JP5299961B2 - Ultrasonic diagnostic apparatus, image processing apparatus, and control program for ultrasonic diagnostic apparatus - Google Patents

Abstract

<P>PROBLEM TO BE SOLVED: To display a diastolic function of a specific tissue more suitably in an ultrasonic diagnostic apparatus. <P>SOLUTION: An ultrasonic diagnostic apparatus 10 has an image forming section for receiving an echo signal obtained by scanning a subject with ultrasound and forming data of a tomographic image based on the echo signal, an image memory 26 for memorizing the tomographic image corresponding to a time phase signal, a displacement computing section 46 for computing the displacement of the subject for each time phase based on the tomographic image corresponding to the time phase signal in a predetermined term, a distortion computing section 47 and a distortion lowering rate computing section 48 for computing the lowering rate of the displacement based on the displacement for each time phase and the displacement of the initial time phase in the predetermined term, an integration value computing section 49 for computing the integrated value of the lowering rate from the initial time phase to the predetermined time phase in the predetermined term, a standardizing section 50 and a color setting section 51 for forming the display information based on the integrated value, and a display control section 27 for displaying the display information. <P>COPYRIGHT: (C)2010,JPO&amp;INPIT

Description

  The present invention relates to a technique for obtaining an ultrasonic image of a subject using ultrasonic waves and obtaining the movement state of the subject using the ultrasonic image, and particularly, an ultrasonic recognition method for recognizing a difference in local movement during diastole. The present invention relates to a control program for an ultrasonic diagnostic apparatus, an image processing apparatus, and an ultrasonic diagnostic apparatus.

  An ultrasound diagnostic apparatus is a diagnostic apparatus that acquires and displays an ultrasound image of in-vivo information, and is less expensive, less exposed, and non-exposed compared to other diagnostic imaging apparatuses such as an X-ray diagnostic apparatus and an X-ray computed tomography apparatus. It is used as a useful device for invasive observation in real time. Due to such characteristics, the application range of the ultrasonic diagnostic apparatus is wide, and it is used for diagnosis of a circulatory organ such as the heart, abdomen such as the liver and kidney, peripheral blood vessels, obstetrics and gynecology, and cerebral blood vessels.

  Objective and quantitative evaluation of the function of a living tissue such as the heart myocardium is very important for diagnosis of the living tissue. For example, a quantitative evaluation method based on acquiring image data of the heart with an ultrasonic diagnostic apparatus and based on the image data has been proposed.

  For example, a method has been devised that uses motion information of tissue strain or displacement calculated from tissue velocity information acquired using tissue Doppler or pattern matching. In particular, the rate of decrease in strain from the end systole in the diastole is used as one of the indicators when evaluating dilatability. The higher the strain reduction rate is, the higher the expansion ability is, that is, the healthy, while the lower the strain reduction rate is, the lower the expansion ability is, that is, there is some abnormality such as ischemia. As described above, the heart is evaluated by obtaining wall motion information such as displacement and strain.

  In addition, patent document 1 is mentioned as a prior art relevant to this invention.

JP 2003-175041 A

  However, according to the prior art, even in a healthy heart, variation occurs in distortion in each cardiac time phase. Therefore, according to the prior art, the rate of decrease in film thickness variation also varies, making it difficult to properly evaluate the dilatability of each part of the myocardium.

  The present invention has been made in consideration of the above-described circumstances, and reduces the influence of variation in the rate of decrease in strain of a specific tissue, and provides an ultrasonic diagnosis that provides information used for evaluating the motion state of a specific tissue. It is an object to provide a control program for an apparatus, an image processing apparatus, and an ultrasonic diagnostic apparatus.

  In order to achieve the above-mentioned object, an ultrasonic diagnostic apparatus according to the present invention receives an echo signal obtained by scanning a moving subject with ultrasonic waves, and obtains ultrasonic image data based on the echo signal. Based on the ultrasonic image corresponding to the time phase signal within a predetermined period based on the image generating means to generate, the means for storing the ultrasonic image in association with the time phase signal, and the subject for each time phase Displacement calculating means for calculating the displacement of the object, strain calculating means for calculating the distortion of the subject using the displacement, the distortion for each time phase within the predetermined period, and the initial time phase within the predetermined period. Based on the strain, a reduction rate calculating means for calculating a strain reduction rate, and an integral value calculation for calculating an integral value obtained by integrating the strain reduction rate from the initial time phase to a predetermined time phase within the predetermined period And display information for generating display information based on the integral value With a generation unit, and a display control means for displaying the display information.

  In order to achieve the above object, an image processing apparatus according to the present invention stores ultrasonic image data based on an echo signal obtained by scanning a moving subject with ultrasonic waves in association with a time phase signal. Means for calculating the displacement of the subject for each time phase based on the ultrasonic image corresponding to the time phase signal within a predetermined period, and calculating the distortion of the subject using the displacement Based on the distortion for each time phase within the predetermined period and the distortion of the initial time phase within the predetermined period; and a strain reduction rate; and from the initial time phase to the predetermined period Means for calculating an integral value obtained by integrating the rate of reduction of the distortion up to a predetermined time phase, means for generating display information based on the integral value, and means for displaying the display information.

  In order to achieve the above-described object, a control program for an ultrasound diagnostic apparatus according to the present invention receives an echo signal obtained by scanning a moving subject with ultrasound in a computer and is based on the echo signal. Based on the function of generating ultrasonic image data, the function of storing the ultrasonic image in association with the time phase signal, and the ultrasonic image corresponding to the time phase signal within a predetermined period, for each time phase A function for calculating the displacement of the object, a function for calculating the distortion of the object using the displacement, the distortion for each time phase within the predetermined period, and an initial time phase within the predetermined period. A function of calculating a strain reduction rate based on the strain, a function of calculating an integral value obtained by integrating the strain reduction rate from the initial time phase to a predetermined time phase within the predetermined period, and the integral value Generating display information based on the display and the display And a function to display the broadcast, to realize.

  According to the control program of the ultrasonic diagnostic apparatus, the image processing apparatus, and the ultrasonic diagnostic apparatus according to the present invention, by using the output value calculated based on the value obtained by integrating the reduction rate of the distortion of the specific tissue, the tissue distortion It becomes possible to reduce the influence of the variation in the decrease rate. This makes it possible to display the expandability of a specific organization more appropriately.

Schematic which shows the structure of the ultrasonic diagnosing device of this embodiment. The block diagram which shows the function of the ultrasonic diagnosing device of this embodiment. The conceptual diagram of the tomogram on which the marker showing the intima outline of the myocardium in the cardiac phase Tn and the marker showing the epicardial outline were overlaid. The figure which shows typically the intima outline and epicardial outline of the myocardium in the initial cardiac phase T0. The figure which shows typically the intima outline and epicardial outline of the myocardium in the cardiac phase Tn. The figure for demonstrating the setting method of a region of interest. The figure which shows the segment in the case of dividing | segmenting a lumen into six. The figure which shows the example of a display of the two-dimensional wall motion information for evaluating the heart of a subject. The figure which shows the example of a display of the three-dimensional wall motion information for evaluating the heart of a subject. The flowchart which shows operation | movement of the ultrasonic diagnosing device of this embodiment.

  Embodiments of an ultrasound diagnostic apparatus and a control program for the ultrasound diagnostic apparatus according to the present invention will be described with reference to the accompanying drawings.

  FIG. 1 is a schematic diagram illustrating the configuration of the ultrasonic diagnostic apparatus according to the first embodiment.

  FIG. 1 shows an ultrasonic diagnostic apparatus 10 according to the first embodiment. The ultrasonic diagnostic apparatus 10 includes an ultrasonic probe 11, an ECG (electrocardiogram) measuring apparatus 12, an apparatus main body 13, a display 14, and an operation panel 15.

  The ultrasonic probe 11 has a plurality of ultrasonic transducers as acoustic / electric reversible conversion elements such as piezoelectric ceramics. A plurality of ultrasonic transducers are arranged in parallel and are provided at the tip of the ultrasonic probe 11. Each ultrasonic transducer generates an ultrasonic wave at a predetermined timing in accordance with a supplied drive signal (voltage pulse). Ultrasound from each ultrasonic transducer forms a beam and is reflected by a discontinuous surface of acoustic impedance in the subject. Each ultrasonic transducer receives this reflected wave, generates a reception echo, and is taken into the apparatus main body 13 for each channel.

  The ultrasonic probe 11 is either a one-dimensional array probe in which a plurality of ultrasonic transducers are arranged in one direction, or a two-dimensional array probe in which a plurality of ultrasonic transducers are arranged in a two-dimensional matrix. There may be. Further, a one-dimensional array probe in which ultrasonic transducers are arranged in a predetermined direction (scanning direction) and mechanically swingable in a direction (swinging direction) orthogonal to the scanning direction may be used. .

  The ECG measurement device 12 is mainly used in contact with the body surface near the heart of the subject P, measures an ECG (electrocardiogram waveform), and converts the ECG into a digital signal.

  The apparatus main body 13 includes an ultrasonic transmission unit 21, an ultrasonic reception unit 22, an ECG memory 23, a signal processing unit 24, an image generation unit 25, an image memory 26, a display control unit 27, a CPU (central processing unit) 28, and an internal storage. A device 29, an IF (interface) 30, and an external storage device 31 are provided.

  The ultrasonic transmission unit 21 includes a clock generation unit, a transmission delay unit, and a pulser (not shown). The clock generator generates a clock signal that determines the transmission timing and transmission frequency of the ultrasonic signal. The transmission delay unit performs transmission focus with a delay when transmitting ultrasonic waves. The pulsar incorporates as many pulsars as the number of individual paths (channels) corresponding to each ultrasonic transducer of the ultrasonic probe 11. The pulser then generates a drive pulse at the transmission timing multiplied by the delay, and supplies it to each ultrasonic transducer of the ultrasonic probe 11.

  The ultrasonic receiving unit 22 includes a preamplifier, an A / D (analog to digital) conversion unit, and a reception delay / addition unit (not shown). The preamplifier amplifies the echo signal output from each ultrasonic transducer of the ultrasonic probe 11 for each reception channel. The A / D converter performs A / D conversion on the echo signal amplified by the preamplifier. The reception delay / adder circuit emphasizes the reflection component from the direction corresponding to the reception directivity with respect to the echo signal after A / D conversion. Note that the signal added by the ultrasonic receiver 22 may be referred to as “RF data (raw data)”. The ultrasonic receiving unit 22 outputs the RF data to the signal processing unit 24.

  The ECG memory 23 is configured by a nonvolatile semiconductor memory or the like. The ECG memory 23 temporarily stores the ECG signal measured by the ECG measurement device 12.

  The signal processing unit 24 assigns a cardiac time phase T based on the ECG signal output from the ECG memory 23 as a header of the RAW data of the live image. When the cardiac time phase T is added to the RAW data of the live image, the signal processing unit 24 controls the timing of adding the cardiac time phase T to the RAW data according to the ultrasonic transmission / reception conditions.

  The signal processing unit 24 includes a B-mode processing unit 24a and a Doppler processing unit 24b. The B-mode processing unit 24a performs envelope detection on a reception echo output from the ultrasonic reception unit 22 and a calculation echo described later, and outputs the result as detection data.

  The Doppler processing unit 24b extracts the blood flow component using frequency analysis and the blood flow information such as average velocity, variance, and power by extracting the blood flow component using a filter. Blood flow information is obtained as binarized information.

  The image generation unit 25 converts the data after the signal processing represented by the scanning line signal sequence into coordinate system data based on the spatial coordinates (digital scan conversion). For example, the image generation unit 25 performs scan conversion processing on the signal-processed data output from the B-mode processing unit 24a, thereby obtaining tomographic image (B-mode image) data representing the tissue shape of the subject. Generate. Then, the image generation unit 25 outputs an ultrasonic image such as a tomographic image to the image memory 26 as data.

  When the ultrasonic diagnostic apparatus 10 scans the heart of the subject P with ultrasonic waves, the image generation unit 25 generates a tomographic image representing the heart. That is, the image generation unit 25 generates heart moving image data. For example, when the ultrasound diagnostic apparatus 10 scans the heart of the subject P with ultrasound over one cardiac cycle or more, the image generation unit 25 performs the heart in a plurality of cardiac time phases T over one cardiac cycle or more. A tomographic image (moving image) is generated.

  The image memory 26 stores the tomographic image (still image, moving image) output from the image generation unit 25 as data. A plurality of timing tomograms stored in the image memory 26 are associated with a cardiac phase T received at the timing when each tomogram is generated.

  The display control unit 27 acquires a tomographic image from the image memory 26 and causes the display 14 to display the tomographic image. For example, when an operator (diagnostic) inputs an arbitrary cardiac phase T using the operation panel 15, the display control unit 27 displays a tomographic image associated with the input cardiac phase T from the image memory 26. The tomographic image corresponding to the acquired cardiac phase T is displayed on the display 14.

  The CPU 28 is a control device having a configuration of an integrated circuit (LSI) in which an electronic circuit made of a semiconductor is enclosed in a package having a plurality of terminals. The CPU 28 has a function of comprehensively controlling the apparatus main body 13 by executing a program stored in the internal storage device 29. Alternatively, the CPU 28 has a function of loading a program stored in the external storage device 31 and a program transferred from the network N, received by the IF 30 and installed in the external storage device 31 to the internal storage device 29 and executing the program. .

  The internal storage device 29 is a storage device having a configuration that combines elements such as a ROM (read only memory) and a RAM (random access memory). The internal storage device 29 has a function of storing IPL (initial program loading) and BIOS (basic input / output system). Further, the internal storage device 29 has a function of storing a program such as a control program of the ultrasonic diagnostic apparatus 10 or using it for temporary storage of the work memory and data of the CPU 28.

  The IF 30 is configured by a connector that conforms to a parallel connection specification or a serial connection specification. The IF 30 is an interface related to the operation panel 15, a network N such as a hospital backbone LAN (local area network), the external storage device 31, and the operation panel 15. Data such as ultrasound images and analysis results acquired by the apparatus main body 13 can be transferred to other apparatuses via the network N by the IF 30.

  The external storage device 31 is a storage device having a configuration in which a metal disk coated or vapor-deposited with a magnetic material is incorporated in a reading device (not shown) in a non-detachable manner. The external storage device 31 has a function of storing a program (including an OS (operating system) in addition to an application program) installed in the device main body 13. In addition, the OS can be provided with a graphical user interface (GUI) that can use the graphics for displaying information to the operator and perform basic operations by the operation panel 15.

  The internal storage device 29 or the external storage device 31 is a control program such as an ultrasonic diagnostic program according to the present invention, diagnostic information (patient ID (identification), doctor's findings, etc.), diagnostic protocol, transmission / reception conditions, and other data groups. Is stored. Further, the internal storage device 29 or the external storage device 31 is also used for storing a three-dimensional image temporarily stored in the image memory 26 as necessary. Further, the data stored in the internal storage device 29 or the external storage device 31 can be transferred to the network N via the IF 30.

  The display 14 is configured by a liquid crystal display, a CRT (Cathode Ray Tube), or the like. The display 14 displays morphological information in the living body and blood flow information as a still image or a moving image based on the video signal output from the display control unit 27.

  The operation panel 15 includes a keyboard 15a, a mouse 15b, a trackball 15c, a TCS (touch command screen) 15d, and the like. The operation panel 15 is connected to the apparatus main body 13 and has a function of inputting various instructions from the operator, for example, an ROI setting instruction, an image quality condition setting instruction, and the like to the apparatus main body 13. The operator transmits the ultrasonic pulse transmission frequency, transmission drive voltage (sound pressure), transmission pulse rate and scan area, reception conditions, and the like to the apparatus main body 13 via the operation panel 15. Can be entered.

  FIG. 2 is a block diagram illustrating functions of the ultrasonic diagnostic apparatus 10 according to the first embodiment.

  The ultrasonic diagnostic apparatus 10 functions as the scan control unit 39 and the image processing apparatus 40 by the CPU 28 shown in FIG. The image processing apparatus 40 includes an interface unit 41, an initial contour coordinate setting unit 42, a contour coordinate setting unit 43, a marker generation unit 44, a film thickness calculation unit 45, a displacement calculation unit 46, a strain calculation unit 47, and a strain reduction rate calculation unit 48. , An integral value calculation unit 49, a normalization unit 50, and a color setting unit 51. In the first embodiment, the scan control unit 39 and the image processing device 40 constituting the ultrasonic diagnostic apparatus 10 are described as functioning by executing a software program modularized in software. All or part of the unit 39 and the image processing apparatus 40 may be configured by hardware.

  The scan control unit 39 controls the ultrasonic transmission unit 21 in accordance with a scan sequence stored in a storage device such as the external storage device 31, and the ultrasonic pulse transmitted from the ultrasonic probe 11 (shown in FIG. 1). A characteristic including a frequency spectrum such as a center frequency, a frequency distribution, an amplitude, a frequency band, a phase, and a transmission focal point is set, and an ultrasonic pulse having the set characteristic is directed from the ultrasonic probe 11 to a specific tissue of the subject P. Has a function to transmit. Thereby, the image memory 26 stores the cardiac phase T at the time when the tomographic image is generated in association with each of the plurality of tomographic images. Hereinafter, a case where the heart is imaged as the specific tissue will be described.

  The interface unit 41 is an interface such as a GUI. The GUI uses a lot of graphics for display on the display 14 for the operator, and a basic operation can be performed by the operation panel 15.

  The initial contour coordinate setting unit 42 is based on a tomographic image of the heart in the initial cardiac phase T0 arbitrarily set from among a plurality of cardiac time phases T stored in the image memory 26, and the heart in the initial cardiac phase T0. Has the function of setting the two-dimensional coordinate information of the contour of the.

  When the operator inputs the end systole (ES: cardiac phase after elapse of a predetermined time from detection of the R wave) to the interface unit 41 using the operation panel 15, the initial contour coordinate setting unit 42 is a tomogram corresponding to the end systole. An image is acquired from the image memory 26 as a tomographic image of the initial cardiac phase T0. The initial contour coordinate setting unit 42 controls the display control unit 27 to display a tomographic image of the initial cardiac phase T0 on the display 14. Since the cardiac phase T is associated with each of the plurality of tomographic images stored in the image memory 26, the initial contour coordinate setting unit 42 uses the tomographic image corresponding to the end systole as the tomographic image of the initial cardiac phase T0. Can be obtained from the image memory 26. The initial cardiac phase T0 is not limited to the end systole but may be, for example, the end diastole (ED: cardiac phase when an R wave is detected) or the like.

  Specifically, the initial contour coordinate setting unit 42 based on the tomogram of the initial cardiac phase T0 acquired from the image memory 26, the coordinate information of the intimal contour of the myocardium in the initial cardiac phase T0, and the initial cardiac The coordinate information of the epicardial contour of the myocardium in the time phase T0 is set. In the tomogram of the heart, papillary muscles, chordae, etc. appear in addition to the intima and outer membranes of the myocardium. While observing the tomographic image of the initial cardiac phase T0 displayed on the display 14, the operator uses the operation panel 15 to display the papillary muscles and tendons displayed in the tomographic image of the initial cardiac phase T0 on the interface unit 41. The contour line of the intima of the myocardium is input so that the cord is not included. In the evaluation of the myocardium, the papillary muscles and chordae are noisy, so the contour line of the intima is input avoiding the papillary muscles and chordae. For example, when the operator traces the two-dimensional contour of the intima appearing in the tomographic image of the initial cardiac phase T0 displayed on the display 14, the initial contour coordinate setting unit 42 causes the myocardium in the initial cardiac phase T0. Sets the coordinate information of the intimal contour.

  On the other hand, when the operator traces the two-dimensional contour of the epicardium that appears in the tomographic image of the initial cardiac phase displayed on the display 14, the initial contour coordinate setting unit 42 allows the epicardial contour of the myocardium in the initial contour to be determined. Set coordinate information.

  The initial contour coordinate setting unit 42 obtains a normal vector of each point constituting the intimal contour of the initial cardiac phase T0, and sets the position outside the intimal contour by a certain distance in the direction of the normal vector from the initial cardiac phase. It may be defined as the epicardial contour of the myocardium at the time phase T0. For example, the initial contour coordinate setting unit 42 defines a position 8 mm outside the position of the intimal contour as the epicardial contour. This constant distance can be changed to an arbitrary value by the operator.

  The contour coordinate setting unit 43 includes an intimal contour and an epicardial contour in the initial cardiac phase T0 set by the initial contour coordinate setting unit 42, and cardiac time phases Tn after the initial cardiac phase T0 acquired from the image memory 26. Based on each tomographic image of the heart at (n = 1, 2,...), It has a function of setting coordinate information of a two-dimensional contour of the heart at the cardiac phase Tn.

For example, the outline coordinate setting unit 43 acquires the initial contour coordinate setting unit 42 tomographic image I _T1 generated in the next cardiac phase T1 of the tomographic image I _T0 in the initial cardiac phase T0 obtained by the image memory 26 To do. Then, the contour coordinate setting unit 43 performs pattern matching between two temporally continuous tomographic images (tomographic images I _T0 and I _T1 ) using the speckle pattern, whereby the intima of the initial cardiac phase T0. The movement vector of each point constituting the contour is obtained. This movement vector represents the displacement of each point constituting the intimal contour of the initial cardiac phase T0 and the movement direction in which each point is displaced. That is, the contour coordinate setting unit 43 calculates a speckle movement amount by performing pattern matching between two tomographic images, thereby obtaining a movement vector of each point constituting the intimal contour of the initial cardiac phase T0. . In this way, by obtaining the movement vector of each point constituting the intimal contour of the initial cardiac phase T0, the position of each point constituting the intimal contour of the cardiac phase T1 from which the tomographic image _IT1 is generated is determined. Desired.

Further, the contour coordinate setting unit 43 acquires the tomographic image _IT2 generated in the cardiac time phase T2 next to the cardiac time phase T1 from the image memory 26, and two temporally continuous tomograms using the speckle pattern. By performing pattern matching between images (tomographic images I _T1 , I _T2 ), a movement vector of each point constituting the intimal contour of the cardiac phase T1 is obtained. Thereby, coordinate information of each point constituting the intimal contour of the cardiac phase _T2 where the tomographic image _IT2 is generated is obtained.

The marker generation unit 44 generates a marker MB _Tn representing the intimal contour B _Tn of the myocardium based on the coordinate information of the intimal contour in the cardiac phase Tn set by the contour coordinate setting unit 43, and in the cardiac phase Tn A function of generating a marker MC _Tn representing the _epicardial contour C _Tn of the myocardium based on the coordinate information of the _epicardial contour, and the tomographic image I acquired by the contour coordinate setting unit 43 on the display 14 via the display control unit 27 _Tn the marker _MB Tn, and a function of displaying overlapping the _{MC Tn.} The marker _{MB Tn} representing the endocardium contour _{B Tn,} the concept of the tomographic image _{I Tn} of the marker _{MC Tn} is superimposed to represent the adventitia contour _{C Tn} shown in Fig.

  The film thickness calculator 45 shown in FIG. 2 uses the initial cardiac phase T0 based on the coordinate information of each point constituting the intimal contour and the coordinate information of each point constituting the epicardial contour in the initial cardiac phase T0. A function of calculating the distance between the intimal contour and the epicardial contour as the film thickness of the initial cardiac phase T0, coordinate information of each point constituting the intimal contour in the cardiac phase Tn, and each constituting the epicardial contour A function of calculating the distance between the intimal contour and the epicardial contour of the cardiac phase Tn as the thickness of the cardiac phase Tn based on the coordinate information of the points.

The film thickness calculation unit 45 is based on the coordinate information of each point constituting the intimal contour B _Tn of the cardiac phase Tn and the coordinate information of each point constituting the _epicardial contour C _Tn of the cardiac phase Tn. The film thickness in the wall thickness direction at the cardiac phase Tn is calculated.

Figure 4 is a diagram schematically showing the intimal contour B _T and adventitia contour C _T of the myocardium in the initial cardiac phase T0.

Thickness calculating unit 45, a point _B T0 on the endocardium contour _{B T0 [u (u = 1,2} , ..., U)] perpendicular line orthogonal to the inner film contoured _{B T0} from _L T0 [u] to each u Ask for each. Then, the film thickness calculation unit 45 obtains a point C _T0 [u] where the orthogonal line L _T0 [u] intersects the outer membrane contour C _T0 for each u. Further, the film thickness calculation unit 45 sets the distance D _T0 [u] between the point B _T0 [u] on the intimal outline B _T0 and the point C _T0 [u] on the _epicardial outline C _T0 for each u. Ask for each.

Alternatively, the film thickness calculation unit 45 shown in FIG. 2 has a total of 360 (U = 360) in the initial cardiac phase T0 at intervals of 1 ° around the center of gravity position of the cross-sectional image (short axis image) of the heart. A minute point B _T0 [u], a point C _T0 [u], and an orthogonal line L _T0 [u] are obtained for each u.

Then, the film thickness calculation unit 45 calculates the myocardial film thickness D _T0 [u] in the cardiac phase T0 for each u using the following equation (1).

5, the inner membrane contour of the myocardium in cardiac phase Tn B _Tn and adventitia contour C _Tn is a diagram schematically illustrating.

Thickness calculating unit 45 calculates each point _B Tn on the endocardium contour _{B Tn} [u] perpendicular line _L Tn perpendicular to the inner film contoured _{B Tn} from [u] for each u. Then, the film thickness calculator 45 obtains points C _Tn [u] at which the orthogonal line L _Tn [u] intersects the outer membrane contour C _Tn for each u. Furthermore, the film thickness calculation unit 45 calculates the distance D _Tn [u] between the point B _Tn [u] on the intimal contour B _Tn and the point C _Tn [u] on the outer membrane contour C _Tn for each u. Ask for each.

Alternatively, the film thickness calculator 45 shown in FIG. 2 performs a total of 360 points B _Tn [u] and C in the cardiac phase Tn at intervals of 1 ° centered on the center of gravity of the cross-sectional image of the heart. _Tn [u] and orthogonal line L _Tn [u] are obtained for each u.

Then, the film thickness calculation unit 45 calculates the myocardial film thickness D _Tn [u] in the cardiac phase Tn for each u using the following equation (2).

The displacement calculation unit 46 calculates between the initial cardiac phase T0 and the cardiac phase Tn based on the initial cardiac phase T0 and the cardiac phase Tn calculated by the thickness calculation unit 45. It has a function to calculate the film thickness displacement. Based on the film thickness D _T0 [u] of the initial cardiac phase T0 and the film thickness D _Tn [u] of the cardiac phase Tn, the displacement calculating unit 46 uses the following equation (3) to The difference ΔD _Tn [u] in the phase Tn is calculated for each u as the film thickness displacement.

  The displacement calculation unit 46 may be configured to calculate the displacement and rotation angle of the intima (outer membrane) between the initial cardiac phase T0 and the cardiac phase Tn. The film thickness calculator 45 may calculate the distance between the epicardial contours of the initial cardiac phase T0 in the direction perpendicular to the wall thickness direction as the thickness of the initial cardiac phase T0. Further, the displacement calculation unit 46 may obtain a rotation angle in a direction perpendicular to the wall thickness direction.

The strain calculation unit 47 calculates the cardiac phase based on the film thickness displacement of the cardiac phase Tn calculated by the displacement calculation unit 46 and the film thickness displacement of the initial cardiac phase T0 calculated by the film thickness calculation unit 45. It has a function of calculating myocardial strain in the wall thickness direction at Tn. The strain calculation unit 47 uses the following equation (4) based on the film thickness displacement ΔD _Tn [u] of the cardiac phase Tn and the film thickness D _t0 [u] of the initial cardiac phase T0 to calculate the cardiac The strain Sn [u] at the time phase Tn is calculated for each u.

  The distortion calculation unit 47 calculates the distortion Sn [u] for each cardiac interval phase Tn by calculating the distortion Sn [u] for each 1 ° interval.

The strain reduction rate calculation unit 48 has a function of calculating the myocardial strain reduction rate in the wall thickness direction in the cardiac phase Tn based on the strain Sn [u] calculated by the strain calculation unit 47. The strain reduction rate calculation unit 48 calculates the strain S _ES [u] of the end systole ES based on the ECG signal (the strain S _T0 [u] of the initial cardiac phase T0) and the strain S _ED [u] of the end diastole ED. Based on the following equation (5), the strain reduction rate Sn ⁻ [u] of the cardiac phase Tn as the diastole from the end systole ES to the end diastole ED is calculated for each u.

The integrated value calculation unit 49 integrates the strain reduction rate of the cardiac phase Tn calculated by the strain reduction rate calculation unit 48 on the time axis from the initial cardiac phase T0 to the cardiac phase Tn. It has a function to calculate a rate integral value. The integral value calculation unit 49 integrates the strain reduction rate Sn ⁻ [u] of the cardiac phase Tn on the time axis from the initial cardiac phase T0 to the cardiac phase Tn, and the integrated value ΣSn ^{− of} the cardiac phase Tn. [U] is calculated for each u.

The normalization unit 50 has a function of calculating the ED ratio of the integrated value of the strain reduction rate of the cardiac phase Tn calculated by the integrated value calculation unit 49 with respect to the integrated value of the strain reduction rate of the end diastole ED. Normalization unit 50, the strain decrease rate integrated value of cardiac phase _Tn ΣS Tn ^- [u] and end diastole ED distortion reduction rate integration value [sigma] s _ED ^- based on the [u], the following equation (6) The ED ratio R _Tn [u] is calculated for each u.

  Here, since the ED ratio Rn [u] does not take an absolute value, the negative value of the distortion reduction rate in the early expansion stage is particularly emphasized. The fact that the strain reduction rate is negative means that the contraction is not yet completed even in the early expansion stage. Since the delay in the cardiac phase when the contraction is completed is an index indicating an abnormal diastolic ability of the heart, the ability to detect the negative value of the strain reduction rate in the early diastole with high sensitivity has a great merit in the diastolic evaluation.

The color setting unit 51 sets a region of interest including the orthogonal line L _Tn [u] of the cardiac phase Tn, and sets a color corresponding to the magnitude of the ED ratio calculated by the normalization unit 50 for the region of interest. It has the function to do. Color setting unit 51 sets a region of interest _L'Tn [u] to an orthogonal line _L Tn [u], the region of interest _L'Tn [u], corresponding to the size of the ED ratio _R Tn [u] The color to be determined is determined for each u. The color setting unit 51 has a function of setting a color corresponding to the magnitude of the integral value calculated by the integral value calculating unit 49 for the region of interest.

  Note that the color setting unit 51 may associate different singular colors with the region of interest when the integral value, average value, and ED ratio of the region of interest are equal to or less than the threshold value.

  FIG. 6 is a diagram for explaining a method of setting the region of interest L′ n [u].

FIG. 6 shows an intima contour B _Tn , an _epicardial contour C _Tn , an orthogonal line L _Tn [u], and a region of interest L ′ _Tn [u]. The region of interest L ′ _Tn [u] has a predetermined width in the circumferential direction of the intimal contour B _Tn with the point B _Tn [u] on the intimal contour B _Tn as the center, and the point C on the _epicardial contour C _{Tn. This} is a region having a predetermined width in the circumferential direction of the outer membrane contour _CTn with _Tn [u] as the center. For example, the region of interest _L'Tn [1] corresponding to the intima point _B Tn [1] on the contour _{B Tn} at cardiac phase Tn is the circumferential direction of the inner film contoured _{B Tn} around the point _B Tn [1] in conjunction with a predetermined width, a region having a predetermined width in a circumferential direction of adventitia contour C _Tn about a point on the adventitia contour C _Tn C _{Tn [1].}

Or, the color setting unit 51 shown in FIG. 2, radially pull the straight V present in the wall thickness direction from the mean center-of-gravity position O _Tn of cardiac phase Tn, the lumen of the V by dividing the V-number segment A _Tn [v] (v = 1, 2,..., V) may be set. In that case, the segment _A Tn [v], the representative value of ED ratio _R Tn [u] corresponding to all of u included in the segment _A Tn [v], sets the color corresponding to the magnitude of for example, an average value . Hereinafter, a case where the color setting unit 51 sets a color in units of the segment A _Tn [v] will be described.

FIG. 7 is a diagram illustrating a segment A _Tn [v] when the lumen is divided into six.

As shown in FIG. 7, the average center-of-gravity position O _Tn of cardiac phase Tn radially pull 6 (V = 6) This linear in the wall thickness direction, the lumen of the six by divided into six segments A _Tn [v] is set. In the following, the six segments A _Tn [v] are _{divided into} “int (lower wall)” that is the segment A _Tn [1] and “pst (rear wall)” that is the segment A _Tn [2], segment is _a Tn [3] "lat (side wall)" is a segment _a Tn [4] "ant (front wall)" is a segment _a Tn [5] "asp (front wall septum)", and It is defined as “sp (septal wall septum)” which is the segment A _Tn [6].

The display control unit 27 shown in FIGS. 1 and 2, a tomographic image I _Tn of cardiac phase Tn outputted from the image memory 26, sequentially updated in accordance with changes in n to be displayed on the display 14. Further, the display control unit 27 assigns respectively area of interest on the tomographic image _{I Tn} at cardiac phase Tn _L'Tn [u] the color determined by the color setting unit 51 for each u, ROI L' _The color assigned to _Tn [u] is sequentially updated according to the transition of n and displayed on the display 14. Or, the display control unit 27 assigns each for the segment on the tomographic image _{I Tn} at cardiac phase Tn _A Tn [v] the color determined by the color setting unit 51 for each v, the segment _A Tn [v] Are sequentially updated according to the transition of n and displayed on the display 14.

Further, the display controller 27 to overlap the tomographic image I _Tn, produced by the marker generator 44, and the marker MB _Tn representing the endocardium contour B _Tn myocardial corresponding to cardiac phase Tn, cardiac phase The marker MC _Tn representing the _epicardial contour C _Tn corresponding to _Tn is sequentially updated according to the transition of n and displayed on the display 14.

Since different colors are assigned to each u depending on the size of the ED ratio Rn [u] and displayed on the display 14, the operator can refer to the color of each segment A _Tn [v] in the cardiac phase Tn. Can easily recognize the magnitude of the ED ratio R _Tn [u] corresponding to each segment A _Tn [v], and can evaluate the diastolic ability of the heart. That is, when the color of the segment A _Tn [v] in the cardiac phase Tn is different from the colors of the other segments, the operator can easily grasp the abnormality of the expandability in the segment A _Tn [v]. For example, when the segment A _T46 [1] (int) in the cardiac phase T46 (n = 46) is assigned a color different from the segment such as the segment A _T46 [2] (pst), the segment A _T46 [ It is possible to easily grasp that the expandability of 1] is abnormal. Specifically, it becomes possible to easily grasp the decrease or enhancement of the expandability in the segment A _T46 [1].

  FIG. 8 is a diagram illustrating a display example of two-dimensional wall motion information for evaluating the heart of the subject P.

In the display example illustrated in FIG. 8, for example, a tomographic image IT46 of the cardiac phase _T46 is displayed among the tomographic images as a cross-sectional image displayed as a moving image with the transition of n of the cardiac phase Tn. Yes. In FIG. 8, the marker MB _T46 of the cardiac phase T46 output from the marker generation unit 44 and the marker MC _T46 are displayed so as to overlap the tomographic image _IT46 .

In the display example illustrated in FIG. 8, the average value R _T46 [u] of the ED ratios R _T46 [u] corresponding to all u included in the segment A _T46 [v] of the cardiac phase T46 output from the color setting unit 51. v] (R _Tn [v]), the color mapping CM _T46 in which the color corresponding to the segment A _T46 [v] is assigned for each v is displayed superimposed on the tomographic image _IT46 . For example, a color corresponding to asp of the cardiac phase T46 is assigned to asp and is superimposed on the tomographic image _IT46 . The color corresponding to the average value of the ED ratio R _T46 [u] corresponds to the color bar K.

In the display example shown in FIG. 8, the color corresponding to the average value R _T46 [v] of the segment A _Tn [v] in the cardiac phase Tn changes with time from the initial cardiac phase T0 to the cardiac phase T46 (heart A graph group G _T46 (G _Tn ) arranged for each v is displayed as the ratio [%] of the time phase Tn. In the graph group G _T46 , the six graphs arranged side by side correspond to the segment A _T46 [v] for each v. The color corresponding to the average value R _T46 [v] of the ED ratio R _T46 [u] corresponds to the color bar K.

In the display example shown in FIG. 8, the average value R _T46 (R _Tn ) of the ED ratios R _T46 [u] corresponding to all u included in the cardiac phase T46 is changed from the initial cardiac phase T0 to the cardiac phase T46. The graph _gT46 ( _gTn ) arranged by the time change until is shown. In graph _{g T46,} the horizontal axis shows the percentage of cardiac phase Tn [%] in the diastole, and the vertical axis represents the average value _{R T46} cardiac phase T46.

In the display example shown in FIG. 8, a waveform E in which ECG signals corresponding to the tomographic image In of the cardiac phase Tn output from the image memory 26 are arranged with a time change from the initial cardiac phase T0 to the cardiac phase T46. _T46 (E _Tn ) is shown. Then, by moving the bar F on the waveform E _T46 time series going waveform E _T46, displayed on the display 14 to obtain a tomographic image In corresponding to cardiac phase Tn the position of the bar F from the image memory 26 Let Further, the marker MBn and the marker MCn corresponding to the tomographic image In can be displayed on the tomographic image In corresponding to the cardiac phase Tn at the position of the bar F.

In the display example shown in FIG. 8, a color bar k corresponding to the color bar K and a marker m for designating a portion of the color bar k are displayed. Then, the operator moves the marker m using the operation panel 15 to instruct the initial contour coordinate setting unit 42 so that the cardiac time phase indicated by the bar F becomes the initial cardiac time phase T0. Based on the initial cardiac phase T0 indicated by the bar F and the cardiac phase Tn indicated by the marker m, the color value corresponding to the size of the average value R _T46 [v] of each segment A _T46 [v] (color bar The color (assigned by K) is assigned to each segment A _T46 [v] and displayed on the display 14.

Conventionally, since the strain reduction rate is used, if a variation occurs in the distortion, the strain reduction rate is affected by the variation. As a result, the color assigned to the segment A _Tn [v] of the cardiac phase Tn also varies, making it difficult to stably evaluate the expandability. On the other hand, in the ultrasonic diagnostic apparatus 10 according to the present embodiment, even when distortion occurs in the distortion, a color corresponding to the magnitude of the integral value ratio is assigned to the segment A _Tn [v] and displayed. Can be reduced. As a result, it is possible to display with the color variation assigned to the segment A _Tn [v] reduced. Further, it is possible to know the ratio of how much the extension of the segment A _Tn [v] is completed. For this reason, it is possible to more stably evaluate the expandability.

Further, by assigning a color corresponding to the magnitude of the integral value to the segment A _Tn [v] and displaying it on the display 14, by grasping the difference in the color of the segment A _Tn [v], the segment A _Tn It becomes possible to easily evaluate the expandability in [v]. Specifically, the difference in color of the segment A _{Tn [v],} since the ratio of the integral value of the reduction ratio of the strain of the segment A _{Tn [v]} can be easily grasped, the segment A _Tn of _[v] It is possible to easily grasp the decrease or enhancement of the expandability.

  When volume scanning is performed by the scan control unit 39, the image generation unit 25 receives volume data from the signal processing unit 24 and performs volume rendering on the volume data to generate 3D image data. . Furthermore, the image generation unit 25 may generate data of an MPR image (an arbitrary cross-sectional image) by performing MPR (multi-planar reconstruction) processing on the volume data. Then, the image generation unit 25 outputs an ultrasonic image such as a three-dimensional image or an MPR image to the image memory 26. The initial contour coordinate setting unit 42, based on the three-dimensional image of the initial cardiac phase T0 acquired from the image memory 26, the three-dimensional coordinate information of the intimal contour of the myocardium in the initial cardiac phase T0, and the initial heart Three-dimensional coordinate information of the epicardial contour of the myocardium in the time phase T0 is set. Further, the contour coordinate setting unit 43, based on the three-dimensional image of the cardiac phase Tn acquired from the image memory 26, the three-dimensional coordinate information of the intimal contour of the myocardium in the cardiac phase Tn, and the cardiac phase The three-dimensional coordinate information of the outer membrane contour of the myocardium at Tn is set.

  FIG. 9 is a diagram illustrating a display example of three-dimensional wall motion information for evaluating the heart of the subject P.

In FIG. 9, for example, a three-dimensional image of the cardiac phase T46 is displayed among the three-dimensional images as a cross-sectional image displayed as a moving image with the transition of n of the cardiac phase Tn. In FIG. 9, the marker MB _T46 of the cardiac phase T46 output from the marker generation unit 44 and the marker MC _T46 are displayed superimposed on the three-dimensional cut image.

  Next, the operation of the ultrasonic diagnostic apparatus 10 will be described using the flowchart shown in FIG.

First, the operator brings the ECG measurement device 12 into contact with the body surface near the heart of the subject P, and applies the ultrasonic probe 11 of the ultrasonic diagnostic apparatus 10 to the body surface near the heart. The ultrasonic probe 11 transmits an ultrasonic wave to the subject P and receives an echo signal corresponding to the transmitted ultrasonic wave. Based on the echo signal, by the image generating unit 25, data of the tomographic image I _T in cardiac phase T (moving image data heart) is generated. The image memory 26 receives the ECG signal from the ECG memory 23 and stores the generated tomographic image in association with the cardiac phase T in which the tomographic image is generated (step S1). For example, when the ultrasonic diagnostic apparatus 10 transmits and receives ultrasonic waves over one cardiac cycle, a tomographic image IT of the cardiac phase _T is generated over one cardiac cycle and stored in the image memory 26. .

  Next, a predetermined period is set by an input by the operator using the operation panel 15 (step S2). For example, a predetermined period of one cardiac cycle is set by an input using the operation panel 15 by the operator.

  Next, based on the tomographic image of the heart in the initial cardiac phase T0 arbitrarily set from the plurality of cardiac time phases T stored in the image memory 26, the two-dimensional contour of the heart in the initial cardiac phase T0 is obtained. Coordinate information is set (step S3). In step S3, when the operator inputs the end systole using the operation panel 15, a tomographic image corresponding to the end systole is acquired from the image memory 26 as a tomographic image of the initial cardiac phase T0. In step S3, a tomographic image of the initial cardiac phase T0 is displayed on the display 14. Since the cardiac phase T is associated with each of the tomographic images stored in the image memory 26, in step S3, the tomographic image corresponding to the end systole is used as the tomographic image of the initial cardiac phase T0. Can be obtained from.

  Specifically, in step S3, based on the tomographic image of the initial cardiac phase T0 acquired from the image memory 26, the intimal contour of the myocardium in the initial cardiac phase T0 and the outer myocardium in the initial cardiac phase T0. Set the membrane contour. In the tomogram of the heart, papillary muscles, chordae, etc. appear in addition to the intima and outer membranes of the myocardium. While observing the tomographic image of the initial cardiac phase T0 displayed on the display 14, the operator uses the operation panel 15 to include the papillary muscles and chordae expressed in the tomographic image of the initial cardiac phase T0. Enter the intimal contour line of the myocardium so that there is no. In the evaluation of the myocardium, the papillary muscles and chordae are noisy, so the contour line of the intima is input avoiding the papillary muscles and chordae. For example, when the operator traces the two-dimensional contour of the intima appearing in the tomographic image of the initial cardiac phase T0 displayed on the display 14, the initial contour coordinate setting unit 42 causes the myocardium in the initial cardiac phase T0. Sets the coordinate information of the intimal contour.

  On the other hand, in step S3, the operator sets the coordinate information of the epicardial contour of the myocardium in the initial contour by tracing the two-dimensional contour of the epicardium that appears in the tomographic image of the initial cardiac phase displayed on the display 14. To do.

Next, as described with reference to FIG. 4, the above formula (1) is based on the coordinate information of each point constituting the intimal contour and the coordinate information of each point constituting the epicardial contour in the initial cardiac phase T0. ) Is used to calculate the film thickness D _T0 [u] of the initial cardiac phase T0. (Step S4).

  Next, the intimal and epicardial contours of the initial cardiac phase T0 set in step S3, and the cardiac phase Tn (n = 1, 2,...) After the initial cardiac phase T0 acquired from the image memory 26. The coordinate information of the two-dimensional outline of the heart in the cardiac time phase Tn is set based on the tomographic images of the heart in ().

Next, a marker MB _Tn representing the intimal contour B _Tn of the myocardium is generated based on the coordinate information of the intimal contour in the cardiac phase Tn set in step S5, and the epicardial contour coordinate information in the cardiac phase Tn is generated. Based on this, a marker MC _Tn representing the _epicardial contour C _Tn of the myocardium is generated (step S6). The marker _{MB Tn} representing the endocardium contour _{B Tn,} the concept of the tomographic image _{I Tn} of the marker _{MC Tn} is superimposed to represent the adventitia contour _{C Tn} shown in Fig.

Next, as described with reference to FIG. 5, based on the coordinate information of each point constituting the intimal contour in the cardiac phase Tn and the coordinate information of each point constituting the epicardial contour, the above formula (2) Is used to calculate the film thickness D _Tn [u] of the cardiac phase Tn (step S7).

Based on the film thickness D _T0 [u] of the initial cardiac phase T0 calculated in step S4 and the film thickness D _Tn [u] of the cardiac phase Tn calculated in step S7, the above equation (3) is obtained. The difference ΔD _Tn [u] between the initial cardiac phase T0 and the cardiac phase Tn is calculated as the film thickness displacement (step S8).

  Based on the film thickness displacement of the cardiac phase Tn calculated in step S8 and the film thickness of the initial cardiac phase T0 calculated in step S4, the wall thickness in the cardiac phase Tn is calculated using the above equation (4). A distortion of the myocardium in the direction is calculated (step S9).

  Based on the strain Sn [u] calculated in step S9, the myocardial strain reduction rate in the wall thickness direction in the cardiac phase Tn is calculated using the above equation (5) (step S10).

  An integrated value of the strain reduction rate of the cardiac phase Tn obtained by integrating the strain reduction rate of the cardiac phase Tn calculated in step S10 on the time axis from the initial cardiac phase T0 to the cardiac phase Tn is calculated (step S11). .

  The ED ratio of the integrated value of the strain reduction rate of the cardiac phase Tn calculated in step S11 to the integrated value of the strain reduction rate of the end diastole ED is calculated using the above formula (6) (step S12).

Next, a region of interest including the orthogonal line L _Tn [u] of the cardiac phase Tn is set, and a color corresponding to the magnitude of the ED ratio calculated in step S12 is set for the region of interest (step S13). .

The display control unit 27, as shown in FIG. 8, and displays a tomographic image I _Tn of cardiac phase Tn outputted from the image memory 26 on the display 14. Further, the display controller 27, as shown in FIG. 8, assigns the color determined by the step S13 to the upper tomogram I _Tn at cardiac phase Tn is displayed on the display 14 (step S14).

  Next, it is determined whether or not the cardiac time phase Tn + 1 at the next timing of the cardiac time phase Tn is outside the predetermined period set in step S2 (step S15). If YES in step S15, that is, if it is determined that the cardiac phase Tn + 1 is outside the predetermined period set in step S2, the operation is terminated.

  On the other hand, if the determination in step S15 is NO, that is, if it is determined that the cardiac phase Tn + 1 is not outside the predetermined period set in step S2, the cardiac phase Tn is set as the cardiac phase Tn + 1 (step S16). Return to S3.

  According to the ultrasonic diagnostic apparatus 10 of the present embodiment, by using an output value calculated based on a value obtained by integrating the rate of decrease in strain of a specific tissue, the influence of variation in the rate of decrease in tissue strain is reduced. Is possible. This makes it possible to display the expandability of a specific organization more appropriately.

DESCRIPTION OF SYMBOLS 10 Ultrasonic diagnostic apparatus 11 Ultrasonic probe 12 ECG measuring device 13 Apparatus main body 14 Display 15 Operation panel 21 Ultrasonic transmission part 22 Ultrasonic reception part 23 ECG memory 24 Signal processing part 25 Image generation part 26 Image memory 27 Display control part 39 Scan control unit 40 Image processing device 41 Interface unit 42 Initial contour coordinate setting unit 43 Contour coordinate setting unit 44 Marker generating unit 45 Film thickness calculating unit 46 Displacement calculating unit 47 Strain calculating unit 48 Strain reduction rate calculating unit 49 Integral value calculating unit 50 Standardization part 51 Color setting part

Claims (13)

Image generation means for receiving an echo signal obtained by scanning a moving subject with ultrasonic waves and generating ultrasonic image data based on the echo signal;
Means for storing the ultrasonic image in association with a time phase signal;
A displacement calculating means for calculating the displacement of the subject for each time phase based on the ultrasonic image corresponding to the time phase signal within a predetermined period;
Strain calculation means for calculating strain of the subject using the displacement;
A reduction rate calculating means for calculating a strain reduction rate based on the distortion for each time phase within the predetermined period and the initial time phase distortion within the predetermined period;
An integral value calculating means for calculating an integral value obtained by integrating the rate of decrease in distortion from the initial time phase to the predetermined time phase within the predetermined period;
Display information generating means for generating display information based on the integral value;
Display control means for displaying the display information;
An ultrasonic diagnostic apparatus comprising: The ultrasound according to claim 1, wherein the displacement calculating unit calculates the displacement of the myocardium by calculating coordinate information of an intimal contour and an outer contour of a myocardium of the heart as the subject. Diagnostic device. The ultrasonic diagnostic apparatus according to claim 2, wherein the integral value calculation unit sets one cardiac cycle from the end systole of the heart or one heart cycle from the end diastole of the heart as the predetermined period. . The display information generation unit generates the display information that divides the subject into a plurality of segments and changes a display form in accordance with a size of a representative value based on the plurality of integral values included in each segment. The ultrasonic diagnostic apparatus according to claim 1, wherein the ultrasonic diagnostic apparatus is characterized. 5. The display information generation unit according to claim 1, wherein the display information is an image obtained by superimposing a color image corresponding to a size of the integral value or the representative value on the ultrasonic image. The ultrasonic diagnostic apparatus as described in any one of them. The display information generating unit is configured to display the display information by integrating the integrated value or the representative value from the initial time phase to the predetermined time phase, and the integrated value from the initial time phase to the end time phase within the predetermined period. Or it is set as a ratio with the said representative value, The ultrasonic diagnostic apparatus as described in any one of Claims 1 thru | or 5 characterized by the above-mentioned. The display information generating means is configured to display the display information by the integration value or the representative value from the initial time phase to the predetermined time phase, and the rate of decrease from the initial time phase to the end time phase within the predetermined time period. The ultrasonic diagnostic apparatus according to any one of claims 1 to 6, wherein a ratio of the integral value from the initial time phase to the end time phase is 100%. The display information generation means displays, as the display information, when the integral value, the representative value, or the ratio is equal to or less than a threshold value, the position where the integral value, the representative value, or the ratio is to be displayed is different. The ultrasonic diagnostic apparatus according to claim 1, wherein the ultrasonic diagnostic apparatus is displayed in a form. The ultrasonic diagnostic apparatus according to claim 1, wherein the image generation unit generates a tomographic image as the ultrasonic image. The ultrasonic diagnostic apparatus according to claim 1, wherein the image generation unit generates a three-dimensional image based on volume data as the ultrasonic image. 11. The ultrasonic diagnostic apparatus according to claim 1, wherein the image generation unit generates an MPR (Multi Planar Reconstruction) image based on volume data as the ultrasonic image. Means for storing ultrasonic image data based on an echo signal obtained by scanning a moving subject with ultrasonic waves in association with a time phase signal;
Means for calculating the displacement of the subject for each time phase based on the ultrasound image corresponding to the time phase signal within a predetermined period;
Means for calculating distortion of the subject using the displacement;
Means for calculating a strain reduction rate based on the distortion for each time phase within the predetermined period and the initial time phase distortion within the predetermined period;
Means for calculating an integral value obtained by integrating the rate of decrease in distortion from the initial time phase to the predetermined time phase within the predetermined period;
Means for generating display information based on the integral value;
Means for displaying the display information;
An image processing apparatus comprising: On the computer,
A function of receiving an echo signal obtained by scanning a moving subject with ultrasound and generating ultrasonic image data based on the echo signal;
A function of storing the ultrasonic image in association with a time phase signal;
A function of calculating the displacement of the subject for each time phase based on the ultrasound image corresponding to the time phase signal within a predetermined period;
A function of calculating distortion of the subject using the displacement;
A function of calculating a strain reduction rate based on the distortion for each time phase within the predetermined period and the initial time phase distortion within the predetermined period;
A function of calculating an integral value obtained by integrating the rate of decrease in distortion from the initial time phase to a predetermined time phase within the predetermined period;
A function of generating display information based on the integral value;
A function of displaying the display information;
A control program for an ultrasonic diagnostic apparatus characterized by realizing the above.