JP6026466B2 - Image processing apparatus and ultrasonic diagnostic apparatus - Google Patents

Description

  The present invention provides information that can be analyzed by directly understanding the state of spatiotemporal changes in the mechanical excitement of the heart using three-dimensionally analyzed heart wall motion information. The present invention relates to an image processing apparatus and an ultrasonic diagnostic apparatus that support diagnosis of blood diseases and the like.

  Objective and quantitative evaluation of movements and functions related to biological tissues such as the myocardium is very important for diagnosis of the tissues. In image diagnosis using an ultrasonic image processing apparatus, various quantitative evaluation methods have been tried mainly using the heart as an example. For example, during normal myocardial contraction, it is known that the thickness increases in the wall thickness direction (short axis) and the length decreases in the long axis direction. In general, thickening and shortening are said to have different directions of motion and perpendicular to each other. On the other hand, by observing these motions and evaluating myocardial wall motion, for example, heart disease such as myocardial infarction The possibility of diagnosis support is suggested.

  In addition, as a technique for displaying the movement of the intimal surface of the heart or the like, for example, three-dimensional surface rendering display or bullseye display (or Polar-map display) is known. Typical examples include 4-dimensional TSI (Tissue Strain Imaging) and CFM (Contraction Front Mapping). By using these methods, it is possible to quantitatively observe the three-dimensional distribution of heart wall motion information.

  By the way, in recent studies, for example, in the diagnosis of ischemic heart disease, it has been found that it is effective to examine the state of spatiotemporal propagation of mechanical movement (mechanical excitement) as a heart pump. ing.

[Search on March 13, 2007], Internet <http://www.pac.ne.jp/71stJCS/jp/program.asp?session id = OE04 & program id = 11933 & free str = Contraction>

  However, the conventional display method of heart wall motion information cannot directly grasp or quantify the state of spatiotemporal propagation of mechanical excitement. For example, since CFM is intended to grasp the difference between the portions of the contraction peak timing, it cannot directly grasp the state of spatiotemporal propagation of the heart wall motion. For example, in the technique disclosed in Non-Patent Document 1, a distribution image of a site at a contraction peak at a certain time phase is provided. For this reason, it is possible to grasp the difference between the contraction peak timing parts, but it is impossible to directly grasp the spatiotemporal propagation state of the wall motion.

  The present invention has been made in view of the above circumstances, and it is possible to directly grasp and analyze the state of spatiotemporal propagation of the mechanical excitation of the heart using the three-dimensionally analyzed heart wall motion information. An object of the present invention is to provide an image processing apparatus and an ultrasonic diagnostic apparatus that provide useful information and mainly support diagnosis of ischemic diseases and the like.

  In order to achieve the above object, the present invention takes the following measures.

An image processing apparatus according to an embodiment generates motion information of the heart over a plurality of time phases by using a plurality of volume data related to the subject's heart collected along a time series. Region for which the tissue motion information is to be generated, using a threshold value that is a product of the means, the tissue motion information , and a spatial peak value in each time phase and a value α that is arbitrarily set to 0 or more and less than 1 The analysis means for extracting a specific region having a value related to the tissue motion information equal to or greater than the threshold value in a plurality of time phases, and the specific region for each of the plurality of time phases extracted by the analysis device are sequentially changed over time. And a control unit that causes the display unit to display propagation information in which the temporal variation of the singular region is expressed.

The ultrasonic diagnostic apparatus according to an embodiment uses the plurality of volume data related to the subject's heart collected along a time series, and exercise information that generates tissue motion information of the heart over a plurality of time phases. Using the generation means , a threshold value that is a product of the tissue motion information , and a spatial peak value at each time phase and a value α that is arbitrarily set to 0 or more and less than 1 , the tissue motion information is generated. An analysis unit that extracts a specific region having a value related to the tissue motion information in the region having the threshold value or more in a plurality of time phases, and the specific region for each of the plurality of time phases extracted by the analysis unit over time. And a control unit that causes the display unit to display propagation information in which temporal variations of the singular region are expressed by updating one after another.

  As described above, according to the present invention, using the heart wall motion information analyzed three-dimensionally, it is possible to provide information that can directly grasp and analyze the state of spatiotemporal propagation of the mechanical excitement of the heart. In addition, an image processing apparatus and an ultrasonic diagnostic apparatus that support diagnosis of an ischemic disease or the like can be realized.

FIG. 1 is a configuration diagram of an ultrasonic diagnostic apparatus 1 according to the first embodiment. FIG. 2 is a flowchart showing the flow of each process executed in the process according to the excitement propagation information generation function (excitement propagation information generation process). FIG. 3 is a diagram for explaining the wall thickness direction, the major axis direction, and the circumferential direction of the heart. FIG. 4 is a diagram showing a position example of the display form of the mapping image (surface rendering image) and the excitation propagation information on the display unit 23. FIG. 5 is a diagram illustrating an example of a display form of a mapping image (Polar-Mapping image) and excitement propagation information according to the first embodiment. FIG. 6 is a diagram showing a display example when a locus line is drawn by assigning different colors for each time phase. FIG. 7 is a diagram illustrating another example of the display form of the mapping image and the excitation propagation information according to the first embodiment. FIG. 8 is a flowchart showing the flow of each process executed in the excitement propagation information generation process according to the second embodiment. FIG. 9 is a diagram illustrating an example of a display form of a mapping image and excitement propagation information according to the second embodiment. FIG. 10 is a diagram showing another example of the display form of the mapping image and excitement propagation information according to the second embodiment.

  Hereinafter, first and second embodiments of the present invention will be described with reference to the drawings. In the following description, components having substantially the same function and configuration are denoted by the same reference numerals, and redundant description will be given only when necessary.

  In the following embodiments, a case where the technical idea of the present invention is applied to an ultrasonic diagnostic apparatus will be described as an example. However, without being bound by this, the technical idea of the present invention can be applied to an ultrasonic image processing apparatus such as a workstation or a personal computer.

  In addition, for each component according to each embodiment, particularly, a movement vector processing unit 19, a motion information calculation unit 37, and an excitation propagation analysis unit 38 (see FIG. 1) described later, the same processing as that of each component is executed. It can also be realized by installing a software program in a computer such as a workstation, an ultrasonic diagnostic apparatus having a computer function, etc., and developing these on a memory. At this time, a program capable of causing the computer to execute the technique is stored in a recording medium such as a magnetic disk (floppy (registered trademark) disk, hard disk, etc.), an optical disk (CD-ROM, DVD, etc.), or a semiconductor memory. It can also be distributed.

(First embodiment)
FIG. 1 is a configuration diagram of an ultrasonic diagnostic apparatus 1 according to the first embodiment. The ultrasonic diagnostic apparatus 10 includes an ultrasonic probe 11, a transmission unit 13, a reception unit 15, a B-mode processing unit 17, a movement vector processing unit 19, an image generation unit 21, a display unit 23, a control unit (CPU) 31, and tracking. A processing unit 33, a volume data generation unit 35, a motion information calculation unit 37, an excitement propagation analysis unit 38, a storage unit 39, an operation unit 41, and a transmission / reception unit 43 are provided. When the present invention is applied to an ultrasonic image processing apparatus, the inside of the dotted line in FIG.

  The ultrasonic probe 11 generates ultrasonic waves based on a drive signal from the transmission unit 13 and converts a reflected wave from the subject into an electrical signal, a matching layer provided in the piezoelectric vibrator, It has a backing material that prevents the propagation of ultrasonic waves from the piezoelectric vibrator to the rear. When an ultrasonic wave is transmitted from the ultrasonic probe 11 to the subject, various harmonic components are generated along with the propagation of the ultrasonic wave due to nonlinearity of the biological tissue. The fundamental wave and the harmonic component constituting the transmission ultrasonic wave are back-scattered by the boundary of acoustic impedance of the body tissue, minute scattering, and the like, and are received by the ultrasonic probe 11 as a reflected wave (echo).

  The transmission unit 13 has a delay circuit, a pulsar circuit, etc. (not shown). In the pulsar circuit, a rate pulse for forming a transmission ultrasonic wave is repeatedly generated at a predetermined rate frequency fr Hz (period: 1 / fr second). Further, in the delay circuit, a delay time necessary for focusing the ultrasonic wave into a beam shape for each channel and determining the transmission directivity is given to each rate pulse. The transmission unit 13 applies a drive pulse to each transducer so that an ultrasonic beam is formed toward a predetermined scan line at a timing based on the rate pulse.

  The receiving unit 15 has an amplifier circuit, an A / D converter, an adder and the like not shown. The amplifier circuit amplifies the echo signal captured via the probe 11 for each channel. In the A / D converter, a delay time necessary for determining the reception directivity is given to the amplified echo signal, and thereafter, an addition process is performed in the adder. By this addition, an ultrasonic echo signal corresponding to a predetermined scan line is generated.

  The B mode processing unit 17 performs an envelope detection process on the ultrasonic echo signal received from the receiving unit 15, thereby generating a B mode signal corresponding to the amplitude intensity of the ultrasonic echo.

  The movement vector processing unit 19 detects the movement position of the tissue using pattern matching processing between two volume data having different time phases, and obtains the movement amount (or speed) of each tissue based on the movement position. Specifically, for the region of interest in one volume data, the corresponding region in the other volume data with the highest similarity is obtained. By obtaining the distance between the region of interest and the corresponding region, the amount of movement of the tissue can be obtained. Further, the moving speed of the tissue can be obtained by dividing this moving amount by the time difference between the volumes. By performing this processing volume-by-volume at each position on the volume, it is possible to acquire temporal and temporal distribution data relating to displacement (movement vector) of each tissue or tissue displacement. Here, the volume data is defined as a set of received signals having three-dimensional position information (that is, a set of received signals having spatial information).

  The image generation unit 21 generates a B-mode ultrasonic image representing a two-dimensional distribution related to a predetermined slice of the B-mode signal. Further, the image generation unit 21 generates a two-dimensional image or a three-dimensional image to which the motion information is mapped based on the calculated tissue motion information using a technique such as surface rendering or Polar-Mapping.

  Based on the video signal from the image generation unit 21, the display unit 23 displays tissue motion information and the like as an image in a predetermined form as will be described later. Further, the display unit 23 displays a marker for supporting the association of positions between images when displaying a plurality of images.

  The control unit (CPU) 31 has a function as an information processing apparatus (computer) and statically or dynamically controls the operation of the ultrasonic diagnostic apparatus main body. In particular, the control unit 31 implements a tissue exercise information display function to be described later by developing a dedicated program stored in the storage unit 39 in a memory (not shown).

  The motion information calculation unit 37 generates tissue motion information for each time phase based on the spatiotemporal distribution data output from the movement vector processing unit 19. Here, the tissue motion information is physical information that can be acquired regarding displacement, displacement rate, strain, strain rate, moving distance, speed, velocity gradient, and other tissue motions in a predetermined direction of a predetermined tissue such as a heart wall.

  The excitement propagation information analysis unit realizes an excitement propagation information generation function to be described later.

  The storage unit 39 is a device that reads a recording medium such as a magnetic disk (floppy (registered trademark) disk, hard disk, etc.), optical disk (CD-ROM, DVD, etc.), semiconductor memory, etc., and information recorded on these media. . In this storage unit 37, transmission / reception conditions, a predetermined scan sequence, raw data corresponding to each time phase and ultrasonic image data (for example, tissue image data photographed in tissue Doppler mode, B mode, etc.) are generated in advance. Volume data for each time phase, spatio-temporal distribution data related to movement vectors, programs for realizing the excitement propagation generation function described later, diagnosis information (patient ID, doctor's findings, etc.), diagnosis protocol, body mark generation program, etc. Remember.

  The operation unit 41 is connected to the apparatus main body, and includes various instructions from the operator, a region of interest (ROI) setting instruction, various image quality condition setting instructions, arbitrary tissue motion information and an arbitrary heart rate in the excitation propagation generation function described later. A mouse, a trackball, a mode changeover switch, a keyboard, etc. are provided for selecting a phase.

  The transmission / reception unit 43 is a device that transmits / receives information to / from other devices via a network. Data such as ultrasound images and analysis results obtained by the ultrasound diagnostic apparatus 1 can be transferred by the transmission / reception unit 43 to other apparatuses via a network.

(Excitement propagation information generation function)
Next, the excitement propagation information generation function provided in the ultrasonic diagnostic apparatus 1 will be described. This function generates information (excitement propagation information) that can directly grasp the state of spatiotemporal propagation of mechanical excitement of the heart, using heart wall motion information analyzed in three dimensions. It is to provide.

  FIG. 2 is a flowchart showing the flow of each process executed in the process according to the excitement propagation information generation function (excitement propagation information generation process). Hereinafter, each process will be described.

[Collecting time-series volume data: Step S1]
First, time series volume data (hereinafter referred to as a “time series volume data group”) over a period of at least one heartbeat regarding a desired observation site of the heart or the entire heart of a certain patient, which is a reference. Items with different collection times are collected (step S1).

  That is, volume data of a time series (at least for one heartbeat) is collected from a desired apex observation site of a patient using a two-dimensional array probe from the apex approach with reference to a certain time ti. Here, the reference time ti is time information for identifying the data collection time.

[Generation of Tissue Movement Information: Step S2]
Next, each tissue motion information is generated (step S2). That is, the movement vector processing unit 19 is based on an instruction from the user or the like in the volume data in a predetermined time phase among the volume data corresponding to each time phase of one heartbeat or more constituting the collected time-series volume data group. Then, the myocardial region is extracted, and the extracted local myocardial region is temporally tracked by three-dimensional pattern matching processing to calculate spatio-temporal movement vector information (step S2a). The motion information calculation unit 37 calculates heart wall motion information three-dimensionally using the calculated spatio-temporal movement vector information, and a tissue motion information group composed of three-dimensional motion information of one or more heartbeats. Is generated (step S2b).

In the present embodiment, it is assumed that a tissue motion information group related to radial-strain is generated in step S <b> 2 for specific explanation. However, this is exemplary and is not bound by this example. Examples of heart wall motion information to be generated include motion information related to changes in the wall thickness direction (Radial-strain and Radial-strain rate) and motion information related to changes in the long axis direction (Longitudinal-strain and Longitudinal-strain rate). ), Information on movement in the circumferential direction (Circumferential-strain and Circuit-strain rate), information on the center of gravity in the short axis plane (Rotation and Rotation rate), and the difference in rotation between different short axis planes Some movement information (Twist and Twist rate), movement information (Torsion and Torsion rate) that standardizes the Twist information by the distance between short axis planes, movement information (Displacement and Velocity) related to the movement distance, and the like can be mentioned. The wall thickness direction, the major axis direction, and the circumferential direction are illustrated in FIG. Which of the above-described heart wall motion information is generated is determined by an initial setting or a selection operation from the operation unit 41. [Step S3: Generation of Exercise Information Mapping Image]
Next, a time-series mapping image in which exercise information is mapped is generated using the tissue exercise information group (step S3). For example, the image generation unit 21 color-codes the generated radial-strain related to the change in the wall thickness direction using the tissue motion information group and maps it to the corresponding part of the myocardium, thereby rendering the surface rendering image each time. Create for each phase. Note that the method for mapping tissue motion information is not limited to the surface rendering process. For example, any display may be used as long as the display has a list property such as Polar-map.

[Search for Local Peak Value: Step S4a]
Next, using the generated time-series (that is, for each time phase) surface rendering image, a search for a local peak value in each time phase is executed (step S4a). In other words, the excitement propagation analysis unit 38 searches for a region where the motion information has the maximum value in the entire surface rendering image in the initial time phase t0 selected by a predetermined method. The excitement propagation analysis unit 38 sets a predetermined local region on the basis of the position corresponding to the part searched in the time phase t0 on the surface rendering image in the next time phase t1, and the motion in the local region A part (not necessarily one) having the maximum value (local peak value) of information is searched. Further, the excitement propagation analysis unit 38 sets a predetermined local region based on the position corresponding to the part searched in the time phase t1 on the surface rendering image in the time phase t2 next to the time phase t1. A part having a local peak value in the region is searched. Thereafter, the same local peak value search is executed for all time-series surface rendering images.

  The excitement propagation information generation function is not particularly limited by the shape and size of the local region. However, it is preferable to change according to, for example, the cardiac cycle or medical condition of the subject. Further, for example, the shape and size of the local region in the above time phase may be adaptively changed according to the moving speed of the local region set in the initial time phase. The moving speed of the local region can be calculated based on the moving amount between time phases and the frame time interval.

[Generation of Excitement Propagation Information: Step S5]
Next, excitation propagation information is generated using the searched local peak value for each time phase (step S5). That is, the excitement propagation analysis unit 38 generates a trajectory line indicating the temporal variation of the part having the local peak value as excitement propagation information based on the searched local peak value for each phase.

[Excitation propagation information and mapping image display: Step S6]
Next, the control unit 31 controls the display unit 23 so that the excitement propagation information is displayed together with the mapping image.

  FIG. 4 is a diagram showing a position example of the display form of the mapping image (surface rendering image) and the excitation propagation information on the display unit 23. FIG. 5 is a diagram showing an example of the position of the display form of the mapping image (Polar-Mapping image) and the excitation propagation information on the display unit 23. In each figure, the state of excitement propagation is superimposed and displayed on the current mapping image as a trajectory line, and is updated successively over time. Therefore, the observer can directly and visually grasp the propagation state of the mechanical excitement of the heart by observing the excitation propagation information and the mapping image displayed in a moving image.

  The mapping image and the excitation propagation information can be displayed as a still image related to a desired time phase as necessary.

  Further, in the display of the excitation propagation information and the mapping image, as shown in FIGS. 4 and 5, support information (ie, Sept / Ant /) for orienting an anatomical segment related to the myocardial region of the mapping image. Lat / Post / Inf text information) can be assigned to the corresponding heart wall position and displayed as a marker.

  For the correspondence between the image for orientation and the anatomical segment, for example, a cross section (eg, apex four-chamber image or apex two-chamber image) defined in advance at the time of data collection is assigned as the display format, and the display format This can be realized by adjusting the probe position by the user. By performing such marker display, it becomes possible to observe information indicating the state of spatiotemporal propagation of the mechanical excitement of the heart while grasping where the heart is looking anatomically. .

(Application 1)
In this excitement propagation information generation function, it is also possible to calculate the speed of the local peak position for each time phase together with the trajectory and display it in the excitement propagation information. The velocity of the local peak position can be calculated based on the moving direction and moving amount in each time phase and the time between frames. The local peak position velocity may be displayed as a graph, or may be expressed as the length of the vector with the trajectory line corresponding to each time phase as a vector.

(Application example 2)
In this excitement propagation information generation function, it is also possible to draw and display a locus line by assigning a different color for each time phase so as to correspond to the cardiac time phase. At this time, for example, as shown in FIG. 6, it is preferable to simultaneously display a color bar indicating which color corresponds to which time phase. When displaying a color bar in this way, it is preferable to add a display that contrasts the electrocardiogram (ECG) waveform with coloring as shown in FIG.

  Note that the method of displaying the trajectory for each time phase is not limited to this example. For example, any display form capable of determining the time phase, such as adding character information indicating the time phase for each segment of the trajectory, may be used.

(Application 3)
In step S1, a plurality of time-series volume data with different reference times (for example, two reference times, ti and tj, respectively) are collected and used to generate excitement propagation information generation processing according to steps S2 to S4. The excitement propagation information obtained as a result may be displayed simultaneously (or displayed alternately) as shown in FIG. 7, for example. In this application example, for example, when one time series volume data group is before treatment and the other time series volume data group is after treatment, or different time phases in stress echo (for example, before stress and after stress) This is especially beneficial when observing the situation at regular intervals, such as when comparing

  In the example shown in FIG. 7, the case where both pieces of exercise information are radial-strain is illustrated. However, regardless of this, different types of exercise information may be displayed for Phase (i) and Phase (j).

(Application 4)
In step S2, a plurality of different pieces of motion information (for example, radial-strain and longitudinal-strain) are generated from one time-series volume data group, and excitement propagation information generation processing according to steps S3 and S4 is executed using each of them. The mapping images on which the respective excitation propagation information obtained as a result are superimposed may be displayed simultaneously (or alternately displayed).

  According to such a configuration, it is possible to quickly and easily visually recognize a plurality of different heart wall motion information and excitement propagation information, and it is possible to grasp the complex state three-dimensionally.

(effect)
According to the configuration described above, the following effects can be obtained.

  According to this ultrasonic diagnostic apparatus, the peak value of the motion information in the local region is searched for each time phase by using the three-dimensional mapping image for each time phase to which the motion information is mapped. A trajectory line or the like representing a temporal variation of a peak part is created and displayed, for example, superimposed on a mapping image. The observer can directly grasp the state of spatiotemporal propagation of the mechanical excitation of the heart by observing the trajectory line on the displayed mapping image.

  Moreover, in this ultrasonic diagnostic apparatus, the movement speed for every time phase of the part corresponding to the local peak can be calculated as necessary, and can be displayed by including it in the excitation propagation information. Therefore, the observer can quantitatively grasp the state of spatiotemporal propagation of the mechanical excitement of the heart by observing the moving speed for each time phase included in the excitement propagation information.

(Second Embodiment)
Next, a second embodiment of the present invention will be described.

  The ultrasonic diagnostic apparatus according to the first embodiment traces a region having a local peak value in space and time, and uses the result to grasp the state of spatiotemporal propagation of the mechanical excitation of the heart. there were. On the other hand, the ultrasonic diagnostic apparatus according to the present embodiment is not limited to the local peak value, and a part having a value equal to or higher than a certain reference value (threshold value) is extracted as a specific region, and the result is used to excite. Propagation information is generated.

  Note that the application example described in the first embodiment can also be applied to the ultrasonic diagnostic apparatus according to the present embodiment.

  FIG. 8 is a flowchart showing the flow of each process executed in the excitement propagation information generation process according to this embodiment. Hereinafter, each process will be described.

[Steps S1, S2, S3]
This is substantially the same as the first embodiment.

[Extraction of Singular Region: Step S4b]
Next, extraction of a singular region in each time phase is executed using the generated time-series (that is, for each time phase) surface rendering image (step S4b). That is, the excitement propagation analysis unit 38 extracts a region (singular region) where the motion information is equal to or greater than a predetermined threshold in the entire surface rendering image at the initial time phase t0 selected by a predetermined method. The excitement propagation analysis unit 38 similarly extracts a singular region where the motion information is equal to or greater than a predetermined threshold on the surface rendering image at the next time phase t1. Thereafter, similar singular region extraction is executed for all time-series surface rendering images.

  An example of how to set the threshold value used in the extraction process of the specific region is a spatial peak value at each time phase × α (0 ≦ α <1.0), for example, α = about 0.9. Can be set. Of course, the value of α can be arbitrarily set. For example, it is possible to extract a portion near the peak point by increasing α and by limiting a portion of a peak region having a spread by decreasing α. it can.

[Generation of Excitement Propagation Information: Step S5]
Next, the excitement propagation analysis unit 38 generates the temporal variation of the extracted singular region for each time phase as excitement propagation information (step S5).

[Excitation propagation information and mapping image display: Step S6]
Next, the control unit 31 controls the display unit 23 so as to display the excitement propagation information superimposed on the mapping image.

FIG. 9 is a diagram showing an example of the display form of the mapping image and the excitation propagation information according to the present embodiment. Further, FIG. 10 is a diagram value showing an example of a display form of map images and excitation propagation information is less than 9 of the alpha. In each figure, a singular region having motion information of a predetermined value or more is displayed on the current mapping image and is updated successively over time. Therefore, the observer can directly and visually grasp the propagation state of the mechanical excitement of the heart by observing the excitation propagation information and the mapping image displayed in a moving image.

(effect)
According to the configuration described above, the following effects can be obtained.

  According to this ultrasonic diagnostic apparatus, using a three-dimensional mapping image for each time phase to which motion information is mapped, a part having a value equal to or greater than a reference value for predetermined motion information is extracted as a specific region for each time phase. Then, based on the result, excitement propagation information expressed as a temporal variation of the specific region is created and displayed, for example, superimposed on the mapping image. The observer can directly grasp the state of spatiotemporal propagation of the mechanical excitement of the heart by observing a specific region on the displayed mapping image.

  Moreover, in this ultrasonic diagnostic apparatus, the moving speed for every time phase of a specific area | region can be calculated as needed, and this can be displayed including excitement propagation information. Therefore, the observer can quantitatively grasp the state of spatiotemporal propagation of the mechanical excitement of the heart by observing the moving speed for each time phase included in the excitement propagation information.

  Note that the present invention is not limited to the above-described embodiment as it is, and can be embodied by modifying the constituent elements without departing from the scope of the invention in the implementation stage. Specific examples of modifications are as follows.

  In addition, various inventions can be formed by appropriately combining a plurality of components disclosed in the embodiment. For example, some components may be deleted from all the components shown in the embodiment. Furthermore, constituent elements over different embodiments may be appropriately combined.

  As described above, according to the present invention, using the heart wall motion information analyzed three-dimensionally, it is possible to provide information that can directly grasp and analyze the state of spatiotemporal propagation of the mechanical excitement of the heart. In addition, an image processing apparatus and an ultrasonic diagnostic apparatus that support diagnosis of an ischemic disease or the like can be realized.

DESCRIPTION OF SYMBOLS 1 ... Ultrasonic diagnostic apparatus, 11 ... Ultrasonic probe, 13 ... Transmission unit, 15 ... Reception unit, 17 ... B mode processing unit, 19 ... Movement vector processing unit, 21 ... Image generation unit, 23 ... Display unit, 31 ... Control unit (CPU), 37 ... motion information calculation unit, 39 ... storage unit, 41 ... operation unit, 43 ... transmission / reception unit.

Claims (10)

Motion information generating means for generating tissue motion information of the heart over a plurality of time phases by using a plurality of volume data about the heart of the subject collected along a time series;
The tissue motion information, and using the threshold value is the product of the spatial peak value and a value of less than 1 0 or more, which is set to an arbitrary α at each time phase, the tissue in the generation subject to regions of the tissue motion information An analysis means for extracting a specific region having a value related to motion information equal to or greater than the threshold in a plurality of time phases;
Control means for causing the display means to display the propagation information expressing the temporal variation of the singular area by successively updating the singular area for each of a plurality of time phases extracted by the analyzing means over time. When,
An image processing apparatus.   The image processing apparatus according to claim 1, wherein the analysis unit calculates the threshold based on the tissue motion information.   The image processing apparatus according to claim 2, wherein the analysis unit calculates the threshold value by multiplying the tissue motion information by a predetermined value.   The image processing apparatus according to claim 3, further comprising a setting unit that can arbitrarily set the predetermined value.   The image processing apparatus according to claim 2, wherein the control unit displays the singular region on the display unit by assigning a different color to each region extracted by the analysis unit. Motion information generating means for generating tissue motion information of the heart over a plurality of time phases by using a plurality of volume data about the heart of the subject collected along a time series;
The tissue motion information, and using the threshold value is the product of the spatial peak value and a value of less than 1 0 or more, which is set to an arbitrary α at each time phase, the tissue in the generation subject to regions of the tissue motion information An analysis means for extracting a specific region having a value related to motion information equal to or greater than the threshold in a plurality of time phases;
Control means for causing the display means to display the propagation information expressing the temporal variation of the singular area by successively updating the singular area for each of a plurality of time phases extracted by the analyzing means over time. When,
An ultrasonic diagnostic apparatus comprising:   The ultrasonic diagnostic apparatus according to claim 6, wherein the analysis unit calculates the threshold based on the tissue motion information.   The ultrasonic diagnostic apparatus according to claim 7, wherein the analysis unit calculates the threshold value by multiplying the tissue motion information by a predetermined value.   The ultrasonic diagnostic apparatus according to claim 8, further comprising a setting unit that can arbitrarily set the predetermined value.   The ultrasonic diagnostic apparatus according to claim 7, wherein the control unit displays the singular region on the display unit by assigning a different color to each region extracted by the analysis unit.