JP2007143606A - Ultrasonograph - Google Patents

Abstract

<P>PROBLEM TO BE SOLVED: To provide an art visually catching the movements of tissues over a plurality of time phases. <P>SOLUTION: Segments are dynamically set across a plurality of frames according to the movement of the cardiac muscle using a method of pattern matching. Each segment of a segment group 8 is a segment that is set along the thickness direction of the cardiac muscle 1 and connects a specific portion in the tunica intima to a specific portion in the tunica externa, and the movement of the segment expresses the motion of the cardiac muscle. A graph 16 of length changes indicates changes in the lengths of the segments dynamically set across a plurality of frames and comprises a vertical axis indicating the lengths of the segments of the respective frames to the segment of a criterion frame and a time axis (a lateral axis) indicating the time phases of the respective frames. A graph 18 of angle changes indicates the changes in angles of the segments dynamically set across the plurality of frames, and comprises a vertical axis indicating the angles of the segments of the respective frames to the segment of the criterion frame and a time axis (a lateral axis) indicating the time phases of the respective frames. <P>COPYRIGHT: (C)2007,JPO&INPIT

Description

  The present invention relates to an ultrasonic diagnostic apparatus, and more particularly to an ultrasonic diagnostic apparatus that forms a display image that reflects the movement of a tissue.

  By using an ultrasonic diagnostic apparatus, for example, the motion of a tissue such as the heart can be displayed as an ultrasonic image. It is also possible to measure the movement speed of the tissue from the Doppler information.

  Patent Document 1 describes a technique for obtaining velocity vectors in a plurality of sample volumes based on Doppler echoes, and further displaying an arrow corresponding to the velocity vector at the position of each sample volume on a tomographic image of the myocardium. (See Patent Document 1 FIG. 20).

  In Patent Document 2, the position coordinates and motion speed of each part are obtained from a time series image of the heart using pattern matching, and the motion speed is further classified into contraction / expansion direction components and other direction components. A technique for displaying the velocity vector of the contraction / expansion direction component on an image of the heart with an arrow is described (see Patent Document 2 FIG. 5).

  Incidentally, it is suggested in Patent Document 3 and Patent Document 4 that the velocity vector is displayed as an arrow on the ultrasonic image.

JP-A-6-114059 JP 2003-265480 A JP-A-8-299333 JP 2005-130877 A

  As described in the above patent documents, by displaying the velocity vector at each position in the tissue with an arrow on the ultrasound image, it is possible to visually capture the movement of the myocardium at each time phase. Become. However, it has been difficult to visually capture the motion of the tissue over a plurality of time phases, for example, the motion of one cardiac cycle of myocardial expansion and contraction.

  The present invention has been made in such a background, and an object of the present invention is to provide a technique for visually capturing the movement of a tissue over a plurality of time phases.

  In order to achieve the above object, an ultrasonic diagnostic apparatus according to a preferred aspect of the present invention includes a transmission / reception unit that transmits and receives an ultrasonic wave in a space including a target tissue to obtain an echo signal, and an echo signal obtained from the echo signal. Specific part tracking means for tracking each of the two specific parts of the target tissue moving with the movement of the target tissue over a plurality of frames in the data space composed of the data to be detected, and two specifics for each frame Evaluation image formation that forms an evaluation image of tissue motion that reflects the movement of a line segment that is set so as to connect regions and is dynamically set over a plurality of frames according to the movement of the target tissue And means.

  In the above-described configuration, an evaluation image of tissue motion reflecting the motion of line segments that are dynamically set over a plurality of frames is formed. As the evaluation image, for example, an angle change graph showing the angle change of the line segment dynamically set over a plurality of frames is formed. Preferably, the angle change graph includes an axis indicating the angle of the line segment of each frame with respect to the line segment of the reference frame and a time axis indicating the time phase of each frame. Further, as the evaluation image, for example, a line segment display image is formed in which a plurality of line segment images set over a plurality of frames are displayed superimposed on the image of the target tissue of a predetermined frame. With the above-described configuration, it is possible to visually capture the motion of a tissue over a plurality of time phases from an evaluation image such as an angle change graph or a line segment display image.

  In order to achieve the above object, an ultrasonic diagnostic apparatus according to a preferred aspect of the present invention includes a transmission / reception unit that transmits and receives ultrasonic waves in a space including the myocardium to obtain an echo signal, and an echo signal obtained from the echo signal. A specific part tracking means for tracking each of a specific part of the myocardium in the myocardium and a specific part of the adventitia that moves with the motion of the myocardium over a plurality of frames Evaluation of myocardial motion that reflects the movement of the line segment that is set to connect the specific part of the intima and the specific part of the adventitia and is dynamically set over multiple frames as the myocardium moves Evaluation image forming means for forming an image.

  In a desirable mode, the evaluation image forming means displays a plurality of line segment images set over a plurality of frames as the evaluation image so as to be superimposed on a tomographic image of a myocardium of a predetermined frame in a different display mode. A line segment display image is formed. Further, in a desirable mode, the evaluation image forming unit includes an angle change graph including an axis indicating an angle of a line segment of each frame with respect to a line segment of a reference frame and a time axis indicating a time phase of each frame as the evaluation image. And a marker is formed at a time phase where the angle of the line segment becomes a predetermined value on the angle change graph.

  The present invention makes it possible to visually capture the movement of a tissue over multiple time phases.

  DESCRIPTION OF EXEMPLARY EMBODIMENTS Hereinafter, preferred embodiments of the invention will be described with reference to the drawings.

  First, the principle of the tracking process executed in this embodiment will be described with reference to FIGS. This process is executed in the ultrasonic diagnostic apparatus, but may be executed in a computer that acquires data from the ultrasonic diagnostic apparatus.

  FIG. 1 shows an ultrasound image including a myocardium that is a target tissue. That is, the ultrasonic image shown in FIG. 1 is a B-mode image formed from echo signals obtained by transmitting and receiving ultrasonic waves in a space including the myocardium 1. In the present embodiment, a color Doppler image that expresses the velocity of the myocardium 1 or blood flow by color may be formed as the ultrasound image. That is, based on the Doppler information obtained from the echo signal, the color Doppler image that calculates the velocity for each position of the blood flow in the myocardium 1 and the heart chamber surrounded by the myocardium 1 and expresses the calculated velocity by color. May be formed.

  The myocardium 1 functions as a pump that circulates blood throughout the body by changing its thickness. For this reason, in the evaluation of the function of the heart, the evaluation of the movement of the myocardium 1 is one important evaluation factor. For example, when the myocardial infarction symptom progresses, the thickness change of the myocardium 1 is affected. In this embodiment, first, an inner end point 3 for designating a specific part of the intima and an outer end point 4 for designating a specific part of the outer membrane are set for the myocardium 1, and these two end points are set. A line segment 2 passing through is set. The end point 3 and the end point 4 are set at desired positions along the thickness direction of the myocardium 1 while the user views the ultrasonic image, for example.

  FIG. 2 is a diagram for explaining the movement of the myocardium 1, and is an enlarged view near the line segment 2 in FIG. As a result of changing the thickness of the myocardium 1, the intima surface (solid line) 10 and the outer membrane surface (solid line) from the contours shown by the intima surface (dashed line) 10 ′ and the outer membrane surface (dashed line) 11 ′ in FIG. 2. It changes to the contour shown by 11. At this time, the tissue sites at the positions of the end points 3 and 4 set for the myocardium 1 move to the positions of the moving point 6 and the moving point 7, respectively.

  The movement of the end points 3 and 4 can be confirmed from the B-mode image by a pattern matching method. That is, for example, the B-mode image of the frame in which the end point 3 and the end point 4 are set (previous frame) and the B-mode image of the frame in which the moving point 6 and the moving point 7 are detected (current frame) are compared. The moving point 6 is detected by extracting an image similar to the image in the vicinity of the current frame from the current frame, and the moving point 7 is detected by extracting an image similar to the image in the vicinity of the end point 4 from the current frame. Can do. Examples of the pattern matching technique include known techniques such as a template matching method and a PG matching method. Of course, in this embodiment, other pattern matching techniques may be used. As a result of the movement of the end points 3 and 4, the line segment 2 also moves to the line segment 5.

  In the present embodiment, the end point 3 and the end point 4 are tracked over a plurality of frames using a pattern matching technique, and a line segment is dynamically set according to the movement of the myocardium. Then, an evaluation image of tissue motion reflecting the movement of the line segment is formed. 3 to 8 show examples of evaluation images formed by the ultrasonic diagnostic apparatus according to this embodiment.

  FIG. 3 is a diagram showing a line segment display image that is an evaluation image of tissue motion. That is, it is an image in which the line segment group 8 dynamically set over a plurality of frames is superimposed and displayed on the ultrasonic image of the myocardium 1 of a predetermined frame. As shown in FIG. 3, a plurality of line segments (line segment group 8) dynamically set over a plurality of frames are collectively displayed on an ultrasonic image of a predetermined frame (for example, the latest frame). The movement of the line segment across the frame can be easily captured visually.

  Each line segment of the line segment group 8 is a line segment that connects a specific part of the intima and a specific part of the adventitia set along the thickness direction of the myocardium 1. That is, the movement of the line segment captures the movement of the myocardium 1 (particularly movement in the thickness direction). For this reason, the motion of the myocardium 1 over a plurality of frames can be visually captured from the line segment display image shown in FIG.

  A plurality of line segments included in the line segment group 8 may be displayed in different display modes depending on the time phase. For example, a line segment is displayed in a different color for each time phase. Moreover, you may display a line segment with a brightness | luminance different for every time phase. Further, the line segment group 8 may be composed of, for example, line segments within one heartbeat period. That is, using the timing of the R wave obtained from the electrocardiogram signal, the line segment group 8 within one heartbeat period is formed by superimposing the line segments obtained one after another from the line segments of the frame corresponding to the R wave. A display mode in which the line segment group 8 in the next one heartbeat period is reconfigured after the line segment group 8 is erased at the timing of the wave may be used.

  FIG. 4 is a diagram illustrating a length change graph which is an evaluation image of tissue motion. That is, the graph shown in FIG. 4 is a graph showing a change in the length of a line segment that is dynamically set over a plurality of frames, and a vertical length indicating the length of the line segment of each frame with respect to the line segment of the reference frame. It is comprised by the axis | shaft and the time axis (horizontal axis) which shows the time phase of each flame | frame. Each line segment is a line segment that connects a specific part of the intima and a specific part of the adventitia set along the thickness direction of the myocardium. Therefore, the change in the length of each line segment corresponds to the change in the thickness of the target portion of the myocardium. That is, from the graph of FIG. 4, it is possible to visually capture the change in the thickness of the myocardium over a plurality of frames (a plurality of time phases).

When evaluating the function of the heart, it is common to normalize the thickness of the myocardium (the length of the line segment) on the vertical axis with reference to the end diastole of the heart. Further, a strain ε (t) indicating a change in the thickness of the myocardium may be calculated. The strain is defined as ε (t) = (L (t) −L ₀ ) / L ₀ . Here, L (t) is the myocardial thickness (the length of the line segment) in the time phase of interest, and L ₀ is the myocardial thickness in a specific time phase for normalization (for example, end diastole). (Length of line segment).

  FIG. 5 is a diagram showing an angle change graph as an evaluation image of tissue motion. That is, the graph shown in FIG. 5 is a graph showing a change in the angle of a line segment dynamically set over a plurality of frames, and a vertical axis indicating the angle of the line segment of each frame with respect to the line segment of the reference frame; And a time axis (horizontal axis) indicating the time phase of each frame. Each line segment is a line segment that connects a specific part of the intima and a specific part of the adventitia set along the thickness direction of the myocardium. The change in the angle of each line segment is caused by a torsional motion or the like in the expansion / contraction motion of the myocardium. That is, from the graph of FIG. 4, the myocardial twisting state over a plurality of frames (a plurality of time phases) can be visually captured.

  FIG. 6 is a diagram for explaining the display mode of the line segment display image and the change graph. FIG. 6A shows a line segment display in which the line segment group 8 is displayed on the ultrasound image of the myocardium 1. An image is shown, and a length change graph 16 and an angle change graph 18 are shown in FIG. 6B. FIG. 6 is a configuration example of a display screen displayed on the monitor (display) of the ultrasonic diagnostic apparatus of the present embodiment, for example. As shown in FIG. 6, for example, a line segment display image is displayed on the left side of the screen. Then, a length change graph 16 and an angle change graph 18 are displayed on the right side of the screen.

  A marker 20 is formed on the length change graph 16 and the angle change graph 18. The marker 20 is attached to a time phase in which the length of the line segment is a predetermined value or a time phase in which the angle of the line segment is a predetermined value. For example, the marker 20 is formed at the time phase when the angle of the line segment is 0 (zero) on the angle change graph 18. Thus, the marker 20 indicates a specific time phase (specific frame) among a plurality of time phases. The marker 20 is not limited to the linear shape shown in FIG. For example, an arrow or the like may be provided on the time axis (horizontal axis) of the length change graph 16 or the angle change graph 18. Further, in the line segment group 8 of the line segment display image shown in FIG. 6A, emphasis processing such as a thick line may be performed on the time phase line segment corresponding to the marker 20. The marker 20 may be set to a predetermined time phase by the operator.

  In the description using FIGS. 1 to 6, only one line segment (reference numeral 2 in FIG. 1) is set for the myocardium (reference numeral 1 in FIG. 1). However, a plurality of line segments may be set for a plurality of regions of interest in the myocardium.

  FIG. 7 is a diagram illustrating an evaluation image when a plurality of line segments are set in a plurality of regions of interest. That is, the line segments 2a to 2d are set in a plurality of different regions of interest of the myocardium 1. Each of the line segments 2a to 2d is set by two end points as described with reference to FIG. A line segment group (reference numeral 8 in FIG. 3) is formed for each of the line segments 2a to 2d, and a length change graph (reference numeral 16 in FIG. 6) and an angle change graph (see FIG. 6) for each line segment 2a to 2d. 6) is formed.

  As shown in FIG. 7, it is desirable that the line segments 2a to 2d set in a plurality of different regions of interest are displayed in different display modes. That is, a display mode in which the line segments can be distinguished from each other by the color, thickness, line type, brightness, etc. of the line segments is desirable. Further, the display mode may be changed according to the time phase for each of the line segments 2a to 2d. Moreover, you may display only the line segment of a specific time phase for every line segment 2a-2d. For example, for each line segment 2a to 2d, only the line segment of the time phase where the length of the line segment is the maximum may be displayed, or only the line segment of the time phase where the angle of the line segment is zero is displayed. May be.

  FIG. 8 is a diagram illustrating a display example of an evaluation image when a plurality of line segments are set in a plurality of regions of interest. The display image 90 includes a line segment length or angle change graph group 92, a color Doppler image 100, and a B-mode image 102. For the convenience of illustration, the color Doppler image 100 does not express the color according to the speed, but actually, the color according to the speed is displayed on each part of the tomographic image of the myocardium as the target tissue. Applied.

  The change graph group 92 includes a change graph bar 80 for each of a plurality of line segments. Each change graph bar 80 corresponds to a change graph of the length of each line segment (reference numeral 16 in FIG. 6) or an angle change graph (reference numeral 18 in FIG. 6). 80 is described as corresponding to the change graph of the angle of each line segment. Each change graph bar 80 is a bar that is colored so that the angle of the line segment at each time can be identified by color and extends in the time axis direction. For the convenience of illustration, the color of each change graph bar 80 is omitted in FIG. 8, but in reality, the angle of the line segment at each time is represented by the color in each change graph bar 80. .

  The change graph group 92 is formed by arranging a plurality of change graph bars 80 so that the time phases are aligned. In FIG. 8, the time axis extends in the horizontal direction. Accordingly, by viewing the colors of the plurality of change graph bars 80 in the vertical direction at a predetermined position (time) on the horizontal axis, the angles of the plurality of line segments at the same time (same time phase) can be confirmed.

  The change graph bar 80 reflected in the change graph group 92 corresponds to a plurality of line segments. These multiple line segments are displayed on the color Doppler image 100 and the B-mode image 102. That is, for the myocardium 1 in the color Doppler image 100 and the B-mode image 102, a line segment 2 is set for each of a plurality of regions of interest. In FIG. 8, ten line segments 2 are set at ten regions of interest.

  In order to clearly show the correspondence between each line segment 2 and each change graph bar 80, a line segment number 94 is shown. This line segment number 94 is colored according to the corresponding line segment 2. That is, for example, different colors are applied to each of the ten line segments 2 on the B-mode image 102, and each line segment number 94 has a line segment 2 corresponding to that number. The same color is applied, and the correspondence between the line number 94 and the line segment 2 is indicated by the color. Further, each number of the line segment number 94 is arranged next to the corresponding change graph bar 80, whereby the correspondence between each change graph bar 80 and the line segment 2 becomes clear.

  Further, in the present embodiment, the feature value of the angle within a predetermined period may be extracted for each change graph bar 80, and the feature line 96 connecting the angle feature values in the plurality of change graph bars 80 may be displayed. The feature line 96 is, for example, a line that connects the maximum values of the angles of the change graph bars 80, or a line that connects 0 (zero) values of the angles of the change graph bars 80. Of course, a feature line 96 connecting the reference values set by the user may be formed.

  The change graph group 92 is formed by arranging a plurality of change graph bars 80 so that the time phases are aligned. If it is assumed that each part in the heart is performing a heartbeat motion uniformly, uniform motion is measured at a plurality of regions of interest where the line segment 2 is set. The waveform extends in a straight line in the direction. However, in practice, each part in the heart does not necessarily perform a completely uniform heartbeat motion, so that each feature line 96 deviates from a straight line and becomes a polygonal waveform. For this reason, the uniformity of the heartbeat motion can be evaluated based on the deviation of each feature line 96 formed in a polygonal line from the straight line. For example, the feature line 96 is very effective in diagnosing a medical condition such as asynchrony in which the heart contraction is not uniform.

  Next, the apparatus configuration of the ultrasonic diagnostic apparatus of this embodiment will be described.

  FIG. 9 is a functional block diagram of the ultrasonic diagnostic apparatus of the present embodiment. The probe 50 is a transducer that transmits and receives ultrasonic waves. In the present embodiment, an array transducer composed of a plurality of transducer elements is provided in the probe 50, and an ultrasonic beam is formed by the array transducer. In this embodiment, the ultrasonic beam is electronically scanned by an electronic sector scanning method, and a fan-shaped scanning surface is constructed. Incidentally, it is possible to apply a control for simultaneously forming a plurality of reception beams per transmission beam, and the probe 50 may be a so-called 3D probe. For example, when performing an ultrasonic diagnosis of the heart, the position and posture of the probe 50 abutted on the chest surface of the living body are appropriately adjusted. In that case, for example, a B-mode image displayed on the display is observed. In order to execute the tissue Doppler imaging method (TDI method), transmission and reception of ultrasonic waves may be executed a plurality of times for each beam address.

  The transmission / reception unit 52 is configured as a digital beam former. That is, the transmission / reception unit 52 has a transmission beam former and a reception beam former. A plurality of transmission signals are supplied to the array transducer by the transmission beam former, thereby forming a transmission beam. On the other hand, a plurality of reception signals output from the array transducer are subjected to phasing addition processing in the reception beamformer, whereby a reception signal after phasing addition is obtained. That is, a reception signal corresponding to the reception beam is obtained. The reception signal output from the transmission / reception unit 52 is output to the tissue echo processing unit 56 and the tissue velocity processing unit 58.

  The tissue echo processing unit 56 executes various signal processes for forming a tissue echo image. The process includes, for example, a logarithmic conversion process. The scan conversion unit 64 performs coordinate conversion processing, interpolation processing, and the like. That is, the scan conversion unit 64 has a so-called DSC (digital scan converter) function. Through processing by the tissue echo processing unit 56 and the scan conversion unit 64, the data of each frame is output, and the 2D echo image processing unit 68 forms image data of a two-dimensional B-mode image.

  A cine memory 60 is provided at the subsequent stage of the tissue echo processing unit 56, and data of each frame before coordinate conversion is stored in the cine memory 60 in chronological order. A memory for storing the data of each frame after coordinate conversion processed in the scan conversion unit 64 may be provided.

  The tissue velocity processing unit 58 functions as a Doppler processing unit, and performs complex signal conversion processing, autocorrelation calculation processing, and the like on the reception signal output from the transmission / reception unit 52, thereby obtaining tissue velocity information. Arithmetic. The scan conversion unit 62 performs coordinate conversion processing, interpolation processing, and the like, and the 2D velocity image processing unit 70 further applies a color image (color color) for each tissue site to which the positive or negative velocity and a color corresponding to the value are applied. Doppler image) image data is formed. Note that a cine memory 60 is provided at the subsequent stage of the tissue velocity processing unit 58, and data of each frame output from the tissue velocity processing unit 58 is stored in chronological order.

  In the present embodiment, the cine memory 60 stores the tissue echo data processed by the tissue echo processing unit 56 and the tissue velocity data processed by the tissue velocity processing unit 58. In these two types of data, a plurality of data in time series order within a certain time range are stored in association with each other. The cine memory 60 has a ring buffer structure, and has a function of storing a frame sequence over a time range from the latest frame to a frame of a past fixed time. By using the cine memory 60, it is possible to read out the frame sequence stored in the cine memory 60 later for loop reproduction.

  By storing the data temporarily stored in the cine memory 60 in the external recording medium 54, it is possible to store frame data for a long time exceeding the capacity of the cine memory 60. In the present embodiment, for example, various processes are performed on a plurality of frame data in time series within a certain time range stored in the cine memory 60 or the external recording medium 54.

  The end point tracking unit 66 is based on the tissue echo data (data for the B-mode image) of each frame output through the processing by the tissue echo processing unit 56 and the scan conversion unit 64, and the end point inside and outside the myocardium. To track. That is, as described with reference to FIGS. 1 and 2, the end point tracking unit 66 uses a pattern matching technique to divide the inner end point and the outer end point that move with the movement of the myocardium into a plurality of frames. Track over. In addition, the end point tracking unit 66 also applies the tissue velocity data (color Doppler image data) of each frame output through the processing by the tissue velocity processing unit 58 and the scan conversion unit 62 to the case of the B mode image. Similarly, the inner end point and the outer end point of the myocardium are tracked.

  The evaluation image forming unit 72 forms an evaluation image of myocardial motion based on line segments obtained from two end points tracked over a plurality of frames. That is, the evaluation image forming unit 72 forms a line segment display image (see FIG. 3), a length change graph (see FIG. 4), and an angle change graph (see FIG. 5). In addition, the evaluation image forming unit 72 displays the line segment display image and the change graph simultaneously (see FIG. 6), and the evaluation image when a plurality of line segments are set in a plurality of regions of interest (see FIG. 8). Form.

The strain calculation unit 74 calculates a strain ε (t) indicating a change in the thickness of the myocardium from the length of the line segment obtained in the evaluation image forming unit 72, that is, the thickness of the myocardium. As described above, the strain is defined by ε (t) = (L (t) −L ₀ ) / L ₀ .

  The composition processing unit 76 is a module that composes a plurality of image data selected in accordance with the display mode from a plurality of input image data to form one display image. The image data output from the synthesis processing unit 76 is output to the display 78, and the evaluation image shown in FIGS. 6 and 8 is displayed on the display 78, for example. The display device 78 may be configured by, for example, a CRT or a liquid crystal display. Alternatively, two displays of a CRT and a liquid crystal display may be connected to the subsequent stage of the composition processing unit 76, and one of them may be a main display and the other may be a sub display.

  The control unit 82 performs operation control of each component included in the ultrasonic diagnostic apparatus. The control unit 82 includes a CPU and an operation program. Although the display processing unit indicated by reference numeral 200 in FIG. 9 is illustrated as a module different from the control unit 82 in the present embodiment, the display processing unit 200 may be configured by a CPU and a processing program. Alternatively, the display processing unit 200 may be configured by dedicated hardware. Alternatively, only some of the functions of the display processing unit 200 may be realized by software processing, and the rest may be realized by hardware.

  The control unit 82 controls the operation of the cine memory 60 in the present embodiment. The cine memory 60 is constituted by a semiconductor memory or the like, in which a frame sequence is stored. Under the control of the control unit 82, loop reproduction or the like is performed on the frame sequence stored in them. For example, when a loop playback instruction is issued to the cine memory 60, the time-series frame sequence stored in the cine memory 60 is sequentially called and displayed as a moving image on the display 78. Note that the image forming process in the present embodiment can also be performed in real time. Further, the image data after freezing or the image data stored in the apparatus or on the external recording medium 54 may be processed.

  The input unit 84 is configured by an operation panel or the like, and by using the input unit 84, the user can set end points, specify a time phase, select a display mode, and the like. In addition to being output to the control unit 82, the electrocardiographic signal output from the electrocardiograph 86 is output to the synthesis processing unit 76. The electrocardiogram signal is used as a synchronization signal in the loop reproduction described above, and an electrocardiogram waveform may be displayed on the display 78.

  As mentioned above, although preferred embodiment of this invention was described, embodiment mentioned above is only a mere illustration in all the points, and does not limit the scope of the present invention.

It is a figure which shows the ultrasonic image containing the myocardium which is an object structure | tissue. It is a figure for demonstrating the change of the thickness of a myocardium. It is a figure which shows a line segment display image. It is a figure which shows the change graph of length. It is a figure which shows the change graph of an angle. It is a figure for demonstrating the display mode of a line segment display image and a change graph. It is a figure which shows the evaluation image when a some line segment is set to the some site | part of interest. It is a figure which shows the example of a display of the evaluation image when a several line segment is set to the some region of interest. It is a functional block diagram of the ultrasonic diagnostic apparatus of this embodiment.

Explanation of symbols

  1 myocardium, two line segments, 3, 4 endpoints, 66 endpoint tracking unit, 72 evaluation image forming unit.

Claims (7)

A wave transmitting / receiving means for transmitting and receiving an ultrasonic wave in a space including the target tissue to obtain an echo signal;
In a data space composed of data obtained from echo signals, a specific part tracking means for tracking each of two specific parts of the target tissue that moves with the movement of the target tissue over a plurality of frames,
Tissue motion evaluation that reflects the movement of a line segment that is set to connect two specific parts for each frame and that is dynamically set over multiple frames as the target tissue moves Evaluation image forming means for forming an image;
Having
An ultrasonic diagnostic apparatus. The ultrasonic diagnostic apparatus according to claim 1,
The evaluation image forming unit forms an angle change graph showing an angle change of a line segment dynamically set over a plurality of frames as the evaluation image.
An ultrasonic diagnostic apparatus. The ultrasonic diagnostic apparatus according to claim 2,
The angle change graph includes an axis indicating an angle of a line segment of each frame with respect to a line segment of a reference frame and a time axis indicating a time phase of each frame.
An ultrasonic diagnostic apparatus. The ultrasonic diagnostic apparatus according to claim 1,
The evaluation image forming means forms, as the evaluation image, a line segment display image in which a plurality of line segment images set over a plurality of frames are displayed superimposed on an image of a target tissue of a predetermined frame.
An ultrasonic diagnostic apparatus. Wave transmitting / receiving means for transmitting and receiving ultrasonic waves in a space including the myocardium to obtain an echo signal;
A specific part tracking means for tracking each of an intima specific part and an outer membrane specific part of the myocardium moving with the movement of the myocardium over a plurality of frames in a data space composed of data obtained from echo signals;
It is set to connect the intima specific part and the epicardial specific part for each frame, and the movement of the line segment is reflected in the line segment that is dynamically set over a plurality of frames according to the movement of the myocardium. Evaluation image forming means for forming an evaluation image of myocardial motion;
Having
An ultrasonic diagnostic apparatus. The ultrasonic diagnostic apparatus according to claim 5,
The evaluation image forming means displays, as the evaluation image, a line segment display image in which a plurality of line segment images set over a plurality of frames are displayed on a tomographic image of a myocardium of a predetermined frame in a different display mode. Forming,
An ultrasonic diagnostic apparatus. The ultrasonic diagnostic apparatus according to claim 5,
The evaluation image forming unit forms, as the evaluation image, an angle change graph including an axis indicating an angle of each line segment with respect to a line segment of a reference frame and a time axis indicating a time phase of each frame, and changes the angle. A marker is formed at a time phase where the angle of the line segment is a predetermined value on the graph
An ultrasonic diagnostic apparatus.

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