WO2013018964A1 - Appareil et procédé de focalisation de faisceaux de réception adaptatifs - Google Patents

Appareil et procédé de focalisation de faisceaux de réception adaptatifs Download PDF

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Publication number
WO2013018964A1
WO2013018964A1 PCT/KR2012/000347 KR2012000347W WO2013018964A1 WO 2013018964 A1 WO2013018964 A1 WO 2013018964A1 KR 2012000347 W KR2012000347 W KR 2012000347W WO 2013018964 A1 WO2013018964 A1 WO 2013018964A1
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Prior art keywords
sub
coefficient
ultrasonic
calculated
diameter
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PCT/KR2012/000347
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English (en)
Korean (ko)
Inventor
유양모
강지운
장진호
송태경
Original Assignee
한국보건산업진흥원
서강대학교 산학협력단
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Publication of WO2013018964A1 publication Critical patent/WO2013018964A1/fr

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Classifications

    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
    • G01N29/00—Investigating or analysing materials by the use of ultrasonic, sonic or infrasonic waves; Visualisation of the interior of objects by transmitting ultrasonic or sonic waves through the object
    • G01N29/22—Details, e.g. general constructional or apparatus details
    • G01N29/26—Arrangements for orientation or scanning by relative movement of the head and the sensor
    • G01N29/262—Arrangements for orientation or scanning by relative movement of the head and the sensor by electronic orientation or focusing, e.g. with phased arrays
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
    • A61B8/13—Tomography
    • A61B8/14—Echo-tomography
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
    • G01N29/00—Investigating or analysing materials by the use of ultrasonic, sonic or infrasonic waves; Visualisation of the interior of objects by transmitting ultrasonic or sonic waves through the object
    • G01N29/22—Details, e.g. general constructional or apparatus details
    • G01N29/24—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
    • 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
    • G01S3/00—Direction-finders for determining the direction from which infrasonic, sonic, ultrasonic, or electromagnetic waves, or particle emission, not having a directional significance, are being received
    • G01S3/80—Direction-finders for determining the direction from which infrasonic, sonic, ultrasonic, or electromagnetic waves, or particle emission, not having a directional significance, are being received using ultrasonic, sonic or infrasonic waves
    • G01S3/802—Systems for determining direction or deviation from predetermined direction
    • G01S3/805—Systems for determining direction or deviation from predetermined direction using adjustment of real or effective orientation of directivity characteristics of a transducer or transducer system to give a desired condition of signal derived from that transducer or transducer system, e.g. to give a maximum or minimum signal
    • 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
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
    • G01N2291/00—Indexing codes associated with group G01N29/00
    • G01N2291/10—Number of transducers
    • G01N2291/106—Number of transducers one or more transducer arrays

Definitions

  • the present invention relates to a receiving focusing apparatus, and more particularly, to reduce the influence of interference and noise outside the target reflector in the medium, thereby reducing distortion and noise of an image unintentionally generated by a coherence factor (CF).
  • the present invention relates to a collapsing receiver focusing apparatus and method.
  • Ultrasonic image acquisition is performed by receiving and focusing the ultrasonic signal returned after focusing by the ultrasonic array transducer.
  • Receive focusing is to obtain a focused signal by compensating for and adding different delays of ultrasonic signals reflected by the array transducer at a desired focusing point.
  • the CF method among the red light receiving beam focusing methods amplifies the received focused area and reduces image degradation caused by the side lobe.
  • this performance improvement is compromised with image distortion, so it is necessary to determine the compromise in the appropriate line.
  • Equation 1 The conventional CF method is expressed by Equation 1 below.
  • M ⁇ ⁇ x f] (m, k) x d (m, k) represents channel data to which a delay time at the depth of the k-th image point of the m-th channel is applied.
  • M is the total number of channels.
  • the denominator of Equation 1 represents the total energy of the channel data to which the delay time is applied at the depth of the kth image point
  • the numerator of Equation 1 represents the main energy of the channel data to which the delay time is applied to the depth of the kth image point.
  • CF calculated by Equation 1 is a ratio of total energy of delayed channel data and mainlobe energy of channel data, and is applied in a form of multiplying the beam combiner output. This improves the quality of the image by amplifying the part focused by the reflector and reducing the energy caused by the side lobe, but it is vulnerable to interference outside the target reflector in the medium. need.
  • the first problem to be solved by the present invention is an adaptation that can reduce the error that occurs when the received signal reflected at the interference point overlaps the received signal reflected at the image point due to the presence of the interference point near the image point It is to provide a receiver focusing device.
  • the second problem to be solved by the present invention is to provide a method for receiving a collapsing receiver that can improve the quality of the image can obtain a C value similar to the case of using a conventional CF while minimizing the loss of the image information.
  • the present invention provides a computer-readable recording medium having recorded thereon a program for executing the above method on a computer.
  • a transducer for receiving an ultrasonic signal reflected from the image point;
  • a delay offset applying unit configured to calculate a delay time of the received ultrasonic signal and apply the delayed set for each channel of the received ultrasonic signal to the received ultrasonic signal;
  • Delay time compensated ultrasonic signal for each channel Pan synthesis unit to synthesize;
  • a coefficient calculation unit for dividing an aperture into a plurality of sub-diameters, and calculating an overall coefficient to be applied to the synthesized ultrasound signal by using the CF coefficient for each sub-diameter;
  • a coefficient applying unit configured to apply the calculated total coefficients to the synthesized ultrasound signal.
  • the coefficient calculating unit may calculate the total coefficient from the ratio of the total energy of the channel data calculated for each sub-diameter and the channel data main lobe energy calculated for the sub-diameter.
  • the coefficient calculating unit estimates the actual ultrasonic speed in the medium from the CF coefficient for each sub-diameter, calculates a delay offset using the estimated actual ultrasonic speed, and the delay offset applying unit The delay offset calculated by the coefficient calculator may be applied to the received ultrasonic signal.
  • the coefficient calculating unit calculates an ultrasonic speed for maximizing the CF coefficient for each sub-diameter, and transfers the calculated ultrasonic speed to the transmitting ultrasonic signal generator, for each sub-diameter.
  • the ultrasonic waves can be transmitted at different speeds.
  • the present invention to achieve the second object, the step of receiving the ultrasonic signal reflected from the image point to the transducer; Calculating a delay time of the received ultrasonic signal and compensating for the delay time for each channel of the ultrasonic signal; Synthesizing the ultrasonic signal whose delay time is compensated for each channel; Dividing an aperture into a plurality of sub-diameters, and calculating total coefficients to be applied to the synthesized ultrasound signal using the CF coefficients for each sub-diameter; And applying the calculated total coefficients to the synthesized ultrasound signal.
  • the present invention provides a recording medium that can be read by a computer that records a program for executing the above-described method of performing the above-described ung hom receive beam method on a computer.
  • FIG. 1 is a block diagram of an adaptive receiving focusing apparatus according to a preferred embodiment of the present invention.
  • FIG. 2 conceptually illustrates the difference in channel-by-channel delay time of an ultrasonic signal traveling through a heterogeneous medium.
  • FIG. 4 conceptually illustrates signals processed by the adaptive receiving focusing apparatus according to the preferred embodiment of the present invention shown in FIG. 1.
  • FIG. 5 conceptually illustrates signals processed by the adaptive receiving focusing apparatus according to the preferred embodiment of the present invention illustrated in FIG. 1.
  • FIG. 6 illustrates a case where a high CF coefficient is calculated and a low CF coefficient is calculated for each sub-diameter when an interference point is located near an image point.
  • FIG. 7 is a flowchart of a method for receiving a collimation group according to a preferred embodiment of the present invention.
  • the method of focusing a red light receiver is performed from an image point.
  • a red-eye receiver focusing apparatus performs a red-eye receiver focusing by applying an average of CF obtained by dividing the entire aperture by a minor diameter to the image. do.
  • This method uses the SSCFCSpatial Smoothing Coherence Factor (SSCFCSpatial Smoothing Coherence Factor). It will be called a method.
  • FIG. 1 is a block diagram of an adaptive receiving focusing apparatus according to a preferred embodiment of the present invention.
  • a red-eye receiving focusing apparatus includes a transducer 110, an ADCC120, a delay time calculating unit 130, a delay offset applying unit 140, a beam combining unit 150, and coefficient calculation.
  • Transducer 110 receives the ultrasonic signal reflected from the tissue through the medium.
  • the received ultrasonic signal will be an analog ultrasonic signal.
  • the ADC 120 converts the received analog ultrasound signal into a digital ultrasound signal.
  • the delay time calculator 130 calculates a delay time by using the distance between the transducer 110 and the tissue and the ultrasonic speed for each channel.
  • the delay offset application unit 140 estimates the delay offset by calculating a difference between the delay time calculated for each channel and the actual delay time of the received ultrasonic signal. In addition, the estimated delay offset is applied to the received ultrasonic signal and output to the pan synthesizer 150.
  • the beam combiner 150 synthesizes an ultrasonic signal to which a delay offset is applied.
  • the coefficient calculator 160 obtains a CF coefficient for each sub-diameter for the ultrasonic signal to which the delay offset is applied, and calculates an SSCF coefficient from the average of the CF coefficients.
  • the coefficient calculation unit 160 may divide the entire aperture into M-L + 1 sub-diameters and determine the SSCF coefficients by averaging the CF coefficients of the sub-diameters.
  • L is the subcaliber length and M is the total number of channels.
  • the final coefficient calculated by the coefficient calculating unit 160 is called SSCFCSpatial Smoothing Coherence Factor, and using the SSCF coefficient calculated by the coefficient calculating unit 160 reduces the influence of interference and noise outside the target reflector in the medium, Unintentionally caused by the brain was able to reduce the distortion and DOS 3 ⁇ 4 phase of the image
  • the coefficient calculating unit 160 obtains the SSCF coefficient from the CF coefficients of each sub-diameter, in this embodiment, the method of calculating the average is used, but the present invention is not limited thereto.
  • the SSCF's performance changes according to the L value of the SSCF coefficient.
  • L 1
  • the performance of the SSCF is the same as that of the conventional delay-sum receive focusing technique.
  • the closeness to the CF coefficient allows the compromise between image distortion and resolution by the user.
  • the coefficient calculation unit 160 may estimate the actual ultrasonic speed by the sub-diameter from the CF coefficient for the sub-diameter. Accordingly, the actual ultrasonic velocity in the medium may be estimated from the CF coefficient calculated by the coefficient calculating unit 160, and the delay offset to be provided to the delay offset applying unit 140 may be calculated using the estimated actual ultrasonic velocity. will be.
  • the coefficient calculating unit 160 calculates an ultrasonic speed for maximizing the CF coefficient for each sub-diameter, and transmits the transmitted ultrasonic signal by varying the ultrasonic signal having the calculated ultrasonic speed for each sub-diameter, by sub-diameter.
  • the CF coefficient can be controlled to be maximum.
  • the coefficient applying unit 170 applies the SSCF coefficients calculated by the coefficient calculating unit 160 to the ultrasonic signals synthesized by the beam combining unit 150.
  • the beam buffer unit 180 stores the ultrasound signal to which the SSCF coefficient is applied for each image point depth.
  • FIG. 2 conceptually illustrates the difference in channel-by-channel delay time of an ultrasonic signal traveling through a heterogeneous medium.
  • the delay time of the reflected ultrasonic signal deviates from the calculated delay time curve 210.
  • the delay calculation unit 130 calculates the delay time by using the distance between the transducer 110 and the tissue, and the ultrasonic speed for each channel. However, the ultrasonic signal passing through the surrounding medium and other medium 200 will be earlier or later than the calculated delay time.
  • the nonuniform diameter of each subcaliber can be used to determine the ultrasonic velocity at which the greatest number of values is to be cut off.
  • the faster the ultrasonic speed the smaller the delay time.
  • a signal having a slower ultrasonic speed may reduce the difference from the calculated delay time curve.
  • a larger CF coefficient will be computed. 3 divides the entire aperture into a plurality of sub-calibers and shows the CF coefficients for each sub-caliber.
  • CF coefficient X d k) of the sub-diameter means channel data to which the delay time at the depth of the k-th image point of the first sub-diameter is applied, and Xd M ′′ L + 1 (k) is the M-L + 1 th sub
  • Equation 2 After dividing the entire aperture by M-L + 1 sub-diameter, the method of calculating the average of the CF coefficients for each sub-diameter is shown in Equation 2 below.
  • Equation 2 shows an equation for calculating the ratio of the sum of the total channel data energy calculated for each sub-diameter and the channel data main lobe energy calculated for each sub-diameter as an SSCF coefficient according to an embodiment of the present invention.
  • FIG. 4 conceptually illustrates signals processed by the red-eye receive beam focusing apparatus according to the preferred embodiment of the present invention shown in FIG. 1.
  • FIG. 5 conceptually illustrates signals processed by the adaptive receiving beam focusing apparatus shown in FIG. 1 according to an exemplary embodiment of the present invention.
  • the difference between the actual delay time and the calculated delay time of the channel data does not appear significantly only for the lower channel data as shown in FIG. 4, and the actual delay of the channel data is irregular.
  • the difference between the time and the calculated delay time is shown.
  • the difference in delay time is such that the ultrasonic signal reflected at the image point 610 and the ultrasonic signal reflected at the interference point 620 do not overlap. There is no overlap between them.
  • FIG. 7 is a flowchart illustrating a method of focusing a receiving beam according to a preferred embodiment of the present invention.
  • the method of collapsing the beam of the red light receiving beam according to the present embodiment may be processed into difficulty processed as a clock stone at the cross beam receiving beam focusing upper region shown in FIG. Therefore, even if omitted below, the above descriptions of the red-eye receive beam focusing apparatus shown in FIG. 1 also apply to the red-eye receive beam focusing method according to the present embodiment.
  • step 700 the detox receiver focusing apparatus receives the ultrasonic signal reflected from the image point to the transducer.
  • the detox beam receiving apparatus collects the received ultrasonic signal.
  • the delay time is calculated to compensate the delay time for each channel of the ultrasonic signal.
  • the defocusing focusing apparatus synthesizes an ultrasound signal having a delay time compensated for each channel.
  • the red light receiving beam focusing apparatus divides an aperture into a plurality of sub-diameters, and calculates an overall coefficient to be applied to the synthesized ultrasound signal using the CF coefficients for each sub-diameter.
  • the total coefficient (SSCF coefficient) may be calculated from the ratio of the total energy of the channel data calculated for each sub-diameter and the channel data main lobe energy calculated for the sub-diameter.
  • the actual ultrasonic velocity for each channel in the medium is estimated from the CF coefficient for each sub-caliber, the delay offset is calculated using the estimated actual ultrasonic velocity, and then the calculated delay offset is applied to the received ultrasonic signal.
  • the delay offset is calculated using the estimated actual ultrasonic velocity, and then the calculated delay offset is applied to the received ultrasonic signal.
  • the red light receiving beam focusing apparatus applies the calculated total coefficient to the synthesized ultrasound signal.
  • 8 is an in vivo image of a human thyroid gland imaged at a center frequency of a 7.5 MHz linear probe and a sampling frequency of 2.54 MHz.
  • (A) shows images by delay-sum reception beam focusing technique (C0NV image),
  • (b) shows images of decompression and focusing technique based on conventional CF coefficients, and
  • (c) shows the length of sub-caliber 16 This is an image with SSCF coefficient set to.
  • CNR Contrast-to-noise ratio
  • Embodiments of the present invention may be implemented in the form of program instructions that can be executed by various computer means and recorded in a computer readable medium.
  • the computer readable medium may include a program command, a data file, a data structure, etc. alone or in combination.
  • Program instructions recorded on the media may be those specially designed and constructed for the purposes of the present invention, or they may be of the kind well-known and available to those having skill in the computer software arts.
  • Examples of computer-readable recording media include magnetic media such as hard disks, floppy disks, and magnetic tape, optical media such as CD-ROMs, DVDs, and magnetic disks, such as floppy disks.
  • Examples of program instructions include not only machine code generated by a compiler, but also high-level language code that can be executed by a computer using an interpreter or the like.
  • the hardware device described above may be configured to operate as one or more software modules to perform the operations of the present invention, and vice versa.
  • the present invention relates to an efficient structure and configuration of a single shear chip included in an ultrasound medical imaging system.
  • the present invention can be applied to the photoacoustic imaging system in addition to the ultrasonic medical imaging system.

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Abstract

La présente invention concerne un appareil de focalisation de faisceaux de réception adaptatifs, comprenant : un transducteur qui reçoit un signal d'ondes ultrasonores réfléchies par un point d'image ; une unité d'application de compensation de retard qui calcule un temps de retard d'un signal d'onde ultrasonore reçu, et qui applique une compensation de retard pour chaque canal du signal d'onde ultrasonore reçu au signal d'onde ultrasonore reçu ; une unité de synthèse des faisceaux qui synthétise le signal d'onde ultrasonore, qui a été compensé pour un temps de retard de chaque canal ; une unité de calcul de coefficient qui divise une ouverture en une pluralité de sous-ouvertures, et qui calcule ensuite un coefficient entier à appliquer au signal d'onde ultrasonore synthétisé en utilisant des coefficients CF selon les sous-ouvertures ; et une unité d'application de coefficient qui applique le coefficient entier calculé au signal d'onde ultrasonore synthétisé, réduisant ainsi les erreurs lorsque la présence d'un point d'interférence à proximité d'un point d'image entraîne le chevauchement d'un signal de réception réfléchi par le point d'image et d'un signal de réception réfléchi par le point d'interférence.
PCT/KR2012/000347 2011-08-01 2012-01-16 Appareil et procédé de focalisation de faisceaux de réception adaptatifs WO2013018964A1 (fr)

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KR1020110076504A KR101312309B1 (ko) 2011-08-01 2011-08-01 적응 수신 빔 집속 장치 및 방법
KR10-2011-0076504 2011-08-01

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KR101555267B1 (ko) * 2013-11-29 2015-09-24 알피니언메디칼시스템 주식회사 비집속 초음파를 이용한 빔포밍 방법 및 장치
KR101590481B1 (ko) * 2014-07-31 2016-02-01 서강대학교산학협력단 수신 동적 빔 집속을 위한 lut기반의 시간 지연 생성 방법 및 장치
KR101581686B1 (ko) * 2015-01-30 2015-12-31 서강대학교산학협력단 다목적 빔 집속 시스템
KR101627821B1 (ko) * 2015-12-03 2016-06-07 알피니언메디칼시스템 주식회사 가상음원 기반 초음파 집속방법 및 이를 이용한 초음파 장치
KR101968158B1 (ko) * 2017-05-29 2019-08-13 주식회사 에스원 유효 신호 분리 장치 및 방법
EP3447486A1 (fr) * 2017-08-25 2019-02-27 Kabushiki Kaisha Toshiba Appareil d'inspection par ultrasons à balayage linéaire et procédé d'inspection par ultrasons à balayage linéaire
KR102069949B1 (ko) * 2017-10-23 2020-01-23 서강대학교산학협력단 3차원 초음파 영상 복원 방법 및 그 초음파 영상 장치
KR102087269B1 (ko) * 2017-12-13 2020-03-10 서강대학교산학협력단 수신 동적 빔 집속을 위한 시간 지연 장치 및 방법
JP6926011B2 (ja) * 2018-02-07 2021-08-25 株式会社東芝 超音波探傷装置および超音波探傷方法
KR102173404B1 (ko) * 2018-11-15 2020-11-03 서강대학교산학협력단 빔포머 및 이를 포함하는 초음파 영상 장치

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