JP4652780B2 - Ultrasonic diagnostic equipment - Google Patents

Description

  The present invention relates to an ultrasonic diagnostic apparatus, and more particularly to a technique for evaluating the function of the heart.

  Conventionally, when cardiac function (especially left ventricular function) is evaluated using an ultrasonic diagnostic apparatus, a tomographic image of the heart is formed, and the contour of the heart cavity or heart wall is extracted on the tomographic image, and the contour is extracted. Or the difference between the end-diastolic contour and the end-systolic contour is detected and evaluated. However, in this method, since the cardiac function is evaluated only on a specific cut surface, it is difficult to recognize even if a disease (such as a myocardial infarction) occurs at a site that is not on the cut surface. Patent Document 1 listed below discloses a configuration for displaying a three-dimensional form image (wire frame model). Patent Document 2 below discloses a configuration in which coronary blood flow or perfusion information of the heart is displayed in a three-dimensional manner while being distinguished from intracardiac blood flow.

JP 2000-139917 A JP 2000-210289 A

  An object of the present invention is to provide an ultrasonic diagnostic apparatus capable of evaluating cardiac function on various cross sections in a three-dimensional space.

  Another object of the present invention is to provide an ultrasonic diagnostic apparatus that can easily evaluate cardiac function on a plurality of cross sections set over the entire three-dimensional space.

  Another object of the present invention is to provide an ultrasonic diagnostic apparatus capable of forming an image that can easily recognize a motion abnormality site in a three-dimensional space.

(1) The present invention provides a transmitting / receiving unit that transmits / receives ultrasonic waves to / from a three-dimensional space including a moving tissue, a slice plane setting unit that sets a plurality of slice planes in the three-dimensional space, and the super A motion evaluation chart having first and second polygonal graphs simulating contours of motion tissue in the first and second time phases for each slice plane based on data obtained by transmitting and receiving sound waves And a chart generating means for generating.

  According to the above configuration, a plurality of slice planes (cut planes) are set for the three-dimensional space (or volume data). It is desirable that the plurality of cut surfaces be set to be uniformly distributed throughout the three-dimensional space, but may be set to be non-uniformly distributed or set at a high density with respect to a part of the three-dimensional space. May be. The position and number of slice planes are set automatically or by the user. Desirably, a common reference line is set on the center line for motion evaluation of the heart (particularly the left ventricle), and a plurality of slice planes that intersect radially with the common reference line are set. The volume data is acquired by scanning the entire three-dimensional space with an ultrasonic beam, and slice data corresponding to each slice plane is extracted from the volume data, and scanning that matches each slice plane is possible. The ultrasonic beam may be scanned only on the surface.

  For each slice plane, a motion evaluation chart is created based on data (slice plane data) corresponding to the slice plane. The motion evaluation chart includes at least one polygonal graph. In the above configuration, at least the first polygonal graph and the second polygonal graph are included. Three or more polygonal graphs corresponding to three or more time phases may be included, and when a polygonal graph can be formed in real time, it may be displayed as a moving image. Each polygonal graph is a graph simulating a contour of a moving tissue (for example, a heart chamber contour) as a polygon. Particularly preferably, a polygonal graph is created at the end diastole and the end systole, and these are superposed to create a motion evaluation chart. According to such a motion evaluation chart, an abnormal movement portion (a portion where movement is slow, a portion moving in the opposite direction, etc.) is easy due to the difference in form between the first polygon graph and the second polygon graph. Can be specified. In addition, quantitative evaluation becomes easy. If a plurality of exercise evaluation charts corresponding to a plurality of slice planes are displayed side by side, it is possible to easily grasp spatially by which the disease is present in which part. These exercise evaluation charts can be sequentially switched and displayed as a slide show.

  In the above configuration, the first polygonal graph is formed based on the first time phase data, and the second polygonal graph is formed based on the second time phase data. If the coordinate systems of two polygonal graphs are made to coincide with each other, the area between the two graphs represents the tissue momentum. Abnormalities in tissue motion may be automatically determined based on a tissue motion evaluation chart having two polygonal graphs, or the chart may be displayed for diagnosis by user observation. When simultaneously displaying a plurality of tissue motion evaluation charts, it is desirable to display information indicating the spatial positional relationship between them together.

  In any case, according to the above configuration, the shape of the moving tissue and the state of the change can be evaluated as a schematic figure on a plurality of cut surfaces in the three-dimensional space, so that the movement abnormality can be identified quickly and easily. it can.

(2) In the above configuration, preferably, the slice plane setting means sets a plurality of slice planes that intersect each other on a common reference axis. According to this configuration, since a common coordinate axis exists on each slice plane, the positional relationship between the slice planes can be easily recognized. The common reference axis is preferably coincident with the beam direction, but may not be coincident.

  Preferably, the graph origin set on each slice plane is a common reference point on the common reference axis. According to this configuration, since there is a common origin on each slice plane, it is easy to recognize the relationship between each slice plane (or a polygonal graph on each slice plane).

  Desirably, a region of interest setting means for setting a three-dimensional region of interest in the three-dimensional space, and generating the first and second polygon graphs for each slice plane in the region of interest. Is executed. By setting the region of interest, unnecessary processing can be reduced by limiting the processing range, and erroneous calculation can be prevented to improve calculation accuracy.

  Preferably, the region-of-interest setting means includes: means for forming a plurality of two-dimensional images reflecting the three-dimensional space; and means for defining positions and shapes of the regions of interest on the plurality of two-dimensional images. Including. According to this configuration, it is possible to easily set a three-dimensional region of interest in relation to a focused moving tissue. The two-dimensional image is preferably a projection image, but may be another image. It is desirable that the plurality of two-dimensional images have a spatial relationship (particularly preferably orthogonal) with each other. The three-dimensional space has a predetermined shape such as a cubic shape or a pyramid shape, which depends on the scanning method of the ultrasonic beam.

  Preferably, the region of interest is a cylindrical region having a common reference axis as a central axis, and the plurality of slice planes intersect each other on the common reference axis. If a plurality of slice planes are set around the common reference axis in the cylindrical shape, the shape of each slice plane becomes a rectangle having the same size. When a spherical region of interest is set, the shape of each slice surface is a circle having the same size. The three-dimensional region of interest desirably has a shape obtained by rotating a slice plane having a specific shape with the center line (common reference axis) as a rotation axis. Note that it is desirable that the region of interest is set as necessary, and the position and size thereof can be varied.

  Preferably, the motor tissue is a heart, the first time phase corresponds to end diastole, and the second time phase corresponds to end systole. Desirably, the heart, particularly the left ventricle, is to be evaluated. It is desirable that a common reference axis is set on the center line of the left ventricle and a common reference point is set at the center of the left ventricle.

  Preferably, it includes means for displaying a multi-chart image having the plurality of motion evaluation charts corresponding to the plurality of slice planes. According to this configuration, it is possible to easily recognize the presence / absence, degree, spread degree, etc. of movement abnormality by performing comparative observation of each chart. In particular, since the tissue outline is expressed as a simple figure, it is easy to evaluate.

(3) In the above configuration, preferably, the chart generation unit includes a reference line setting unit that sets a plurality of reference lines radially from a reference point on each slice plane, and each of the slice planes Intersection detection means for detecting an intersection of a reference line and the contour of the moving tissue, and a polygonal graph generation means for generating a polygonal graph by connecting adjacent intersections with connecting lines on each slice plane; It is characterized by having.

  According to the above configuration, when creating a polygonal graph, a plurality of reference lines (corresponding to edge search lines) are set radially from a predetermined reference point on the slice plane. They are preferably set with a uniform angular pitch, but non-uniform pitches can also be set. Those numbers can be set arbitrarily. As in the case of the slice plane, if the number of reference lines is small, the amount of calculation can be reduced, and if the number is large, a finer evaluation can be performed. Preferably, prior to edge detection, edge extraction processing such as binarization (or inversion binarization) is performed on slice data for tissue discrimination (preferably heart wall heart chamber discrimination). Pixel data (echo data) on each reference line is referred to, and an edge is detected by threshold determination or the like. That point is the intersection. Various known methods can be applied to detect the tissue contour point. When an intersection point is obtained on each reference line, two intersection points specified on two adjacent reference lines are connected to each other. Thereby, a polygonal graph simulating the tissue contour is constructed. In order to recognize the entire tissue contour, many calculations are required. According to the above configuration, a polygonal graph corresponding to the tissue contour can be easily obtained.

  Preferably, a plurality of evaluation areas are defined by the plurality of reference lines for each slice plane, and the first polygonal graph is configured as an aggregate of a plurality of first triangular graph elements belonging to the plurality of evaluation areas. The second polygon is configured as an aggregate of a plurality of second triangular graph elements belonging to the plurality of evaluation areas, and the area of the first triangular graph element and the second triangular graph for each of the evaluation areas. Motion evaluation value calculation means for calculating a motion evaluation value based on the area of the element is provided.

  According to the above configuration, the motion evaluation value can be calculated from the area of the first triangular graph element and the area of the second triangular graph element for each reference area. In that case, it is desirable to standardize so that the motion evaluation values can be compared for each evaluation area. Preferably, the motion evaluation value is an area change rate. Note that the rate of change in length from the common reference point to the intersection can be used as the evaluation value.

  Preferably, the motion evaluation value calculating means calculates, for each evaluation area, a horizontal coordinate of one intersection and a vertical coordinate of the other intersection among two intersections on two reference lines defining the evaluation area. Use to compute the area of the triangular graph element. According to this configuration, the area of the triangular graph element can be easily calculated using the formula for obtaining the area of the triangle.

  Desirably, a determination means for determining a movement abnormality based on a movement evaluation value for each reference area on each slice plane is included. According to this configuration, since the motion of each part is quantified as the motion evaluation value, it is possible to automatically determine the motion abnormality of each part.

  Preferably, means for forming a multi-chart image having the plurality of motion evaluation charts corresponding to the plurality of slice planes, and a specific slice plane and a specific evaluation area where the motion abnormality is recognized with respect to the multi-chart image And means for performing processing for identifying at least one of the above. According to this configuration, it is possible to easily identify the location where the motion abnormality has occurred on the multi-chart image. Only the specific slice plane may be identified and displayed, and the user may determine the abnormal movement location, or the specific evaluation area may be identified and displayed so that the abnormal movement location can be recognized instantaneously. If there are a plurality of abnormal movement locations, identification display processing is performed accordingly. In that case, the degree of abnormality may be expressed by a hue change or the like.

  Desirably, a means for forming a tomographic image corresponding to a specific slice plane in which the movement abnormality is recognized, and a process for identifying the specific evaluation area in which the movement abnormality is recognized are applied to the tomographic image. Means for displaying a tomographic image. According to this configuration, it is possible to recognize an abnormal movement location on a tomographic image. The tomographic image is preferably a still image, but may be a real-time tomographic image.

  Desirably, a composite image in which a two-dimensional image representing a cross-sectional structure corresponding to a specific slice plane in which the movement abnormality is recognized and a three-dimensional image representing a tissue form on the back side of the specific slice plane is synthesized. Means for forming, and means for displaying the identification processed composite image by performing processing for identifying the specific evaluation area in which the movement abnormality is recognized on the composite image. According to this configuration, for example, not only the heart wall cross-sectional structure but also the three-dimensional shape of the inner surface of the heart wall can be imaged simultaneously, and the abnormal movement location can be identified and displayed on the image.

(4) In the present invention, a transmitting / receiving unit for transmitting / receiving ultrasonic waves to / from a three-dimensional space including a moving tissue and a plurality of slice planes intersecting the common reference axis with respect to the three-dimensional space are distributed. A motion evaluation chart having a polygonal graph simulating the contour of the motion tissue for each slice surface based on the slice surface setting means to be automatically set and the data obtained by transmitting and receiving the ultrasonic wave It includes: a chart generating means; a means for forming a multi-chart image in which a plurality of motion evaluation charts corresponding to the plurality of slice planes are arranged; and a means for displaying the multi-chart image.

  According to the above configuration, since a plurality of motion evaluation charts corresponding to a plurality of slice planes crossing each other can be displayed over the entire three-dimensional space, the motion tissue can be displayed over the entire three-dimensional space based on their mutual comparison. Can easily grasp the state of exercise.

  Preferably, for each partial evaluation area in each slice plane, means for determining the presence / absence of movement abnormality based on the contents of the tissue movement evaluation chart, and the movement among the plurality of movement evaluation charts And a means for identifying and displaying a specific exercise evaluation chart in which an abnormality is recognized.

  As described above, according to the present invention, cardiac function can be evaluated on various cross sections in a three-dimensional space. In particular, the evaluation can be performed easily. According to the present invention, it is possible to form an image capable of easily recognizing a motion abnormality site in a three-dimensional space.

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

  The contents of image processing in the ultrasonic diagnostic apparatus according to the embodiment will be described below with reference to FIGS.

  FIG. 1 shows a relationship between a three-dimensional space (3D space) 10 and a three-dimensional ROI (region of interest) 12. The 3D space 10 is formed by two-dimensional scanning with an ultrasonic beam and corresponds to a volume data space. For example, the scanning surface is formed by electronic scanning of the ultrasonic beam in one direction, and the 3D space 10 is configured by electronic scanning of the scanning surface in the other direction. In FIG. 1, the X direction is, for example, the electronic scanning direction of the ultrasonic beam, the Z direction is the ultrasonic beam direction, that is, the depth direction, and the Y direction is the scanning direction of the scanning surface. Electronic linear scanning, electronic sector scanning, and the like can be given as the ultrasonic beam electronic scanning method. The ultrasonic beam or the scanning surface may be mechanically scanned.

  As is clear from the above description, the 3D space 10 has a form corresponding to the scanning method of the ultrasonic beam. In FIG. 1, the cubic 3D space 10 is shown. As the tenth form, other forms such as a pyramid shape can be given. In the present embodiment, ultrasonic transmission / reception is performed on the entire 3D space 10, and volume data is acquired thereby. However, ultrasonic transmission / reception is performed only on a plurality of slice planes described later. It is also possible to do this.

  As shown in FIG. 1, a three-dimensional ROI 12 is set automatically or by the user for the 3D space 10. This ROI 12 limits the range of image processing, and setting such ROI 12 has the advantage that unnecessary calculations can be omitted and calculation accuracy can be improved. As shown in FIG. 1, the ROI 12 has a cylindrical shape in the illustrated example, that is, formed when the rectangular surface is rotated 180 degrees around the common reference axis that is the central axis thereof. It has a form. Of course, as the form of the ROI 12, in addition to the cylindrical shape, a spherical form or other forms can be given. As will be described later, when displaying a plurality of motion evaluation charts, it is desirable to employ the cylindrical ROI 12 as described above in order to match the size and shape of each chart. A plurality of slice planes to be described later may be defined without setting such ROI 12. The direction and position of the common reference axis, which is the central axis in the ROI 12, are preferably set by the user as appropriate, but the common reference axis may coincide with the beam direction.

  FIG. 2 shows an example of a method for setting the ROI 12. A first image 16 and a second image 18 are displayed on the display screen 14. In the example illustrated in FIG. 2, the first image 16 is a projection image configured by projecting the 3D space 10 illustrated in FIG. 1 from above, and the second image 18 is the front or the 3D space 10 illustrated in FIG. 1. It is a projection image comprised by projecting from a horizontal direction. In forming a projection image, a maximum value method, an integration method, and other rendering methods can be used. A wire frame model 20 is further displayed on the display screen 14, and the wire frame model 20 is set in a cube-shaped frame image 30 composed of a plurality of straight lines that schematically represent a 3D space and the inside thereof. And an ROI image 32 representing the outer shape of the ROI to be performed. With this wire frame model 20, the positional relationship between the ROI and the 3D space that the user is trying to set can be easily recognized.

  When a cylindrical ROI is set, a circular cursor 24 is displayed on the first image 16 and its position and size are set as appropriate by the user. In this case, the circular cursor 24 is set so that the entire target organ 22 or the portion of interest is surrounded. In addition, on the second image 18, two line-shaped cursors 26 and 28 arranged in the vertical direction are set to arbitrary heights, and more specifically, each of the target tissues 22 is included between them. Cursors 26 and 28 are set. Incidentally, lines A and B representing the side position of the ROI are displayed on the second image 18, and a common axis Q representing the central axis of the ROI is represented. On the other hand, the common reference axis is represented as a point Q on the first image 16.

  As described above, it is possible to arbitrarily set the position and shape of the ROI by appropriately setting the respective cursors on the first image 16 and the second image 18, and the setting results are sequentially displayed in the wire frame. It is reflected in the model 20 and the setting content can be spatially confirmed by referring to it. In the above example, the region of interest is artificially set, but the process can be automated.

  FIG. 3 shows a plurality of slice planes (cut planes) set for the three-dimensional space. In the present embodiment, the ROI is set as described above, and the graph creation processing described later is applied within the range, and therefore, in FIG. 3, a plurality of slice planes are schematically represented in relation to the ROI. Has been. In the example shown in FIG. 3, eight slice planes # 1 to # 8 are set for the ROI. These slice planes intersect each other along a common reference axis Q, and are set in a radial distribution. In the example shown in FIG. 3, the pitch between adjacent slice planes is uniform in the θ direction, but it is also possible to set it non-uniformly, that is, increase the density of slice planes for the region of interest, etc. Is also possible. The number of slice planes to be set is set by the user or automatically, and the number is arbitrary. For example, the number in the range of 4 to 16 is set. In any case, by setting a plurality of slice planes in a distributed manner over the entire ROI, it becomes possible to evaluate the movement abnormality over the entire three-dimensional area. In the example shown in FIG. 3, the center lines in each slice plane coincide with each other as the common reference axis Q, and later-described reference points on each slice plane also coincide with each other. When a plurality of motion evaluation charts are formed, the coordinate relationship between them can be easily recognized.

  In this embodiment, as shown in FIGS. 1 and 2, when the ROI 12 is set by the user or automatically, as shown in FIG. 3, the ROI 12 is automatically set based on the common reference axis Q existing there. A plurality of slice planes are set in. The common reference axis Q can be set automatically or with an arbitrary inclination and position by the user. In this case, if the common reference axis is coincident with any one of the beam orientations, each slice plane is scanned with the beam. In such a case, only a plurality of scanning planes corresponding to a plurality of slice planes can be formed to eliminate useless ultrasonic wave transmission / reception. Further, the above embodiment has an advantage that the dead zone can be prevented from increasing because the slice planes are provided at regular intervals throughout the three-dimensional space.

  Next, a motion evaluation chart creation process executed for each slice plane will be described with reference to FIG.

  FIG. 4 shows a slice plane. In this embodiment, the target tissue is the left ventricle, and the contour of the heart chamber in the left ventricle is extracted by the edge detection method. Reference numeral 34 represents the contour at the end systole, and reference numeral 35 represents the contour at the end diastole. Specifically, a binarized image is obtained by applying reverse binarization processing or the like to the tomographic image corresponding to the slice plane at the end systole, and the contour 34 is specified by the binarized image. Similarly, a binarized image is obtained by applying reverse binarization processing or the like to the tomographic image at the end diastole, and the contour 35 is specified by the binarized image. Then, the polygon graph creation processing described below is sequentially applied to each contour.

  The origin O is a common reference point, and the common reference point O corresponds to the center point on the common reference axis described above. A plurality of reference lines L1 to L8 are set radially from the common reference point O. Each reference line L1 to L8 functions as an edge search line, and in the example shown in FIG. 4, the pitch between the reference lines is uniform, but the pitch may be set non-uniformly. The number of reference lines can be set automatically or arbitrarily by the user. For example, the number from 4 to 16 is selected. In the example shown in FIG. 4, eight reference lines L1 to L8 are set at 45 degree intervals. The inclination angle of each reference line is represented by φ in the figure. Evaluation areas E1 to E8 are defined by a plurality of reference lines L1 to L8.

  In creating a polygonal graph, first, edge detection is sequentially performed along each reference line from the common reference point O, and when an edge is detected, it is set as an intersection. In the example shown in FIG. 4, the intersection point with the end-systolic contour 34 on the reference line L1 is represented by P1, and similarly, the intersection point with the end-systolic contour on the reference line L2 is represented by P2. Incidentally, in relation to the contour 35 at the end diastole, the intersection point P3 is detected on the reference line L1, and the intersection point P4 is detected on the reference line L2.

  As described above, when an intersection point is obtained on each reference line, a polygonal graph is constructed by connecting two intersection points between adjacent reference lines with a connecting line. Specifically, in the example shown in FIG. 4, the intersection point P1 on the reference line L1 and the intersection point P2 on the reference line L2 are connected by the connection line r1. Thereby, a triangular graph element is defined as a triangle connecting the common reference point O-intersection point P1-intersection point P2, and its area is S1. When the connection between adjacent intersections is executed for each evaluation area, a polygonal graph R1 simulating the end-systolic contour 34 is constructed. This polygonal graph R1 can be regarded as a polygon inscribed in the contour 34, and the shape thereof represents the shape of the contour 34 at the end systole. Even at the end of diastole, intersection points on each reference line are connected by a connecting line, thereby forming a polygonal graph R2. Specifically, an intersection point P3 on the reference line L1 and an intersection point P4 on the reference line L2 are connected by a connection line r2, and a triangular graph element is formed as a triangle connecting three points of the common reference point O-intersection point P3-intersection point P4. Defined. Its area is S2. Like the polygon graph R1, the polygon graph R2 can be regarded as a polygon inscribed in the contour 35 at the end diastole, and a complex shape can be simulated with a simple polygon and evaluated. Is possible. Usually, the polygon corresponding to the end diastole is created before the polygon corresponding to the end systole, but it may be reversed.

  According to the above method, it is not necessary to recognize the form of each contour itself, and the area calculation in each evaluation area is easy. Therefore, there is an advantage that the calculation amount can be extremely reduced, and the calculation can be speeded up. There is an advantage. As a modification of the method shown in FIG. 4, a process of connecting adjacent intersections with a curve or the like can be given. In this case, it is desirable to apply a spline interpolation method or the like.

  FIG. 5 shows a simple calculation method of the area of the triangular graph element. In FIG. 5, the evaluation area E1 and the evaluation area E2 opened at 45 degrees are shown as enlarged views, and FIG. 5 represents only a part of the polygonal graph R1 corresponding to the end systole. That is, the polygonal graph R2 is not shown.

  Each intersection is defined by a coordinate on the x-axis as the horizontal coordinate defined in FIG. 4 and a coordinate on the y-axis as the vertical coordinate. Here, as is well known, the area of the triangle is obtained by (d × h) / 2 when the base is d and the height is h, and on the assumption that, for example, the area S1 is obtained, The vertical coordinate d1 of the intersection point P1 and the horizontal coordinate h1 of the intersection point P2 are referred to, and by substituting them into the above formula, the area S1 of the triangular element can be easily obtained. The same applies to the evaluation area E2, and the area of the triangular element can be easily calculated using the vertical coordinate h2 of the intersection P2 and the horizontal coordinate d2 of the intersection P5.

  That is, in the present embodiment, since a plurality of reference lines are set at intervals of 45 degrees on the slice plane, lines corresponding to the vertical axis or the horizontal axis appear every other reference line. Since such a reference line constitutes the base of the calculation of the triangular area, the area of the triangular element can be calculated simply by using one of the coordinate elements at each intersection.

  However, it is also possible to store the relationship between the intersection coordinates and the area of the triangle on a table or the like, and to obtain the area instantaneously when the coordinates of each intersection are specified. It is not limited to what is shown.

  As described above, in this embodiment, a polygonal graph corresponding to the end diastole and a polygonal graph corresponding to the end systole are configured for each slice plane. Therefore, a chart for evaluating tissue motion is constructed by superimposing these polygonal graphs while making their coordinate systems coincide with each other. FIG. 6 shows a multi-chart image. In this embodiment, the multi-chart image includes eight tissue motion evaluation charts 36A to 36H corresponding to eight slice planes. Each chart includes a polygonal graph at the end systole and a polygonal graph at the end diastole. Each chart includes an identification symbol for the slice plane and represents the rotation angle of the slice plane. Information on coordinate axes in the three-dimensional space is included as necessary. In addition to the multi-chart image shown in FIG. 6, for example, a graphic showing the correlation between a plurality of slice planes as shown in FIG. 3 can be displayed together as, for example, a wire frame model. Such display of the reference image has an advantage that the positional relationship between the slice planes can be intuitively recognized. If a multi-chart image as shown in FIG. 6 is provided to the user, for example, the state of exercise in each part of the left ventricle can be easily grasped, and the diseased part and its spread can be easily identified by comparing the contents between charts. Is possible.

  In this embodiment, the area change rate is calculated from the area S1 of the triangular graph element at the end systole and the graph area S2 of the triangular element at the end diastole for each evaluation area in each chart, and this is used as the motion evaluation value. It's being used. The area change rate is obtained by a calculation formula such as (S2-S1) / S2. Then, by comparing the area change rate with a predetermined threshold value for each evaluation area on each slice plane, the presence or absence of movement abnormality is determined. Here, the threshold value may be common in each evaluation area, or may be set individually in advance for each evaluation area. By such threshold determination, it is possible to automatically recognize a slice plane (specific slice plane) in which movement abnormality has occurred and an evaluation area (specific evaluation area) in which movement abnormality has occurred.

  In this embodiment, a chart corresponding to a specific slice plane is identified and displayed on the multi-chart image based on the automatic recognition as described above. In the example shown in FIG. As highlighted. In addition, the specific evaluation area is displayed with a predetermined coloring as indicated by reference numerals 40 and 42 between the two polygonal graphs. When a user observes a multi-chart image with such an identification display, the surface where the movement abnormality occurs can be easily recognized spatially, and the part where the movement abnormality occurs can be recognized easily spatially. Can do. The identification display process may use another method instead of the highlight process or the coloring process as described above. In any case, it is desirable to perform processing so that an abnormal movement site can be easily identified on the image. When each chart is formed, a two-dimensional tomographic image or a two-dimensional binarized image may be displayed as the background of two polygonal graphs.

  As described above, by displaying the multi-chart image as shown in FIG. 6 on the screen, it is possible to intuitively easily recognize the movement of the left ventricle, which is the target tissue, in a half cycle. There is an advantage that the momentum can be intuitively recognized as a difference. By the way, depending on the disease, there is a part that moves reversely to other parts, but in such a case, the area has a minus sign, and a display process for identifying such a part on the screen is applied. Is desirable. The multi-chart image shown in FIG. 6 is meaningful in its display itself, and it is possible to support disease diagnosis by applying the automatic analysis described above. In the above-described embodiment, two polygonal graphs of end diastole and end systole are shown. However, if at least one polygonal graph is displayed, the form of the target tissue is typically recognized for diagnosis. It can be useful. If real-time processing is possible, a polygonal graph can be displayed as a moving image. In any case, by setting a plurality of observation planes as a plurality of slice planes over the entire three-dimensional space, the whole movement of the target organ can be easily recognized, and an increase in the dead zone can be prevented to detect a diseased part. Leakage can be effectively prevented.

  In the above embodiment, when two polygonal graphs are displayed in a superimposed manner, if the influence of translational motion or rotational motion of the left ventricle cannot be ignored, such motion component is detected and the motion component is canceled. You may make it do.

  In the present embodiment, a composite image (composite image) as described below is formed by designating a specific chart (that is, a slice plane) in which motion abnormality is recognized on the multi-chart image shown in FIG. This will be described below with reference to FIGS. Here, in the example shown in FIGS. 7 and 8, a 3D space having a pyramid shape or a cone shape is assumed. A 3D space having a pyramid shape is formed by swinging a fan-shaped scanning surface formed by electronic sector scanning, while a 3D space having a cone shape is a fan-shaped scanning formed by electronic sector scanning. The surface is formed by rotating the surface about its central axis as a rotation axis.

  FIG. 7A shows a binarized image 40. This binarized image 40 is formed by applying reverse binarization processing or the like to a B-mode image formed by slice plane data. In the binarized image 40, the value of the pixel corresponding to the heart wall is set to 1, and the value of the pixel corresponding to the heart chamber is set to 0. Incidentally, the binarized image 40 may be a binarized image used in the polygon graph creation processing shown in FIG. 4 or may be an image created anew separately. Here, the binarized image 40 is an image corresponding to a predetermined time phase, for example, an image corresponding to the end diastole.

  FIG. 7B shows a mask image 42. The mask image 42 is an image that specifies an evaluation area where a movement abnormality is determined. In the example shown in FIG. 7B, the evaluation area E7 is recognized as an evaluation area where movement abnormality is recognized, and 1 is given to the value of the pixels belonging to the area, and 0 is assigned to the other pixels. Is given. In the example shown in FIG. 7, the outer edge of the mask image 42 is defined by the ROI.

  As shown in FIG. 7C, a colored image 44 is generated as an image for specifying a region of abnormal movement by taking an AND condition for each pixel between the binarized image 40 and the mask image 42. Is done. That is, the colored portion 44 a in the colored image 44 corresponds to the heart wall in the binarized image 40 and belongs to the evaluation area where the movement abnormality is determined in the mask image 42. Then, the synthesized image 46 is formed by synthesizing the colored image 44 on the B-mode image corresponding to the slice surface currently focused on. For example, an abnormal movement region is identified and displayed with a predetermined hue such as red or orange on a black and white tomographic image. In this case, a plurality of reference lines representing a plurality of evaluation areas may be combined and displayed as a graphic image as necessary. Further, guidance display such as a wire frame model for specifying the slice plane currently focused on in the three-dimensional space when displaying the composite image 46 may be performed together. In the composite image 46 shown in FIG. 7, the B-mode image is a still image, but it may be a moving image.

  By displaying the composite image 46 as shown in FIG. 7D, for example, the heart wall portion in which the movement abnormality in the left ventricle has occurred can be clearly expressed, and for example, the occurrence site of myocardial infarction can be easily expressed There is an advantage that can be specified. The hue to be colored may be changed according to the degree of movement abnormality, and the luminance thereof may be changed.

  In the display example shown in FIG. 7, the abnormal movement site is expressed in color on the two-dimensional tomographic image, but the abnormal movement site may be expressed in color on the composite image as shown in FIG. 8. That is, FIG. 8 shows a composite image 50 in which a B-mode tomographic image and a three-dimensional image are combined. That is, the B-mode tomographic image 50A corresponding to the slice plane and the three-dimensional images 50B, 50C, and 50D in which the portion corresponding to the heart chamber is expressed with a sense of depth are expressed. Then, in such an anatomical expression form, the abnormal movement portion is identified and displayed as the colored portion 52 using the above-described method. By the way, it is also possible to identify and express abnormal movement sites by coloring the surface of the organ in a three-dimensional image formed by using, for example, a volume rendering method or a surface method.

  Next, a configuration example of the ultrasonic diagnostic apparatus according to the present embodiment will be described with reference to FIG.

  The 3D probe 60 has a 2D array transducer in the example shown in FIG. The 2D array transducer is a two-dimensional array of a plurality of transducer elements. A scanning plane is formed by electronic scanning of the ultrasonic beam in one direction, and the 3D space is configured by electronic scanning of the scanning plane in the other direction. Of course, when a plurality of scanning planes and a plurality of slice planes are matched, a plurality of scans corresponding to the plurality of slice planes are performed without scanning the ultrasonic beam over the entire three-dimensional space. You may scan an ultrasonic beam only about a surface. Examples of the electronic scanning method include electronic sector scanning and electronic linear scanning. The scanning plane may be formed by a 1D array transducer, and the scanning plane may be mechanically moved by moving the 1D array transducer in parallel or swinging. The 3D probe 60 is normally used in contact with the body surface, but may be used by being inserted into a body cavity such as an esophagus or a blood vessel.

  The transmission / reception unit 62 functions as a transmission beam former and a reception beam former. Transmission signals are supplied to the plurality of vibration elements by the transmission unit 62, thereby forming a transmission beam. On the other hand, the plurality of reception signals output from the plurality of vibration elements are subjected to phasing addition processing in the transmission / reception unit 62, and the reception signals after the phasing addition are output to the 3D memory 64 as echo data. In the example shown in FIG. 9, the 3D memory 64 has a three-dimensional storage space corresponding to the 3D space where ultrasonic waves are transmitted and received, and each echo data corresponds to the spatial position from which it was acquired. Stored at the address to be So-called volume data is stored on the 3D memory 64.

  Under the control of the control unit 76, the B-mode image forming unit 66 forms a B-mode image as a two-dimensional tomographic image based on echo data on a specified arbitrary slice or slice plane. The image data is output to the display processing unit 72. Based on the volume data stored on the 3D memory 64, the 3D image forming unit 68 forms a three-dimensional ultrasonic image, that is, a 3D image using, for example, a volume rendering method. The image data is output to the display processing unit 72. For example, when the display form shown in FIG. 8 is adopted, an image portion corresponding to a three-dimensional image is formed by the 3D image forming unit 68.

  The heart wall motion analysis unit 70 has a function of creating the motion evaluation chart as described above based on slice plane data corresponding to each slice plane read from the 3D memory 64. This will be described in detail later. The control unit 76 controls the operation of each component shown in FIG. An operation panel 78 is connected to the control unit 76, and the user can perform various inputs and settings using the operation panel 78. An electrocardiogram signal from the electrocardiograph 80 is input to the control unit 76, and each time phase in the heartbeat cycle can be recognized based on the electrocardiogram signal.

  The heart wall motion analysis unit 70 will be described in detail below. Each component included therein is realized by hardware or as a function of software. The ROI setting unit 82 is a means for setting a three-dimensional ROI for the 3D space. When the ROI is designated by the user, an image as shown in FIG. 2 is displayed on the display unit 74, and the ROI is designated by the user using the operation panel 78. Incidentally, in FIG. 9, a module for forming a projection image to be displayed when the ROI is designated is not shown. Although it is difficult to directly specify the three-dimensional form in the three-dimensional space, two orthogonal projection images as shown in Fig. 2 are displayed simultaneously, and the shape and position of the ROI are specified on them. Then, there is an advantage that a three-dimensional ROI can be set appropriately and easily in relation to the target tissue.

  As shown in FIG. 3, the frame extraction / processing unit 84 automatically defines a plurality of slice planes that intersect with a common reference axis specified together with the ROI, and slice plane data from the 3D memory 64 for each slice plane. Is a module that executes image processing on each slice plane data. As described above, each slice plane data is read at the end systole and the end diastole. Correspondingly, the volume data of the end systole and the volume data of the end diastole may be stored together on the 3D memory 64, or the volume data of any one of the phase phases may be stored to perform necessary processing on it. After execution, volume data of other time phases may be stored on the 3D memory 64, and the same processing may be executed on the volume data. The frame extraction / processing unit 84 applies reverse binarization processing or the like to the read slice plane data, that is, assigns 1 to the pixel corresponding to the heart wall, and corresponds to the heart chamber on one side 0 is assigned to the pixels to be processed, thereby forming a binarized image. The created binarized image may be stored on the memory 85 as necessary. That is, a binarized image necessary for creating the colored image 44 shown in FIG. 7 may be stored on the memory 85.

  The polygon graph creating unit 86 creates a polygon graph corresponding to the end systole and a polygon graph corresponding to the end diastole based on the method shown in FIG. When either one is created in advance, data representing the previously created polygonal graph is temporarily stored in the buffer memory 88. As described with reference to FIG. 4, the polygonal graph creation unit 86 sets a plurality of reference lines radially from the common reference point on each slice plane, detects the intersection with the contour on each reference line, A polygonal graph is created by connecting a plurality of intersections to each other.

  The area change rate calculation unit 90 calculates the area change rate for each evaluation area by calculating the difference between the polygonal graph at the end systole and the polygonal graph at the end diastole for each slice plane. Calculate as That is, the area change rate calculation unit 90 is a module that creates the chart shown in FIG. 4 and analyzes the contents of the chart.

  The abnormality determination unit 92 determines an evaluation area, that is, an abnormal part where a movement abnormality occurs by comparing the area change rate with a predetermined threshold value α for each evaluation area on each slice plane. In this case, the threshold value α may be a fixed value, or may be a value that varies depending on the slice plane or the evaluation area. Usually, α as a fixed value is compared with the standardized area change rate, and when the area change rate falls below α, it is determined that the movement is abnormal. Information representing the determination result is sent to the control unit 76, the multi-chart image forming unit 94, the colored composite image forming unit 96, and the colored composite image forming unit 98 in the configuration example shown in FIG. Instead of automatically determining the movement abnormality, the slice surface or the evaluation area where the movement abnormality has occurred may be specified by the user based on the comparison between the charts on the multi-chart image.

  The multi-chart image forming unit 94 forms the multi-chart image shown in FIG. That is, a multi-chart image is created by superposing and synthesizing a polygonal graph created for each time phase on each slice plane for each slice plane and arranging a plurality of charts in an array. The image data is sent to the display processing unit 72.

  The colored composite image creation unit 96 is a module that creates the composite image 46 shown in FIG. 7, that is, a composite image is formed on the B-mode image, thereby forming a composite image. As described above, the colored image is generated by a combination of the binarized image and the mask image. The B mode image is formed by the B mode image forming unit 66. The image data of the composite image formed by the colored composite image forming unit 96 is output to the display processing unit 72.

  The colored composite image forming unit 98 forms the B-3D composite image shown in FIG. 8 as a composite image. A 3D image necessary for this is formed by the 3D image forming unit 68, a B-mode image is formed by the B-mode image forming unit 66, and a colored image representing a colored portion is generated by the colored composite image forming unit 98 itself. . The image data of the formed image is output to the display processing unit 72.

  The display processing unit 72 has a function of outputting the input image data to the display unit 74, and in that case, the graphic image 100 is synthesized as necessary. A predetermined image is displayed on the display unit 74.

  According to the above embodiment, a plurality of slice planes can be set with a certain relationship to the 3D space, and the motion of the target tissue can be evaluated for each slice plane. There is an advantage that can be performed. In other words, there is an advantage that it is possible to effectively prevent the problem that the space where measurement cannot be performed increases. Also, by setting a plurality of slice planes with a spatial relationship as shown in FIG. 3, there is an advantage that the spatial positional relationship between the charts can be easily recognized when a multi-chart image is displayed. . That is, since the common reference axis and the common reference point coincide with each other between the charts, it is possible to easily recognize the position and degree of the abnormal part and the spatial extent thereof. In the above-described embodiment, a plurality of evaluation areas are set on each slice plane, and movement abnormalities can be automatically evaluated for each evaluation area. Therefore, there is an advantage that disease diagnosis can be effectively supported. In addition, since quantitative evaluation can be performed in particular, there is an advantage that information useful for disease diagnosis can be provided. Moreover, there is an advantage that an abnormal movement region can be easily specified in relation to the structure or form of the living tissue by displaying a detailed image as shown in FIGS. 7 and 8 as necessary. In the present embodiment, a polygon that simulates the contour of the tissue can be used as the basis of the calculation, so that there is an advantage that the calculation amount can be reduced and the calculation can be speeded up.

It is a figure which shows the relationship between 3D space and three-dimensional ROI. It is a figure for demonstrating the setting method of ROI. It is a figure which shows the positional relationship of a some slice surface. It is a figure for demonstrating the creation process of a polygonal graph. It is a figure for demonstrating the area calculation of a triangular graph element. It is a figure which shows the multi chart image containing the several chart for exercise | movement evaluation. It is a figure for demonstrating the production method of the synthesized image by which the B mode image and the coloring image were synthesize | combined. It is a figure which shows the synthesized image by which the B mode image, the three-dimensional image, and the coloring image were synthesize | combined. It is a block diagram which shows the structure of the ultrasonic diagnosing device which concerns on this embodiment.

Explanation of symbols

  10 3D space, 12 ROI (region of interest), 36A to 36H motion evaluation chart, 46 composite image, 50 B-3D composite image, 70 heart wall motion analysis unit, 82 ROI setting unit, 84 frame extraction / processing unit, 86 Polygon graph creation unit, 90 area change rate calculation unit, 92 abnormality determination unit, 94 multi-chart image forming unit, 96 colored image forming unit, 98 colored composite image forming unit.

Claims (17)

Transmitting and receiving means for transmitting and receiving ultrasonic waves to and from a three-dimensional space including a moving tissue;
Slice plane setting means for setting a plurality of slice planes for the three-dimensional space;
Motion evaluation having first and second polygonal graphs simulating the contours of the moving tissue in the first and second time phases for each slice plane based on the data obtained by transmitting and receiving the ultrasonic waves A chart generating means for generating a chart for use;
Means for forming a multi-chart image in which a plurality of motion evaluation charts corresponding to the plurality of slice planes are arranged;
Means for displaying the multi-chart image;
In addition,
Means for determining the presence or absence of movement abnormality based on the content of the tissue movement evaluation chart for each slice plane;
Means for identifying and displaying a specific exercise evaluation chart in which the movement abnormality is recognized among the plurality of exercise evaluation charts;
An ultrasonic diagnostic apparatus comprising: The apparatus of claim 1.
The ultrasonic diagnostic apparatus characterized in that the slice plane setting means sets a plurality of slice planes that intersect each other on a common reference axis. The apparatus of claim 2.
Wherein Ri common reference point der on the common reference axis graph origin is a common point in the plurality of slice plane of the first and second polygonal graph is set on each slice plane,
A plurality of reference lines for contour detection are set radially from the graph origin on each slice plane . The apparatus of claim 1.
A region of interest setting means for setting a three-dimensional region of interest with respect to the three-dimensional space;
An ultrasonic diagnostic apparatus, wherein processing for generating the first and second polygonal graphs is executed for each slice plane in the region of interest. The apparatus of claim 4.
The region of interest setting means includes
Means for forming a plurality of two-dimensional images reflecting the three-dimensional space;
Means for defining the position and shape of the region of interest on the plurality of two-dimensional images;
An ultrasonic diagnostic apparatus comprising: The apparatus of claim 4.
The region of interest is a cylindrical region having a common reference axis as a central axis,
The ultrasonic diagnostic apparatus, wherein the plurality of slice planes intersect each other on the common reference axis. The apparatus of claim 1.
The athletic tissue is a heart;
The ultrasonic diagnostic apparatus, wherein the first time phase corresponds to an end diastole and the second time phase corresponds to an end systole. The apparatus of claim 1.
An ultrasonic diagnostic apparatus , wherein an image showing the motion tissue is displayed as a background of each motion evaluation chart constituting the multi-chart image . The apparatus of claim 1.
The chart generating means includes
On each slice plane, a reference line setting means for setting a plurality of reference lines radially from a reference point;
On each of the slice planes, an intersection detection means for detecting an intersection of each reference line and the contour of the moving tissue;
On each of the slice planes, a polygonal graph generating means for generating a polygonal graph by connecting adjacent intersections with connecting lines;
An ultrasonic diagnostic apparatus comprising: The apparatus of claim 9.
A plurality of evaluation areas are defined by the plurality of reference lines for each slice plane,
The first polygonal graph is configured as an aggregate of a plurality of first triangular graph elements belonging to the plurality of evaluation areas,
The second polygon is configured as an aggregate of a plurality of second triangular graph elements belonging to the plurality of evaluation areas,
A movement evaluation value calculating means for calculating a movement evaluation value based on the area of the first triangular graph element and the area of the second triangular graph element is provided for each evaluation area.
An ultrasonic diagnostic apparatus. The apparatus of claim 10.
The ultrasonic diagnostic apparatus, wherein the motion evaluation value is an area change rate. Transmitting and receiving means for transmitting and receiving ultrasonic waves to and from a three-dimensional space including a moving tissue;
Slice plane setting means for setting a plurality of slice planes for the three-dimensional space;
Motion evaluation having first and second polygonal graphs simulating the contours of the moving tissue in the first and second time phases for each slice plane based on the data obtained by transmitting and receiving the ultrasonic waves A chart generating means for generating a chart for use;
Including
The chart generating means includes
On each slice plane, a reference line setting means for setting a plurality of reference lines radially from a reference point;
On each of the slice planes, an intersection detection means for detecting an intersection of each reference line and the contour of the moving tissue;
On each of the slice planes, a polygonal graph generating means for generating a polygonal graph by connecting adjacent intersections with connecting lines;
Including
A plurality of evaluation areas are defined by the plurality of reference lines for each slice plane,
The first polygonal graph is configured as an aggregate of a plurality of first triangular graph elements belonging to the plurality of evaluation areas,
The second polygon is configured as an aggregate of a plurality of second triangular graph elements belonging to the plurality of evaluation areas,
A movement evaluation value calculating means for calculating a movement evaluation value based on the area of the first triangular graph element and the area of the second triangular graph element is provided for each evaluation area,
The motion evaluation value calculation means uses a horizontal coordinate of one intersection and a vertical coordinate of the other intersection among two intersections on two reference lines defining each evaluation area. An ultrasonic diagnostic apparatus characterized by calculating an area of a graph element. The apparatus of claim 10.
An ultrasonic diagnostic apparatus comprising: determination means for determining a movement abnormality based on a movement evaluation value for each reference area on each slice plane. Transmitting and receiving means for transmitting and receiving ultrasonic waves to and from a three-dimensional space including a moving tissue;
Slice plane setting means for setting a plurality of slice planes for the three-dimensional space;
Motion evaluation having first and second polygonal graphs simulating the contours of the moving tissue in the first and second time phases for each slice plane based on the data obtained by transmitting and receiving the ultrasonic waves A chart generating means for generating a chart for use;
Including
The chart generating means includes
On each slice plane, a reference line setting means for setting a plurality of reference lines radially from a reference point;
On each of the slice planes, an intersection detection means for detecting an intersection of each reference line and the contour of the moving tissue;
On each of the slice planes, a polygonal graph generating means for generating a polygonal graph by connecting adjacent intersections with connecting lines;
Including
A plurality of evaluation areas are defined by the plurality of reference lines for each slice plane,
The first polygonal graph is configured as an aggregate of a plurality of first triangular graph elements belonging to the plurality of evaluation areas,
The second polygon is configured as an aggregate of a plurality of second triangular graph elements belonging to the plurality of evaluation areas,
A movement evaluation value calculating means for calculating a movement evaluation value based on the area of the first triangular graph element and the area of the second triangular graph element is provided for each evaluation area,
A determination means for determining a movement abnormality based on the movement evaluation value for each reference area on each slice plane is provided,
The ultrasonic diagnostic apparatus further includes:
Means for forming a multi-chart image having the plurality of motion evaluation charts corresponding to the plurality of slice planes;
Means for performing processing for identifying at least one of a specific slice plane and a specific evaluation area where the movement abnormality is recognized with respect to the multi-chart image;
An ultrasonic diagnostic apparatus comprising: Transmitting and receiving means for transmitting and receiving ultrasonic waves to and from a three-dimensional space including a moving tissue;
Slice plane setting means for setting a plurality of slice planes for the three-dimensional space;
Motion evaluation having first and second polygonal graphs simulating the contours of the moving tissue in the first and second time phases for each slice plane based on the data obtained by transmitting and receiving the ultrasonic waves A chart generating means for generating a chart for use;
Including
The chart generating means includes
On each slice plane, a reference line setting means for setting a plurality of reference lines radially from a reference point;
On each of the slice planes, an intersection detection means for detecting an intersection of each reference line and the contour of the moving tissue;
On each of the slice planes, a polygonal graph generating means for generating a polygonal graph by connecting adjacent intersections with connecting lines;
Including
A plurality of evaluation areas are defined by the plurality of reference lines for each slice plane,
The first polygonal graph is configured as an aggregate of a plurality of first triangular graph elements belonging to the plurality of evaluation areas,
The second polygon is configured as an aggregate of a plurality of second triangular graph elements belonging to the plurality of evaluation areas,
A movement evaluation value calculating means for calculating a movement evaluation value based on the area of the first triangular graph element and the area of the second triangular graph element is provided for each evaluation area,
A determination means for determining a movement abnormality based on the movement evaluation value for each reference area on each slice plane is provided,
The ultrasonic diagnostic apparatus further includes:
Means for forming a tomographic image corresponding to a specific slice plane in which the movement abnormality is recognized;
Means for performing a process of identifying a specific evaluation area in which the movement abnormality is recognized with respect to the tomographic image, and displaying an identification processed tomographic image;
An ultrasonic diagnostic apparatus comprising: Transmitting and receiving means for transmitting and receiving ultrasonic waves to and from a three-dimensional space including a moving tissue;
Slice plane setting means for setting a plurality of slice planes for the three-dimensional space;
Motion evaluation having first and second polygonal graphs simulating the contours of the moving tissue in the first and second time phases for each slice plane based on the data obtained by transmitting and receiving the ultrasonic waves A chart generating means for generating a chart for use;
Including
The chart generating means includes
On each slice plane, a reference line setting means for setting a plurality of reference lines radially from a reference point;
On each of the slice planes, an intersection detection means for detecting an intersection of each reference line and the contour of the moving tissue;
On each of the slice planes, a polygonal graph generating means for generating a polygonal graph by connecting adjacent intersections with connecting lines;
Including
A plurality of evaluation areas are defined by the plurality of reference lines for each slice plane,
The first polygonal graph is configured as an aggregate of a plurality of first triangular graph elements belonging to the plurality of evaluation areas,
The second polygon is configured as an aggregate of a plurality of second triangular graph elements belonging to the plurality of evaluation areas,
A movement evaluation value calculating means for calculating a movement evaluation value based on the area of the first triangular graph element and the area of the second triangular graph element is provided for each evaluation area,
A determination means for determining a movement abnormality based on the movement evaluation value for each reference area on each slice plane is provided,
The ultrasonic diagnostic apparatus further includes:
Means for forming a composite image in which a two-dimensional image representing a cross-sectional structure corresponding to a specific slice plane in which the motion abnormality is recognized and a three-dimensional image representing a tissue form on the back side of the specific slice plane are combined When,
Means for performing a process of identifying a specific evaluation area in which the movement abnormality is recognized with respect to the composite image, and displaying the identification processed composite image;
An ultrasonic diagnostic apparatus comprising: Transmitting and receiving means for transmitting and receiving ultrasonic waves to and from a three-dimensional space including a moving tissue;
Slice plane setting means for dispersively setting a plurality of slice planes intersecting at a common reference axis with respect to the three-dimensional space;
Chart generation means for generating a motion evaluation chart having a polygonal graph simulating the contour of the motion tissue for each slice plane based on the data obtained by transmitting and receiving the ultrasonic wave,
Means for forming a multi-chart image in which a plurality of motion evaluation charts corresponding to the plurality of slice planes are arranged;
Means for displaying the multi-chart image;
In addition,
Means for determining the presence or absence of movement abnormality based on the contents of the tissue movement evaluation chart for each partial evaluation area in each slice plane;
Means for identifying and displaying a specific exercise evaluation chart in which the movement abnormality is recognized among the plurality of exercise evaluation charts;
An ultrasonic diagnostic apparatus comprising:

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