JP5134787B2 - Ultrasonic diagnostic apparatus, ultrasonic image processing apparatus, and ultrasonic image processing program - Google Patents

Description

Set Oyugami Imaging (TSI: Tissue Strain Imaging) method relates to an image of the heart using, in particular, shrinkage in the major axis direction in the systole of the heart (Shortening) mapped to the short axis image of the information, or cardiac KokorokabeAtsu the direction of stretch (Thickening) information about mapping to the long axis image.

  In general, objective and quantitative evaluation of movement and function of a living tissue such as a myocardium is very important for diagnosis of the tissue. 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, it has been found that normal myocardium thickens in the wall thickness direction (short axis) during contraction and shortens 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 well-known document relevant to this application, there exist the following, for example.
JP 2003-175041 A

  However, the conventional ultrasonic diagnostic apparatus has the following problems, for example. That is, when taking and observing a short-axis tomogram, biological information perpendicular to the scanning plane of the short-axis tomogram cannot be acquired due to the characteristics of the ultrasonic diagnostic apparatus. It cannot be expressed at the same time. For example, when a cardiac apical long-axis tomographic image is taken and observed by, for example, tissue Doppler method, thickening information cannot be expressed at the same time because a Doppler limit angle exists.

The present invention has been made in view of the above circumstances, and in the case of displaying a two-dimensional tomographic image, the motion information related to the direction orthogonal to the tomographic image can be mapped to the tomographic image and imaged. As a specific example, it is possible to observe shortening information at the same time even when taking and observing a short-axis tomogram, and when taking and observing a long-axis tomogram. It is another object of the present invention to provide an ultrasonic diagnostic apparatus , an ultrasonic image processing apparatus, and an ultrasonic image processing program capable of simultaneously observing thickening information.

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

An ultrasonic diagnostic apparatus according to an embodiment relates to a motion information generation unit that obtains motion information regarding a first direction and a second direction of cardiac tissue in a three-dimensional space, and the three-dimensional space acquired by ultrasonic transmission / reception. A two-dimensional image generation unit that generates a two-dimensional image related to a first direction in the three-dimensional space and a second direction orthogonal to the first direction based on volume data; and the first direction A first mapping image in which motion information about the second direction is mapped to a two-dimensional image, and a second mapping information about motion information about the first direction to a two-dimensional image about the second direction ingredients and mapping image generating unit that generates a mapping image, and a display unit configured to display the first or the second mapping image, the An ultrasonic diagnostic apparatus characterized by.

As described above, according to the present invention, even when a short-axis tomographic image is captured and observed, shortening information can be observed simultaneously, and a long-axis tomographic image is captured and observed. In addition, an ultrasonic diagnostic apparatus , an ultrasonic image processing apparatus, and an ultrasonic image processing program that can simultaneously observe thickening information can be realized.

  Hereinafter, first to third 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.

  Each component according to the present embodiment, particularly a TSI processing unit 20, a volume data generation unit 21, a mapping processing unit 24, and a tracking processing unit 27 (see FIGS. 1 and 14), which will be described later, It can also be realized by installing a software program for executing the same processing 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 10 according to the first embodiment. The ultrasonic diagnostic apparatus 10 includes an ultrasonic probe 11, a transmission unit 12, a reception unit 13, a B-mode processing unit 14, a tissue Doppler processing unit 15, a display control unit 17, a display unit 18, a TSI processing unit 20, and volume data generation. A unit 21, a storage unit 22, a control unit (CPU) 23, a mapping processing unit 24, and an input unit 25 are provided. In addition, when applying this invention to an ultrasonic processing apparatus, the inside of the dotted line of FIG. 1 becomes the component.

  The ultrasonic probe 11 generates ultrasonic waves based on a drive signal from the transmission unit 12 and converts a reflected wave from the subject into an electric 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 ultrasonic waves are transmitted from the ultrasonic probe 11 to the subject, various harmonic components are generated along with the propagation of the ultrasonic waves due to nonlinearity of the living 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 12 has a delay circuit, a pulsar circuit, and the like (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 12 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 13 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 14 performs an envelope detection process on the ultrasonic echo signal received from the receiving unit 13, thereby generating a B mode signal corresponding to the amplitude intensity of the ultrasonic echo.

  The tissue Doppler processing unit 15 performs orthogonal detection processing, autocorrelation processing, and the like on the echo signal received from the receiving unit 13, and based on the Doppler shift component of the ultrasonic echo signal subjected to delay addition processing, The tissue Doppler signal corresponding to the velocity, dispersion, and power of the moving tissue is obtained.

  The display control unit 17 generates a B-mode ultrasonic image representing a dimensional distribution related to a predetermined slice of the B-mode signal. Further, the display control unit 17 generates a tissue Doppler ultrasound image representing a two-dimensional distribution relating to a predetermined slice of velocity, dispersion, and power value based on the tissue Doppler signal. Furthermore, the display control unit 17 generates a superimposed image of the B-mode ultrasound image and the tissue Doppler ultrasound image, a superimposed image of the B-mode ultrasound image and the image related to the tissue motion information, and the like as necessary. Here, the tissue motion information is physical information that can be acquired regarding tissue strain, strain rate, moving distance, speed, and other tissue motion. Hereinafter, a general term of images including such tissue motion information is referred to as a “TSI image”.

  The display unit 18 displays in vivo morphological information and blood flow information as an image based on the video signal from the display control unit 17. Further, when a contrast agent is used, it is displayed as a luminance image or a color image based on a quantitative distribution of the contrast agent, that is, a blood flow or an area where blood is present.

  The TSI processing unit 20 receives a B mode signal output from the B mode processing unit 14, a Doppler signal output from the tissue Doppler processing unit 16, B mode image data, Doppler image data, a velocity distribution image, and the like stored in the storage unit 22. The TSI processing is executed using the TSI processing to generate a TSI image that is an image related to tissue distortion. Here, the velocity distribution image is an image representing the velocity at a plurality of positions on the diagnosis target tissue for each time phase.

  The volume data generation unit 21 performs a spatial interpolation process using the TSI images related to a plurality of slices related to the predetermined object generated by the TSI processing unit 20 as necessary. Thereby, the volume data of the TSI image regarding the predetermined target is generated.

  The storage unit 22 includes ultrasonic image data corresponding to each time phase (for example, tissue image data captured in tissue Doppler mode, B mode, etc.), and velocity distribution corresponding to each time phase generated by the TSI processing unit 20. Images and TSI images are stored. Further, the storage unit 22 stores the volume data of the TSI image generated by the volume data generation unit 21 as necessary. Note that the ultrasonic image data stored in the storage unit 22 may be so-called raw image data before scan conversion.

  The control unit (CPU) 23 has a function as an information processing apparatus (computer) and statically or dynamically controls the operation of the ultrasonic diagnostic apparatus main body.

  The mapping processing unit 24 performs mapping processing for mapping Shortening information on the selected short-axis slice based on the volume data of the TSI image generated by the volume data generation unit 21. Similarly, the mapping processing unit 24 performs mapping processing for mapping the thickening information on the selected long-axis slice based on the volume data of the TSI image.

  The input unit 25 is connected to the apparatus main body, and includes a mouse, a trackball, a mode changeover switch, a keyboard for incorporating various instructions from the operator, a region of interest (ROI) setting instruction, various image quality condition setting instructions, and the like. Etc.

(Tissue strain imaging: TSI)
Next, the tissue strain imaging method, which is a technology that is the premise of the present embodiment, will be briefly described. This tissue strain imaging method visualizes parameters such as local displacement and strain obtained by integrating signals derived from velocity information while tracking the tissue position accompanying the motion as tissue motion information. It is. According to this method, it is possible to create and display an image related to the distortion and displacement of the local myocardium of the heart, and support the analysis of the temporal change of the image output value with respect to the local region.

  For example, when observing thickening using a short-axis tomogram, in the tissue strain imaging method, a field of motion toward the center of contraction (contraction field: The concept and setting of Contraction Motion Field are used. In addition, the tissue strain imaging method can be applied to a temporally variable motion field by moving the position of the contraction center in time, taking into account the effects of translational motion (also called “translation”) of the entire heart. ing. Therefore, it is possible to follow the change in the contraction center position due to the translational motion. Further details of this tissue strain imaging method are described in, for example, Japanese Patent Application Laid-Open No. 2003-175041.

  In the tissue strain imaging method, velocity distribution images relating to a plurality of time phases are required. The velocity distribution image is generated from two-dimensional or three-dimensional ultrasound image data related to a plurality of time phases collected by the tissue Doppler method, or a plurality of two-dimensional or three-dimensional information related to a plurality of time phases collected by the B mode or the like. It is obtained by applying pattern matching processing to the dimensional tissue image. In this embodiment, for the sake of specific explanation, it is assumed that a two-dimensional velocity distribution image generated by performing pattern matching processing on a B-mode image for each time phase is used. However, the present invention is not limited to this. For example, a two-dimensional or three-dimensional velocity distribution image generated by a tissue Doppler method may be used.

(Acquisition of volume data)
In the mapping process described later, for example, volume data of a TSI image related to a diagnosis target (in this case, the heart) is necessary. Therefore, the ultrasonic diagnostic apparatus 10 has several functions for acquiring volume data of TSI images. Hereinafter, this function will be described.

  FIG. 2 shows a first method for acquiring volume data of a TSI image, and is a diagram showing a method of acquiring volume data by volume scanning that actually scans a three-dimensional region including a diagnostic region. . That is, a volume scan using a two-dimensional array probe (that is, a probe in which ultrasonic transducers are arranged in a matrix), a one-dimensional array probe, a mechanical or a procedure, etc. Volume data can be acquired by performing a volume scan by performing a beating operation. In addition, volume data can be acquired for each time phase by performing volume scan continuously, and volume data of a TSI image for each time phase related to a diagnosis target can be acquired by performing TSI processing using these. it can.

  3 and 4 show a second method for acquiring volume data. As shown in each figure, for example, three long-axis tomographic images of heart chamber 2 tomography (2-CH), apex long-axis image (3-CH), and heart chamber 4 tomography (4-CH) are acquired for each time phase. Then, TSI processing using these is performed. By interpolating the obtained TSI images related to the three long-axis tomographic images, the volume data of the TSI images related to the diagnosis target can be acquired for each time phase.

  5 and 6 show a third method for acquiring volume data. As shown in each figure, for example, three off-axis images of the basal level (Basal), the central level (Mid), and the apex level (Apex) are acquired for each time phase, and TSI using these is obtained. Process. By interpolating the obtained TSI images relating to the three short-axis tomographic images, the volume data of the TSI images relating to the diagnosis target can be acquired for each time phase.

  When the first method is compared with the second and third methods, the second and third methods are inferior to the first method in spatial resolution depending on the specifications of the apparatus, but the temporal resolution is lower. May win. In such a case, it is necessary to determine which method should be adopted according to the purpose of diagnosis. In the second and third methods, the interpolation process based on the three faults has been described as an example. However, regardless of this, as long as interpolation is possible, any number of tomographic images (based on interpolation processing) acquired by imaging may be used.

(Orthogonal mapping process)
Next, the orthogonal mapping function of the ultrasonic diagnostic apparatus 1 will be described. In the case of displaying a two-dimensional tomographic image, this function uses the volume data of the TSI image to color and map (color mapping) the movement information related to the direction orthogonal to the tomographic image to the image. Is. Thereby, it is possible to observe the movement in the direction along the scanning line on the tomographic image and the movement in the direction orthogonal to the tomographic image on the same two-dimensional tomographic image.

  7 and 8 are examples of conceptual diagrams for explaining the orthogonal mapping function. As shown in FIG. 7, it is assumed that volume data V1 related to a diagnosis target is generated by interpolation processing using TSI images related to, for example, three different long-axis tomographic images (see FIGS. 3 and 4). An arbitrary short-axis tomographic plane E1 is designated for the volume data V1, and the shorting information of each point on the tissue on the short-axis tomographic plane E1 is used according to the magnitude of the distortion, for example. The color conversion is performed according to the brightness to generate the mapping image F1. By displaying this mapping image F1 superimposed on, for example, a normal ultrasonic image of the short-axis tomographic plane E1, shorting information can be observed in the short-axis tomographic image.

  FIGS. 9 and 10 are other examples of conceptual diagrams for explaining the orthogonal mapping function. As shown in FIG. 9, for example, it is assumed that volume data V2 relating to a diagnosis target is generated by interpolation processing using TSI images relating to three different short-axis tomographic images (see FIGS. 5 and 6). An arbitrary long-axis tomographic plane E2 is designated for the volume data V2, and thickening information of each point on the tissue on the long-axis tomographic plane E2 is used according to the magnitude of the distortion, for example. The color conversion is performed according to the brightness to generate the mapping image F2. By displaying this mapping image F2 superimposed on, for example, a normal ultrasound image of the long-axis tomographic plane E2, thickening information can be observed in the long-axis tomographic image.

  The orthogonal mapping process according to each of the above examples is a mapping using volume data related to a TSI image to be diagnosed. The acquisition of volume data relating to the TSI image can be performed by the method described above including interpolation processing. Therefore, according to this method, for example, only a plurality of long-axis (plural short-axis) tomographic images are taken as shown in the upper part of FIG. Shortening information can be mapped to an image.

Example 1
Next, an operation in the orthogonal mapping process of the ultrasonic diagnostic apparatus 1 will be described. In the first embodiment, a case where distortion shorting information is mapped on a short-axis tomographic image will be described as an example.

  FIG. 12 is a flowchart illustrating the flow of each process executed in the orthogonal mapping process according to the present embodiment. As shown in the figure, first, a short axis slice at an arbitrary (desired) position is selected for the volume data of the TSI image (step S1).

  Next, the mapping processing unit 24 uses the volume data to acquire the contraction in the major axis direction (Shortening information) regarding each position of the tissue existing on the designated minor axis fault, and this is used as the strain intensity and Color mapping is performed so that the density corresponds. A mapping image is generated by this mapping processing (step S2).

  Next, the display control unit 17 superimposes a normal ultrasound image (short axis tomographic image) on the designated short axis tomogram and the generated mapping image, and displays them on the screen of the display unit 18 (step S3). ).

(Example 2)
Next, an operation in the orthogonal mapping process of the ultrasonic diagnostic apparatus 1 will be described. The first embodiment will be described by taking as an example the case where distortion thickening information is mapped on a long-axis tomographic image.

  FIG. 13 is a flowchart illustrating the flow of each process executed in the orthogonal mapping process according to the present embodiment. As shown in the figure, first, a long-axis slice at an arbitrary (desired) position is selected for the volume data of the TSI image (step S11).

  Next, the mapping processing unit 24 uses the volume data to acquire the short-axis direction extension (Thickening information) for each position of the tissue existing on the designated long-axis tomogram, and obtains the strain intensity and the strain intensity. Color mapping is performed so that the density corresponds. A mapping image is generated by this mapping processing (step S12).

  Next, the display control unit 17 superimposes a normal ultrasonic image (long-axis tomographic image) on the designated long-axis tomogram and the generated mapping image, and displays them on the screen of the display unit 18 (step S13). ).

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

  In the ultrasonic diagnostic apparatus, when displaying a two-dimensional tomographic image, motion information related to a direction orthogonal to the tomographic image is mapped to the tomographic image and imaged. Thereby, display information that could not be obtained conventionally is obtained, and it is possible to determine in a combined manner shorting information and thickening information that are said to be orthogonal to each other and have different origins. As a result, in the diagnostic imaging of the heart, it is easy to grasp the local myocardial wall motion, and the diagnosis of myocardial infarction and the like can be supported.

  Further, according to the present ultrasonic diagnostic apparatus, volume data relating to a TSI image to be diagnosed is generated by interpolation processing using a TSI image of a long axis (short axis) tomographic image, for example. Therefore, for example, it is possible to map Shortening (Thickening) information on a two-dimensional image by simply taking a plurality of long-axis (plural short-axis) tomographic images, and to determine the Shortening information and Thickening information in a composite manner. It becomes. As a result, it is not necessary to take both the long-axis tomographic image and the short-axis tomographic image, the working time in the image diagnosis can be shortened, and the burden on the operator and the subject can be reduced.

(Second Embodiment)
Next, a second embodiment of the present invention will be described. The ultrasonic diagnostic apparatus 1 according to the present embodiment is capable of simultaneously mapping and imaging the shorting information and thickening information on an arbitrary tomographic image.

  FIG. 14 is a configuration diagram of the ultrasonic diagnostic apparatus 10 according to the second embodiment. When compared with the ultrasonic diagnostic apparatus 10 of FIG. 1, the point that the tracking processing unit 27 is further provided is different. This tracking processing unit 27 performs two-dimensional or three-dimensional speckle tracking (tracking processing) on a tissue image for each time phase acquired by, for example, B-mode imaging, and calculates thickening information in the direction of the myocardial wall thickness. To do.

  FIG. 15 is a diagram for explaining the concept of the mapping process of the present embodiment. As shown in FIG. 15, the volume data V related to the TSI image to be diagnosed is generated by the above-described method, and shorting information is calculated using this.

  Next, an arbitrary short-axis tomographic image E1 is designated, and thickening information in the wall direction is calculated by speckle tracking of a black and white image in the short-axis tomographic image. In parallel with this, an arbitrary long-axis tomographic image E2 is designated, and thickening information in the wall direction is calculated by speckle tracking of a black and white image in the long-axis tomographic image.

  Next, the mapping image F1 is obtained by assigning a color corresponding to the motion, such as red for the expansion component of the calculated Shortening information, blue for the contraction component, green for the thickness increase component of the thickening information, and then performing color conversion. , F2 is generated. Each generated mapping image is displayed so as to be superimposed on a black and white image (short axis tomographic image or long axis tomographic image) of the background.

  The above procedure is shown in the flowchart of FIG.

  According to the configuration described above, it is possible to simultaneously display a short-axis tomographic image mapped with Shortening information and a long-axis tomographic image mapped with thickening information as necessary. Therefore, the observer can observe thickening information and shortening information on both the short-axis tomographic image and the long-axis tomographic image, and it becomes easy to grasp the local myocardial wall motion in cardiac image diagnosis. Diagnosis of infarction and the like can be favorably supported.

(Third embodiment)
In the first embodiment and the second embodiment, an example in which thickening information and shortening information are used as exercise information has been described. However, the exercise information that can be used for the mapping function of the ultrasonic diagnostic apparatus is not limited to thickening information and shortening information. Therefore, in the present embodiment, an example will be described in which the mapping process described in the first embodiment and the mapping process described in the second embodiment are executed using exercise information other than thickening information and shortening information.

  The ultrasonic diagnostic apparatus 10 according to the present embodiment has a configuration substantially similar to that shown in FIG. Hereinafter, the mapping function using each exercise information will be described.

(Exercise information: Twist exercise)
First, an example in which the state of the torsional motion of the heart wall is adopted as the exercise information will be described with reference to FIGS. When the measurement image region is designated on the tomographic image displayed on the display unit 18, the tracking processing unit 27 uses the tomographic image constituting a plurality of time-series volume data to perform two-dimensional tracking of the intima m1. To calculate the rotation angle (local motion information) of the intima m1 about the direction orthogonal to the cross section of the apex short axis image G1 (the long axis direction of the heart) (step S31). Similarly, for the papillary muscle short-axis image G2 and the cardiac base short-axis image G3, the rotation angles (local motion information) of the intima m2 and m3 about the long-axis direction of the heart are calculated (step S32)). Instead of the inner membranes m1, m2, and m3, the rotation angles of the outer membranes M1, M2, and M3 may be calculated.

  At this time, for example, for each time phase, the tracking processing unit 27 calculates the rotation angle of the intima m1, m2, m3 as the rotation angle with respect to the time phase (reference time phase) to which the intima m1 or the like is input in step S31. . Further, the rotation angles of the inner membranes m1, m2, and m3 in adjacent frames (that is, continuous frames) along the time series may be sequentially calculated.

  The TSI processing unit 20 calculates the difference (relative rotation angle) between the rotation angle of the intima m1 and the rotation angle of the intima m2 (step S33). Similarly, the difference (relative rotation angle) between the rotation angle of the intima m2 and the rotation angle of the intima m3 is calculated (step S34).

  The processing of step S33 and step S34 will be specifically described with reference to FIG. By a predetermined operation from the input unit 25, for example, a counterclockwise direction is defined as a positive rotation direction (+ θ direction). The rotation angle of the inner membrane m1 is θ1, the rotation angle of the inner membrane m2 is θ2, and the rotation angle of the inner membrane m3 is θ3.

  At this time, the relative rotation angle Δθ12 calculated in step S33 is calculated by Δθ12 = θ1-θ2 (or θ2-θ1). Further, the relative rotation angle Δθ23 calculated in step S34 is calculated by Δθ23 = θ2-θ3 (or θ3-θ2).

  The relative rotation angle Δθ12 obtained in step S33 is information reflecting the state (magnitude) of torsional motion of the heart wall between the cross-sectional position of the apex short-axis image G1 and the cross-sectional position of the papillary muscle short-axis image G2. is there. That is, when the relative rotation angle Δθ12 = 0 (θ1 = θ2), the heart wall is rotated by the same angle in the same direction at any position between these cross-sectional positions, and there is no twist in the rotation direction. Can be considered a thing.

  On the other hand, when | Δθ12 | ≠ 0, there is a difference in rotation angle between these cross-sectional positions, and the heart wall is twisted in the rotation angle direction. This heart wall twist increases as the absolute value of the relative rotation angle Δθ12 increases. For example, when the sign of θ1 is different from the sign of θ2, that is, when the rotation direction of the intima m1 and the rotation direction of the intima m2 are opposite, the absolute value of the relative rotation angle Δθ12 is relatively large.

  Similarly, the relative rotation angle Δθ23 obtained in step S34 is information reflecting the magnitude of the torsional motion of the heart wall between the cross-sectional position of the papillary muscle short-axis image G2 and the cross-sectional position of the base proximal short-axis image G3. is there.

  The mapping processing unit 24 uses the relative rotation angles Δθ12 and Δθ23 calculated in step S33 and step S34 as motion information indicating the magnitude of the torsional motion of the heart wall, and performs color mapping, for example, on a long-axis tomogram. To generate a mapping image. The display control unit 17 superimposes and displays this mapping image on the morphological image of the tissue or the mapping image on which predetermined motion information is mapped (step S35). By referring to the displayed relative rotation angles Δθ12 and Δθ23, the user can grasp the magnitude of the torsional motion of the heart wall. Here, relative rotation angles can be calculated for the intima and epicardium of the heart wall, and the magnitude of the torsional motion can be evaluated based on the two relative rotation angles (for example, the average value of the two relative rotation angles). Etc.).

  The speed of the torsional motion of the heart wall between the intima m1 and m2 can be determined by differentiating the relative rotation angle Δθ12 with respect to time. Similarly, the speed of the torsional motion of the heart wall between the intima m2 and m3 can be obtained by differentiating the relative rotation angle Δθ23 with respect to time. It is possible to configure the display unit 81 to display these speeds. Here, “differentiation” includes processing for dividing the relative rotation angle by a time interval between frames for which the relative rotation angle is obtained, in addition to a normal differentiation operation.

(Motion information: Relative rotational gradient)
Processing for acquiring the relative rotation gradient of the heart wall as motion information will be described with reference to FIGS. This relative rotational gradient is motion information indicating the degree of torsional motion of the heart wall.

  First, the tracking processing unit 27 performs the rotation angle θ1 of the intima m1 of the apex short axis image G1, the rotation angle θ2 of the intima m2 of the papillary muscle short axis image G2, and the intima m3 of the base base short axis image G3. Are respectively calculated (step S41).

  Next, the tracking processing unit 27 calculates a relative rotation angle Δθ12 between the rotation angle θ1 of the intima m1 and the rotation angle θ2 of the intima m2 (step S42), and the rotation angle θ2 of the intima m2 The rotation angle θ3 of m3 and the relative rotation angle Δθ23 are calculated (step S43).

  The tracking processing unit 27 calculates a distance d12 between the apex short-axis image G1 and the papillary muscle short-axis image G2 (step S44), and between the papillary muscle short-axis image G2 and the base basal short-axis image G3. The distance d23 is calculated (step S45). The distances d12 and d23 can be calculated based on, for example, the coordinates of the cross-sectional positions of the apex short axis image G1, the papillary muscle short axis image G2, and the base base short axis image G3.

  Next, as shown in FIG. 24, the TSI processing unit 20 divides the relative rotation angle Δθ12 obtained in step S42 by the distance d12 obtained in step S44, so that it is between the intima m1 and the intima m2. Relative rotational gradient δθ12 = Δθ12 / d12 is calculated (step S46). Similarly, the TSI processing unit 20 divides the relative rotation angle Δθ23 obtained in step S43 by the distance d23 obtained in step S45 to obtain a relative rotation gradient δθ23 = Δθ23 / between the intima m2 and the intima m3. d23 is calculated (step S47).

  The mapping processing unit 20 uses the relative rotational gradients δθ12 and δθ23 calculated in steps S46 and S47 as motion information indicating the degree of torsional motion of the heart wall, and color-maps this to, for example, a long-axis tomogram. Generate a mapping image. The display control unit 17 superimposes and displays the mapping image on the tissue morphological image or the mapping image on which predetermined motion information is mapped (step S48).

  The relative rotational gradient δθ12 indicates the magnitude of twist per unit distance between the intima at the apex level and the intima at the papillary muscle level. The relative rotational gradient δθ23 indicates the magnitude of twist per unit distance between the intima of the intima at the papillary muscle level and the intima at the heart base level. That is, the relative rotational gradients δθ12 and δθ23 are motion information reflecting the degree of twist of the heart wall (intima). The user can grasp the degree of the torsional motion of the heart wall by referring to the displayed relative rotational gradients δθ12 and δθ23. It is also possible to calculate relative rotational gradients for the intima and epicardium of the heart wall and evaluate the degree of twisting motion based on these two relative rotational gradients (for example, the average value of the two relative rotational gradients is calculated). Etc.)

(Exercise information: Long axis strain)
Processing for acquiring the strain in the long axis direction of the heart wall as motion information will be described with reference to FIGS. 25 and 26. FIG. This strain is information indicating the degree of distortion of the heart wall, and indicates the distortion state of the heart wall.

  First, the tracking processing unit 27 performs tomographic image three-dimensional displacement (Δx1, Δy1, Δz1), (Δx2, Δy2,...) In which a measurement image region is designated for each of the intima m1, intima m2, and intima m3. (Δz2), (Δx3, Δy3, Δz3) are calculated (step S51), and displacements Δz1, Δz2, and Δz3 in the Z direction (major axis direction) are extracted from these three-dimensional displacements (step S52). .

  Next, the tracking processing unit 27 calculates the expansion / contraction Δz12 = Δz1−Δz2 of the heart wall between the apex level and the papillary muscle level (step S53), and the heart wall between the papillary muscle level and the base level. Expansion / contraction Δz23 = Δz2−Δz3 is calculated (step S54).

  In addition, the tracking processing unit 27 performs the apex short axis image G1 and the papillary muscle short axis image G2 for the apex short axis image G1, the papillary muscle short axis image G2, and the base basal short axis image G3 in which the measurement image region is specified. Is calculated (step S55), and a distance d23 between the papillary muscle short-axis image G2 and the base proximal short-axis image G3 is calculated (step S56).

  The TSI processing unit 20 calculates the strain δz12 = Δz12 / d12 in the major axis direction between the apex level and the papillary muscle level by dividing the expansion / contraction Δz12 calculated in step S53 by the distance d12 calculated in step S45. (Step S57). Further, the TSI processing unit 20 divides the expansion / contraction Δz23 calculated in step S44 by the distance d23 calculated in step S46, whereby the strain δz23 in the long axis direction between the papillary muscle level and the basal level is equal to Δz23 / d23. Is calculated (step S58).

  The mapping processing unit 20 uses the heart wall strains δz12 and δz23 calculated in steps S57 and S58 as motion information indicating the size of the heart wall strain, and performs color mapping on, for example, a short-axis tomogram. To generate a mapping image. The display control unit 17 superimposes and displays the mapping image on the tissue morphological image or the mapping image on which predetermined motion information is mapped (step S59). The user can grasp the magnitude of the distortion of the heart wall by referring to the displayed strains δz12 and δz23 of the heart wall.

  It is also possible to calculate a strain for each of the intima and outer membranes of the heart wall and evaluate the magnitude of distortion based on the two strain values (for example, taking the average value of the two strain values). ).

(Exercise information: Long axis strain rate)
Processing for acquiring the strain rate in the long axis direction of the heart wall as motion information will be described. This strain rate is information indicating the temporal change rate of the strain (strain) of the heart wall, and indicates the strain state of the heart wall.

  When obtaining the strain rate, the same processing as in steps S51 to S58 of the flowchart of FIG. 25 is performed, and the strain δz12 in the major axis direction between the apex level and the papillary muscle level, the papillary muscle level, and the base level are determined. The strain δz23 in the major axis direction between the two is calculated.

  Here, the strain δz12 and the strain δz23 are calculated for the apex short-axis image G1, the papillary muscle short-axis image G2, and the base-base short-axis image G3 in two time phases t1 and t2. The TSI processing unit 20 calculates the strain rate in the long axis direction between the apex level and the papillary muscle level by dividing the strain δz12 by the time interval Δt = | t1-t2 |. Further, by dividing the strain δz23 by the time interval Δt, the strain rate in the major axis direction between the papillary muscle level and the base portion level is calculated. Note that the strain rate may be calculated from the strain by executing a normal differential operation.

  The mapping processing unit 20 uses the calculated heart wall strain rates δz12 / Δt and δz23 / Δt as motion information indicating the temporal rate of change of the heart wall strain, and performs color mapping on the short-axis tomogram, for example. To generate a mapping image. The display control unit 17 displays the mapping image superimposed on the morphological image of the tissue or the mapping image on which predetermined motion information is mapped. The user can grasp the time change rate of the distortion of the heart wall by referring to the displayed strain rate of the heart wall.

  It is also possible to calculate a strain rate for each of the intima and outer membrane of the heart wall, and to evaluate the time change rate of the strain based on these two strain rate values (for example, the average of the two strain rate values). Take the value etc.).

  According to the configuration described above, the mapping process described in the first embodiment and the mapping process described in the second embodiment can be realized even when motion information such as torsion information is used. it can.

  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.

  (1) In each of the above embodiments, the mapping image is displayed so as to be superimposed on the monochrome image of the cross section. On the other hand, a mapping image in which both thickening information and shortening information are mapped to a single short-axis tomographic image or long-axis tomographic image may be generated and displayed. In this case, for example, as shown in FIG. 17, different hues may be assigned to thickening information and shortening information, and this may be displayed with a density corresponding to the intensity of the distortion.

  (2) In each of the above-described embodiments, the mapping image for displaying the thickening information or the shortening information as a hue is generated and displayed. On the other hand, for example, as shown in FIGS. 18 and 19, the heart tissue on the mapping image may be divided into small regions, and the motion information may be digitized and displayed for each small region.

  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.

  (3) In each of the above-described embodiments, for concrete explanation, volume data of a TSI image related to a diagnosis target is generated using volume data acquired by a three-dimensional scan or the like, and the orthogonal direction using this is generated. Explained the mapping process.

It was. However, the orthogonal mapping process does not necessarily require the volume data of the TSI image related to the diagnosis target. That is, this orthogonal mapping process is performed by the motion information about the direction orthogonal to the tomographic plane at each point of the tissue displayed in the short-axis tomogram or the long-axis tomogram selected to generate the mapping image. There may be image data that can be obtained.

  Therefore, for example, as shown in FIG. 20, even in the case of image data v including a tomographic image E1 selected for generating a mapping image and having a certain thickness with respect to the direction orthogonal to the tomographic image, Mapping processing can be realized. When acquiring the image data v, it is sufficient to acquire a plurality of tomographic images substantially orthogonal to the tomographic image E1 and perform the above-described interpolation processing, or at least scan an area corresponding to the image data v by ultrasonic scanning. It is.

  (4) In each of the above embodiments, an example in which a TSI image is used has been described. However, the mapping processing in the orthogonal direction can be applied as long as the image is related to the motion information of the tissue without being limited to this. Therefore, for example, even when a tissue Doppler image is used, the orthogonal mapping process can be performed, and the same effect can be obtained.

  (5) In each of the above-described embodiments, the example in which the mapping image obtained by the mapping process is displayed while being superimposed on another image has been described. However, regardless of this, a projection image (for example, a volume rendering image, a surface rendering image, a developed image by polar coordinates, etc.) is generated and displayed using a plurality of mapping images obtained by the mapping process. Also good.

  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, even when a short-axis tomographic image is captured and observed, shortening information can be observed simultaneously, and a long-axis tomographic image is captured and observed. In addition, an ultrasonic diagnostic apparatus , an ultrasonic image processing apparatus, and an ultrasonic image processing program that can simultaneously observe thickening information can be realized.

FIG. 1 is a configuration diagram of an ultrasonic diagnostic apparatus 10 according to the first embodiment. FIG. 2 shows a first method for acquiring volume data of a TSI image. FIG. 3 is a diagram for explaining a second method for acquiring volume data. FIG. 4 is a diagram for explaining a second method for acquiring volume data. FIG. 5 is a diagram for explaining a third method for acquiring volume data. FIG. 6 is a diagram for explaining a third method for acquiring volume data. FIG. 7 is an example of a conceptual diagram for explaining the mapping function in the orthogonal direction. FIG. 8 is an example of a conceptual diagram for explaining the mapping function in the orthogonal direction. FIG. 9 is another example of a conceptual diagram for explaining the mapping function in the orthogonal direction. FIG. 10 is another example of a conceptual diagram for explaining the orthogonal mapping function. FIG. 11 is a conceptual diagram for explaining the mapping function in the orthogonal direction. FIG. 12 is a flowchart illustrating the flow of each process executed in the orthogonal mapping process according to the first embodiment. FIG. 13 is a flowchart illustrating the flow of each process executed in the orthogonal mapping process according to the second embodiment. FIG. 14 is a configuration diagram of the ultrasonic diagnostic apparatus 10 according to the second embodiment. FIG. 15 is a diagram for explaining the concept of mapping processing according to the second embodiment. FIG. 16 is a flowchart showing the flow of the mapping process according to the second embodiment. FIG. 17 is a diagram illustrating a modification of the display form of thickening information or shortening information in the mapping image. FIG. 18 is a diagram illustrating a modification of the display form of thickening information or shortening information in the mapping image. FIG. 19 is a diagram illustrating a modification of the display form of thickening information or shortening information in a mapping image. FIG. 20 is a diagram for explaining a modification of the embodiment of the present invention. FIG. 21 is a flowchart showing the flow of mapping processing when the torsional motion is motion information. FIG. 22 is a diagram for explaining the mapping process when the torsional motion is motion information. FIG. 23 is a flowchart showing the flow of mapping processing when the relative rotation gradient is used as motion information. FIG. 24 is a diagram for explaining mapping processing when the relative rotation gradient is used as motion information. FIG. 25 is a flowchart showing the flow of mapping processing when the strain in the long axis direction is used as motion information. FIG. 26 is a diagram for explaining the mapping process when the strain in the long axis direction is used as motion information.

Explanation of symbols

DESCRIPTION OF SYMBOLS 10 ... Ultrasound diagnostic apparatus, 11 ... Ultrasonic probe, 12 ... Transmission unit, 13 ... Reception unit, 14 ... B mode processing unit, 15 ... Tissue Doppler processing unit, 17 ... Display control unit, 18 ... Display unit, 20 ... TSI processing unit, 21 ... volume data generation unit, 22 ... storage unit, 23 ... control unit (CPU), 24 ... mapping processing unit, 25 ... input unit 25

Claims (18)

A motion information generation unit for obtaining motion information regarding the first direction and the second direction of the cardiac tissue in a three-dimensional space;
Based on the volume data related to the three-dimensional space acquired by ultrasonic transmission / reception, a two-dimensional image related to a first direction in the three-dimensional space and a second direction orthogonal to the first direction is generated 2 A dimensional image generation unit;
A first mapping image obtained by mapping motion information related to the second direction on a two-dimensional image related to the first direction, and motion information related to the first direction relative to a two-dimensional image related to the second direction. A mapping image generation unit that generates a second mapping image obtained by mapping
A display unit for displaying the first or second mapping image;
An ultrasonic diagnostic apparatus comprising: A setting unit for setting the first direction;
The first direction corresponds to the long axis direction of the heart, the second direction, the ultrasonic diagnostic apparatus according to claim 1, wherein the corresponding short axis direction of the heart. A motion information generating unit for determining motion information about the major axis direction of the heart tissue in a three-dimensional space and motion information about the minor axis direction orthogonal to the major axis direction;
Based on the volume data related to the three-dimensional space acquired by ultrasonic transmission / reception, a short-axis image that is a two-dimensional image related to the short-axis tomography and a long-axis image that is a two-dimensional image related to the long-axis tomography are generated. A two-dimensional image generation unit that
A first mapping image is generated by mapping motion information about the long axis direction of the heart tissue to the short axis image, and a first mapping image is generated by mapping motion information about the short axis direction of the heart tissue to the long axis image. A mapping image generation unit for generating two mapping images;
A display unit for displaying the first and second mapping images;
An ultrasonic diagnostic apparatus comprising: The motion information generation unit, by performing speckle tracking processing on the volume data, as claimed in any one of claims 1 to 3, wherein the determination of the motion information on the 3-dimensional space Ultra Ultrasonic diagnostic equipment. The motion information generation unit further determines motion information regarding the short axis direction of the cardiac tissue from the motion information,
The mapping image generation unit has different colors depending on the degree of motion for each of the motion information about the long axis direction of the heart tissue on the short axis slice and the motion information about the short axis direction of the heart tissue on the short axis slice. Generating the mapping image to which
The ultrasonic diagnostic apparatus according to claim 2 . A motion information generating unit for determining motion information about the major axis direction of the heart tissue in a three-dimensional space and motion information about the minor axis direction of the heart tissue from the motion information;
A two-dimensional image generation unit that generates a two-dimensional image related to a short-axis tomogram orthogonal to the long-axis direction based on volume data related to the three-dimensional space acquired by ultrasonic transmission and reception;
With respect to the two-dimensional image , motion information regarding the major axis direction of the heart tissue on the short axis slice and motion information regarding the minor axis direction of the heart tissue on the minor axis slice differ depending on the degree of motion. A mapping image generation unit for generating a mapping image to which colors are assigned ;
A display unit for displaying the mapping image;
An ultrasonic diagnostic apparatus comprising: The motion information generation unit further determines motion information regarding the short axis direction of the cardiac tissue from the motion information,
The mapping image generation unit is assigned a different color according to the degree of motion for motion information related to the major axis direction of the heart tissue on the minor axis slice, and motion related to the minor axis direction of the heart tissue on the minor axis slice For the information, generating the mapping image assigned a numerical value according to the degree of exercise,
The ultrasonic diagnostic apparatus according to claim 2 . A motion information generating unit for determining motion information about the major axis direction of the heart tissue in a three-dimensional space and motion information about the minor axis direction of the heart tissue from the motion information;
A two-dimensional image generation unit that generates a two-dimensional image related to a short-axis tomogram orthogonal to the long-axis direction based on volume data related to the three-dimensional space acquired by ultrasonic transmission and reception;
For the two-dimensional image , motion information related to the long axis direction of the heart tissue on the short axis slice is assigned a different color depending on the degree of movement, and related to the short axis direction of the heart tissue on the short axis slice. For exercise information, a mapping image generation unit that generates a mapping image assigned a numerical value according to the degree of exercise ,
A display unit for displaying the mapping image;
An ultrasonic diagnostic apparatus comprising: A motion information generating unit for determining motion information about the short axis direction of the heart tissue in a three-dimensional space and motion information about the long axis direction of the heart tissue from the motion information;
A two-dimensional image generation unit that generates a two-dimensional image related to a long-axis tomogram orthogonal to the short-axis direction based on volume data related to the three-dimensional space acquired by ultrasonic transmission and reception;
With respect to the two-dimensional image , motion information regarding the short axis direction of the heart tissue on the long axis slice and motion information regarding the long axis direction of the heart tissue on the long axis slice differ depending on the degree of motion. A mapping image generation unit for generating a mapping image to which colors are assigned ;
A display unit for displaying the mapping image;
An ultrasonic diagnostic apparatus comprising: A motion information generating unit for determining motion information about the short axis direction of the heart tissue in a three-dimensional space and motion information about the long axis direction of the heart tissue from the motion information;
A two-dimensional image generation unit that generates a two-dimensional image related to a long-axis tomogram orthogonal to the short-axis direction based on volume data related to the three-dimensional space acquired by ultrasonic transmission and reception;
For the motion information related to the long axis direction of the heart tissue on the long axis slice, different colors are assigned to the two-dimensional image according to the degree of movement, and the motion information related to the long axis direction of the heart tissue on the long axis slice is related to the two-dimensional image. For exercise information, a mapping image generation unit that generates a mapping image assigned a numerical value according to the degree of exercise ,
A display unit for displaying the mapping image;
An ultrasonic diagnostic apparatus comprising: The motion information generation unit generates motion information regarding the long axis direction of the cardiac tissue in each of a plurality of short axis slices of the heart,
The two-dimensional image generation unit generates the two-dimensional image corresponding to each of the plurality of short-axis slices;
The mapping image generation unit generates a plurality of mapping images in which at least motion information related to the major axis direction of the corresponding cardiac tissue is mapped to each two-dimensional image,
The display unit displays the plurality of mapping images;
The ultrasonic diagnostic apparatus according to claim 6 or 8 . The motion information generation unit generates motion information related to the short axis direction of the cardiac tissue in each of a plurality of long axis slices of the heart,
The two-dimensional image generation unit generates the two-dimensional image corresponding to each of the plurality of long axis slices,
The mapping image generation unit generates a plurality of the mapping images in which at least the motion information related to the minor axis direction of the corresponding cardiac tissue is mapped to each two-dimensional image,
The display unit displays the plurality of mapping images;
The ultrasonic diagnostic apparatus according to claim 9 or 10 . The information about the torsional motion of the heart tissue, information about the relative rotational gradient of the heart tissue, information about the distortion or strain rate of the heart tissue, or information about the displacement of the heart tissue. The ultrasonic diagnostic apparatus according to any one of 1 to 12 . The luck information generation unit generates either three-dimensional motion information generated by performing a three-dimensional scan of a subject or motion information generated by interpolation processing based on a plurality of two-dimensional scans. The ultrasonic diagnostic apparatus according to any one of claims 1 to 13 . A motion information generation unit for obtaining motion information regarding the first direction and the second direction of the cardiac tissue in a three-dimensional space;
Based on the volume data related to the three-dimensional space acquired by ultrasonic transmission / reception, a two-dimensional image related to a first direction in the three-dimensional space and a second direction orthogonal to the first direction is generated 2 A dimensional image generation unit;
A first mapping image obtained by mapping motion information related to the second direction on a two-dimensional image related to the first direction, and motion information related to the first direction relative to a two-dimensional image related to the second direction. A mapping image generation unit that generates a second mapping image obtained by mapping
A display unit for displaying the first or second mapping image;
An ultrasonic image processing apparatus comprising: A motion information generating unit for determining motion information about the major axis direction of the heart tissue in a three-dimensional space and motion information about the minor axis direction orthogonal to the major axis direction;
Based on the volume data related to the three-dimensional space acquired by ultrasonic transmission / reception, a short-axis image that is a two-dimensional image related to the short-axis tomography and a long-axis image that is a two-dimensional image related to the long-axis tomography are generated. A two-dimensional image generation unit that
A first mapping image is generated by mapping motion information about the long axis direction of the heart tissue to the short axis image, and a first mapping image is generated by mapping motion information about the short axis direction of the heart tissue to the long axis image. A mapping image generation unit for generating two mapping images;
A display unit for displaying the first and second mapping images;
An ultrasonic image processing apparatus comprising: On the computer,
A motion information generation function for obtaining motion information relating to the first direction and the second direction of the cardiac tissue in a three-dimensional space;
Based on the volume data related to the three-dimensional space acquired by ultrasonic transmission / reception, a two-dimensional image related to a first direction in the three-dimensional space and a second direction orthogonal to the first direction is generated 2 Dimensional image generation function,
A first mapping image obtained by mapping motion information related to the second direction on a two-dimensional image related to the first direction, and motion information related to the first direction relative to a two-dimensional image related to the second direction. A mapping image generation function for generating a second mapping image obtained by mapping
A display function for displaying the first or second mapping image;
An ultrasonic image processing program characterized by realizing the above. On the computer,
A motion information generation function for obtaining motion information about the major axis direction of the heart tissue in a three-dimensional space and motion information about the minor axis direction orthogonal to the major axis direction;
Based on the volume data related to the three-dimensional space acquired by ultrasonic transmission / reception, a short-axis image that is a two-dimensional image related to the short-axis tomography and a long-axis image that is a two-dimensional image related to the long-axis tomography are generated. A two-dimensional image generation function,
A first mapping image is generated by mapping motion information related to the long axis direction of the cardiac tissue to the short axis image, and a motion information related to the short axis direction of the cardiac tissue is mapped to the long axis image. A mapping image generation function for generating two mapping images;
A display function for displaying the first and second mapping images;
An ultrasonic image processing program characterized by realizing the above.

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