WO2014155272A1 - Contrôle de qualité en temps réel pour l'acquisition d'images échographiques 3d - Google Patents

Contrôle de qualité en temps réel pour l'acquisition d'images échographiques 3d Download PDF

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Publication number
WO2014155272A1
WO2014155272A1 PCT/IB2014/060091 IB2014060091W WO2014155272A1 WO 2014155272 A1 WO2014155272 A1 WO 2014155272A1 IB 2014060091 W IB2014060091 W IB 2014060091W WO 2014155272 A1 WO2014155272 A1 WO 2014155272A1
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Prior art keywords
image
ultrasound
imaging system
images
display
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PCT/IB2014/060091
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English (en)
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Alasdair Dow
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Koninklijke Philips N.V.
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Publication of WO2014155272A1 publication Critical patent/WO2014155272A1/fr

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    • 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
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
    • A61B8/52—Devices using data or image processing specially adapted for diagnosis using ultrasonic, sonic or infrasonic waves
    • A61B8/5269—Devices using data or image processing specially adapted for diagnosis using ultrasonic, sonic or infrasonic waves involving detection or reduction of artifacts
    • G—PHYSICS
    • G06—COMPUTING; CALCULATING OR COUNTING
    • G06T—IMAGE DATA PROCESSING OR GENERATION, IN GENERAL
    • G06T7/00—Image analysis
    • G06T7/20—Analysis of motion
    • G06T7/223—Analysis of motion using block-matching
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
    • A61B8/08—Detecting organic movements or changes, e.g. tumours, cysts, swellings
    • A61B8/0866—Detecting organic movements or changes, e.g. tumours, cysts, swellings involving foetal diagnosis; pre-natal or peri-natal diagnosis of the baby
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
    • A61B8/08—Detecting organic movements or changes, e.g. tumours, cysts, swellings
    • A61B8/0883—Detecting organic movements or changes, e.g. tumours, cysts, swellings for diagnosis of the heart
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
    • A61B8/46—Ultrasonic, sonic or infrasonic diagnostic devices with special arrangements for interfacing with the operator or the patient
    • A61B8/461—Displaying means of special interest
    • A61B8/463—Displaying means of special interest characterised by displaying multiple images or images and diagnostic data on one display
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
    • A61B8/46—Ultrasonic, sonic or infrasonic diagnostic devices with special arrangements for interfacing with the operator or the patient
    • A61B8/461—Displaying means of special interest
    • A61B8/466—Displaying means of special interest adapted to display 3D data
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
    • A61B8/52—Devices using data or image processing specially adapted for diagnosis using ultrasonic, sonic or infrasonic waves
    • A61B8/5269—Devices using data or image processing specially adapted for diagnosis using ultrasonic, sonic or infrasonic waves involving detection or reduction of artifacts
    • A61B8/5276—Devices using data or image processing specially adapted for diagnosis using ultrasonic, sonic or infrasonic waves involving detection or reduction of artifacts due to motion
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
    • A61B8/54—Control of the diagnostic device
    • A61B8/543—Control of the diagnostic device involving acquisition triggered by a physiological signal
    • G—PHYSICS
    • G06—COMPUTING; CALCULATING OR COUNTING
    • G06T—IMAGE DATA PROCESSING OR GENERATION, IN GENERAL
    • G06T2207/00—Indexing scheme for image analysis or image enhancement
    • G06T2207/10—Image acquisition modality
    • G06T2207/10132—Ultrasound image
    • G06T2207/10136—3D ultrasound image
    • G—PHYSICS
    • G06—COMPUTING; CALCULATING OR COUNTING
    • G06T—IMAGE DATA PROCESSING OR GENERATION, IN GENERAL
    • G06T2207/00—Indexing scheme for image analysis or image enhancement
    • G06T2207/30—Subject of image; Context of image processing
    • G06T2207/30004—Biomedical image processing
    • G06T2207/30044—Fetus; Embryo
    • G—PHYSICS
    • G06—COMPUTING; CALCULATING OR COUNTING
    • G06T—IMAGE DATA PROCESSING OR GENERATION, IN GENERAL
    • G06T2207/00—Indexing scheme for image analysis or image enhancement
    • G06T2207/30—Subject of image; Context of image processing
    • G06T2207/30004—Biomedical image processing
    • G06T2207/30048—Heart; Cardiac
    • G—PHYSICS
    • G06—COMPUTING; CALCULATING OR COUNTING
    • G06T—IMAGE DATA PROCESSING OR GENERATION, IN GENERAL
    • G06T2207/00—Indexing scheme for image analysis or image enhancement
    • G06T2207/30—Subject of image; Context of image processing
    • G06T2207/30168—Image quality inspection

Definitions

  • This invention relates to ultrasonic diagnostic imaging systems and, in particular, to ultrasound systems which provide an indication of the
  • Ultrasonic imaging system are commonly used to assess the medical condition of a patient. Usually these exams entail not only the assessment of physiological characteristics of the organs of a patient but also the measurement of both structural and functional attributes of the body. One type of exam where measurements are always important is an obstetrical exam where the growth and health of a developing fetus is assessed. Structural assessment can identify the possible presence of developing birth defects and measurements are made of the sizes and shapes of developing bones of a fetus to
  • acquiring the necessary high quality images is the fact that the fetus will move in the mother' s womb, particularly in the later stages of a pregnancy when the developing baby is more active.
  • the image will become distorted and contaminated with motion artifacts.
  • One artifact which can render measurements inaccurate if not impossible is image discontinuities caused by the fetus being in one position during the initial part of a scan, then in a different position during the latter part of the scan. The appearance of an organ in the image is thus inaccurate since the organ was in different orientations during different parts of image acquisition.
  • obstetrical exams are often performed by scanning the patient and acquiring images, then analyzing the images and making
  • STIC spatial- temporal image correlation
  • transducer array through the fetal heart region while acquiring planar images at incremental transducer positions. Both require that images be acquired at each spatial plane of the heart and at each phase of the heart cycle needed for the required temporal resolution. As each plane is acquired both its spatial position and heart cycle phase is recorded, the latter usually being done by synthesis of the fetal heart rate as the fetal ECG cannot be acquired in the presence of the mother' s much stronger ECG signal. See US Pat. 7,261,695 (Brekke et al . ) which describes a technique for developing a synthetic heart cycle trigger signal.
  • image frames of the desired anatomy created by MPR reconstruction if necessary, are reordered both spatially and temporally into a loop of images of a single heart cycle according to their phase sequence in the fetal heart cycle. Due to the extensive amount of time needed to acquire all the images needed for a STIC heart loop reconstruction, the possibility of contamination by fetal motion artifacts is highly likely.
  • a matrix array probe performs electronic beam steering of a one dimensional or two dimensional array transducer without the need to physically move the probe or transducer at all. This significantly shortens the image acquisition time.
  • To acquire a full heart image it is often necessary to acquire sectional views of portions of the heart individually, then assemble them into a full view as described in US Pat. 5, 993,390 (Savord et al . ) If there is motion during the time needed to acquire all of the partial views, there can be discontinuity artifacts due to heart motion where the sections are joined together. It is thus desirable to be able to detect these image artifacts when performing both mechanical and fully electronic scanning, and to do so at the time of scanning so that contaminated images can be
  • a diagnostic ultrasound imaging system which detects artifacts in ultrasound images which can prevent precise anatomical
  • the system alerts the operator to the presence of such artifacts so that the operator can take immediate action such as to re-scan the patient.
  • anatomical measurements in an image include motion artifacts and shadowing artifacts. In examples illustrated below these artifacts are detected by image processing including lateral filtering and pixel block matching.
  • the alerting device may be a needle gauge, colored bar indicator, numerical indicator, or a simple binary yes/no indicator.
  • FIGURE 1 illustrates in block diagram form an ultrasonic diagnostic imaging system constructed in accordance with the principles of the present
  • FIGURES 2a, 2b, and 2c illustrate the
  • FIGURE 3 illustrates the problem of image discontinuity due to motion which is addressed by an implementation of the present invention.
  • FIGURE 4 illustrates the problem of image shadowing which is addressed by an implementation of the present invention.
  • FIGURES 5a and 5b illustrate the operation of a lateral filter in accordance with the present
  • an ultrasound system constructed in accordance with the principles of the present invention is shown in block diagram form.
  • the illustrated ultrasound system operates through two major subsystems, a front end acquisition subsystem 10A and a display subsystem 10B.
  • An ultrasound probe is coupled to the acquisition subsystem to transmit ultrasound waves and receive ultrasound echo signals.
  • the probe may do this with a linear (one-dimensional) row of transducer
  • micro-beamformer contains circuitry which controls the signals applied to groups of elements of the array transducer 70 and does some processing of the echo signals received by elements of each group.
  • Micro-beamforming in the probe advantageously reduces the number of conductors in the cable between the probe and the ultrasound system and is described in US Pat. 5,997,479 (Savord et al.) and in US Pat. 6,436,048 (Pesque) , and provides electronic steering and focusing of beams on transmit and during beam reception for the production of highly resolved image data of volumetric regions of the body in real time and suitable for anatomical quantification and measurement.
  • the probe 70,72 is coupled to the acquisition subsystem 10A of the ultrasound system.
  • acquisition subsystem includes a beamform controller
  • microbeamformer 72 instructing the probe as to the timing, frequency, direction and focusing of transmit and receive beams.
  • the beamformer controller can also control the timing of acquisition so as to be synchronized to physiological activity of the body indicated by gating signals.
  • the beamform controller also controls the beamforming of echo signals
  • A/D converters 18 and a system beamformer 20 receive signals from the acquisition subsystem by its control of analog-to-digital (A/D) converters 18 and a system beamformer 20.
  • Partially beamformed echo signals received by the probe are amplified by preamplifier and TGC (time gain control) circuitry 16 in the acquisition subsystem, then digitized by the A/D converters 18.
  • the digitized echo signals are formed into fully steered and focused beams by the main system beamformer 20.
  • the echo signals are processed by a signal processor 22 which performs digital filtering, B mode and M mode detection, and Doppler processing, and can also perform other signal
  • Image acquisition is directed by commands from a user control panel 40 operated by a system operator.
  • the echo signals produced by the acquisition subsystem 10A are coupled to the display subsystem 10B, which processes the echo signals for display in the desired image format on a display screen 62.
  • the echo signals are processed by an image line processor 24, which is capable of sampling the echo signals, splicing segments of beams into complete line
  • the image lines for a 2D (two dimensional) image are scan converted into the desired image format by a 2D image processor 26 which performs R-theta conversion as is known in the art.
  • the 2D image processor can thus format rectilinear or sector image formats.
  • the 2D images are stored in an image memory 28 with other 2D images from which they can be displayed on the display 62.
  • the images in memory are also overlaid with graphics to be displayed with the images, which are generated by a graphics generator 34. Individual images or image sequences can be stored in the image memory 28 for display of image loops or live
  • the display subsystem 10B also includes a 3D (three dimensional) image processor 30 which receives image lines from the image line processor 24 for the rendering of real-time three dimensional images.
  • the 3D images can be displayed as live (real time) 3D images on the display 62 or stored in the image memory 28 for later review and diagnosis.
  • the 2D and 3D images are coupled to an artifact detector 32 which detects image artifacts in accordance with the present invention that could degrade anatomical measurements using the images.
  • the artifact detector 32 is coupled to a quality indicator circuit 36 which produces a graphic or numeric indication of image quality on the display screen 62 by means of the graphic generator 34.
  • ECG leads 50 can be adhesively attached to a patient and provide ECG signals for a QRS processor 52 which identifies the R-wave peak of each heartbeat.
  • the timing of the R-wave is used to acquire images at particular phases of the heart cycle.
  • Images of the heart can be acquired at specific phases of the heart cycle by coupling the R- wave timing as a trigger signal from a trigger signal generator 54 to the beamform controller 74 and the controls of the control panel 40 are used to select the desired heart phases at which heart phase-gated images are to be acquired by the ultrasound system.
  • FIGURES 2a-2c illustrate the acquisition of a wide view image of the heart 100 using the sectional approach described in the above-mentioned US Pat. 5,993,390 (Savord et al . )
  • the heart images being acquired are 3D images acquired with a matrix array probe having a two dimensional array transducer 70. Since only a small section or subvolume of the heart is being imaged, the number of scanlines transmitted and received is relatively low, meaning that a sectional image can be acquired in a relatively short time and a significant number of phases of the heart can be imaged during one heartbeat.
  • an adjacent section of the heart is scanned as shown in FIGURE 2b. This section is scanned during a
  • a sequence of full heart images can now be produced by forming each image of the sequence with adjacent sub-images of the three sectional images of a common heart phase. The sequence can be replayed as a loop, enabling the clinician to view a wide 3D image of the heart beating in real time due to the temporal alignment of the heart sections used to form each wide view image.
  • the image sections are properly spatially aligned. If the patient is still during the image acquisition the image sections will be spatially aligned and the wide view images useful for quantified measurement, but if the patient moves during the image acquisition this will not be the case. This is particularly true during fetal imaging. While an adult patient can be asked to remain stationary and will do so during scanning, a fetus in the womb of the mother can move at any time. This can result in a 3D image with motion artifacts as shown in FIGURE 3. In this example the two dimensional matrix array transducer
  • the array transducer scans the next (e.g., adjacent) image plane, the time interval between acquisition of the two planes can be significant enough that motion artifact can manifest themselves more severely. This is especially true for a group of image planes of a section acquired during one heartbeat relative to a group of image planes acquired during another
  • a plane which is images by consecutively acquired scanlines will be referred to as an azimuth planes and the adjacent positioning of such azimuth planes over the 3D volume will be referred to as the elevation dimension.
  • the 3D ultrasound probe is a
  • FIGURE 3 is an elevation view of the heart formed from multiple adjacent azimuth images oriented normal to the page with groups of azimuth images being acquired of sections of the heart 100 during different heartbeats.
  • the 3D image exhibits distortion due to motion artifacts. While the section of the heart between section boundary lines 42 and 44 is seen to be smooth and continuous, it is seen that the adjacent section between boundary lines 46 and 48 does not spatially align at lines 44, 46. The patient has moved between acquisition of these two volume segments as seen by the slightly lower offset of the section to the right of 44,46. This is also the case albeit to a lesser degree when the boundary 44 of the first section is matched with the middle of the section between boundary lines 56 and 58. The motion offset is seen again where the boundary 58 of the center section fall in the middle of the third section between boundaries 46 and 48. A disjuncture or break in the wall of the heart is seen at the top and bottom of the heart along boundary line 58 in FIGURE 3. Accordingly measurements taken of the heart such as chamber dimensions and volumes will be inaccurate due to the effect of motion on the 3D images .
  • FIGURE 4 illustrates the problem.
  • a two dimensional matrix array transducer 70 is scanning the heart volume.
  • the path of acoustic energy between the array transducer and the heart 100 is seen to contain an object 60 which absorbs or scatters acoustic energy, such as a rib of the body.
  • an object 60 which absorbs or scatters acoustic energy, such as a rib of the body.
  • the anatomy of the heart below the rib 60 receives less transmitted energy and returning energy is also scattered or absorbed by the intervening object 60.
  • the resultant image manifests a faint region due to the paucity of acoustic energy below the object as illustrated by the faint region 62 down the middle of the heart image 100.
  • the boundary of the anatomy can appear blurred or indistinct where shadowing has occurred, rendering measurements inaccurate or impossible where shadowing has affected the image .
  • the ultrasound system of FIGURE 1 includes an artifact detector 32 which detects artifacts in 3D ultrasound images which can affect the accuracy of quantified measurements such as dimensions, volumes and functional characteristics.
  • detector 32 operates on real time images so that images which are deleteriously affected by artifacts can be identified immediately and the images
  • the artifact detector provides an indication of artifact contamination to a quality indicator 36 which
  • FIGURES 3 and 4 show two exemplary quality indicators in association with ultrasound images.
  • the quality indicator 82 of FIGURE 3 is a needle gauge type indicator where the position of the needle on the gauge indicates the degree of artifact contamination in the image and the suitability of the image for quantification. In this example the needle is seen to be positioned toward the left side of the gauge, indicating a poor image for quantification.
  • the needle When the image is a high quality artifact-free image the needle will be positioned at the upper end (right side) of the gauge.
  • the quality indicator 92 is a bar-type indicator with color shades ranging to red at the bottom of the bar and colors ranging toward green at the top.
  • An arrow or carat on the side of the bar indicates the quality of the image for quantification. For a highly contaminated image the carat will be down toward the red end of the bar and for a high quality artifact- free image the carat will move to the upper green end of the bar.
  • the artifact detector 32 comprises a lateral filter which assesses an image in a lateral direction, as motion artifacts are most likely to be most severe in the lateral elevation dimension.
  • the lateral filter compares laterally (e.g., elevationally) distinct scanlines, image planes or volumes to look for discontinuities in an image which are characteristic of motion. The operation of a lateral filter of the present
  • FIGURE 5a depicts a series of grids of pixels 102 which are portions of elevationally adjacent image planes 201-209. Such image plane portions illustrate the pixels of the outer surface 106 of the heart at the top of the image of FIGURE 3 which are located as indicated at 80 in the drawing.
  • the dark groups of pixels of the outer surface are in lateral alignment or at least partially overlap from plane 201 to plane 205 where the surface appears continuous in FIGURE 3.
  • FIGURE 3 shows that the surface
  • the dark group of pixels of the heart surface in image plane 207 is offset from alignment with the dark group of pixels of the heart surface in the adjacent image plane 205.
  • the adjacent section of the heart is located upward in its new position relative to the previous section image as indicated by the upward transition of the alignment arrow 104. The transition is seen at the top of the heart image in FIGURE 3 by the discontinuity in the surface at the top of the image at 80.
  • the lateral filter of the artifact detector 32 will detect this motion artifact by the failure of the blocks of pixels in the laterally disposed image planes to align in a smoothly continuous way and will control the quality indicator 36 accordingly. The user will then know that the image of FIGURE 3 is adversely affected by an artifact which can affect quantified measures of the anatomy of the 3D image.
  • FIGURE 5b illustrates the operation of a lateral filter in an implementation of the present invention when assessing a image with shadowing artifacts such as that shown in FIGURE 4.
  • FIGURE 4b illustrates the surface at the top of the heart image appears sharply defined by a distinctly dark border where shadowing is not present, but becomes faintly defined and indistinct in the
  • Block matching is often used to detect motion in images of the same anatomy which are temporally different, or in spatially different images of stationary images when aligning the images as in panoramic imaging. In the examples described above block matching can be used to identify
  • discontinuity in offset such as that occurring between the darkened block of pixels in plane 205 of FIGURE 5a and the darkened block of pixel in adjacent plane 207 is a mark of, not a sudden transition of the organ boundary, but a discontinuity due to a motional effect between image plane acquisition times .

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Abstract

La présente invention concerne un système échographique qui acquiert des images échographiques 3D par acquisition d'images de sous-volumes d'un objet volumétrique 3D, puis alignement spatial de sous-volumes adjacents pour former une image 3D en vue large. Si les sous-volumes sont acquis pendant la survenue d'un mouvement ou d'un masquage acoustique, l'image 3D peut être trop contaminée par des artefacts pour être adaptée pour une mesure quantifiée précise. Un détecteur d'artefacts évalue l'image 3D pour la présence de tels artefacts et contrôle un indicateur de qualité qui donne une indication de la conformité d'une image 3D pour quantification pendant une imagerie en temps réel. Cela peut suggérer à l'utilisateur de réexaminer le patient afin d'acquérir à nouveau une image de l'anatomie qui est sans artefact et plus adaptée pour une quantification précise.
PCT/IB2014/060091 2013-03-28 2014-03-24 Contrôle de qualité en temps réel pour l'acquisition d'images échographiques 3d WO2014155272A1 (fr)

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WO2017181288A1 (fr) 2016-04-21 2017-10-26 The University Of British Columbia Analyse d'image échocardiographique
CN108778142A (zh) * 2016-03-01 2018-11-09 皇家飞利浦有限公司 颈部褶皱半透明带的自动超声测量
WO2019084411A1 (fr) * 2017-10-27 2019-05-02 Butterfly Network, Inc. Indicateurs de qualité pour la collecte et la mesure automatisée sur des images ultrasonores
CN110464380A (zh) * 2019-09-12 2019-11-19 李肯立 一种对中晚孕期胎儿的超声切面图像进行质量控制的方法
CN111281425A (zh) * 2018-12-10 2020-06-16 通用电气公司 用于显示目标对象质量水平的超声成像系统和方法
US10751029B2 (en) 2018-08-31 2020-08-25 The University Of British Columbia Ultrasonic image analysis
CN111629670A (zh) * 2017-12-20 2020-09-04 韦拉索恩股份有限公司 用于超声系统的回波窗口伪影分类和视觉指示符
JP2021501656A (ja) * 2017-11-02 2021-01-21 コーニンクレッカ フィリップス エヌ ヴェＫｏｎｉｎｋｌｉｊｋｅ Ｐｈｉｌｉｐｓ Ｎ．Ｖ． 画像アーチファクトを検出するインテリジェント超音波システム
US20210236083A1 (en) * 2020-02-04 2021-08-05 Samsung Medison Co., Ltd. Ultrasound imaging apparatus and control method thereof

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