patent (USP) the 6th that its full content is incorporated into as proof, 292, No. 433 describe is illustrational like that with Fig. 1, brick and tile/submatrix 120 is done enough for a short time, so that when object is placed in the visual field of imaging system, can use far-field approximation to handle to every " brick and tile " incident radiation 122 from object.Additional delay element is merged, because the second level handle to allow all submatrix additions coherently (that is, global near field wave beam generates and can realize by the summation that postpones simply and calculate subsequently from the output of all submatrixs).Postpone to allow the signal of each submatrix " searching " from specific direction emission with the summation beamformer.By adjusting the delay that is associated with each array element, the direction of gaze of array can be controlled towards source radiation with electronics method.Therefore, not as the direction of seeing at 124a of searching for, but can control the direction of brick and tile 120 along different direction 124b.The delay line demand of each element may be less than hundred grades in the submatrix.The long delay that only is useful on total is that last near field focuses on needed.
In order to use the beamformer system scan image plane that to control, can use the sort of program as shown in Figure 2.The transducer array 264 that raster scanning 260 can be used for using 2D to control scans image planes 262.
Detail drawing according to the wave beam generation system with electronics method control of the present invention is illustrated among Fig. 3 A.This system generates processor 330 by the parallel time delay wave beam of a group 1-330 NForm.Each processor 330 has two ingredients: be used for the 2D submatrix beamformer 332 of far field wave beam generation/focusing and allow the additional period of carrying out the wave beam generation of layering near field from the output of each corresponding submatrix is postponed processor 334.Submatrix 332 comprises programmable delay line 340, multiplex adapter 344 and adder 346 outputs of m band branch line selector 342.As what in Fig. 3 A, see, for the system that n submatrix arranged, n parallel near field, programmable second level time delay is to allow all n parallel output needed by addition coherently 354 with indivedual delay adjustment that A/D converter 352 is changed, successively, the output after this addition provides the 3D rendering of target object after filtering 338.Processor 336 control submatrix operations.
Probe uses in Fig. 3 B with the digital beamformer in the second level to be showed.In this embodiment, numerous in preferred embodiments can be as the N submatrix beamformer 400 of near field beamformer, each all receives the signal that the element of transducer of individual delays line is arranged from m, its output is summed and be provided for beamformer 420, so that this beamformer may be the legacy system with conventional processors 480.Independently submatrix processor 460 is controlled beamformers 400.
After not using this layering submatrix elder generation far field under the situation of the wave beam generation method near field,, transducer array and traditional wave beam generation system are coupled together the cable that need be made up of 6,400 lines for the 2D array of 80 * 80 elements.As shown in Figure 3A, the number of input equals the sum of delay element in the submatrix concerning each submatrix processor, and each submatrix has only single output.The number of input equals the number of 2D array element concerning the submatrix group, and equal the membrane transducer array elements sum divided by the submatrix parts number from the number of this submatrix group's output, that is, be reduced the multiple that equals the submatrix size with reference to the number of input from the number of submatrix group's output.For instance, if select to use 5 * 5 submatrixs to realize this stratified wave beam to generate notion, after first order submatrix wave beam generates, be connected needed total number of electrical with the generation of near field, second level wave beam and be reduced 25 times so.More particularly, as mentioned above, under the situation of not using this 2D submatrix wave beam to generate, the 2D transducer array of 80 * 80 elements and traditional rear end wave beam generation system are coupled together 6400 electric wires of needs.Use 5 * 5 submatrixs to handle the group, be connected required number of wires with rear end wave beam generation system and be reduced to 256.Based on the present invention, the beamformer group energy of 256 5 * 5 element submatrixs is integrated in the probe with 80 * 80 element 2D arrays, so, there is the cable of 256 lines to be fit to integrated probe and near field, rear end wave beam generation system are coupled together.Be important to note that 5 * 5 submatrix far field wave beams generate processor and may be easy to be integrated in undersized silicon (Si) integrated circuit, eight 5 * 5 such submatrix beamformers can be integrated on the chip.In this embodiment, have only 32 or chip still less to be integrated among the probe, whereby the cable specification is reduced to 256 lines from 6400 lines.
The processing system of beamformer is the time domain processor, and this processor can be handled the inverse signal of big 2D array simultaneously, and the low-power that can handle whole array in the portable system in real time, the beamformer system of high integration are provided.When system's support of 192 parallel receive channels was used for the dot matrix 2D array probe of real-time 3D/4D imaging applications, stratified multistage wave beam generated and can unify to use with lower powered miniature ultrasonic wave system.
Fig. 3 B shows stratified wave beam generation structure structure, wherein the wave beam of the receiving element of a group vicinity generates and realizes in two-stage, promptly, be not to replace a long delay with each receiving element, public long delay is shared by these colony's all elements of the inside, but each has its short programmable delay in the long delay front.In each colony the inside, added together from each short output that postpones, be applied to public long delay then.The a small set of adjacent reception element that this public long delay characteristic arranged is defined as " submatrix " of transducer array.For instance, for the application that 2D dot matrix array is used for real-time 3D imaging, submatrix may be that 4 * 4 or 5 * 5 little arrays that adjoin element are arranged.First order programmable delay at this each element of submatrix the inside is integrated in the transducer probe the inside; Then, received back-end processor from total output of each submatrix.So, for 64 * 48 element 2D arrays (3072 or more element of transducer),, 4 * 4 submatrixs generate if being used to first order wave beam, so preceding probe and back-end processor are coupled together only 192 I/O cable elements of needs.
In preferred embodiments, stratified wave beam generates and also can be applicable to one dimension (1D) array that is used for real-time 2D imaging applications.For instance, for the one-dimensional array of 128 elements, 8 adjacent elements of a group can be got together as submatrix.In each submatrix the inside, each all has its programmable short delay 8 elements, and then, the output of eight delays is added earlier together, then is applied to public long delay.Be important to note that two kinds of diverse ways can be used for this two-stage embodiment.In the first embodiment, all comprise that the wave beam generative circuit of short delay and long delay all is placed in the back-end processor, so for 128 element one-dimensional arraies, 128 connection cords are used as the I/O cable between transducer probe and the back-end processor.Alternate embodiments is that all submatrix processors are integrated in the transducer probe the inside, promptly, array for 128 elements, 16 submatrix processors (each all has 8 programmable delays) all are integrated in the transducer probe the inside, so preposition integration probe and back-end processor coupled together only needs 16 cable elements.In the rear end, finishing the wave beam systematic function only needs 16 long delay wave beam generative circuits.Equally, for integrated 64 element arrays of eight 8 element submatrix processors in probe, back-end processor can being simplified to having only 8 wave beam generative circuits, only need 8 cable elements for preposition integration probe and back-end processor are coupled together.In addition, low power transmissions circuit and A/D converter can be integrated among the preposition probe, so radio communication can be used for connecting preposition probe and back-end processor.Can use wireless USB to connect or wireless FireWire connection.
With the structure of 64 * 48 element 2D transducer probes 485 of 4 * 4 integrated submatrix processors in Fig. 3 C illustrated.64 * 48 element 2D arrays 487 can comprise 48 row 1D arrays of stacking, 64 elements of every row.With being connected of element of each 64 element one dimension transducer array be by flexible cable, so the transducer head assembly can comprise 2D transducer array and 48 flexible cables 486.Shown in Fig. 3 C, every submatrix can comprise 4 * 4 elements (perhaps other rectangle or 2D geometry, preferred each submatrix has at least 16 elements, up to 256 elements), article 48, flexible cable is divided into 12 groups, every group of four flexible cables that adjoin are connected with a printed circuit board, promptly, be connected with first printed circuit board (PCB) 488 to row 4 the corresponding flexible cable of one dimension transducer with row 1, row 5 is connected with second printed circuit board (PCB) 487 to row 8 flexible cable, the rest may be inferred, is connected with the 12 printed circuit board (PCB) to row 48 flexible cable up to row 45.One end of every flexible cable is connected with all element of transducers, and the other end of flexible cable is connected with the flexible connector of 64 elements on being installed in printed circuit board (PCB).In each printed circuit board (PCB) the inside, 16 4 * 4 element submatrix processors 489 and one piece of high voltage multiplex adapter chip 491 are arranged.The submatrix processor is made up of 16 parallel programmable delay lines, and every delay line has at the low-noise preamplifier of its input and the multiplier able to programme that separates as apodizer and the output addition of 16 multipliers forms single output.In each plate the inside, high voltage multiplexing chip is also arranged, operate or press the receiving mode operation so allow 4 * 64 element transducer to press emission mode.Memory chip 490 also is installed in the programmed delays that is used for storing every delay line on each printed circuit board (PCB).In addition, there is power line to be connected with each printed circuit board (PCB) by interface 495 with digital input 492.
Embodiment with 64 element one-dimensional arraies of integrated first order submatrix processor also can use the design of Fig. 3 C to realize, but 64 element transducer arrays 491 are connected with flexible cable 497, one end of this flexible cable is connected with each element of transducer, and the other end of this cable is connected with the flexible connector of 64 pins.Connector is installed on the printed circuit board (PCB).In printed circuit, eight 8 element submatrix processors are arranged.Each submatrix processor has eight programmable delay lines, and every delay line has its low-noise preamplifier that separates, and in the output of delay line, apodizer is arranged, and, is used for the multiplier of beam-shaping function that is.The output addition of eight multipliers forms simulation output.High voltage multiplex adapter circuit chip also is included on the circuit board of printing, therefore allows 64 element transducer to operate by the emission mode operation or by receiving mode.Memory chip also is installed in the programmed delays that is used for storing every delay line on the printed circuit board (PCB).In addition, there is power line to be connected with each printed circuit board (PCB) with digital input.
Preferred embodiment with 64 elements of integrated submatrix processor (or more, for example, 128 or 256 elements) one-dimensional array 496 is illustrated among Fig. 3 D.In this embodiment, be not to use printed circuit board (PCB), but submatrix process chip 499a, high voltage multiplex adapter circuit chip 449b and memory chip 449c are directly installed on flexible print circuit or the cable (497,498).System described here can be used for cardiac imaging (4D) or internal organs in being inserted in body cavity conduit or probe use.Probe or conduit tube component can include the circuit housing of first group of numerous beamformer described here.
The present invention is used for the preferred embodiment (each all minimizes noise and cable loss with improved S/N performance) of 2D array beams generation and describes at Fig. 4, Fig. 5 and Fig. 6.In three all embodiments, m parallel submatrix wave beam generation processor 520 and multiplex adapter 528 is integrated in 2D transducer array 525, forms compact low noise probe 500.Fig. 4 describes compact probe and the system that special-purpose processing module links together, and has accommodated m parallel preamplifier/TGC522, emission/receiving chip 524 and second level time delay processing unit 526 in this system.This special-purpose processing module is communicated by letter with main frame 540 by FireWire IEEE 1394 or USB or pci bus 542.Control and be to finish synchronously by the system controller 544 that is arranged in processing module or housing 546.Fig. 5 describes the identical architecture with Fig. 4 statement, but in the dedicated processes module second level time delay processing unit be clearly by with hand-held probe 660 and housing 620 that computer case 648 is connected in use 600 realizations of charge-domain programmable (CDP) time delay line.Fig. 6 B describes a kind of thinned array probes 700 and system traditional, that commercially availabie time domain digital type ultrasound wave imaging system 700 couples together that generate 760 compactnesses of channel with n parallel wave beam.Be easy to see that in Fig. 6 A, time delay processor 720 also can be realized by using CDP time delay line 740.In these embodiments, the near field wave beam generates and is housed in the housing identical with other image processing function 720,780.These systems are at international patent application PCT/US2007/014526 number of the application in 22 days June in 2007 that is assigned to the U.S. and the U.S. Patent application the 11/474th of application on June 23rd, 2006, describe in No. 098, by quoting as proof these two parts of applications are all incorporated at this.
By changing systematically that beamformer postpones and along the visual angle shading of 2D transducer array, the echo of returning along the sight line of represent the 3D source radiation can be used for by scanning angle generation scanogram.This system can provide with 20 frame/seconds or higher speed and spread all over wide-field successive real-time big sector scanning image.Under this frame speed, this system can be used for showing successive 3D rendering over time, and therefore the 4D information of scanned object is provided.As shown in Figure 7, the CDP wave beam generates chip 810, time-sharing multiplex computer configuation can be used for producing a plurality of wave beams, that is, for each transmitted pulse, the colony of near field, the second level time delay line of 2D submatrix beamformer 818 and correspondence thereof can provide a plurality of wave beams continuously.Counting circuit produces continuously and is used for forming K the delay that wave beam is required.This device operation is as follows.In case one group of echo of returning that is sampled is sampled circuit 814 at time t1 and loads in delay line, 1 required delay is calculated 812 and is then added to all delay lines abreast in each module 822 for the formation wave beam.The echo of returning that is sampled is formed first wave beam with suitable delay by addition coherently 802 and filtering 804.At time t2, be used for forming wave beam 2 required delays and in each module, calculated and added to abreast all delay lines.The return echo that is sampled is formed second wave beam with suitable delay by addition coherently.Repeat this program, coherently formed up to K wave beam.
For instance, if build with CDP submatrix and second level time delay line,, can produce 16 wave beams or scanning line along different scanning angles for each transmitted pulse with the counting circuit of 16 successive addressable outputs.For downward depth bounds is 256 pulses of 15cm, and this system can produce 4096 wave beams with 64 * 64 pixel resolutions under the frame speed of 20 frame/seconds.This system is programmable fully; Wave beam generate that electronic device can be adjusted in case for the zoom of high-resolution or higher frame speed to the less visual field.For instance, use downward depth bounds to be similarly 192 transmitted pulses of 15cm, this system can produce 3072 wave beams with 64 * 48 pixel resolutions under the frame speed in 30 frames/second.
Described array uses the 2cm * 2cm ARRAY PROCESSING ultrasonic imaging of two dimension to use under the frequency of 3MHz.Can be housed in big as far as possible hole in the close package to the regulation that needs less than the resolution of about half wavelength.In order to inquire 90 degree scan volume and, to be desirable less than 0.25 millimeter element gradient or lens separation, thereby to cause 80 * 80 element arrays for the influence of grating lobe being reduced to minimum.Use above-mentioned submatrix treatment technology, probe together with the back follow near field, second level wave beam control/the integrated submatrix wave beam generative circuit of beam focusing system provides actual embodiment.Yet this embodiment still needs at least 32 submatrix chipsets to become on probe.Alternate pseudo-random array design methodology can be used for realizing this resolution with the handling components of quantity much less in probe.
Actual for thinned array is become, the combination that is inserted into loss and wide bandwidth performance is important for the acceptable imaging performance of realization under low illumination level.Acoustic impedance is low but physically cause being converted to the strong array that loss aspect the electric energy has only the 3-4 decibel in the signal energy of receiving for the quarter-wave matching layer of hard backing.Array bandwidth more than 75% is the typical case of this design and construction process.In addition, transducer array uses element location and the interconnection system that is suitable for the beamformer circuit.Electronic device is installed on the printed circuit board (PCB), and the latter is attached on the element of transducer via flexible cable.In practice, most of array element uses flexible cable to be connected with output.Yet, have only total a fraction of element to receive on the circuit board with metal wire.Yet a large amount of array elements connects the unique style that is enough to guarantee active component position in final array.
As the example of thinned array, suppose that 2 * 2cm array has 256 active components, consequent volumetric efficiency is 4%.The ratio of the output signal of this array and noise and the number of active component are proportional, and therefore, with when the filling array of same size is compared, this volumetric efficiency is corresponding to the loss of sensitivity that meets-13 decibels.In order to compensate this loss, the transmission signal of selecting broader bandwidth is to increase array sensitivity.With the method that proposes here, sensitivity is increased about 10 decibels.Further details about the thinned array device can be at United States Patent (USP) the 6th, 721, finds in No. 235, and the content of this patent is all incorporated into by quoting as proof at this.
Defer to someway the location of element in the array, must be noted that in the method to eliminate any periodicity that will produce the grating lobe of competing with main lobe.Can use array pseudo-random or at random (Fig. 8 A).In order when the clutter echo with graing lobe and secondary lobe minimizes, to make the efficient of beamformer reach maximum, researched and developed the active element placement geometry.Switching between numerous different array of figure is used for being scanned the zone or volume provides the most effective beam pattern with different beam angles with respect to interested.Therefore, first pattern can utilize the illustrational pattern of Fig. 8 A, and this pattern is switched to second pattern that is fit to certain different scanning angle.This may be included in the element of transducer of point element adjacent domain 880 the insides selection on every side with second angle scanning.
The main purpose of optimization method is that average side-lobe energy is minimized.In particular, this finishes by the interactive assessment optimisation criteria:
( 1 ) - - - J = 1 2 u mnx 2 ∫ ∫ s W ( u x , u y ) B ( u x , u y ) d u x du y ,
Weighting function wherein, W (u x, u y), more power is added to the zone that needs to reduce secondary lobe in the array response.Never weighting of this optimization method (that is W (u, x, u y)=1) do not begin then by selecting to make the satisfied better weighting function of optimisation criteria proceed continuously.Because the secondary lobe and the previous beam pattern that calculates, B (u that need amplitude peak to reduce x, u y) relevant, so weighting is chosen such that so that W (u x, u y)=B (u x, u y).This is undertaken by interactively mode, up to convergence.
Basically, the ratio that random array can produce main lobe and average secondary lobe is the imaging point spread function of N, and wherein N is the sum of active component in the array.With regard to the thinned array example of 256 elements, consequent ratio is-13 decibels.The method of using wide bandwidth with this than improving 10 decibels.Based on aforesaid optimisation criteria, the pseudo-random that has produced array element is arranged (Fig. 8 A).
Fig. 8 B is the array performance of 256 element sparse sampling arrays under 3MHz, the curve chart that sensitivity changes with lateral separation.Getting the peaked peak value of side lobe levels is about 30 decibels.In order to improve this performance, system is configured to realize the possible maximum main lobe and the ratio of clutter echo level, and this is confirmed independently.
Fig. 9 B describes thinned array probe 900 usefulness m parallel wave beams and generates channel and system traditional, that commercially availabie time domain digital type ultrasound wave imaging system 940 is connected.Be easy to see in Fig. 9 A, the time delay processor also can by use with housing 925 that the computer 927 that separates is connected in 920 realizations of CDP time delay line.The array of M multiplex adapter 906 is used for switching between the sequence of the scintigram that uses software program and system controller 940 or processor 950 operations.Therefore, the sequence of thinned array figure is for treating that with the different scanning angle scanning object of imaging provides its 3D ultrasonic imaging selected.
Commercially availabie 3D visual software based on window can be used for manifesting, handling and analyze the 3D multi-beam volumetric image data of the acoustics conformal lens combination generation of being adjusted by available electron method.Traditionally, the clinician with the diagnosis of 2D ultrasonography will see the 2D scanogram with cutting into slices one by one and diligently this information will be reconstructed into the 3D expression of judging that patient anatomy is learned.This process need clinician has the experience of taking facts as the basis and to the very complicated understanding of human anatomy.In order to produce " complete " image of 3D structure, the clinician must consider the section that all can get.See that hundreds of sections are too time-consuming, even for a patient.Can help to address this problem by offering the clinician to the 3D expression of patient anatomy that utilizes multiple scaaning wave beam generation data set to rebuild so that the 3D of 3D volume data is visual.
Commercially availabie software tool (for example, KB-VO13D of KB-VIS technologies, Chennai India) provides and shows or watch the 3D feature, for example:
-quick volume rendering
-cover the surface to show
Cover all surfaces in easy visible this volume of surperficial module permission.The surface may be by with intensity being basic setting threshold generation.As an alternative, the sowing option allows to select interested special syndeton.
-MIP (MIP) of radius arranged
-band Xie Xian ﹠amp; Oblique stroke and with the MPR (reorganization of many planes) of 3D dependency relation
-MRP sheet and many otch
-crooked MPR
The Yan Se ﹠amp of-tape editor; Opacity preestablishes
-region growing and cubing
The section of-tape thickness sheet volume and interactive VOI is in real time observed
Use " section is observed (Cutaway-Viewing) " instrument to be easy to see internal volume.Cutting planes is used for by this volume slice, the reveal internal zone.Cutting planes is easy to use mouse location and directed.
VOI (volume of interest) instrument allows the interested volume of real-time demonstration of human computer conversation's formula.User can use be easy to click and drags mouse action isolated easily and observe interested sub-volumes.
The image of-multiple form is preserved
Can obtain with various picture format (comprising DICOM, JPEG and BMP or the like) with the image that KB-Vol3D shows.
The film of-AVI form is caught
Visualized operation also can be obtained then with AVI movie.le and play on the player of Windows Media Player, QuickTime and Real Player and so on.
The present invention can use the probe 12 that is connected with portable computer 14 to realize as shown in figure 10.Ultrasonic system 10 also can comprise the cable 16 that probe 12 and processor housing 14 are coupled together.Specific embodiment can be used the interface unit 13 that may comprise the beamformer device.As at United States Patent (USP) the 6th, 106,472 and 6,869, what describe in detail in No. 401 is such, probe 12 may comprise transducer array 15A (2D) and can accommodate multiplex adapter and/or the circuit housing 15B of wave beam generator device, the full content of these patents be incorporated into by quoting as proof at this.
The 2D array configurations is used for emission to thinned array, and nonoverlapping full packing array is used for receiving.For N * M element arrays, have only m the optimised thinned array of element to arrange and be used for emission, and a remaining NM-m element is used as receiving array.For instance, for the 2D array of 40 * 60 elements, 256 elements are used as radiated element, and the layout of radiated element is based on that choice criteria optimizes, and remaining 2144 elements are used as receiving element.This embodiment has been simplified the needed multiplex adapter demand of 2D array, and in this case, multiplex adapter can be installed in the interface hull.
For 40 * 60 receiving arraies 50 of the housing of almost completely filling, the example of position of components is illustrated among Figure 11.Disallowable 256 the thinned array radiated elements of the array of 2400 elements obtain 2144 receiving element positions.These elements are independently and not overlapping with the thinned array radiated element.In preferred embodiments, radiated element is less than 25% of array element sum, preferably is less than 15%.
The azimuth of the beam pattern of above-mentioned receiving array and cross section, the elevation angle are illustrated among Figure 12.First secondary lobe is approximately-13 decibels with respect to the peak of central authorities.Graing lobe with respect to this peak less than-30 decibels.Suppose the 2D array-width greater than height, beamwidth in azimuth (drawing with blue (solid line)) is narrower slightly than elevation beam width (drawing with green (dotted line)).
In Figure 13, the zoomed-in view of above-mentioned azimuth beam directional diagram is showed detailed main lobe and sidelobe structure.For this situation, beam angle is about 1.5 degree.Beam pattern is almost completely consistent with 60 * 40 element beam patterns of complete filling.The receiving array beam pattern is illustrated among Figure 14.As mentioned above, receiving thinned array is made up of 2144 elements.Owing to reject 256 (emissions) so element does not have secondary lobe in the central authorities of array.
The example of last position of components is illustrated among Figure 15 with regard to 256 emission thinned arrays 60.256 position of components dishes are according to 32 * 32 elements of full packing array central authorities.These elements are independently and not overlapping with the receiving array element.The sectional view of emission thinned array beam pattern is illustrated among Figure 16.First secondary lobe is approximately-17 decibels with respect to the peak of central authorities.Graing lobe with respect to this peak less than-27 decibels.Thinned array optimize algorithm will+/-45 degree elevations angle and+side-lobe energy at/-45 degree elevations angle minimize.
Figure 17 shows the beam pattern of sparse emission array shown in Figure 15.Transmit beam direction figure is designed to cover equably 4 * 4 beam data pyramids.Emission thinned array is formed (about 10% filling rate) by 256 element subclass of 2400 element arrays of complete filling.The layout design of emission/receiving array need surpass 750 iteration algorithm so as at+/-45 degree azimuths ,+will transmit and receive side-lobe energy in the zone at/-45 degree elevations angle to minimize.As shown in figure 18, after 750 iteration, the position of components of last sparse emission array is restricted to central peak with respect to beam pattern less than-35 decibels with average side-lobe energy.
The low power ultrasound wave system system of real-time three-dimensional (3D) stereo-picture of having the ability to produce with the speed greater than per second 20 frame 3D renderings with 64 * 64 (4096) scanning beams with electronics method scanning two dimension (2D) dot matrix array is described below.With regard to each transmitted pulse, this system can produce 16 received beams.In addition, this design can drive one and two/unidimensional array and can support to be used for the transmitted waveform that compression pulse improves the wide bandwidth coding of system sensitivity.Wide bandwidth allows to the linear frequency modulation of the length of expansion low power transmissions pulse under the situation of not losing axial resolution or the use of coding waveforms (PN sequence) becomes possibility.These combination of features cause the imaging array with the electronic system that is assemblied in portable handheld devices the inside.
The beamformer processing system is to handle the time domain processor that returns of big 2D array simultaneously; The integrated beamformer of lower powered height provides the real-time processing of whole array and therefore will provide energy portable low-cost unit.
The real-time 3D ultrasonic imaging that uses 2D dot matrix array there is intensive demand.In this section, analyze the minimal amount of in ultrasonic system, supporting the needed wave beam of real-time 3D imaging to generate receive channel.The result shows that minima is that 192 parallel wave beams generation receive channels are to support that the array of fair-sized (for example, 48 * 64 elements) is needed.
The example of system that the acoustics conformal lens of available electron method adjustment are arranged is that the surface of 2D transducer array is divided into can be by on this plane " brick and tile " by the less relatively submatrix quoting United States Patent (USP) that its content is incorporated into as proof and form for the 6th, 292, No. 33; The wave beam of whole array generates can be divided into two-stage, and first order aperture submatrix wave beam generates the back followed by the relevant summation of second level macropore from the output of each submatrix.As described, brick and tile/submatrix can be done enough for a short time so that when object is placed in the visual field of imaging system, use far-field approximation to handle from object to each " brick and tile " incident radiant energy.Yet near field wave beam generative capacity has been merged in the true embodiment of submatrix wave beam generation system to allow more wide application.Additional delay element is handled as the second level and is incorporated into, in order that allow the addition coherently of all submatrixs.Postpone to allow each submatrix " search " from the radiating signal of specific direction with the summation beamformer.By adjusting the delay that is associated with each array element, the direction of gaze of array can be controlled towards source radiation with electronics method.The delay line demand of each element may be less than 100 grades in the submatrix.The long delay that only is useful on global addition is that last near field focuses on needed.Be illustrated in United States Patent (USP) the 6th, 292 according to the present invention with the detailed figures of the wave beam generation system of electronics method control, among Figure 14 A of No. 433.This system generates processor by the parallel time delay wave beam of a group and forms.Each processor is made up of two parts: be used for 2D submatrix beamformer that the aperture wave beam controls/focuses on and additional time delay processor with the layering near field wave beam generation of permission from the output of each corresponding submatrix.As what see among Figure 14 A that mentions with regard to the system that m submatrix arranged in front, m parallel near field, programmable second level time delay is needed in order to allow all m parallel output by addition coherently indivedual delays to be adjusted, and the output after this addition provides the 3D rendering of target object.
Be readily appreciated that if do not use this stratified first submatrix aperture method that generates of macropore wave beam then,, transducer array and traditional wave beam generation system coupled together the cable that need be made up of 6,400 lines for 80 * 80 element 2D arrays.United States Patent (USP) the 6th, 292 as previously mentioned, and shown in Figure 14 A of No. 433, the number of the input of each submatrix processor equals the sum of delay element in the submatrix, and each submatrix has only an output.That is to say that the input number of submatrix equals the number of the element of transducer that is associated with that submatrix.The number of submatrix output equals the membrane transducer array elements sum divided by the submatrix number.For instance, if select to use 5 * 5 submatrixs to realize this stratified wave beam generation system, after first order submatrix wave beam generated, connection near field, second level wave beam generated needed total number of electrical and is reduced 25 times.More particularly, as mentioned above, do not use this 2D submatrix wave beam to generate, 80 * 802D transducer array and traditional rear end wave beam generation are coupled together 6400 electric wires of needs.Use 5 * 5 submatrixs to handle the group, connect the needed number of wires of rear end wave beam generation system and be reduced to 256.Based on this example of the present invention, the colony of 256 5 * 5 element submatrix beamformers can be integrated in the probe with 80 * 80 element 2D arrays, so the cable of being made up of 256 electric wires is fit to integrated probe and near field, rear end wave beam generation system are coupled together.
Be important to note that 5 * 5 submatrix aperture wave beams generate processor and are easy to be integrated on the undersized silicon integrated circuit, eight 5 * 5 such submatrix wave beams generate and can be integrated on the integrated circuit.Please note: submatrix has and corresponding 9 to 64 element of transducers of 3 * 3 submatrixs to 8 * 8 submatrixs usually.With regard to square array geometry, preferable range be or between 4 * 4 and 6 * 6 arrays.3 * 4,4 * 5 or 4 * 6 rectangle submatrix also can preferentially be used.Please note: 1/4 λ minimum error standard is in usefulness.Have only 32 IC apparatus need be merged in probe, it can reduce to 256 electric wires from 6400 electric wires with cable dimension.Equally, for 64 * 48 element 2D arrays, at first use 4 * 4 submatrixs to handle the group in transducer housing, the number that the rear end wave beam generates channel is reduced to 192.
In the present invention, the embodiment preferred (each all minimizes noise and cable loss with the signal-to-noise performance that improves) that is used for the generation of 2D array beams is described at Fig. 4-6B.In these embodiments, m parallel submatrix wave beam generates the colony of processor and the low noise probe that the 2D transducer array integrates the formation compactness.Fig. 4 describes the system that compact probe is connected with the dedicated processes module, has accommodated m parallel preamplifier/TGC, emission/receiving chip and second level time delay processing unit in this dedicated processes module.This dedicated processes module is communicated by letter with main frame 540 via FireWire, USB or pci bus.Control and be preformed synchronously by the system controller that is arranged in this processing module.Fig. 5 describes the identical architecture described with Fig. 4, and difference is that the second level time delay processing unit of dedicated processes module the inside is clearly by using the programmable time delay line of charge-domain to realize.Fig. 6 A and Fig. 6 B describe compact probe and can buy the system that time domain digital type ultrasound wave imaging system is connected with on m parallel wave beam generation channel and the traditional market.Be easy to see that the time delay processor also can be realized by using CDP time delay line in Fig. 6 A and Fig. 6 B.
In the preferred embodiment of this system, macropore wave beam generation system is merged in the primary processor housing of ultrasonic imaging system, as together with shown in Figure 19-24B.
The speed of sound in tissue is about 1500 cels, is about 20 microseconds so sound wave penetrates the round trip propagation time of 15 centimetres of degree of depth.With regard to real-time 3D imaging, need at least 64 * 64 scanning beams that the image of quality of diagnosis is provided with the frame speed greater than 20 3D stereo-pictures of per second.For each launching beam, real-time 3D imaging system must form at least 16 the preferred 3D frame speed of wave beam support demands in each transmitted pulse.In this part, propose that successive time-sharing multiplex wave beam generates and time domain wave beam generation embodiment parallel the time.
In order to realize 16 beam scanning demands, can use the combination of serial and parallel architecture, promptly, this system can use front end time-sharing multiplex serial wave beam to generate Element Technology and form two wave beams, be at the heel generating at 8 of back-end processor parallel wave beams then, perhaps this system can form 4 serial wave beams at each serial beamformer output, then, back-end processor forms 4 parallel beams, and the rest may be inferred.
Systematically change beamformer by the visual angle along the 2D transducer array and postpone and shading, the echo of returning along the sight line of representing the 3D source radiation can be used for producing scanogram with this scanning angle.The frame speed of this system's energy more than 20 frame/seconds is to provide the successive in real time big sector scanning image that spreads all over big visual field.As shown in Figure 7, generate in the chip at the CDP wave beam, the computer configuation of time-sharing multiplex can be used for producing a plurality of wave beams, that is, for each transmitted pulse, 2D submatrix group and corresponding near field, second level time delay line thereof can provide a plurality of wave beams continuously.Counting circuit produces continuously and forms K the delay that wave beam is required.This device uses the following order operation: in case one group of echo that is sampled is loaded in the delay line, at time t1, forms wave beam 1 required delay and calculated and be applied to simultaneously all delay lines in each module the inside.The echo that is sampled forms first wave beam with suitable delay addition coherently.At time t2, form wave beam 2 required delays and calculated and be applied to simultaneously all delay lines in each module the inside.The echo that is sampled by addition coherently, forms second wave beam with suitable delay.Repeat this program, coherently formed up to K wave beam.
For instance, if having the counting circuit of 16 successive addressable outputs and processor submatrix and second level time delay line to merge, for each transmitted pulse, can produce 16 wave beams or scanning line, each is all along different scanning angles.For downward depth bounds is 256 pulses of 15 centimetres, and this system can produce 4096 wave beams that resolution is 64 * 64 pixels with the frame speed of 20 frame/seconds.This system is programmable fully; Wave beam generates electronic device can be by adjusting the less visual field of the fast higher image of the high-resolution or frame of amplification.For instance, use downward depth bounds to be similarly 192 transmitted pulses of 15 centimetres, this system can produce 3072 wave beams that resolution is 64 * 48 pixels with the frame speed of 30 frame/seconds.
The purpose of wave beam generation system is that the signal focus that will receive from picture point lists at transducer array.By inserting the wavefront that suitable delay is harmonized and propagated along specific direction in beamformer, the signal that arrives from interested direction is by addition coherently, and from those of other direction not by addition coherently or be cancelled.Flight time from the radiation source to the focus can be calculated and be stored in is used for each channel of arriving at simultaneously from a plurality of directions in the memorizer.Aspect traditional embodiment, independently electronic circuit is that each wave beam is requisite; For multiple-beam system, required electronic device is along with the increase of wave beam number becomes not only huge but also expensive apace.For instance, the wave beam that is used for the linear array of 192 elements generates 192 parallel delay lines of needs, and every all has the programmable delay length greater than 128 λ.For instance, in order to form four parallel wave beams, need add up to 768 long delay line able to programme.In order to simplify the required electronic device of multi-beam, a kind of stratified secondary wave beam generation system is described.
The notion that the layering wave beam generates is the flight time to be calculated be divided into two parts: first is used for short delay that low resolution aperture wave beam generates, and is thereafter to be used for the long delay that high-resolution macropore wave beam generates.Shown in Figure 19 is the 3D differential delay equation that is used for the 2D array.This equation shows array element (x m, y m) locate the change of differential delay (with respect to 2D array center) with distance and angle θ and φ.This equation can pass through all y m(the y coordinate of position of components) is set at 0 and is simplified as one-dimensional array.Differential delay can be limited in a plane (rather than volume) by set angle φ=0.
The operation that two-stage postpones is described for example, must produces the differential delay scattergram at elements all in one dimension or the two-dimensional array.In order to do this part thing, computing differential postpones equation and all is made form in given distance with the differential delay that angle θ and φ change.For instance, as shown in figure 20, the differential delay scattergram is to draw near the element 2D array center.
In 2 grades of delay systems, be broken down into coarse delay and thin the delay from the tabulated data of abovementioned steps.In order to determine how this distinguishes coarse delay and thin the delay, and maximum differential delay error is restricted (being set with the maximum differential delay error that is less than or equal to an increment usually).When the delay (from aforesaid step) of tabulation also activates receiving element with deciding.For instance, Figure 21 describes with the differential delay error apart from change at several elements.The differential delay of worst case (with blue data of drawing) is to attempt to receive from direction θ=-45 degree, the element of the view data of φ=-45 degree in the corner (θ=+ 45 degree, φ=+ 45 degree) at the 2D array.For this situation, maximum differential delay is greater than restriction (＞one increment error); So this element is inaccurate to be received, up to scope greater than about 100 increments.
The shown in block diagrams of stratified two-stage parallel beam generation system 958 is in Figure 22 A.Before being connected in the input with wave beam generation system 964, the two-dimensional transducer array 960 that weight is less than 15 pounds hand-held probe (for example, 12 among Figure 10) is coupled with amplifier 962 earlier.This wave beam generation system may comprise numerous short delay lines, and these short delay lines are coherently sued for peace at summing circuit 968, and output is delivered to long delay line 970 there, and the latter is also in summing circuit 972 summations.The thick wave beam of the first order generates and comprises the echo addition coherently that will return from aperture, for instance, in this specific embodiment with the receptor of 8 vicinities.Because the size in hole is little, each short delay length that postpones has only about 8 λ.So for the input of 192 elements, 24 such apertures just can form thick wave beam.Then, each programmable long delay line that is all added to the length of its correspondence of those 24 wave beams is used for the high-resolution wave beam of macropore and generates.In order to form four parallel wave beams, need four such wave beam generating structuries.As what can see in Figure 22 A, this layering embodiment that forms 24 thick wave beams only needs 192 short delays and 24 at the heel long delays, and each all has the programmable delay length shorter than 128 λ.For four parallel wave beams, only need 192 short delays to add 96 long delays, this is presenting huge saving aspect electronic devices and components and the power.
In addition, in each aperture short delay line the inside, the flight time control circuit is used for predicting from non-destructive ground the output of the charge-domain treatment circuit selection tap position of tapped delay line output.Each receptor is useful on wave beam and covers/become the multiplier of mark.In each processor, the output of all multiplier sharing of common.Then, the electric charge after the addition is added to matched filter so that echo decoding and the compression of returning produced imaging pulse with the signal to noise ratio that decreases.Charge-domain A/D converter on modulus (A/D) transducer or the chip can be used as such, so that the layering summation can be finished with digital form.
In preferred embodiments, it is important using high-speed digital communication to connect between beamformer output and back-end processor.As previously described, the analog echo that each element of transducer is received is converted to digital signal by analog-digital converter (A/D) during signal processing.Shown in the beamformer 974 of Figure 22 B, A/D converter 976 can be used in the input of every short delay line, and time delay is to finish digitally.Perhaps as an alternative, shown in the embodiment 980 of Figure 22 C, A/D converter 982 can be used in the outfan of each thick wave beam, and long delay can be finished digitally.The A/D conversion can use the discrete component that can get to finish, and perhaps in preferred embodiments, the charge-domain A/D converter can form on the same integrated circuit that the charge-domain beamformer of finishing the layering summation is arranged digitally.
Use coding or spread-spectrum signal to obtain the huge support of communication community.It is used for artificial satellite, honeycomb fashion and cabled digital communication system at present routinely.What Figure 23 A showed is the 5 cycle 3MHz sine curve examples that do not have spread spectrum coding.Coding or spread spectrum system are with the pumping signal of the time lengthening of limited time bandwidth product transmission broadband.The signal of receiving is decoded so that produce the imaging pulse that signal to noise ratio makes moderate progress.Using the benefit of coded signal in ultrasonic imaging system is to provide high-resolution imaging when reducing the peak value acoustic power significantly.These signals also provide the signal processing that improves whole system receiving sensitivity gain.Directly the order modulation is the coded sequence modulation of carrier wave.In practice, this signal may be AM (pulse), FM, amplitude, phase place or angle modulation.It also may be the pseudo-random or the PN sequence that can be included in multiple binary number value sequence after the specified time cycle.
Aspect ultrasound wave, use the notion of spread spectrum/code-excited transmitted waveform to comprise with the disruptive password of coded sequence modulation N of code length as N.The keying sequence of a password pulse is adjusted the transmitted pulse basis sequence that length is P.The coded pulse sequence of N pulse is called as N-chirp sign indicating number (N-chip code) often.3MHz sine curve example with 5-Chip Barker coding (decoding of 5-chip Bark) [111-11] gating is illustrated among Figure 23 B.Each " chip " is corresponding to by the one-period of gating transmitted waveform.Therefore, as if Figure 23 B is almost consistent with Figure 23 A except the 4th cycle was inverted.In Figure 23 A and Figure 23 B, successive line representative is by the sinusoidal wave form of continuous sampling, otherwise fine rule decussation point is the signal that is sampled, and wherein each cycle is obtained 10 increments.Length is that the coded pulse sequence of N * P can be composed the peak power that reduces effectively in the transmission medium by extended power in the long persistent period.In reception spread spectrum/coding echo, the signal decoding that the pulse compression matched filter can be used for receiving produces the improved imaging pulse of signal to noise ratio (snr).It is (NP) denary logarithm that the SNR of N * P coded pulse sequence improves.Therefore, be 7 the Barker code and the burst transmissions waveform in two cycles for length, can realize that 11.4 decibels SNR improves.Yet, in present system, transmit and receive waveform with super sample rate S over-extraction sample.Usually, the super sample rate of S=4 is used.Next, at receiver end, tap length is that echo decoding and the compression generation SNR that the matched filter of N * P * S can be used for returning is improved as the logarithmic imaging pulse that (NPS) is the end with 1O.In above-mentioned example, work as N=7, P=2, in the time of S=4,17.5 decibels SNR can realize.
The preferred method that forms the transmission signal is illustrated among Figure 24 A-24C.The basis sequence is the pulse that can see in Figure 24 A.Use 5 chip Barker codes [111-11], Figure 24 B shows basic sequence Barker code convolution.At last, the over-extraction example edition of this system transmissions continuous wave basis, shown in Figure 24 C, 6 times of over-extraction sample waveforms use as transmitted waveform
The 192 channel received beam generation systems that can form four parallel compression wave beams at the extended coding excitation waveform of each emission are the beamformer systems 985 shown in Figure 25 A.In this embodiment, use two-stage layering wave beam generation structure structure, at first, aperture is short to postpone signal after the echo addition coherently that beamformer 986 outputs will return from 8 transducers that adjoin, pulse compression matched filter 987 is following closely with the signal decoding of receiving, the signal 988 of this compression is added to long delay line then and finishes wave beam generation demand.In the system shown in Figure 25 B 990, A/D converter 992 is merged in each matched filter outfan.To use second level digital delay line embodiment to finish long delay following closely digitally.
The matched filter embodiment is illustrated among Figure 25 C.Wave filter 994 is made up of from the K-level tapped delay line of the signal of sample circuit 995 and programmable K level multiplier reception.The thick wave beam of expansion generates signal (f n) constantly added to the input of delay line.In each delay-level, signal can by non-destructive predict and multiply by tap weight 996 (W k), wherein k=1,2,3 ..., K-2, K-1, K.The summed circuit 997 of signal after the weighting adds together, produces the output g of compression m998.Can find out at time t=n,
g n＝f n-1W 1+f n-2W 2+f n-3W 3+…+f n-k-2W K-2+f n-K-1W k-1+f n-KW K
Use the example shown in Figure 24 A-24C, if 5 chip Barker codes of 6 times of over-extraction samples of system's emission, and the power of matched filter is chosen to be the time reversal of the 5 chip Barker code excitation waveforms that are transmitted, matched filter produces the output 999 of cross-correlation so, this output is the decode pulses signal (seeing Figure 25 D) of compression, filter gain log 10(5 * 6)=15 decibel.
Claims should not be limited to narrative order or element, unless stated its result.All claims and etc. the embodiment in the scope and spirit scope of value document all be required for protection according to the present invention.

Claims (40)

1. medical ultrasonic imaging system, comprising:
First group of numerous submatrix beamformer in two-dimensional transducer array in the probing shell and the probing shell;
Second group of numerous beamformer in second housing, second group of numerous beamformer and probing shell are linked up, second beamformer is accepted first view data from the submatrix beamformer of first group of numerous second delay line that numerous acceptance first view data are arranged, and the submatrix beamformer moves abreast provides 3 d image data.
2. according to the system of claim 1, further comprise the numerous multiplex adapter circuit in the probing shell.
3. according to the system of claim 1, wherein the array of element of transducer is as thinned array work.
4. according to the system of claim 1, wherein the beamformer device comprises coarse and meticulous delay element.
5. according to the system of claim 1, wherein second beamformer comprises second level beamformer.
6. according to the system of claim 5, further comprise third level beamformer.
7. according to the system of claim 1, wherein this system weight less than is 15 pounds.
8. according to the system of claim 7, wherein this system is included in the transducer array in the probing shell that is connected with the processor housing.
9. according to the system of claim 1, further comprise a thinned array transmission system.
10. according to the system of claim 1, further comprise the thinned array receiver system.
11., further comprise matched filter according to the system of claim 1.
12., further comprise the program of the transmitted waveform of finishing the over-extraction sample according to the system of claim 1.
13. according to the system of claim 1, wherein probing shell further comprises numerous flexible cables, every cable couples together transducer submatrix and circuit board.
14. according to the system of claim 1, wherein probing shell encapsulates numerous circuit boards, each circuit board has one of first group of numerous submatrix beamformer at least, stores the memorizer and the multiplex adapter circuit of beamformer control data.
15., further comprise flexible circuit according to the system of claim 1.
16. according to the system of claim 15, wherein flexible circuit comprises flexible cable.
17. according to the system of claim 15, wherein flexible circuit comprises flexible print circuit.
18. according to the system of claim 11, wherein matched filter comprises the numerous ballasts that are associated with the level of each delay line.
19. according to the system of claim 1, each wave beam in wherein numerous submatrix beamformers all compresses.
20. according to the system of claim 1, wherein second group of numerous beamformer comprises numerous digital beamformers.
21. according to the system of claim 20, wherein first group of numerous beamformer comprises the charge-domain processor.
22., further comprise the program that is used for storing the spread spectrum excitation waveform according to the system of claim 1.
23., further comprise the system processor that is used for finishing scan conversion according to the system of claim 1.
24., further comprise being used for finishing the system processor that Doppler handles according to the system of claim 1.
25. according to the system of claim 1, wherein probing shell further comprise with transducer array be installed on the periphery conduit or the probe body.
26. according to the system of claim 1, wherein this system comprises cardiac imaging system.
27. according to the system of claim 1, wherein second housing comprises that processor housing, display and weight are less than 15 pounds control panel.
28. a medical ultrasonic imaging system, comprising:
Transducer element array in the probing shell, this probing shell comprise first beamformer device;
The second beamformer device in second housing, the second beamformer device and probing shell are linked up, the second beamformer device is accepted to generate imaging data from first wave beam of first submatrix, the second beamformer device has numerous second beamformers, and first submatrix is worked abreast provides view data.
29. according to the system of claim 28, wherein transducer element array comprises single linear array.
30. according to the system of claim 28, wherein the array of element of transducer is connected with the flexible circuit of the top installation first beamformer device.
31. according to the system of claim 28, wherein the beamformer device comprises coarse and meticulous delay element.
32. according to the system of claim 28, wherein second beamformer comprises second level beamformer.
33., further comprise third level beamformer according to the system of claim 32.
34. according to the system of claim 28, wherein this system comprises the control panel of 15 pounds of system processor, display and shortages in weight.
35. according to the system of claim 28, wherein this system comprises the probing shell that is connected with the processor housing.
36., further comprise the flexible PCB in the probing shell according to the system of claim 28.
37., further be included in the probing shell flexible cable that transducer array and circuit board assemblies are coupled together according to the system of claim 28.
38., further comprise matched filter according to the system of claim 28.
39., further comprise the program of the transmitted waveform of finishing the over-extraction sample according to the system of claim 28.
40. according to the system of claim 34, wherein system processor is programmed, so that finish scan conversion and Doppler's processing.
CN2009801454367A 2008-09-15 2009-09-15 Ultrasound 3d imaging system Pending CN102215755A (en)

Applications Claiming Priority (5)

Application Number Priority Date Filing Date Title
US19206308P 2008-09-15 2008-09-15
US61/192,063 2008-09-15
US12/286,555 2008-09-30
US12/286,555 US8551000B2 (en) 2006-06-23 2008-09-30 Ultrasound 3D imaging system
PCT/US2009/056995 WO2010031057A1 (en) 2008-09-15 2009-09-15 Ultrasound 3d imaging system

Publications (1)

Publication Number Publication Date
CN102215755A true CN102215755A (en) 2011-10-12

Family

ID=41226821

Family Applications (1)

Application Number Title Priority Date Filing Date
CN2009801454367A Pending CN102215755A (en) 2008-09-15 2009-09-15 Ultrasound 3d imaging system

Country Status (4)

Country Link
EP (1) EP2323557A1 (en)
JP (1) JP5649576B2 (en)
CN (1) CN102215755A (en)
WO (1) WO2010031057A1 (en)

Cited By (5)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
CN105463332A (en) * 2015-12-30 2016-04-06 安徽悦众车身装备有限公司 Casting steel capable of being used for producing mining truck axle housing
CN106794001A (en) * 2014-10-08 2017-05-31 蝴蝶网络有限公司 For the parameter loader and relevant device and method of ultrasonic probe
CN108186052A (en) * 2017-12-28 2018-06-22 业成科技（成都）有限公司 Ultrasonic sensing device
CN110488303A (en) * 2018-05-14 2019-11-22 科达澳克托普斯集团公司 The method of the sonar data of compression after beamforming
CN113768539B (en) * 2021-09-15 2023-07-14 南京超维景生物科技有限公司 Ultrasonic three-dimensional imaging method and device, computer equipment and storage medium

Families Citing this family (7)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
WO2013042029A1 (en) * 2011-09-22 2013-03-28 Koninklijke Philips Electronics N.V. Excitation schemes for low-cost transducer arrays
GB201216455D0 (en) 2012-09-14 2012-10-31 Isis Innovation Passive ultrasound imaging with sparse transducer arrays
JP6157872B2 (en) * 2013-02-20 2017-07-05 株式会社東芝 Ultrasonic shape measuring apparatus and measuring method
JP6819184B2 (en) * 2016-09-26 2021-01-27 セイコーエプソン株式会社 Ultrasonic measuring device and control method of ultrasonic measuring device
FR3086063B1 (en) * 2018-09-13 2022-11-11 Moduleus ULTRASOUND IMAGING DEVICE
EP4014067A2 (en) * 2019-08-13 2022-06-22 Zed Medical, Inc. Multiple sensor catheter assembly
EP4220220A1 (en) * 2022-01-27 2023-08-02 Pulsify Medical Electronic system

Citations (5)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
WO1998034294A2 (en) * 1997-02-03 1998-08-06 Teratech Corporation Multi-dimensional beamforming device
US5938611A (en) * 1998-03-26 1999-08-17 General Electric Company Method and apparatus for color flow imaging using coded excitation with single codes
US20020091317A1 (en) * 2001-01-08 2002-07-11 Chiao Richard Yung Method and apparatus using golay-coded excitation for echocardiology
US6491634B1 (en) * 2000-10-13 2002-12-10 Koninklijke Philips Electronics N.V. Sub-beamforming apparatus and method for a portable ultrasound imaging system
WO2008002464A2 (en) * 2006-06-23 2008-01-03 Teratech Corporation Ultrasound 3d imaging system

Family Cites Families (16)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JP2632846B2 (en) * 1987-04-30 1997-07-23 ジーイー横河メディカルシステム株式会社 Phased Array Sonar
JP2961903B2 (en) * 1991-02-07 1999-10-12 株式会社日立製作所 Ultrasonic three-dimensional imaging device
US5685308A (en) * 1994-08-05 1997-11-11 Acuson Corporation Method and apparatus for receive beamformer system
JPH09313487A (en) * 1996-05-29 1997-12-09 Ge Yokogawa Medical Syst Ltd Method and device for ultrasonic three-dimensional photographing
US6530887B1 (en) * 1996-12-24 2003-03-11 Teratech Corporation Ultrasound probe with integrated electronics
US6113545A (en) * 1998-04-20 2000-09-05 General Electric Company Ultrasonic beamforming with improved signal-to-noise ratio using orthogonal complementary sets
JP4903928B2 (en) * 1999-04-23 2012-03-28 ゼネラル・エレクトリック・カンパニイ Three-dimensional flow imaging method and apparatus using coded excitation
KR100350026B1 (en) * 2000-06-17 2002-08-24 주식회사 메디슨 Ultrasound imaging method and apparatus based on pulse compression technique using a spread spectrum signal
US7141020B2 (en) * 2002-02-20 2006-11-28 Koninklijke Philips Electronics N.V. Portable 3D ultrasound system
JP3977827B2 (en) * 2003-06-25 2007-09-19 アロカ株式会社 Ultrasonic diagnostic equipment
EP1491913B1 (en) * 2003-06-25 2006-09-27 Aloka Co. Ltd. Ultrasound diagnosis apparatus comprising a 2D transducer with variable subarrays
JP4087762B2 (en) * 2003-07-24 2008-05-21 アロカ株式会社 Ultrasonic diagnostic equipment
JP4557575B2 (en) * 2004-03-25 2010-10-06 株式会社東芝 Ultrasonic diagnostic equipment
US7635334B2 (en) * 2004-04-28 2009-12-22 Siemens Medical Solutions Usa, Inc. Dynamic sub-array mapping systems and methods for ultrasound imaging
US7914454B2 (en) * 2004-06-25 2011-03-29 Wilk Ultrasound Of Canada, Inc. Real-time 3D ultrasonic imaging apparatus and method
US7687976B2 (en) * 2007-01-31 2010-03-30 General Electric Company Ultrasound imaging system

Patent Citations (5)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
WO1998034294A2 (en) * 1997-02-03 1998-08-06 Teratech Corporation Multi-dimensional beamforming device
US5938611A (en) * 1998-03-26 1999-08-17 General Electric Company Method and apparatus for color flow imaging using coded excitation with single codes
US6491634B1 (en) * 2000-10-13 2002-12-10 Koninklijke Philips Electronics N.V. Sub-beamforming apparatus and method for a portable ultrasound imaging system
US20020091317A1 (en) * 2001-01-08 2002-07-11 Chiao Richard Yung Method and apparatus using golay-coded excitation for echocardiology
WO2008002464A2 (en) * 2006-06-23 2008-01-03 Teratech Corporation Ultrasound 3d imaging system

Cited By (7)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
CN106794001A (en) * 2014-10-08 2017-05-31 蝴蝶网络有限公司 For the parameter loader and relevant device and method of ultrasonic probe
US11137486B2 (en) 2014-10-08 2021-10-05 Bfly Operations, Inc. Parameter loader for ultrasound probe and related apparatus and methods
US11733363B2 (en) 2014-10-08 2023-08-22 BFLY Operations, Inc Parameter loader for ultrasound probe and related apparatus and methods
CN105463332A (en) * 2015-12-30 2016-04-06 安徽悦众车身装备有限公司 Casting steel capable of being used for producing mining truck axle housing
CN108186052A (en) * 2017-12-28 2018-06-22 业成科技（成都）有限公司 Ultrasonic sensing device
CN110488303A (en) * 2018-05-14 2019-11-22 科达澳克托普斯集团公司 The method of the sonar data of compression after beamforming
CN113768539B (en) * 2021-09-15 2023-07-14 南京超维景生物科技有限公司 Ultrasonic three-dimensional imaging method and device, computer equipment and storage medium

Also Published As

Publication number Publication date
WO2010031057A1 (en) 2010-03-18
EP2323557A1 (en) 2011-05-25
JP2012502692A (en) 2012-02-02
JP5649576B2 (en) 2015-01-07

Similar Documents

Publication Publication Date Title
CN102215755A (en) Ultrasound 3d imaging system
US8551000B2 (en) Ultrasound 3D imaging system
US11559277B2 (en) Ultrasound 3D imaging system
CN101238390B (en) Curved 2D array ultrasound transducer and method for volumetric imaging
US8641628B2 (en) Aperture synthesis using cMUTs
US6671227B2 (en) Multidimensional beamforming device
US20120179044A1 (en) Ultrasound 3d imaging system
CN1191970A (en) Method and apparatus for providing dynamically variable time delays for ultrasound beamformer
CN101443678A (en) Multi-dimensional CMUT array with integrated beamformation
US20180299537A1 (en) Beamforming apparatus, beamforming method, and ultrasonic imaging apparatus
US20230346344A1 (en) Ultrasound 3d imaging system
Kim et al. Hybrid beamformation for volumetric ultrasound imaging scanners using 2-D array transducers
Liu et al. High-Resolution Sonar Imaging Using Sparse Transmitting and Dense Receiving Arrays
Stergiopoulos Digital 3d/4d ultrasound imaging array

Legal Events

Date Code Title Description
C06 Publication
PB01 Publication
C10 Entry into substantive examination
SE01 Entry into force of request for substantive examination
C02 Deemed withdrawal of patent application after publication (patent law 2001)
WD01 Invention patent application deemed withdrawn after publication

Application publication date: 20111012