JP2011156251A - Ultrasonograph - Google Patents

Abstract

<P>PROBLEM TO BE SOLVED: To actualize a reconfiguration process of an image acquired from a fluid body varying periodically. <P>SOLUTION: A pre-memory 14 stores a plurality of sets of tomographic image data in a time-series order. A Doppler virtual period calculating section 22 calculates a virtual period from the plurality of sets of tomographic image data relating to Doppler images included in the plurality of sets of tomographic image data. A Doppler base image searching section 24 searches for a plurality of base images from the plurality of sets of tomographic image data relating to the Doppler images using the virtual period. A reconfiguration processing section 20 uses each of the plurality of base images as a unit for the division to divide the plurality of sets of tomographic image data stored in the pre-memory 14 into a plurality of image groups. <P>COPYRIGHT: (C)2011,JPO&INPIT

Description

  The present invention relates to an ultrasonic diagnostic apparatus that forms a display image of a fluid that fluctuates periodically.

  2. Description of the Related Art An ultrasonic diagnostic apparatus that forms a three-dimensional ultrasonic image of a tissue that accompanies motion such as the heart is known. For example, there is a technology that scans an ultrasonic beam in a three-dimensional space, collects echo data from the three-dimensional space, forms a three-dimensional ultrasonic image based on the collected echo data, and displays it in real time. It has been. However, in the case of real-time display, there is a principle restriction that the scan rate, the beam density, and the beam range are in a trade-off relationship with each other.

  Techniques for avoiding the fundamental limitations in real-time display of 3D ultrasound images have also been proposed. For example, Patent Document 1 collects a plurality of tomographic image data over a plurality of time phases at each position on the scanning plane while moving the scanning plane little by little in the three-dimensional space in synchronization with an electrocardiogram signal or the like. A technique (reconstruction process or reconstruction process) is described in which a plurality of collected tomographic image data is rearranged and reconstructed to form three-dimensional image data. This technique is difficult to apply to a fetus or the like for which it is difficult to directly obtain an electrocardiogram signal.

  Patent Document 2 describes a technique for scanning and reconstructing at certain time intervals instead of an electrocardiographic signal. However, this technique assumes that the period of the heart, etc. during data collection is constant, so that, for example, if the period of the heart is not constant, the shape of the heart in the reconstructed image is distorted from the actual one. Reliability may be reduced.

Japanese Patent No. 3537594 JP 2005-74225 A

  In view of the background art described above, the inventor of the present application has repeatedly researched and developed a technique for forming an ultrasonic image by reconstruction processing. In particular, we focused on reconstruction processing of images obtained from fluids such as blood flow.

  The present invention has been made in the course of research and development, and an object thereof is to realize a reconstruction process of an image obtained from a fluid that fluctuates periodically. Another object of the present invention is to improve the reliability of a display image related to a fluid that fluctuates periodically.

  An ultrasonic diagnostic apparatus suitable for the above object includes a probe for transmitting and receiving ultrasonic waves in a three-dimensional space including a periodically changing fluid, and a plurality of cycles related to the change of the fluid by controlling the probe. A transmission / reception control unit that forms a plurality of scanning planes in a three-dimensional space while moving the scanning plane, and corresponds to a virtual period related to the variation of the fluid from a plurality of images corresponding to the plurality of scanning planes. By dividing each of the plurality of reference images into a plurality of image groups by dividing each of the plurality of reference images into a plurality of image groups by searching for a plurality of reference images at intervals, An image reconstruction unit that extracts a plurality of images that periodically correspond to each other from each of the image groups, and a display image formation unit that forms a display image of the fluid based on the plurality of images that periodically correspond to each other Have It is characterized in.

  In a preferred embodiment, the reference image search unit searches the plurality of reference images from a plurality of Doppler images included in a plurality of images corresponding to a plurality of scanning planes.

  In a preferred specific example, the ultrasonic diagnostic apparatus further includes a virtual period calculation unit that calculates the virtual period based on a feature amount related to periodicity obtained from the plurality of Doppler images.

  In a preferred embodiment, the image reconstruction unit divides the image sequence including a plurality of Doppler images discretely arranged in the order of arrangement of a plurality of scanning planes in a three-dimensional space into a plurality of image groups. A plurality of images periodically corresponding to each other are extracted from each of the image groups.

  In a preferred embodiment, the display image forming unit indicates flow velocity information of the fluid existing in the tissue based on a plurality of tissue images and a plurality of Doppler images included in the plurality of images periodically corresponding to each other. Forming a displayed image.

  In a desirable specific example, the display image forming unit once obtains a plurality of flow velocity information obtained over a plurality of time phases for each time phase by associating a plurality of images periodically corresponding to one time phase. The display image displayed on is formed.

  According to the present invention, it is possible to reconstruct an image obtained from a periodically changing fluid.

1 is a diagram illustrating an overall configuration of an ultrasonic diagnostic apparatus that is preferable in the practice of the present invention. It is a figure for demonstrating three-dimensional scanning. It is a figure which shows the change of a cross-sectional difference value. It is a figure which shows the change of a mutual difference value. It is a figure for demonstrating the search of a reference | standard image. It is a figure for demonstrating the process by the reconstruction process part. It is a figure for demonstrating another suitable process by the reconstruction process part. It is a figure for demonstrating the image which showed several flow velocity information over several time phases.

  Hereinafter, preferred embodiments of the present invention will be described.

  FIG. 1 is a diagram showing an overall configuration of an ultrasonic diagnostic apparatus suitable for implementing the present invention. The probe 10 transmits and receives ultrasonic waves in a three-dimensional space including a fluid to be diagnosed. The probe 10 includes a plurality of vibration elements that transmit and receive ultrasonic waves. The plurality of vibration elements are transmission-controlled by the beam former 12 to form a transmission beam. In addition, a plurality of vibration elements receive ultrasonic waves reflected from a fluid or the like, and a signal obtained thereby is output to the beam former 12, and the beam former 12 forms a reception beam.

  The probe 10 of the present embodiment is a 3D probe that collects echo data three-dimensionally by scanning an ultrasonic beam (a transmission beam and a reception beam) in a three-dimensional space. For example, the ultrasonic beam is scanned three-dimensionally by mechanically moving a scanning surface formed electronically by a plurality of vibration elements (1D array transducers) arranged one-dimensionally. Alternatively, the ultrasonic beam may be scanned three-dimensionally by electronically controlling a plurality of vibration elements (2D array transducers) arranged two-dimensionally.

  The beam former 12 forms an ultrasonic transmission beam by supplying a transmission signal corresponding to each of a plurality of vibration elements included in the probe 10. In addition, the beam former 12 forms an ultrasonic reception beam by performing a phasing addition process or the like on a reception signal obtained from each of a plurality of vibration elements included in the probe 10, and is obtained along the reception beam. Output echo data.

  The diagnosis target in the present embodiment is a fluid that fluctuates periodically, for example, a fluid such as blood flow. More specifically, for example, blood flow that flows through blood vessels in the brain of the fetus, blood flow that flows through blood vessels in the placenta, and the like. Of course, the diagnosis object in the present invention is not limited to these examples. In the present embodiment, a plurality of scanning planes are formed in the three-dimensional space while moving the scanning plane over a plurality of cycles of fluctuations related to the fluid.

  The tomographic image forming unit 13 forms a tomographic image corresponding to each of the plurality of scanning planes based on the echo data obtained from the beam former 12. The tomographic image forming unit 13 forms a tissue image equivalent to the B-mode image based on the echo intensity (echo size) obtained from the echo data, and color doppler based on the Doppler information obtained from the echo data. The Doppler image is formed.

  FIG. 2 is a diagram for explaining three-dimensional scanning in the present embodiment. In FIG. 2, the three-dimensional space including the fluid to be diagnosed is expressed in an XYZ orthogonal coordinate system. In this embodiment, the scanning plane is formed so as to be substantially parallel to the XY plane, and a plurality of scanning planes are formed along the Z-axis direction while slowly moving the scanning plane in the Z-axis direction. . The scanning plane moves slowly in the Z-axis direction over a plurality of periods related to periodic fluctuations of a fluid such as blood flow, for example, over a period including fluctuations of about 20 heartbeats in about 8 seconds.

  In the present embodiment, the scanning plane B corresponding to the tissue image and the scanning plane D corresponding to the Doppler image are alternately formed along the Z-axis direction. Note that the arrangement of the scanning plane B and the scanning plane D may be changed as appropriate, such as alternately forming a plurality of scanning planes B and a single scanning plane D.

  Returning to FIG. 1, when a plurality of scanning surfaces are formed along the Z-axis direction over a plurality of periods of periodic fluctuations of the fluid, as described above, the tomographic image forming unit 13 performs each scanning surface. A tomographic image is formed, and data of a plurality of tomographic images corresponding to a plurality of scanning planes are successively stored in the previous memory 14.

  The error determination unit 16 determines whether or not the plurality of tomographic image data is good based on the difference amount between the images obtained from the plurality of tomographic image data stored in the previous memory 14. For example, there is a possibility that a good image cannot be obtained because a diagnosis target such as a blood flow greatly moves in the image due to the movement of the fetus, mother or probe. Therefore, the error determination unit 16 determines whether or not a good image for diagnosis can be obtained by using a plurality of tomographic image data related to, for example, a Doppler image stored in the previous memory 14. In the determination, the error determination unit 16 uses a cross-sectional difference value defined by the following equation.

  In Equation 1, x, y, and z are coordinate values on each axis in the XYZ orthogonal coordinate system of FIG. 2, and p is a Doppler shift amount (speed value) corresponding to each coordinate in the tomographic image data regarding the Doppler image. . A difference value between two Doppler images adjacent in the Z-axis direction is calculated by Equation (1).

  FIG. 3 is a diagram showing changes in cross-sectional difference values, and the horizontal axis of FIG. 3 shows the position of each tomographic image data (position of each Doppler image). That is, the horizontal axis in FIG. 3 indicates the position of each scanning plane D in FIG. 2 and corresponds to the Z axis in FIG. 2 (the change direction of the position with the passage of time).

  If the fetal blood vessels and the like do not move greatly, adjacent tomographic image data will be similar to each other, and the difference value obtained from Equation 1 will be relatively small. On the other hand, for example, if there is a movement of the fetus itself, a breathing movement of the mother, a large displacement of the position of the probe 10, the blood vessel of the fetus moves greatly in the tomographic image, and the difference value between adjacent tomographic image data is compared. Become bigger. Therefore, when the cross-sectional difference value exceeds a predetermined threshold value, the error determination unit 16 determines that the blood vessel or the like to be diagnosed has greatly shifted in the image.

  Returning to FIG. 1, when the error determination unit 16 determines that the diagnosis target has greatly deviated, the control unit 40 controls, for example, the beam former 12 to stop collecting tomographic image data. The control unit 40 controls each unit in FIG. 1 in a concentrated manner. For example, when the error determination unit 16 determines that an error has occurred, the display unit 30 displays a display or warning indicating an error. May be displayed. If the error determination unit 16 does not determine an error, a process to be described later is executed based on a plurality of tomographic image data stored in the previous memory 14.

  The Doppler virtual cycle calculation unit 22 calculates a virtual cycle serving as a temporary cycle related to a change in fluid such as blood flow, based on a plurality of tomographic image data stored in the previous memory 14. The Doppler virtual cycle calculation unit 22 calculates a virtual cycle from a plurality of tomographic image data related to the Doppler image. In calculating each virtual period, the Doppler virtual period calculation unit 22 uses a mutual difference value defined by the following equation.

  In Equation 2, x, y, and z are coordinate values on each axis in the XYZ orthogonal coordinate system of FIG. 2, and p is a Doppler shift amount (velocity value) corresponding to each coordinate in the tomographic image data regarding the Doppler image. is there. In Formula 2, one pixel value is multiplied by the difference between two pixel values (Doppler shift amount) between two tomographic image data adjacent in the Z-axis direction. As a result, the relative difference value is relatively large in the case of blood flow when the heart expands compared to the blood flow when the heart contracts, and the time phase corresponding to expansion that is difficult to identify with a simple difference value And the time phase corresponding to the contraction can be identified by the mutual difference value.

  FIG. 4 is a diagram illustrating changes in mutual difference values. The horizontal axis of FIG. 4 indicates the position of each tomographic image data (position and time of each scanning plane), and corresponds to the Z axis of FIG. 2 (change direction of position with time). For example, when a mutual difference value is calculated at each position (z) on the Z-axis for a plurality of tomographic image data related to a Doppler image using Equation 2, a mutual difference value corresponding to the case where the heart expands Is a relatively large value. Therefore, the Doppler virtual cycle calculation unit 22 detects the peak value (maximum value) of the mutual difference value, and determines the interval between adjacent peak values as the cycle of blood flow fluctuation (corresponding to the heartbeat cycle).

  However, for example, in the fetal heart, the heartbeat period may fluctuate, and when the heartbeat period fluctuates, the interval between peak values also fluctuates. Therefore, the Doppler virtual cycle calculation unit 22 sets, for example, the second largest interval among the peak value intervals as the virtual cycle. It should be noted that the most frequently used value or centroid value obtained from the peak value interval histogram may be used as the virtual period. Further, the user or device may select the virtual period from a plurality of preset values, or the user may input the value of the virtual period. As the virtual cycle, a value obtained based on a measurement result (for example, a result of M-mode measurement) of the ultrasonic diagnostic apparatus may be used, or a fixed value may be used constantly.

  Returning to FIG. 1, when the virtual period is set, the Doppler reference image search unit 24 searches the plurality of reference images from the plurality of tomographic image data using the virtual period. The Doppler reference image search unit 24 searches for a plurality of reference images from a plurality of tomographic image data related to the Doppler image.

  FIG. 5 is a diagram for explaining the search for the reference image. Each of FIGS. 5A to 5C shows a change in the mutual difference value described with reference to FIG. The Doppler reference image search unit 24 searches the plurality of tomographic images related to the Doppler image by executing the process shown in FIG. 5 using the virtual period and searches for the plurality of reference images.

  First, the Doppler reference image search unit 24 searches for a representative reference image (representative reference image) from a plurality of tomographic images. As illustrated in FIG. 5A, the Doppler reference image search unit 24 sets tomographic image data corresponding to the position where the mutual difference value is maximum as a representative reference image (representative reference cross section). Then, the Doppler reference image search unit 24 sequentially searches for a tomographic image closest to a position separated by a virtual period from a plurality of tomographic images corresponding to the maximum mutual difference value with the representative reference image as a starting point.

  For example, as shown in FIG. 5A, a tomographic image closest to a position separated from the representative reference image by a virtual period (VHR) in the positive and negative directions in the Z-axis direction is searched and used as the reference image. Next, as illustrated in FIG. 5B, the Doppler reference image search unit 24 searches for a tomographic image closest to a position separated from the searched reference image by a virtual period (VHR) to be a new reference image. . In FIG. 5B, broken arrows indicate the positions of a plurality of reference images (reference cross sections).

  The Doppler reference image search unit 24 searches a plurality of reference images one after another using the representative reference image as a starting point. In this way, a plurality of reference images are searched from a plurality of tomographic images corresponding to the maximum mutual difference values as shown in FIG. In FIG. 5C, dashed arrows indicate the positions of a plurality of reference images (reference cross sections).

  Returning to FIG. 1, when a plurality of reference images are searched, the reconstruction processing unit 20 divides the plurality of tomographic images into several image groups by using each of the plurality of reference images as a unit of division. . And the reconstruction process part 20 implement | achieves a reconstruction process (reconstruction process) by extracting the some tomographic image corresponding to each other periodically from each of several image groups. The reconstruction processing unit 20 reconstructs a plurality of tomographic image data stored in the previous memory 14 and stores it in the rear memory 26.

  FIG. 6 is a diagram for explaining processing by the reconstruction processing unit 20. FIG. 6 shows a correspondence relationship between data stored in the previous memory 14 and data stored in the rear memory 26. . In FIG. 6, “tomographic image Zn (n = 1, 2, 3,..., 60)” means tomographic image data at the position of the coordinate Zn on the Z axis (see FIG. 2).

  The previous memory 14 stores a plurality of tomographic image data corresponding to a plurality of scan planes formed one after another along the Z-axis direction. That is, the previous memory 14 stores a plurality of tomographic image data in the order of tomographic images Z1, tomographic images Z2,..., Tomographic images Z60,.

  For example, among the plurality of tomographic images Zn stored in the previous memory 14, a tomographic image with an odd number n is a tissue image, and a tomographic image with an even number n is a Doppler image. For example, the tissue image and the Doppler image are alternately stored in the previous memory 14 in a state where the tissue image and the Doppler image are mixed.

  The reconstruction processing unit 20 divides the plurality of tomographic image data stored in the previous memory 14 into a plurality of image groups by using each of the plurality of reference images as a unit of division. Then, a plurality of tomographic image data periodically corresponding to each other is extracted from each of the plurality of image groups.

  In FIG. 6, tomographic image Z1, tomographic image Z15,..., Tomographic image Z51 are tomographic images corresponding to the reference image. The reconstruction processing unit 20 first extracts a tomographic image Z1, a tomographic image Z15,..., A tomographic image Z51, which are reference images, as a plurality of tomographic image data periodically corresponding to each other. Then, the extracted tomographic image Z1, tomographic image Z15,..., And tomographic image Z51 are stored in the rear memory 26 as one data block.

  Next, the reconstruction processing unit 20 extracts a plurality of tomographic images adjacent in the positive direction in the Z-axis direction to each of the plurality of reference images as a plurality of tomographic image data periodically corresponding to each other. That is, the tomographic image Z2, the tomographic image Z16,..., And the tomographic image Z52 are extracted and stored in the rear memory 26 as one data block.

  Further, the reconstruction processing unit 20 extracts a plurality of tomographic images adjacent to each of the tomographic image Z2, the tomographic image Z16,. In this way, data blocks of a plurality of tomographic images periodically corresponding to each other from each of the plurality of reference images are sequentially extracted and stored in the rear memory 26.

  In the example shown in FIG. 6, the data block corresponding to the reference image is the head of the plurality of data blocks. For example, a plurality of data blocks are formed so that the data block corresponding to the reference image is at the center. Also good.

  FIG. 7 is a diagram for explaining another preferable process by the reconstruction processing unit 20. Like FIG. 6, FIG. 7 shows data stored in the front memory 14 and stored in the rear memory 26. Correspondences between data are shown.

  In the example shown in FIG. 7, a plurality of division positions are set. The plurality of division positions are set, for example, at locations separated from each of the plurality of reference images by a specified interval. The designated interval is set to, for example, half of the minimum interval among the intervals between the reference images adjacent to each other. Note that the user may be able to set a specified interval (for example, time, number of frames, etc.) as appropriate.

  In the example shown in FIG. 7, the reconstruction processing unit 20 divides a plurality of tomographic images (data) stored in the previous memory 14 into a plurality of image groups by setting each of a plurality of division positions as division boundaries. To do. Then, a plurality of tomographic images periodically corresponding to each other are extracted from each of the plurality of image groups. In FIG. 7, the tomographic image Z5, the tomographic image Z35, and the tomographic image Z65 are images corresponding to the reference image, and the tomographic image Z1, the tomographic image Z31, and the tomographic image Z61 are images corresponding to the division positions.

  The reconstruction processing unit 20 first extracts tomographic images Z1,..., Tomographic images Z31,..., Tomographic images Z61 corresponding to the division positions as a plurality of tomographic images periodically corresponding to each other. The tomographic images Z1,..., The tomographic images Z31,..., And the tomographic images Z61 are stored in the rear memory 26 as one data block.

  Next, the reconstruction processing unit 20 extracts and extracts a plurality of tomographic images adjacent in the positive direction in the Z-axis direction with respect to each of a plurality of division positions as a plurality of tomographic images that correspond periodically to each other. A plurality of tomographic images are stored in the rear memory 26 as one data block. Furthermore, the reconstruction processing unit 20 sequentially forms data blocks based on a plurality of tomographic images that correspond periodically to each other and stores them in the rear memory 26.

  In the process of sequentially forming a plurality of data blocks, the tomographic images Z5,..., The tomographic images Z35,..., And the tomographic images Z65 corresponding to the reference image become one data block in the rear memory 26. The tomographic image Z9,..., The tomographic image Z39,..., And the tomographic image Z69, which are the final images of each image group, are stored as one data block in the rear memory 26, and a plurality of data Block formation is complete. That is, the reconstruction process is completed.

  Returning to FIG. 1, the three-dimensional image forming unit 28 three-dimensionally displays a fluid such as a blood flow to be diagnosed based on a plurality of reconstructed tomographic image data stored in the post-memory 26. Form image data. The 3D image forming unit 28 forms 3D image data of each time phase based on one data block stored in the rear memory 26.

  The three-dimensional image forming unit 28 applies various methods such as a volume rendering method, an integration method, and a projection method, and forms three-dimensional image data for each time phase and over a plurality of time phases. . For example, in the volume rendering method, a plurality of rays are set for a three-dimensional data space composed of a plurality of tomographic image data constituting one data block, and volume rendering calculation is executed for each ray. At that time, for example, the calculation for the tissue image data on each ray and the calculation for the Doppler image data are executed separately. Then, based on the calculation result regarding the tissue image and the calculation result regarding the Doppler image on each ray, the final calculation result regarding the ray is calculated.

  In this way, the three-dimensional image forming unit 28 forms image data (three-dimensional image data) indicating the flow velocity information of the fluid obtained based on the Doppler image in the image in which the tissue is three-dimensionally projected. Then, an image corresponding to the three-dimensional image data formed over a plurality of time phases is displayed on the display unit 30, and a pseudo real-time three-dimensional moving image is displayed. For example, images corresponding to a plurality of time-phase three-dimensional image data may be repeatedly displayed to execute loop reproduction.

  In addition, when forming the display image over a plurality of time phases, the three-dimensional image forming unit 28 forms an image displaying flow velocity information obtained over a plurality of time phases at a time for each time phase. May be.

  FIG. 8 is a diagram for explaining an image showing a plurality of flow velocity information over a plurality of time phases. (A1) to (A3) show images corresponding to three-dimensional image data formed over a plurality of time phases. For example, (A1) is an image corresponding to 3D image data of time phase 1, and (A2) is an image corresponding to 3D image data of time phase 2. In each of the images shown in (A1) to (A3), fluid flow velocity information 50 is displayed on an image showing the tissue in three dimensions. The flow velocity information 50 is an image portion formed based on the Doppler image, and is, for example, an image portion colored according to the flow velocity of the fluid at that position. Accordingly, the portions having different flow velocities are colored differently. In FIG. 8, the difference in color, that is, the difference in flow velocity, is represented by the difference in the painting pattern related to the flow velocity information 50. Of course, in an actual ultrasonic image, instead of a color difference, an expression based on a pattern difference as shown in FIG. 8 may be used.

  As a display image over a plurality of time phases, for example, a moving image displaying images of each time phase may be provided in the order of (A1) to (A3). You may form the display image shown collectively over the time phase.

  (B) is a display image showing a plurality of flow velocity information 50 over a plurality of time phases at a time (simultaneously). That is, in (B), a plurality of flow velocity information 50 corresponding to (A1) to (A3) and subsequent time phases are displayed together. For example, the flow rate information 50 of all time phases is displayed in an overlapping manner according to a logical OR condition. The part based on the tissue image other than the flow velocity information 50 is desirably displayed for each time phase. For example, the part based on the tissue image other than the flow velocity information 50 is a moving image in which images of each time phase are displayed in the order of (A1) to (A3), and a plurality of flow velocities over a plurality of time phases in the moving image. Information 50 may be displayed as shown in FIG. Further, the flow rate information 50 of all time phases may be displayed together at once, or only some flow rate information 50 of some characteristic time phases may be selectively displayed together.

  The preferred embodiments of the present invention have been described above. According to the above-described embodiments, a plurality of reference images are searched from a plurality of Doppler images, and data blocks are reconstructed based on the plurality of reference images. Therefore, for example, even when the blood flow of a fetus whose heartbeat cycle is unstable is targeted for diagnosis, image disturbance associated with the cycle variation is reduced (preferably completely removed) and reliable. A high display image can be obtained.

  The above-described embodiments are merely examples in all respects, and do not limit the scope of the present invention. The present invention includes various modifications without departing from the essence thereof.

  10 probe, 12 beam former, 13 tomographic image forming unit, 16 error determining unit, 20 reconstruction processing unit, 22 Doppler virtual period calculating unit, 24 Doppler reference image searching unit, 28 three-dimensional image forming unit.

Claims (6)

A probe for transmitting and receiving ultrasonic waves in a three-dimensional space including a periodically changing fluid;
A transmission / reception control unit that forms a plurality of scanning planes in a three-dimensional space while moving the scanning planes over a plurality of periods related to fluctuations of the fluid by controlling a probe;
A reference image search unit for searching a plurality of reference images at an interval corresponding to a virtual period related to a change in the fluid from a plurality of images corresponding to a plurality of scanning planes;
By using each of the plurality of reference images as a unit of division, the image sequence composed of the plurality of images is divided into a plurality of image groups, and a plurality of images periodically corresponding to each other from each of the plurality of image groups. An image reconstruction unit for extracting
A display image forming unit for forming a display image of the fluid based on a plurality of images periodically corresponding to each other;
Having
An ultrasonic diagnostic apparatus. The ultrasonic diagnostic apparatus according to claim 1,
The reference image search unit searches the plurality of reference images from a plurality of Doppler images included in a plurality of images corresponding to a plurality of scanning planes.
An ultrasonic diagnostic apparatus. The ultrasonic diagnostic apparatus according to claim 2,
A virtual period calculation unit that calculates the virtual period based on a feature amount related to periodicity obtained from the plurality of Doppler images;
An ultrasonic diagnostic apparatus. The ultrasonic diagnostic apparatus according to any one of claims 1 to 3,
The image reconstruction unit divides the image sequence including a plurality of Doppler images discretely arranged in the arrangement order of a plurality of scanning planes in a three-dimensional space into a plurality of image groups, and each of the plurality of image groups Extract a plurality of images periodically corresponding to each other,
An ultrasonic diagnostic apparatus. In the ultrasonic diagnostic apparatus according to any one of claims 1 to 4,
The display image forming unit forms a display image indicating flow velocity information of the fluid existing in the tissue based on a plurality of tissue images and a plurality of Doppler images included in a plurality of images periodically corresponding to each other. To
An ultrasonic diagnostic apparatus. The ultrasonic diagnostic apparatus according to claim 5,
The display image forming unit displays a plurality of flow velocity information obtained over a plurality of time phases for each time phase by associating a plurality of images periodically corresponding to one time phase at a time. Forming,
An ultrasonic diagnostic apparatus.

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