WO2012141520A2 - Appareil de diagnostic d'image ultrason pour minimiser des artefacts d'image ayant une forme de dent, et procédé de diagnostic associé - Google Patents

Appareil de diagnostic d'image ultrason pour minimiser des artefacts d'image ayant une forme de dent, et procédé de diagnostic associé Download PDF

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Publication number
WO2012141520A2
WO2012141520A2 PCT/KR2012/002801 KR2012002801W WO2012141520A2 WO 2012141520 A2 WO2012141520 A2 WO 2012141520A2 KR 2012002801 W KR2012002801 W KR 2012002801W WO 2012141520 A2 WO2012141520 A2 WO 2012141520A2
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WIPO (PCT)
Prior art keywords
scan line
pulse
bias voltages
transducer elements
different bias
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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.)
Ceased
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PCT/KR2012/002801
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English (en)
Korean (ko)
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WO2012141520A3 (fr
WO2012141520A9 (fr
Inventor
이대현
조성택
노세범
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Alpinion Medical Systems Co Ltd
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Alpinion Medical Systems Co Ltd
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Publication of WO2012141520A2 publication Critical patent/WO2012141520A2/fr
Publication of WO2012141520A3 publication Critical patent/WO2012141520A3/fr
Publication of WO2012141520A9 publication Critical patent/WO2012141520A9/fr
Anticipated expiration legal-status Critical
Ceased legal-status Critical Current

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    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01S—RADIO DIRECTION-FINDING; RADIO NAVIGATION; DETERMINING DISTANCE OR VELOCITY BY USE OF RADIO WAVES; LOCATING OR PRESENCE-DETECTING BY USE OF THE REFLECTION OR RERADIATION OF RADIO WAVES; ANALOGOUS ARRANGEMENTS USING OTHER WAVES
    • G01S7/00—Details of systems according to groups G01S13/00, G01S15/00, G01S17/00
    • G01S7/52—Details of systems according to groups G01S13/00, G01S15/00, G01S17/00 of systems according to group G01S15/00
    • G01S7/52017—Details of systems according to groups G01S13/00, G01S15/00, G01S17/00 of systems according to group G01S15/00 particularly adapted to short-range imaging
    • G01S7/52077—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 with means for elimination of unwanted signals, e.g. noise or interference
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
    • 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
    • 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

Definitions

  • An embodiment of the present invention relates to an ultrasound imaging apparatus and a diagnostic method thereof. More particularly, the present invention relates to an ultrasound imaging apparatus and a diagnostic method thereof, which can minimize tooth-shaped image artifacts appearing in an ultrasound image due to spike voltage generated during a switching operation with respect to a bias voltage of the HVMUX. .
  • the imaging device is a flower of a medical diagnostic device because it can be seen without cutting the inside of the human body.
  • the imaging device includes an X-ray diagnosis device, a magnetic resonance imaging (MRI) diagnosis device, and an ultrasound diagnosis device. Is used, and each has its advantages and disadvantages.
  • the ultrasonic imaging apparatus has the advantage of being able to make a real-time diagnosis and having a very low price at the expense of resolution. Accordingly, the ultrasound imaging apparatus has become an essential diagnostic device in almost all medical fields such as internal medicine, gynecology, pediatrics, urology, ophthalmology, radiology, and the demand is rapidly increasing.
  • the frequency of ultrasound which is mainly used in the ultrasound imaging apparatus, is from several MHz to several tens of MHz.
  • the ultrasound image is basically composed of the reflected wave generated at the interface consisting of different media.
  • the velocity V of the ultrasonic waves propagating in the human body can be expressed by Equation 1 when the density of the medium is ⁇ and the volume fraction is B.
  • the ultrasonic velocity in the human body varies depending on the medium, and accordingly, compensation for the variation of the velocity in the human body has been studied.
  • Equation 2 An important one of the physical properties of ultrasound is the nature of the attenuation as it propagates in the medium.
  • the intensity I of the ultrasonic wave according to the propagation distance z is expressed by Equation 2.
  • ⁇ is the attenuation coefficient.
  • the attenuation coefficient has a large relationship with the frequency, and the attenuation coefficient in the frequency band used in the ultrasound imaging apparatus increases almost linearly with the frequency.
  • Reflection is related to the characteristic impedance Z of the medium.
  • the characteristic impedance Z of the medium is expressed as the product of the density ⁇ of the material and the velocity V of the ultrasonic wave as shown in Equation 3.
  • Equation 4 When incident from the material of the characteristic impedance Z 1 to the material of Z 2 , the reflectivity R is expressed by Equation 4 below.
  • the transducer 110 converts a pulse of the electrical signal generated by the pulse generator 120 into an ultrasonic signal and transmits the pulse to the object, and converts the ultrasonic signal reflected back from the boundary of different media into an electrical signal. Transfer to the signal processor 130.
  • the signal processor 130 may perform TGC (Time Gain Compensation) amplification, Rx Beamforming, Echo Processing, Spectral Doppler Processor (CDP) / CDP (Regarding the signal received from the transducer 110).
  • TGC Time Gain Compensation
  • CDP Spectral Doppler Processor
  • CDP Code Division Multiple Access to Physical channels
  • DCP color doppler processor
  • DSC digital scan converter
  • probe probe
  • the quality of the image varies depending on the number of transducer elements, and also the number of transducer elements Proportional to the circuits for the transmission and reception of ultrasonic waves also increases.
  • the electrical signal is split into: 2 or 1: 3 using a high voltage multiplexer (HVMUX) on a TI interface board of the ultrasound imaging apparatus. do.
  • HVMUX high voltage multiplexer
  • a high bias voltage that is, the first power source V PP and the second power source V NN is applied to the HVMUX , and the first power source V PP or the second power source is applied.
  • a first switching operation 210 for selecting (V NN ) and a second switching operation 220 for determining whether to select a channel are performed.
  • the spike voltage according to the charge injection of the internal circuit is generated during the first switching operation, which acts like another pulse instead of the Tx pulse, thereby causing an image artifact in the ultrasound image.
  • the spike voltage according to the charge injection of the internal circuit is generated during the first switching operation, which acts like another pulse instead of the Tx pulse, thereby causing an image artifact in the ultrasound image.
  • An embodiment of the present invention was devised to solve the above-described problem, and it is possible to minimize the tooth-shaped image artifacts appearing in the ultrasound image due to the spike voltage generated during the switching operation of the bias voltage of the HVMUX.
  • An object of the present invention is to provide an ultrasound imaging apparatus and a diagnostic method thereof.
  • An example of an ultrasound imaging apparatus for achieving the above object is a pulse generator for generating a pulse of an electrical signal; A probe including a plurality of transducer elements, the probe converting a pulse of an electrical signal into an ultrasonic signal through at least one transducer element and transmitting the pulse to an object; A mux for sequentially selecting at least one of the plurality of transducer elements based on different bias voltages applied; And a control unit configured to move the scan line corresponding to the line density of the transducer element, and to perform switching for different bias voltages at every pulse repitition frequency (PRF) when the scan line is moved.
  • PRF pulse repitition frequency
  • the controller may further form a dummy scan line corresponding to the original scan line.
  • the controller may perform switching for different bias voltages corresponding to the dummy scan line.
  • an ultrasound imaging apparatus for achieving the above object is a pulse generator for generating a pulse of an electrical signal;
  • a probe comprising a plurality of transducer elements, the probe converting a pulse of an electrical signal into an ultrasonic signal through at least one transducer element and delivering the ultrasonic signal to an object;
  • a mux for sequentially selecting at least one of the plurality of transducer elements based on different bias voltages applied;
  • a control unit which forms a PRF corresponding to the linear density of the transducer element, and performs switching for different bias voltages for each of the formed PRFs.
  • Ultrasonic imaging method for achieving the above object, generating a pulse of an electrical signal; Forming a PRF corresponding to the linear density for the transducer element, and performing switching of mux different bias voltages for each formed PRF; Sequentially selecting at least one of the plurality of transducer elements; And converting a pulse of the electrical signal into an ultrasonic signal through the selected transducer element and delivering the pulse to the object.
  • the above-described ultrasound imaging method may further include moving the scan line in response to the formed PRF.
  • the ultrasound image diagnosis method may further include forming a dummy scan line corresponding to the scan line.
  • the aforementioned ultrasound image diagnosis method may additionally perform switching for different bias voltages corresponding to the dummy scan line.
  • the spike voltage generated during the switching operation with respect to the bias voltage of the HVMUX may minimize the tooth-shaped image artifacts appearing in the ultrasound image.
  • FIG. 1 is a diagram illustrating the basic principle of an ultrasound imaging apparatus.
  • FIG. 2 is a diagram illustrating an example of spike voltage generated in HVMUX.
  • FIG. 3 is a diagram schematically illustrating an ultrasound imaging apparatus according to an exemplary embodiment of the present invention.
  • FIG. 4 is a diagram illustrating an example of a pulse generated by the pulse generator of FIG. 3.
  • 5 is a diagram illustrating an example of image artifacts due to spike voltages generated by muxes.
  • FIG. 6 is a diagram illustrating an operation mechanism of the linear density mode.
  • FIG. 7 illustrates an example of mux control for the probe of FIG. 6.
  • FIG 8 illustrates an example of an ultrasound image from which image artifacts are removed according to an embodiment of the present invention.
  • FIG. 9 is a flowchart illustrating an ultrasound imaging method according to an exemplary embodiment of the present invention.
  • FIG. 3 is a diagram schematically illustrating an ultrasound imaging apparatus according to an exemplary embodiment of the present invention.
  • the ultrasound imaging apparatus 300 may include a pulse generator 310, a probe 320, a mux 330, and a controller 340.
  • the pulse generator 310 generates a pulse of an electrical signal.
  • the pulse generating unit 310 in order to increase the axial sharpness of the pulse (Axial Resolution), as shown in Figure 4 to shorten the width of the pulse Tp and to increase the S / N (Signal / Noise) ratio size of the pulse Increase V enough to excite the transducer.
  • the probe 320 is a device for generating and measuring ultrasonic waves and includes a plurality of transducer elements.
  • the probe 320 converts the pulse of the electrical signal generated by the pulse generator 310 through the at least one transducer element into an ultrasonic wave and transmits the ultrasonic wave to the object.
  • the returned ultrasonic signal is converted into an electrical signal and transmitted to a signal processor (not shown).
  • the signal processing unit amplifies TGC (Time Gain Compensation), Rx Beamforming, Echo Processing, SDP (Spectral Doppler Processor) / CDP (Color Doppler Processor), and DSC (Digital Scan). Signal processing such as a converter) and display of an image through a display are applied.
  • the probe 320 may be a linear probe, a sector probe, a convex probe, a trapezoidal probe, or the like according to an assembly form of a plurality of transducer elements.
  • the ultrasonic signal When the ultrasonic signal is emitted to the object by the transducer element, reflection occurs at the interface when acoustic interfaces with different acoustic impedances exist in the propagation medium, and some light is transmitted, and when multiple interfaces exist, the echo is sequentially reflected. Come back. At this time, the returned echo puts stress on the piezoelectric element of the transducer element, and generates an electric field proportional to the echo intensity to convert it into an electrical signal.
  • the mux 330 selects at least one of the plurality of transducer elements of the probe 320 to form a channel. At this time, different bias voltages are applied to the mux 330, and the mux 330 performs a switching operation on the different voltages to be applied, thereby generating a pulse of the electrical signal generated by the pulse generator 310. It can be delivered to the probe 320 through the selected channel.
  • the control unit 340 moves the scan line corresponding to the line density of the transducer element of the probe 320, and different bias voltages of the mux 330 at every pulse repitition frequency (PRF) during movement of the scan line.
  • PRF pulse repitition frequency
  • the charge injection spike voltage generated when switching to the different bias voltages of the mux 330 is a major cause of image artifacts, and especially in the line density mode
  • the effect of the image artifacts is prominent since Tx / Rx is performed two to four times per producer element. That is, assuming that the probe 320 uses 128 transducer elements and operates in the linear density mode 2 as shown in FIG. 5, the probe 320 may have the same effect as using the 256 transducer elements. . In this case, the probe 320 virtually divides one transducer element into four quadrants to make a delay curve when the first # 1 Tx / Rx and the second # 2 Tx / Rx are different, and thus the Tx / Rx. This allows you to adjust the resolution.
  • the control unit 340 of the ultrasound imaging apparatus 300 performs an operation for minimizing the tooth-shaped artifacts appearing in the ultrasound image by the switching operation of the HVMUX.
  • the controller 340 forms a PRF corresponding to the linear density of the transducer element of the probe 320, and performs switching on different bias voltages of the mux 330 for each formed PRF.
  • the controller 340 may transmit a pulse signal EMIF_INT for executing the movement of the scan line in response to the linear density of the transducer element of the probe 320.
  • a PRF signal having the same period as that of the pulse signal EMIF_INT may be formed and transmitted.
  • the pulse of the PRF signal precedes the pulse of the EMIF_INT signal.
  • the controller 340 for such an operation may be implemented by a field programmable gate array (FPGA).
  • FPGAs are semiconductor devices that include programmable logic elements and programmable internals. Programmable logic elements can be programmed by duplicating basic logic gate functions such as AND, OR, XOR, NOT, more complex decoders, or combinations of computational functions. Most FPGAs include programmable logic elements (also called logical blocks) that contain memory elements that are either simple flip-flops or more complete memory blocks. Programmable internal hierarchies allow the logic blocks in the FPGA to be interconnected as required by the system designer. These logic blocks and internal lines can be programmed by the consumer / designer after the manufacturing process to perform any logic function required. For this reason, it is called "on-site programmable gate array.” FPGAs are generally slower than ASIC replacements, cannot be applied to complex designs, and consume more power. However, the development time is short, the error can be corrected on-site, and the initial development cost is low.
  • the controller 340 when the moved scan line is an original scan line, the controller 340 further forms a dummy scan line corresponding to the original scan line.
  • the dummy scan line is not an actual scan line executed by the probe 320, but a virtual scan line for forcibly executing switching to the different bias voltages of the mux 330. That is, the controller 340 transmits a switching command to the mux 330 on the assumption that there is a dummy scan line in advance of the original scan line (in the drawing, the switching command corresponding to the original scan line is represented by IDEX, and the dummy scan line is shown in FIG. The switching command corresponding to DUMMY).
  • the scan according to the linear density is performed by the dummy scan line formed by the controller 340. It is determined that there is a line, and thus switching between different bias voltages corresponding to Tx and Rx is possible for each PRF.
  • one dummy scan line is formed in front of the original scan line in the drawing, the number of dummy scan lines formed may vary depending on the linear density mode. For example, when the linear density mode is 3, two dummy scan lines may be formed in front of the original scan line to perform switching for different bias voltages of the mux 330 at every PRF.
  • the dummy scan line is formed in front of the original scan line in the drawing, in some cases, the dummy scan line may be formed behind the original scan line, or may be formed together with the front and back of the original scan line.
  • tooth-shaped image artifacts can be eliminated as shown in FIG.
  • FIG. 9 is a flowchart illustrating an ultrasound imaging method according to an exemplary embodiment of the present invention.
  • the pulse generator 310 generates a pulse of an electrical signal (S910).
  • the pulse generating unit 310 in order to increase the axial sharpness of the pulse (Axial Resolution), as shown in Figure 4 to shorten the width of the pulse Tp and to increase the S / N (Signal / Noise) ratio size of the pulse Increase V enough to excite the transducer.
  • the controller 340 forms a PRF corresponding to the linear density of the transducer element of the probe 320, and performs switching of different bias voltages of the mux 330 for each formed PRF (S920).
  • the controller 340 may transmit a pulse signal EMIF_INT for executing the movement of the scan line in response to the linear density of the transducer element of the probe 320 (S930).
  • a dummy scan line may be further formed (S940). In this case, the number of dummy scan lines may be adjusted differently according to the linear density mode.
  • the mux 330 selects at least one of the plurality of transducer elements of the probe 320 to form a channel (S950). The selection of such transducer elements is made sequentially, thereby scanning the plurality of transducer elements of the probe 320.
  • the probe 320 converts the pulse of the electrical signal generated by the pulse generator 310 through the at least one transducer element into an ultrasonic wave and transmits the ultrasonic wave to the object.
  • the probe 320 reflects back from the boundary of different media of the object and returns back to the object.
  • the ultrasonic signal is converted into an electrical signal and transmitted to the signal processor. Since the function and operation of the probe 320 are well known techniques, detailed description thereof will be omitted.

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Abstract

La présente invention porte sur un appareil de diagnostic d'image ultrason destiné à minimiser des artefacts d'image ayant une forme de dent résultant d'un mouvement de commutation par un HVMUX dans une image ultrason, et un procédé de diagnostic associé. L'appareil de diagnostic de l'image ultrason, selon un mode de réalisation de la présente invention, comprend : un générateur d'impulsions destiné à générer une impulsion dans un signal électrique, une pluralité d'éléments transducteurs, une sonde destinée à convertir l'impulsion dans le signal électrique en un signal d'onde ultrason et à transférer celui-ci à un corps d'objet par l'intermédiaire d'au moins un élément transducteur, un multiplexeur (MUX) destiné à sélectionner de manière séquentielle au moins un élément de la pluralité d'éléments transducteurs en fonction de différentes tensions de polarisation qui sont appliquées, et une unité de commande destinée à déplacer une ligne de balayage selon une densité de ligne des éléments transducteurs, et à commuter entre les différentes tensions de polarisation à chaque fréquence de répétition d'impulsion (PRF) lorsque la ligne de balayage se déplace.
PCT/KR2012/002801 2011-04-15 2012-04-13 Appareil de diagnostic d'image ultrason pour minimiser des artefacts d'image ayant une forme de dent, et procédé de diagnostic associé Ceased WO2012141520A2 (fr)

Applications Claiming Priority (2)

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KR10-2011-0035235 2011-04-15
KR1020110035235A KR101246274B1 (ko) 2011-04-15 2011-04-15 이빨 모양의 이미지 아티팩트를 최소화할 수 있는 초음파 영상 진단장치 및 그 진단방법

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WO2012141520A2 true WO2012141520A2 (fr) 2012-10-18
WO2012141520A3 WO2012141520A3 (fr) 2013-01-10
WO2012141520A9 WO2012141520A9 (fr) 2013-03-14

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US5462057A (en) * 1994-06-06 1995-10-31 Hewlett-Packard Company Ultrasound imaging system using line splicing and parallel receive beam formation
US6126598A (en) 1998-10-01 2000-10-03 Atl Ultrasound, Inc. Ultrasonic diagnostic imaging system with adaptive spatial compounding
KR100413779B1 (ko) * 2001-08-16 2003-12-31 주식회사 이지메딕스 초음파 진단 장치
KR101468417B1 (ko) * 2007-12-26 2014-12-03 삼성메디슨 주식회사 스펙트럴 도플러를 형성하는 초음파 시스템 및 방법

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KR20120117466A (ko) 2012-10-24
WO2012141520A9 (fr) 2013-03-14
KR101246274B1 (ko) 2013-03-25

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