JP6199677B2 - Ultrasonic diagnostic equipment - Google Patents

Description

  The present invention relates to an ultrasonic diagnostic apparatus for diagnosing a site of interest of a subject.

  The ultrasonic diagnostic apparatus is used for diagnosing a site of interest such as a tissue in a subject such as a living body, and is an extremely important apparatus particularly for fetal diagnosis. Under these circumstances, various techniques relating to fetal diagnosis using an ultrasonic diagnostic apparatus have been proposed. For example, Patent Document 1 proposes an epoch-making technique capable of measuring a time difference of movement in each part of the myocardium of a fetal heart.

  However, for example, an early fetus until about the 10th week of gestation is still very small and the heart is very small, making it very difficult to diagnose the heart with an ultrasonic diagnostic apparatus. For example, in M-mode measurement or Doppler measurement of an ultrasonic diagnostic apparatus, it is difficult to set a cursor or the like on a very small heart, and even if the cursor or the like can be set, it is accompanied by maternal breathing or the like. As a result, the fetus moves as a whole and the cursor and the like are displaced from the heart, and it is difficult to maintain the accuracy of measurement relating to heartbeat information and the like.

  Therefore, there has been a demand for an improved technique for improving the accuracy of diagnosis related to the fetal heart, for example, in an ultrasonic diagnostic apparatus.

JP 2011-177338 A

  The present invention has been made in view of the above-described background art, and an object of the present invention is to provide an apparatus that improves the accuracy of diagnosis related to a region of interest (for example, a fetal heart) of a subject.

  An ultrasonic diagnostic apparatus suitable for the above object includes a probe that transmits and receives an ultrasonic wave for a diagnostic region including a subject, a transmission and reception unit that controls the probe to obtain an ultrasonic reception signal from the diagnostic region, and a received signal In the image data of the diagnostic region obtained based on the first reference region, the first reference region is set so as to include the outer region of the target region while avoiding the target region of the subject, and the second reference region so as to include the target region A reference region setting unit for setting the object, a tracking processing unit for tracking a subject that moves in the image data over a plurality of time phases based on the image data in the first reference region, and a result of the tracking And a movement processing unit that moves the second reference region so as to follow the subject moving in the image data over a plurality of time phases, and a movement processing unit that moves over the plurality of time phases. Based on the image data of the second reference area which is characterized by having a diagnostic waveform processing section which forms a diagnostic waveform reflecting the movement of the target site.

  In the above configuration, a specific example of the subject is a living body, and a specific example of the region of interest is a tissue. For example, a fetal heart is included as a specific example suitable as a site of interest of a subject. Further, a specific example suitable as image data of the diagnostic region is image data of a two-dimensional B-mode image (tomographic image), but may be image data of a color Doppler image or a three-dimensional image. Moreover, various modes are possible for the shape of the reference region (the first reference region and the second reference region). For example, if the image data is two-dimensional, a two-dimensional shape (rectangle, other polygons, a circle, An elliptical reference area is used, and if it is three-dimensional image data, a three-dimensional reference area is used. For example, the second reference region is sized according to the site of interest, and is set to include at least a part of the site of interest, and is preferably set to include the entire site of interest. The first reference region is set to the subject so as to include an outer part of the target part while avoiding the target part. The first reference area and the second reference area may be set so as not to overlap each other, or may be set so as to partially overlap each other.

  According to the above configuration, for example, even when the subject moves, the subject is tracked using the first reference region, and the second reference region is moved so as to follow the subject based on the tracking result. Therefore, the second reference region is moved so as to follow the attention site, the reliability of the diagnostic waveform obtained based on the image data in the second reference region is increased, and the accuracy of diagnosis based on the diagnostic waveform is increased.

  In a preferred embodiment, the diagnostic waveform processing unit forms a shaped waveform obtained by shaping a diagnostic waveform by suppressing temporal fluctuations of a bias component in a diagnostic waveform that periodically changes over a plurality of time phases. It is characterized by that.

  In a preferred embodiment, the diagnostic waveform processing unit aligns the sizes of a plurality of extreme values while maintaining the time phase of each extreme value for a plurality of extreme values appearing in the diagnostic waveform over a plurality of time phases. To form the shaped waveform.

  In a preferred embodiment, the diagnostic waveform processing unit maintains a time phase of each intermediate value for a plurality of intermediate values appearing between a maximum value and a minimum value adjacent to each other in the diagnostic waveform over a plurality of time phases. However, the shaped waveform is formed by aligning the sizes of a plurality of intermediate values.

  In a desirable specific example, the diagnostic waveform processing unit evaluates the stability of a period that varies over a plurality of time phases in the diagnostic waveform based on the periodically changing diagnostic waveform, and the evaluation result The display mode according to the above is formed.

  In a preferred specific example, the diagnostic waveform processing unit forms a display mode indicating a period with a stable period in the diagnostic waveform.

  In a preferred embodiment, the reference area setting unit sets a second reference area so as to include a fetal heart in the image data, and sets the first reference area so as to surround the second reference area. It is characterized by. For example, the first reference area may be set so as to completely enclose the entire periphery of the second reference area, or the first reference area surrounding the second reference area by opening a part thereof may be set. Further, the first reference area may be configured by a set including a plurality of partial areas, and the plurality of partial areas may be arranged around the second reference area.

  According to the present invention, an apparatus for improving the accuracy of diagnosis related to a region of interest of a subject is provided. For example, according to a preferred aspect of the present invention, even when the subject moves, the second reference is made so that the subject is tracked using the first reference region and the subject is followed based on the tracking result. Since the region is moved, the second reference region is moved so as to follow the region of interest, the reliability of the diagnostic waveform obtained based on the image data in the second reference region is increased, and the accuracy of diagnosis based on the diagnostic waveform is increased. Is increased.

1 is an overall configuration diagram of an ultrasonic diagnostic apparatus suitable for implementing the present invention. It is a figure which shows the specific example of a body reference area and a heart reference area. It is a figure which shows the specific example of the process by the ultrasonic diagnosing device of FIG. It is a figure which shows the specific example of a heartbeat waveform. It is a figure which shows the example of a display of a heartbeat waveform. It is a figure which shows the specific example of the shaping process using the extreme value of a heartbeat waveform. It is a figure which shows the specific example of the shaping process using the intermediate value of a heartbeat waveform. It is a figure which shows the specific example of the shaping process which arranges the maximum value and minimum value of a heartbeat waveform. It is a figure which shows the other specific example of the shaping process which arranges the maximum value and minimum value of a heartbeat waveform. It is a figure which shows the example of a display of a shaping waveform. It is a figure for demonstrating the determination process of the period where the period was stabilized. It is a figure which shows the example of a display of the stable period in a heartbeat waveform or a shaping waveform. It is a figure which shows the other example of a display of a measurement result.

  FIG. 1 is an overall configuration diagram of an ultrasonic diagnostic apparatus suitable for implementing the present invention. The probe 10 transmits an ultrasonic wave to a diagnostic region including the fetus and receives an ultrasonic wave reflected from the diagnostic region. The probe 10 includes a plurality of vibration elements that transmit and receive ultrasonic waves, and transmission of the plurality of vibration elements is controlled by the transmission / reception unit 12 to form a transmission beam. Further, the plurality of vibration elements receive the ultrasonic waves reflected from the diagnostic region, and signals obtained thereby are output to the transmission / reception unit 12, and the transmission / reception unit 12 forms a reception beam.

  The transmission / reception unit 12 outputs a transmission signal corresponding to each of the plurality of vibration elements included in the probe 10, thereby forming an ultrasonic transmission beam and scanning the transmission beam. In addition, the transmission / reception unit 12 forms a reception beam corresponding to the transmission beam to be scanned by performing a phasing addition process on the reception signal obtained from each of the plurality of vibration elements included in the probe 10, and receives Echo data (received signal) obtained along the beam is output. That is, the transmission / reception unit 12 has functions of a transmission beamformer and a reception beamformer.

  The ultrasound image forming unit 20 forms image data of ultrasound images over a plurality of time phases related to a diagnostic region including the fetus based on echo data (received signals) obtained over a plurality of time phases. For example, the ultrasonic image forming unit 20 forms image data of a tomographic image (B-mode image) showing a fetus over a plurality of frames for each frame (for each time phase). The image data of the tomographic image formed in the ultrasonic image forming unit 20 is output to the reference region setting unit 30 one after another for each frame. The image data formed in the ultrasonic image forming unit 20 is output to the display image forming unit 80, and a tomographic image corresponding to the image data is displayed on the display unit 82.

  The reference region setting unit 30 sets a reference region in the image data of the tomographic image formed by the ultrasonic image forming unit 20. The reference region setting unit 30 sets a body reference region for the fetal body and sets a heart reference region for the fetal heart. For example, the reference region setting unit 30 sets a body reference region and a heart reference region in accordance with a user operation input via the operation device 40. For example, the user operates the operation device 40 so that the body reference region and the heart reference region are set at desired positions while viewing the tomographic image displayed on the display unit 82. The reference region setting unit 30 may analyze the image state in the tomographic image, set the body reference region in the fetal body, and set the heart reference region in the fetal heart.

  When the body reference region and the heart reference region are set in the image data of the tomographic image by the reference region setting unit 30, the tracking processing unit 50 covers a plurality of time phases based on the image data in the body reference region. The moving fetus is tracked in the image data of the tomographic image. Then, the movement processing unit 60 moves the heart reference region based on the tracking result in the tracking processing unit 50 so as to follow the moving fetus in the image data of the tomographic image over a plurality of time phases. Thereby, the heart reference area set for the fetal heart is controlled to follow the moving fetal heart.

  The heartbeat waveform processing unit 70 forms a heartbeat waveform reflecting the periodic motion of the fetal heart, that is, the heartbeat, based on the image data in the heart reference region moving over a plurality of time phases, and the heartbeat waveform Is output to the display image forming unit 80.

  The display image forming unit 80 forms a tomographic image and a display image of the heartbeat waveform based on the image data of the tomographic image obtained from the ultrasonic image forming unit 20 and the heartbeat waveform data obtained from the heartbeat waveform processing unit 70. . The display image formed in the display image forming unit 80 is displayed on the display unit 82.

  In the configuration illustrated in FIG. 1, the transmission / reception unit 12, the ultrasonic image forming unit 20, the reference region setting unit 30, the tracking processing unit 50, the movement processing unit 60, the heartbeat waveform processing unit 70, and the display image forming unit 80 The operation device 40 can be realized by using hardware such as a processor or an electronic circuit, respectively, and the operation device 40 is at least a part of, for example, a mouse, a trackball, a keyboard, a touch panel, and other switches. Can be realized. A suitable specific example of the display unit 82 is a liquid crystal display or the like, but is not limited thereto.

  The overall configuration of the ultrasonic diagnostic apparatus in FIG. 1 is as described above. Next, functions and the like realized by the ultrasonic diagnostic apparatus of FIG. 1 will be described in detail. In addition, about the structure (part) shown in FIG. 1, the code | symbol of FIG. 1 is utilized in the following description.

  FIG. 2 is a diagram illustrating specific examples of the body reference region 31 and the heart reference region 32. The tomographic image (B-mode image) 22 shows the fetus in the mother body (uterus), and the fetus is surrounded by amniotic fluid in the mother body.

  The body reference area 31 is a preferred specific example of the first reference area, and is used to analyze the overall movement of the fetal body. Therefore, it is desirable that the body reference region 31 is set at a place where the movement of the fetal body is easily detected. Specifically, for example, the user designates the position of the body reference region 31 so that the boundary between the fetus and the amniotic fluid is included. Further, the reference region setting unit 30 may determine the boundary between the fetus and the amniotic fluid by image analysis processing such as binarization processing and determine the setting position of the body reference region 31. Note that the body reference region 31 may be set so as to include other places where the movement of the fetal body is easily detected.

  The heart reference region 32 is a preferred embodiment of the second reference region and is used to analyze the movement of the fetus heart. Therefore, it is desirable that the heart reference region 32 is set at a place where the fetal heart motion is easily detected. Specifically, for example, the user designates the position of the heart reference region 32 so that the fetal heart portion having relatively high luminance is entirely included. Further, the reference region setting unit 30 may determine a setting position of the heart reference region 32 by determining a fetal heart portion having a relatively high luminance by image analysis processing such as binarization processing, for example. The heart reference region 32 may be set so as to include only a part of the heart as long as the fetal heart motion can be detected.

  In the specific example shown in FIG. 2, the body reference region 31 and the heart reference region 32 are both rectangular, but these reference regions may be other polygons, circles, or ellipses. Further, as in the specific example shown in FIG. 2, the heart reference area 32 is relatively small in accordance with the size of the fetal heart, and the body reference area 31 is larger than the heart reference area 32 in accordance with the size of the fetal body. Is also desirable to be large.

  The body reference region 31 is set so as to avoid the fetal heart. The body reference region 31 is desirably set so as not to include the heart, but may be set so as to include a part of the heart as long as the movement of the fetal body can be detected. Since the heart reference region 32 is set with respect to the heart, the body reference region 32 is preferably set so as to surround the heart reference region 32 in a shape in which the region corresponding to the heart reference region 32 is hollowed out. The body reference area 31 and the heart reference area 32 may partially overlap each other. Alternatively, only the position of the heart reference region 32 may be specified by the user, and the reference region setting unit 30 may set the body reference region 31 so as to surround the heart reference region 32.

  FIG. 3 is a diagram showing a specific example of processing by the ultrasonic diagnostic apparatus of FIG. First, when image data of a tomographic image relating to a diagnostic region including a fetus is obtained by transmitting and receiving ultrasonic waves, a reference region is set in the image data of the tomographic image by the reference region setting unit 30 (S301). For example, the body reference region 31 and the heart reference region 32 are set in the tomographic image of the reference frame (see FIG. 2).

  Subsequently, image data of tomographic images over a plurality of frames to be processed is acquired for each frame (S302). For example, image data of tomographic images of frames after the tomographic image (reference frame) in which the reference region is set is sent to the tracking processing unit 50 and the movement processing unit 60 one after another for each frame.

  The tracking processing unit 50 uses the body reference region 31 (FIG. 2) set in the tomographic image of the reference frame as a template, and is most similar to the image data in the template in the tomographic image of the frame to be processed. An image portion (highly correlated) is searched, and a matching process is performed with the template moving position. Then, in the tomographic images of a plurality of frames to be processed, the movement position of the template is sequentially searched and tracked (S303).

  The tracking processing unit 50 performs a tracking process using the body reference region 31 as a template over a plurality of frames, and calculates the movement position of the body reference region 31 for each frame. For example, a movement vector from the position of the body reference region 31 in the tomographic image of the reference frame to the movement position of the body reference region 31 in the processing target frame is calculated for each frame. Note that the movement vector of the body reference region 31 between the frames may be calculated by a matching process between the frames that are temporally adjacent to each other.

  The movement processing unit 60 moves the heart reference region 32 by the same distance as the movement distance of the body reference region 31 in the image data of tomographic images over a plurality of frames that are sequentially sent. That is, the heart reference area 32 is moved by the same vector amount as the movement vector of the body reference area 31 calculated for each frame. Thereby, the heart reference area 32 moves so as to follow the movement of the body reference area 31, that is, so as to follow the heart of the moving fetus (S304).

  The heartbeat waveform processing unit 70 forms a heartbeat waveform that periodically changes over a plurality of frames based on the image data in the moving heart reference region 32 (S305). When the heartbeat waveform is formed, a display image including the heartbeat waveform is displayed on the display unit 82 (S306). Then, it is confirmed whether or not the processing for all the frames to be processed has been completed (S307), and the processing from S302 to S306 is repeated until the processing for all the frames is completed.

  FIG. 4 is a diagram showing a specific example of a heartbeat waveform. The heartbeat waveform processing unit 70 calculates a waveform value for each frame based on the image data in the heart reference region 32 (FIG. 2), and forms a heartbeat waveform 72 by connecting the waveform values over a plurality of frames. .

  A preferable specific example of the waveform value is an average value of pixel values related to a plurality of pixels in the heart reference region 32. The fetal heart in the image data has its pixel values (luminance values) changed periodically according to the heart rate as a whole. The heart reference region 32 is controlled so as to follow the moving fetal heart, and therefore, the overall change in pixel values within the heart reference region 32, for example, the average value of the pixel values, is a period according to the heartbeat. Changes. Therefore, the heartbeat waveform processing unit 70 calculates the average value of the pixel values as the waveform value for each frame to form the heartbeat waveform 72.

  The heartbeat waveform 72 may be formed using a difference between an average value of pixel values in the heart reference region 32 of each frame and an average value of pixel values in the heart reference region 32 of the base frame as a waveform value. Further, as a waveform value, for example, a correlation value with a reference frame or the like may be calculated for each frame based on image data in the heart reference region 32. As the correlation value, for example, other arithmetic expressions that are suitable, such as SSD (Sum of Square Difference) or SAD (Sum of Absolute Difference), may be used.

  FIG. 5 is a diagram illustrating a display example of the heartbeat waveform 72. FIG. 5 shows a specific example of the display image formed by the display image forming unit 80 and displayed on the display unit 82.

  FIG. 5 <A> shows a display image in which the tomographic image (B-mode image) 22 and the heartbeat waveform 72 are arranged one above the other, and FIG. 5 <B> shows the heartbeat waveform 72 and the tomographic image 22 arranged side by side. The arranged display image is shown. For example, an average heart rate (BPM) may be displayed in the vicinity of the heartbeat waveform 72 as a numerical value.

  FIG. 5 <C> shows a display image in which the tomographic image 22 and the heart rate waveform 74 are arranged one above the other. The heart rate waveform 74 is a waveform showing a change in heart rate over a plurality of time phases. For example, for each time phase, the heart rate at that time phase (for example, in the vicinity of that time phase), depending on the height of the waveform. It is a waveform showing the average heart rate.

  FIG. 5 <D> shows a display image including the tomographic image 22, the heartbeat waveform 72, and the heartbeat waveform 74. It is desirable that the heart rate waveform 72 and the heart rate waveform 74 are displayed with the time phases aligned (synchronized) with each other.

  6 to 9 are diagrams for explaining the heartbeat waveform 72 shaping process. When the heartbeat waveform 72 is formed using the average value or correlation value of pixels as a waveform value, a bias component that varies with time tends to be included. Therefore, the heartbeat waveform processing unit 70 suppresses temporal variation of the bias component in the heartbeat waveform 72 that periodically changes over a plurality of time phases, and forms a shaped waveform 73 that shapes the heartbeat waveform 72. . Then, a shaped waveform 73 is displayed on the display unit 82 instead of the heartbeat waveform 72 or together with the heartbeat waveform 72.

  FIG. 6 is a diagram illustrating a specific example of the shaping process using the extreme value of the heartbeat waveform 72. The heartbeat waveform processing unit 70 arranges a plurality of extreme values that appear in the heartbeat waveform 72 over a plurality of time phases by aligning the sizes of the plurality of extreme values while maintaining the time phases of the respective extreme values. 73 is formed.

  The heartbeat waveform processing unit 70 first detects a plurality of maximum points (peak points) included in the heartbeat waveform 72 over a plurality of frames, and selects an arbitrary maximum point from the plurality of maximum points as a reference point (reference peak). And Then, the waveform value at the reference point is set as a reference value (for example, 1.0 p), and the waveform values at other local maximum points are normalized based on the reference value. That is, the waveform values at other local maximum points are calculated based on the relative size with respect to the reference value. FIG. 6 shows standardized waveform values (0.5p, 0.9p, 0.9p, 1.0p,...) Of a plurality of maximum points included in the heartbeat waveform 72.

  Next, the heartbeat waveform processing unit 70 calculates an inverse of the ratio between the reference value and the normalized waveform value of the plurality of local maximum points, and calculates the plurality of inverses corresponding to the local maximum points along the time phase direction. A weighting factor connected by a line is formed. FIG. 6 shows a plurality of reciprocals corresponding to a plurality of local maximum points (1.0 / 0.5, 1.0 / 0.9, 1.0 / 0.9, 1.0 / 1.0,... The weighting coefficient connecting ()) with a broken line is shown. A curved weight coefficient obtained by smoothing the polygonal line may be formed.

  Then, the heartbeat waveform processing unit 70 forms a shaped waveform 73 by multiplying the heartbeat waveform 72 by a weighting coefficient. That is, the waveform value of each time phase of the heartbeat waveform 72 is multiplied by the weighting coefficient corresponding to that time phase, and a shaped waveform value corresponding to that time phase is calculated, and a plurality of shaped waveform values corresponding to a plurality of time phases are calculated. Are combined to form a shaped waveform 73.

  The shaped waveform 73 formed in this way has the waveform values (maximum values) of a plurality of maximum points aligned, and the temporal fluctuation of the bias component included in the heartbeat waveform 72 is suppressed. The variation is completely eliminated.

  Instead of the plurality of maximum points, the shaped waveform 73 may be formed by aligning the sizes of the plurality of minimum points. Moreover, the shaping waveform 73 may be formed by aligning an intermediate point between the maximum point and the minimum point.

  FIG. 7 is a diagram illustrating a specific example of the shaping process using the intermediate value of the heartbeat waveform 72. The heartbeat waveform processing unit 70 maintains a time phase of each intermediate value with respect to a plurality of intermediate values appearing between adjacent maximum and minimum values in the heartbeat waveform 72 over a plurality of time phases. By adjusting the size of the intermediate value, the shaped waveform 73 is formed.

  The heartbeat waveform processing unit 70 first detects a plurality of local maximum points (peak points) and a plurality of local minimum points (valley points) included in the heartbeat waveform 72 over a plurality of frames, and detects the local maximum points and local minimum points adjacent to each other. An intermediate point (intermediate point of waveform value or intermediate point of time phase) is set, and an arbitrary intermediate point among a plurality of intermediate points is set as a reference point.

  Then, the heartbeat waveform processing unit 70 sets the waveform value at the reference point as a reference value (for example, 1.0 p), shapes the heartbeat waveform 72 so that the waveform values at the other plurality of intermediate points are aligned with the reference value, and performs shaping. A waveform 73 is formed. As in the case of FIG. 6, the shaped waveform 73 of FIG. 7 may be formed using a weighting factor.

  FIG. 8 is a diagram illustrating a specific example of shaping processing for aligning the maximum value and the minimum value of the heartbeat waveform 72. The heartbeat waveform processing unit 70 arranges a plurality of extreme values that appear in the heartbeat waveform 72 over a plurality of time phases by aligning the sizes of the plurality of extreme values while maintaining the time phases of the respective extreme values. 73 is formed.

  The heartbeat waveform processing unit 70 first detects a plurality of maximum points (peak points) and a plurality of minimum points (valley points) included in the heartbeat waveform 72 over a plurality of frames. Further, the heartbeat waveform processing unit 70 aligns a plurality of local maximum points with a constant size while maintaining the time phase of each local maximum point, and maintains a plurality of local minimum points with a constant size while maintaining the time phase of each local minimum point. Align (smaller than the maximum point). Then, the heartbeat waveform processing unit 70 forms a shaped waveform 73 by connecting a plurality of local maximum points and a plurality of local minimum points with a curve such as a spline.

  FIG. 9 is a diagram showing another specific example of shaping processing for aligning the maximum value and the minimum value of the heartbeat waveform 72. The heartbeat waveform processing unit 70 first detects a plurality of local maximum points (peak points) and a plurality of local minimum points (valley points) included in the heartbeat waveform 72 over a plurality of frames, and detects local maximum points and local minimum points adjacent to each other. Set the interval between. In FIG. 9, as a specific example of the set section, section 1 from the maximum point H (1) to the minimum point L (1) and section 2 from the minimum point L (1) to the maximum point H (2). Is shown.

Then, the heartbeat waveform processing unit 70 calculates a shaped waveform value based on the following equation for each section to form a shaped waveform 73.
[Formula 1] Shaped waveform value = {(graph height) / (maximum value−minimum value)} × (waveform value−minimum value)
In the above equation, “graph height” is the height from the minimum value to the maximum value of the shaped waveform 73, and the “maximum value” and the “minimum value” in section 1 are H (1) and L (1), respectively. The “maximum value” and “minimum value” in section 2 are H (2) and L (1), respectively. The “waveform value” is the waveform value Diff (i) of each time phase (frame number i) in the heartbeat waveform 72.

  FIG. 10 is a diagram illustrating a display example of the shaped waveform 73. FIG. 10 shows a specific example of the display image formed by the display image forming unit 80 and displayed on the display unit 82.

  FIG. 10 <A> shows a display image in which the tomographic image (B-mode image) 22 and the shaped waveform 73 are arranged one above the other. For example, the average heart rate (BPM) may be displayed as a numerical value in the vicinity of the shaped waveform 73. Further, a line-shaped mark indicating the positions of a plurality of maximum points (peaks) included in the shaped waveform 73 may be displayed.

  Note that marks indicating the positions of a plurality of local maximum points (peaks) are not limited to line segments, and for example, dot-like marks shown in FIG. 10 <B> and arrow-like marks shown in FIG. 10 <C> are displayed. May be. Further, a mark indicating the position of a plurality of minimum points may be displayed instead of or together with the plurality of maximum points.

  FIG. 11 to FIG. 13 are diagrams for explaining functions related to the evaluation of the stability with respect to the heart rate or the heart cycle. In the measurement of the fetal heart rate or heartbeat cycle using an ultrasound image, there may be a section in which heartbeat movement can be stably measured and a section in which stable heartbeat movement cannot be measured. Therefore, the heartbeat waveform processing unit 70 determines a period with a stable period in the heartbeat waveform 72 or the shaped waveform 73, and forms a display mode indicating the period with a stable period, for example.

  FIG. 11 is a diagram for explaining a determination process in a period with a stable cycle. In the heartbeat waveform 72 or the shaped waveform 73, the heartbeat waveform processing unit 70 calculates a heartbeat cycle based on, for example, a period of two adjacent maximum points or a period of two adjacent minimum points. . Then, a variance value is calculated for N heartbeat cycles obtained within an N sample length gate period including N local maximum values or local minimum values.

  The heartbeat waveform processing unit 70 calculates the variance value of the heartbeat period for each frame while moving the N sample length gate period frame by frame, for example, and the gate period whose variance value is smaller than the threshold value It is determined that it is a period. Then, in the heartbeat waveform 72 or the shaped waveform 73, a period in which the cycle is stable and a period other than that are different from each other, for example.

  FIG. 11 shows a specific example of a display mode in which the waveform portion of the heartbeat period 72 or the shaped waveform 73 is a solid line and the waveform portion of the heartbeat period is unstable. Has been.

  FIG. 12 is a diagram illustrating a display example of a stable period in the heartbeat waveform 72 or the shaped waveform 73. FIG. 12 shows a specific example of a display image formed by the display image forming unit 80 and displayed on the display unit 82. FIGS. 12A to 12C each show a display image in which the tomographic image (B-mode image) 22 and the heartbeat waveform 72 or the shaped waveform 73 are arranged one above the other.

  FIG. 12 <A> shows a display mode in which a stable period and other periods are identified by a difference in color or brightness in the heartbeat waveform 72 or the shaped waveform 73. Further, FIG. 12 <B> shows a display mode in which markers are formed at, for example, extreme values in the stable period and other periods are identified.

  FIG. 12 <C> shows a display mode in which, for example, a heart-shaped marker blinks or lights up when the heartbeat waveform 72 or the shaped waveform 73 is stably obtained during real-time measurement, for example. Further, a sound effect may be generated in accordance with the blinking or lighting of the marker.

  For example, when the unstable period is set in advance and exceeds a set value, a message or the like that prompts the user (inspector) to perform re-measurement may be displayed. Alternatively, the heart rate and the heart cycle may be calculated using a waveform only during a stable period. In addition, among the multiple heart rate or heart rate cycle obtained within a certain period, the remaining average value excluding some of the upper (large value) and lower (small value) is displayed as a stable heart rate or heart rate cycle. May be.

  FIG. 13 is a diagram illustrating another display example of the measurement result. FIG. 13 shows a specific example of a display image formed by the display image forming unit 80 and displayed on the display unit 82. FIGS. 13A to 13D each show a display image in which the tomographic image (B-mode image) 22 and the heartbeat waveform 72 or the shaped waveform 73 are arranged one above the other.

  FIG. 13 <A> shows a display mode in which the average heart rate (BPM) and the variation in heart rate are represented by numerical values. For example, the variation is calculated from the variance value described with reference to FIG. Note that a variance value, a standard deviation, or the like when a Gaussian distribution is assumed may be displayed as a numerical value. FIG. 13 <B> shows a display mode in which the maximum value (max) of the heart rate and the minimum value (min) of the heart rate are represented by numerical values in addition to the average value (ave) of the heart rate.

  FIG. 13 <C> shows a display mode in which the heart rate in each time phase is represented by a numerical value in the vicinity of the heartbeat waveform 72 or the shaped waveform 73. Further, as shown in FIG. The color and brightness of the heart rate value may be different between the stable period and other periods. In addition, the display mode (color and brightness) of waveforms and numerical values may be different for tachycardia, bradycardia, and normal regions, and since the heart rate generally changes depending on the number of weeks of the fetus, based on the input value of the number of weeks A function for determining tachycardia or bradycardia may be realized.

  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. The present invention includes various modifications without departing from the essence thereof.

  DESCRIPTION OF SYMBOLS 10 probe, 12 transmission / reception part, 20 ultrasonic image formation part, 30 reference area setting part, 50 tracking process part, 60 movement process part, 70 heart rate waveform process part, 80 display image formation part.

Claims (7)

A probe that transmits and receives ultrasound for a diagnostic region including a subject;
A transmission / reception unit for controlling the probe to obtain an ultrasonic reception signal from the diagnostic region;
In the image data of the diagnostic region obtained based on the received signal, the first reference region is set so as to include the outer portion of the target site while avoiding the target site of the subject, and the second reference is set so as to include the target site. A reference area setting unit for setting a reference area;
A tracking processing unit for tracking a subject moving in the image data over a plurality of time phases based on the image data in the first reference region;
A movement processing unit that moves the second reference region so as to follow the subject moving in the image data over a plurality of time phases based on the result of the tracking;
A diagnostic waveform processing unit that forms a diagnostic waveform that reflects the motion of the region of interest based on image data in a second reference region that moves over a plurality of time phases;
Having
An ultrasonic diagnostic apparatus. The ultrasonic diagnostic apparatus according to claim 1,
In the diagnostic waveform that periodically changes over a plurality of time phases, the diagnostic waveform processing unit forms a shaped waveform in which the diagnostic waveform is shaped by suppressing temporal variation of the bias component.
An ultrasonic diagnostic apparatus. The ultrasonic diagnostic apparatus according to claim 2,
The diagnostic waveform processing unit, for a plurality of extreme values appearing in the diagnostic waveform over a plurality of time phases, aligns the magnitudes of the plurality of extreme values while maintaining the time phases of the respective extreme values, thereby shaping the shaped waveform. Form,
An ultrasonic diagnostic apparatus. The ultrasonic diagnostic apparatus according to claim 2,
The diagnostic waveform processing unit is configured to maintain a plurality of intermediate values while maintaining a time phase of each intermediate value for a plurality of intermediate values appearing between a maximum value and a minimum value adjacent to each other in a diagnostic waveform over a plurality of time phases. Forming the shaped waveform by aligning the magnitudes of the values;
An ultrasonic diagnostic apparatus. In the ultrasonic diagnostic apparatus according to any one of claims 1 to 4,
The diagnostic waveform processing unit evaluates the stability of a period that fluctuates over a plurality of time phases in the diagnostic waveform based on the diagnostic waveform that periodically changes, and a display mode according to the evaluation result Forming,
An ultrasonic diagnostic apparatus. The ultrasonic diagnostic apparatus according to claim 5,
The diagnostic waveform processing unit forms a display mode indicating a period with a stable period in the diagnostic waveform;
An ultrasonic diagnostic apparatus. The ultrasonic diagnostic apparatus according to any one of claims 1 to 6,
The reference area setting unit sets a second reference area so as to include a fetal heart in the image data, and sets the first reference area so as to surround the second reference area;
An ultrasonic diagnostic apparatus.

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