WO2006123729A1 - 超音波診断装置及びその画像処理方法 - Google Patents
超音波診断装置及びその画像処理方法 Download PDFInfo
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- WO2006123729A1 WO2006123729A1 PCT/JP2006/309902 JP2006309902W WO2006123729A1 WO 2006123729 A1 WO2006123729 A1 WO 2006123729A1 JP 2006309902 W JP2006309902 W JP 2006309902W WO 2006123729 A1 WO2006123729 A1 WO 2006123729A1
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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
- A61B8/13—Tomography
- A61B8/14—Echo-tomography
-
- 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
-
- 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
- A61B8/48—Diagnostic techniques
- A61B8/483—Diagnostic techniques involving the acquisition of a 3D volume of data
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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
- G01S7/52085—Details related to the ultrasound signal acquisition, e.g. scan sequences
- G01S7/52087—Details related to the ultrasound signal acquisition, e.g. scan sequences using synchronization techniques
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- G—PHYSICS
- G06—COMPUTING; CALCULATING OR COUNTING
- G06T—IMAGE DATA PROCESSING OR GENERATION, IN GENERAL
- G06T7/00—Image analysis
- G06T7/0002—Inspection of images, e.g. flaw detection
- G06T7/0012—Biomedical image inspection
-
- G—PHYSICS
- G06—COMPUTING; CALCULATING OR COUNTING
- G06T—IMAGE DATA PROCESSING OR GENERATION, IN GENERAL
- G06T7/00—Image analysis
- G06T7/20—Analysis of motion
- G06T7/246—Analysis of motion using feature-based methods, e.g. the tracking of corners or segments
-
- 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
- G01S7/52053—Display arrangements
- G01S7/52057—Cathode ray tube displays
- G01S7/52074—Composite displays, e.g. split-screen displays; Combination of multiple images or of images and alphanumeric tabular information
-
- 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
Definitions
- the present invention relates to an ultrasonic diagnostic apparatus and an image processing method thereof, and more particularly to an ultrasonic diagnostic apparatus capable of obtaining a useful ultrasonic image in consideration of the shape and size of speckles and the image thereof. It relates to the processing method.
- Ultrasound images obtained with an ultrasound diagnostic apparatus contain noise called speckle noise. This speckle noise is thought to appear when scattered waves from reflectors in living tissue that are sufficiently smaller than the wavelength of ultrasonic waves are generated and interfered in various phases.
- speckle noise is generally unnecessary noise for image diagnosis and should be reduced.
- a circuit for determining and removing speckle noise is provided.
- Patent Document 1 Japanese Patent Laid-Open No. 9-94248
- An object of the present invention is to provide an ultrasonic diagnostic apparatus capable of obtaining a more useful ultrasonic image by performing a filtering process in consideration of the shape and size of speckles, and an image processing method thereof. There is to do.
- the ultrasonic diagnostic apparatus of the present invention is an ultrasonic diagnostic apparatus comprising means for transmitting and receiving ultrasonic waves in a subject and capturing a moving image of the subject.
- speckle measuring means for measuring the size and / or shape of speckle appearing on each frame, and depending on the size and / or shape of the measured speckle It features a smoothing means that smoothes the image data of each frame! / Speak.
- the ultrasonic image processing method of the present invention includes:
- an ultrasonic image processing method comprising a step of transmitting and receiving ultrasonic waves in a subject and capturing a moving image of the subject
- FIG. 1 is a system configuration diagram of an ultrasonic diagnostic apparatus according to Embodiment 1 of the present invention.
- FIG. 2 is a processing procedure of the ultrasonic diagnostic apparatus 1 according to the first embodiment of the present invention.
- FIG. 3 is a diagram showing a state where a window in the direction of an ultrasonic beam is set on an ultrasonic image (B mode).
- FIG. 4 is a diagram showing an ideal speckle profile.
- FIG. 6 A diagram showing a case where the contrast between the speckles is narrow and the contrast is saturated.
- FIG. 7 is a diagram illustrating an example of characteristics of a two-dimensional Gaussian filter.
- FIG. 8 is a diagram showing a state where manual tracing is completed.
- FIG. 9 is a diagram showing the result of correcting the unevenness and the variation in the interval of the contour points 83 to 85 in step 26.
- FIG. 10 is a diagram for explaining the Simpson method.
- FIG.11 How force (time change) changes with each frame update.
- FIG. 12 is a diagram showing a display example in Example 2.
- FIG. 13 is a diagram showing a display example in Example 3.
- FIG. 14 is a diagram showing another display example on the display device.
- FIG. 1 is a system configuration diagram of an ultrasonic diagnostic apparatus according to Embodiment 1 of the present invention.
- an ultrasonic diagnostic apparatus 1 is an apparatus for measuring cardiac function using ultrasonic waves, and at least includes a known ultrasonic diagnostic apparatus. Configure the equipment.
- the ultrasonic diagnostic apparatus 1 includes a probe 2, a transmission unit 3, a reception unit 4, a transmission / reception separation unit, a phasing addition unit 6, a signal processing unit 7, and an A / D conversion unit 8
- the In Fig. 1 only the main functions of the ultrasonic diagnostic equipment are shown. Hereinafter, each configuration shown in FIG. 1 will be described.
- the probe 2 is configured to transmit an ultrasonic wave toward a diagnostic site (here, the heart) and receive the reflected wave. Inside the probe 2, there are provided a plurality of transducers (not shown) that serve as ultrasonic wave generation sources (transmission sources) and can receive reflected waves.
- the transmitter 3 is configured to generate a transmission pulse signal for driving the probe 2 to transmit ultrasonic waves.
- the receiving unit 4 is configured to receive an echo signal received by the probe 2 and converted into an electric signal.
- the transmission separation unit 5 can send a transmission pulse signal from the transmission unit 3 to the probe 2 at the time of transmission, and can send an echo signal from the probe 2 to the reception unit 4 at the time of reception. It is structured as follows.
- the phasing adder 6 is configured to generate a received beam signal by phasing and adding a plurality of echo signals from the receiver 4.
- the signal processing unit 7, the A / D conversion 8, the frame memory 9a, and the cine memory 9b It is configured to function as a signal processing unit for obtaining a tomographic image (black-and-white tomographic image) of a diagnostic region based on the number. That is, the signal processing unit 7 receives the received beam signal from the phasing addition unit 6 and performs signal processing such as gain correction, log compression, detection, contour enhancement, and filter processing.
- the A / D converter 8 is configured to convert the signal output from the signal processing unit 7 into a digital signal.
- the frame memory 9a is configured to be able to store the digital reception beam signal output from the A / D conversion in units of image frames.
- the cine memory 9b is configured to store a plurality of image frames taken continuously. The images stored in the frame memory 9a and the cineme 7 memory 9b are associated with phase information of the ECG wave meter measured by the electrocardiograph 16.
- the tomographic frame data stored in the frame memory 9a is read out in synchronization with the television based on the control signal of the controller 10.
- the control controller 10 controls each component based on the control program, processes the tomographic frame data read from the cine memory 9b into ultrasonic tomographic image data, and sets contour points and contour lines to be described later. Performs data generation and output control to the display device 15, performs predetermined calculations such as volume calculation and distance calculation related to cardiac function measurement, which will be described later, and performs correction, smoothing processing and tissue tracking, which are also described later. It is configured to be able to perform various processes.
- the control controller 10 is configured to have a so-called microcomputer function.
- the controller 10 has functions such as calculation means, calculation result output means, smoothness processing means, and tissue tracking means as described later.
- the input device 11 is connected to the controller 10 via the interface 12.
- Examples of the input device 11 include a mouse and a trackball.
- the input device 11 allows the operator (operator) to manually trace the contours of the left ventricle, myocardium, and left atrium of the heart on the ultrasound image while referring to the ultrasound image displayed on the display device 15.
- the input device 11 and the controller 10 have the functions of tracing means and correcting means as will be described later.
- the result storage unit 13 uses coordinate data of contour points to be described later, and the controller 10 It has a function as a memory for storing and storing the calculated results. Result storage
- the coordinate data and calculation results stored in 13 are read out based on the control signal of the controller 10, V /!
- the display circuit unit 14 is configured to operate based on a control signal related to an output from the controller 10.
- the display circuit unit 14 is configured to be able to generate an image signal for display by converting ultrasonic tomographic image data from the controller 10, contour points described later, and data of each contour line into analog signals. Yes.
- the display circuit unit 14 is provided with a D / A conversion, a video signal conversion circuit and the like, although not particularly shown.
- the display device 15 is configured to be able to display an ultrasonic image by inputting the video signal output from the display circuit unit 14. As the display device 15, for example, a television monitor is used.
- FIG. 2 is a flowchart showing processing in the controller 10.
- the processing described here includes a procedure for the user to perform various inputs using the input device 11 and the display device 15.
- each step of the flowchart of FIG. 2 shown below will be described with reference to FIGS. 3 to 11 as needed.
- the first frame image is read from the cine memory 9b, and the first frame of the ultrasonic moving image is displayed on the display device 15.
- the image of the first frame displayed in step 21 is filtered by the method described later to improve the image quality.
- This filtering process consists of step 22a and step 22b.
- a smoothing filter of image density is applied to the image data.
- One of the smoothing filters is the 2D Gaussian filter.
- the 2D Gaussian filter In the ultrasonic image, resolution is achieved in the transmission / reception direction of the ultrasonic beam and the scanning direction (direction intersecting the transmission / reception direction). Therefore, it is necessary to apply 2D Gaussian filter processing according to the difference in resolution. More specifically, on the ultrasonic image, there is an unevenness of density called speckle (for example, see JP-A-7-51270), but in the ultrasonic image this speckle is not a perfect circle but an ellipse. The shape (the major axis direction and the minor axis direction are the scanning direction or transmission direction of the ultrasonic beam, respectively). Accordingly, the present inventors have invented a method of applying a two-dimensional Gaussian filter anisotropically in view of the speckle having an elliptical shape.
- Steps 22a and 22b will be described below.
- Fig. 3 shows the window 41 in the direction of the ultrasonic beam set on the ultrasonic image (B mode).
- the average size and / or shape of the speckle inside the window is obtained from the image data in the window 41.
- the specific procedure is to take out the pixel values in the window as they are, perform affine conversion so that the beam transmission direction is vertical on the screen, and then in the horizontal direction in the window shown as 42 And a vertical density co-occurrence matrix (see, for example, Japanese Patent Laid-Open No. 5-123318) are calculated to obtain a contrast feature amount.
- the speckle size and / or shape is ideal, the distance (53) between the pixel position with the highest contrast (51) and the pixel position with the lowest contrast (52), as shown in Figure 4.
- a profile on a certain line segment of the image may not necessarily be ideal as shown in FIG.
- Fig. 6 shows the result of calculating the density co-occurrence matrix
- 61 is the distance between pixels
- 62 is the contrast
- 63 is the horizontal contrast
- 64 is the vertical contrast
- the distance 65 indicated by A and B is the spec.
- the minor axis A and major axis B of the In Fig. 6, the contrast feature of the density co-occurrence matrix where the speckle intervals are narrow is saturated.
- the distance until the pixel value reaches the maximum A and B in Fig. 6 is detected and the speckle size (minor axis A and major axis B) is determined.
- Step 22b In this step, the speckle size (minor axis A and major axis B) obtained in step 22a is used, and a 2D Gaussian filter is applied according to the characteristics.
- FIG. 7 is an example of characteristics of the two-dimensional Gaussian filter (71).
- the two-dimensional Gaussian filter uses a function that uses a normal distribution as a filter for any cross-section in the X-axis and Y-axis directions.
- the cross section becomes an ellipse, which is equivalent to the speckle obtained in step 22a.
- the size of minor axis A and major axis B in step 22a is adjusted as the standard deviation in the X-axis direction and Y-axis direction of the two-dimensional Gaussian filter shown in Fig. 7 to optimize the smoothing process. To do.
- the minor axis As to how to adjust the standard deviation ⁇ jump in the X-axis direction and Y-axis direction of the two-dimensional Gaussian filter with respect to the minor axis A and major axis B obtained in step 22a, the minor axis
- the left atrium (or right atrium) of the heart can be rendered.
- steps 22a and 22b make it possible to clearly display the left atrium of the heart, thus facilitating a manual trace to the left atrium.
- manual tracing refers to the contours of the left ventricle, myocardium, and left atrium (more specifically, the contours of the left ventricle, left ventricular membrane, and left atrium) on the ultrasound image. Says tracing by points (contour points).
- a pair of annulus (the junction of the left ventricle and the left atrium) is treated as a common part when manually tracing the left ventricle and the left atrium.
- An example of a specific procedure for manual tracing here is to place a contour point at the position of one annulus (for example, 81 in Fig. 8), and this contour point force is also contour point in order along the left ventricular membrane. Arrange multiple. After placing multiple contour points along the left ventricular membrane, the position of the other annulus (example For example, a contour point is placed at 82) in FIG. Similarly, a contour point is arranged at the position of one annulus, and a plurality of contour points are arranged in this order along the contour point force left ventricular membrane. After arranging a plurality of contour points along the left ventricular membrane, the contour points are arranged at the position of the other annulus.
- a contour point is arranged at the position of one annulus, and a plurality of contour points are arranged in this order from the contour point along the left atrium. After arranging a plurality of contour points along the left atrium, a contour point is placed at the position of the other annulus.
- the manual tracing procedure shown here is an example, and any contour force may be used for manual tracing.
- manual tracing (allocation of contour points) in either the clockwise or counterclockwise direction of the screen may be performed.
- only the left atrium may be manually traced, and the left ventricle and myocardium may be automatically traced by conventional techniques (for example, the technique disclosed in Japanese Patent Laid-Open No. 8-206117).
- the contour points input and arranged by the input device 11 in step 23 are displayed on the display device 15 so as to be superimposed on the ultrasonic image, and are also stored and stored in the result storage unit 13. It has become.
- Figure 8 shows the completed manual trace, with multiple contour points.
- 81 and 82 in FIG. 8 indicate the positions of a pair of annulus.
- Reference numeral 83 denotes a contour line of the left ventricular membrane formed by a plurality of contour points
- 84 denotes a contour line of the left ventricular membrane
- 85 denotes a contour line of the left atrium.
- the contour lines 83 to 85 have many irregularities and the intervals between the contour points vary.
- the operator clearly considered the fitting error.
- the input device 11 is used for manual correction. More specifically, manual correction is performed by clicking and dragging individual contour points. The coordinate data of each contour point after the manual correction is stored and stored in the result storage unit 13 again.
- the position of the annulus may be slightly shifted by the contours 83 to 85. In such a case, it may be shared depending on the position of the annulus by any one contour line, or the average coordinate of the position coordinates of the annulus by a plurality of contour lines is obtained and this is calculated. You may make it common as a position.
- the left ventricle and the left atrium are connected by a single line, and the blood flow volume flowing between the left ventricle and the left atrium can be measured without omission.
- the region surrounded by the left ventricular membrane and the left ventricular membrane is the myocardium, the area of the myocardial region can be measured without omission.
- step 28 Determine whether manual tracing of the first frame has been performed properly. If it is determined that it has been performed properly, go to step 28. If it is determined that it has not been done properly, go to step 21.
- the Simpson method is used to determine the volume, and a specific description thereof will be given with reference to FIG.
- the midpoint 101 between the annulus is obtained, and the farthest point on the contours of the left ventricular membrane, left ventricular epicardium, and left atrium from that point is searched for, 102, 103, 104 are obtained and the Simpson method is applied.
- a method for quadrature of organs using the Simpson method is disclosed in, for example, Japanese Patent Application Laid-Open No. 7-289545.
- the left ventricular membrane, the left ventricular membrane, the left atrium, the sum of the left ventricle and the left atrium, the myocardium (the left ventricular membrane volume and the left ventricular membrane volume Calculate each volume of difference.
- the length of the axis 102 (the point on the axis 102 that intersects the left ventricular membrane on the uppermost side with respect to the midpoint 101 on the axis 102 and the axis 102 on the axis 102 that is the most downward in the direction of the figure)
- the length of the left ventricle and the left atrial wall (the length connecting the points that intersect the left atrium when extended to the side) (the direction of the line segment connecting the paired annulus of the contour line that constitutes the left ventricular membrane and the left atrium) Width 105, 106, inner and outer myocardium Calculate the distance 107 between. Also, the distance 108 between contour points in the contour direction is calculated.
- step 30 Determine if there is a next frame. If there is a next frame, go to step 30; if there is no next frame, go to step 33.
- the controller 10 reads the image data of the next frame from the cine memory 9b and stores it in the result storage unit 13.
- Step 31 comprises step 31a and step 31b, and performs the same processing as step 22a and step 22b, respectively.
- the contour of each organ generated when the transition from the first frame to the second frame (or the nth frame force n + 1 frame according to the frame reading performed one after another in step 30) is performed.
- tracking the change (movement) of the contour line of each organ is called the tissue tracking process.
- the specific method of the tissue tracking process in the present embodiment uses a highly robust algorithm so that it can be applied even when the image quality is poor.
- an optical flow method can be used, and a block matching method, a gradient method, and a particle tracking method can be applied.
- the gradient method the velocity vector is calculated analytically using the gradient of the image density. Since the access to the image is only differential calculation, the velocity vector can be obtained at high speed.
- a somewhat large differential value is obtained, so that tissue tracking can be performed stably.
- the process proceeds to step 28, and for the second frame (n + 1 frame), the left ventricular membrane, left ventricular epicardium, left atrium, sum of left ventricle and left atrium, myocardium (left ventricular membrane volume) Difference between left and right ventricular volume), length of 102, distance between walls of left ventricle and left atrium, distance between inner and outer walls of myocardium, distance between contour points in contour line direction (hereinafter, step 28)
- the value obtained by (referred to as a parameter) is calculated.
- each parameter is updated with the frame update.
- the change (time change) is displayed on the display device 15 in the form of a graph or the like.
- the horizontal axis indicates the time or frame number
- the vertical axis indicates the calculated value of each parameter, for example, as shown in FIG.
- the left ventricular membrane, left ventricular membrane, left atrium, sum of left and left ventricle, myocardial (left ventricular membrane volume, left ventricular membrane volume) volume changes over time, including the left atrium.
- ECG electrocardiogram
- the top line is the left ventricular epithelium, the next is the sum of the left ventricle and left atrium
- the lengths of the left ventricular membrane, left ventricular outer membrane, and left atrial axis (102, 103, 104 in FIG. 10) can be similarly graphed.
- the distance between the left ventricle and the left atrial wall 105, 106, the distance between the inner and outer membranes of the myocardium, and the distance 108 between the contour points in the contour direction can also be graphed.
- Volume, axial length, and wall-to-wall distance are important indicators for evaluating cardiac function, and are closely related to the left ventricular myocardium and left atrial membrane performance.
- the contour line of each organ is determined by manual tracing or the like in the first one of the moving images of a plurality of frames obtained successively in time, and the first
- filtering of each image data taking into account the size and shape of speckle that appears characteristically on the ultrasound image
- various parameters used for diagnosis of the subject are obtained based on the contours of each organ in each frame, and the temporal changes thereof can be displayed. It became possible to provide a method.
- This embodiment is another example of the display example displayed on the display device 15 in the present invention.
- Example 3 This embodiment is another example of the display example displayed on the display device 15 in the present invention. As shown in Fig. 14, the ventricle, left atrium, and myocardium are divided into several parts and displayed in three dimensions (131), and the frames are displayed continuously to display the three-dimensional ventricle. You can visualize how the left atrium and heart muscle change over time.
- the filtering process applied to each frame in the above steps 22 and 31 may not be performed after step 21 and after step 30, but may be performed on all frames collectively before step 21.
- the two-dimensional Gaussian filter applied in steps 22b and 31b may use other functions that are not necessarily filter processing using Gaussian functions.
- the present invention can also be applied to observation of other organs in addition to observing the dynamics of the heart. For example, it may be used to observe the pulse of the neck carotid artery. It is considered that there is an image quality improvement effect by performing smoothing processing in consideration of the size / and shape of speckles not only in a moving organ but also in normal ultrasonic imaging. Is applicable to ordinary ultrasonic diagnostic equipment and methods.
- the size and / or shape of speckle may vary depending on the location even within one frame of image data. Therefore, depending on the size and / or shape depending on the location, the Gaussian The smoothing process by the filter may be changed.
- the display examples shown in FIGS. 11 to 13 may not be displayed on the display device 15 alone, but may be displayed in parallel with the B-mode image.
- the combination of the B-mode image (141) and the display example of FIG. 11 (142) results in FIG.
- a line indicated by reference numeral 143 indicates which timing of the upper B-mode image in FIG. 14 is on the horizontal time axis of the lower display example.
Abstract
Description
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Priority Applications (4)
Application Number | Priority Date | Filing Date | Title |
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EP06746590A EP1882450B1 (en) | 2005-05-19 | 2006-05-18 | Ultrasonographic device and image processing method thereof |
CN200680014972XA CN101170948B (zh) | 2005-05-19 | 2006-05-18 | 超声波诊断装置及其图像处理方法 |
US11/914,814 US20090216124A1 (en) | 2005-05-19 | 2006-05-18 | Ultrasonic diagnostic apparatus and image processing method thereof |
JP2007516333A JP5138369B2 (ja) | 2005-05-19 | 2006-05-18 | 超音波診断装置及びその画像処理方法 |
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JP2005146656 | 2005-05-19 | ||
JP2005-146656 | 2005-05-19 |
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US (1) | US20090216124A1 (ja) |
EP (1) | EP1882450B1 (ja) |
JP (1) | JP5138369B2 (ja) |
CN (1) | CN101170948B (ja) |
WO (1) | WO2006123729A1 (ja) |
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JP2012090821A (ja) * | 2010-10-27 | 2012-05-17 | Ge Medical Systems Global Technology Co Llc | 超音波診断装置 |
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WO2019156139A1 (ja) * | 2018-02-08 | 2019-08-15 | 興和株式会社 | 画像処理装置、画像処理方法及び画像処理プログラム |
JP7328156B2 (ja) | 2020-01-22 | 2023-08-16 | キヤノンメディカルシステムズ株式会社 | 超音波診断装置、医用画像処理装置、および医用画像処理プログラム |
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US20100113929A1 (en) * | 2008-10-31 | 2010-05-06 | National Tsing Hua University | High-frequency ultrasonic imaging system and method |
CN101912273A (zh) * | 2010-07-23 | 2010-12-15 | 深圳市理邦精密仪器股份有限公司 | 超声动态图像处理方法及系统 |
US10078893B2 (en) * | 2010-12-29 | 2018-09-18 | Dia Imaging Analysis Ltd | Automatic left ventricular function evaluation |
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Also Published As
Publication number | Publication date |
---|---|
CN101170948B (zh) | 2010-09-08 |
EP1882450A4 (en) | 2010-05-26 |
JP5138369B2 (ja) | 2013-02-06 |
EP1882450B1 (en) | 2013-01-02 |
JPWO2006123729A1 (ja) | 2008-12-25 |
EP1882450A1 (en) | 2008-01-30 |
US20090216124A1 (en) | 2009-08-27 |
CN101170948A (zh) | 2008-04-30 |
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