JP6600266B2 - Ultrasonic diagnostic equipment - Google Patents

Description

  The present invention relates to an ultrasonic diagnostic apparatus, and more particularly to measurement of a heart using ultrasonic waves.

  An ultrasonic diagnostic apparatus is an apparatus that forms and displays an ultrasonic image based on reception data obtained by transmitting and receiving ultrasonic waves. Generally, an ultrasonic diagnostic apparatus has a plurality of operation modes (B mode, Doppler mode, etc.). Furthermore, an ultrasonic diagnostic apparatus having a plurality of measurement functions is also known. A suitable example of such a measurement function is a measurement function related to the heart.

  For example, Patent Document 1 describes a technique for identifying the type of an ultrasonic tomographic image as a technique for supporting measurement of the heart by ultrasonic waves. Patent Document 2 describes a technique for extracting the contour of a target part such as a heart in a medical image such as an ultrasonic image. Patent Document 3 describes a technique for specifying a cross section using image recognition processing, and is expected to be applied to measurement of the heart by ultrasonic waves.

Japanese Patent No. 5242163 Japanese Patent No. 575794 International Publication No. WO2010 / 038848 Pamphlet

  In the measurement of the heart by ultrasonic waves, a number of procedures such as selection of a measurement (analysis) type, selection of a measurement cross section, selection of a measurement site, and setting of the contour of the measurement site are required. For example, measurement of ejection fraction, which is an example of heart measurement, requires a number of procedures such as measurement cross-section selection, measurement site selection, and measurement site contour setting, and these procedures are combined with end-diastolic images and contraction. It needs to be repeated for the final image. Conventionally, it has been common to rely on operations from users such as doctors and laboratory technicians for all or most of these complicated settings. Leaving complicated operations related to measurement to the user increases the burden on the user, and there is also a concern that measurement reproducibility and objectivity may be reduced due to variations in judgment according to the user's skill and experience value. .

  An object of the present invention is to provide an automated technique for measuring a heart by ultrasonic waves.

  An ultrasonic diagnostic apparatus suitable for the above object is an ultrasonic diagnostic apparatus that processes volume data obtained by transmitting and receiving ultrasonic waves to and from a three-dimensional space including the heart, and has a first volume corresponding to a first time phase. At least one cross-sectional data is specified in the first volume data according to the shape of the heart in the data, and the second volume is determined according to the shape of the heart in the second volume data corresponding to the second time phase. A cross-section specifying unit for specifying at least one cross-section data in the data; an analysis result of a first time phase obtained from at least one cross-section data in the first volume data; and at least one cross-section in the second volume data. A measurement processing unit for obtaining a measurement value indicating a change in the heart between time phases based on the analysis result of the second time phase obtained from the data , Characterized by having a.

  According to the above configuration, the cross section specifying unit specifies at least one cross section data in the first volume data and the second volume data. Therefore, for example, a complicated user operation for adjusting the position and inclination of the cross-sectional data can be reduced, and preferably, a user operation for adjusting the cross-section can be eliminated. Thereby, the burden on the user for measurement is reduced, and further, the reproducibility and objectivity of measurement due to variations in judgment according to the skill and experience value of the user are suppressed.

  In the above configuration, at least one cross-sectional data is specified in the first volume data according to the form of the heart in the first volume data corresponding to the first time phase, and the second volume corresponding to the second time phase. At least one cross-sectional data is specified in the second volume data in accordance with the shape of the heart in the data. That is, at least one cross-sectional data is specified for each time phase according to the shape of the heart in that time phase. The shape of the heart varies depending on various factors. Changes in the shape of the heart include, for example, changes in the shape of the heart accompanying expansion and contraction movement, movement of the entire heart accompanying expansion and contraction movement, and the like. The movement of the entire heart includes parallel movement, rotational movement, and twisting movement of the entire heart.

  According to the above configuration, at least one cross-sectional data is specified for each time phase according to the shape of the heart at each time phase, taking into account that the heart shape changes in a complex manner even when healthy. For example, for each time phase, cross-sectional data suitable for the shape of the heart in that time phase, preferably optimal cross-sectional data is set. Therefore, for example, the above configuration improves the measurement accuracy compared to the case where common (fixed) cross-sectional data is specified in a plurality of time phases, and the heart-related changes are ignored or neglected, and the measurement related to the heart is performed. To do.

  In a preferred embodiment, the cross-section specifying unit specifies cross-section data corresponding to a four-chamber cross section and a two-chamber cross section including the left ventricle of the heart in the first volume data, and the heart in the second volume data. The cross-sectional data corresponding to the four-chamber cross section including the left ventricle and the two-chamber cross section are specified.

  In a preferred embodiment, the cross-section specifying unit searches the first volume data for a feature point corresponding to the heart apex, a feature point corresponding to the mitral annulus, and a feature point corresponding to the tricuspid annulus. The cross section specified based on these three feature points is the four-chamber cross section of the first volume data, and the feature points corresponding to the apex of the heart and the features corresponding to the mitral annulus in the second volume data A feature point corresponding to the point and the tricuspid annulus is searched, and a cross section specified based on these three feature points is set as a four-chamber cross section of the second volume data.

  In a preferred embodiment, the cross-section specifying section includes a feature point corresponding to the apex of the heart and a feature point corresponding to the mitral annulus in the first volume data, and a cross-section intersecting the four-chamber cross-section is included in the first volume data. A two-chamber cross section of one volume data, and a cross section that intersects the four-chamber cross section including a feature point corresponding to the apex of the heart and a feature point corresponding to the mitral valve annulus in the second volume data. It is characterized by a two-chamber cross section of the data.

  In a preferred embodiment, the cross-section specifying unit specifies cross-section data corresponding to a four-chamber cross section and a two-chamber cross section of the first volume data by image recognition processing on the first volume data, and an image for the second volume data. Cross-sectional data corresponding to the four-chamber cross-section and the two-chamber cross-section of the second volume data are specified by the recognition process.

  In a preferred embodiment, the ultrasonic diagnostic apparatus corresponds to each cross section for each of the four-chamber cross section and the dual-chamber cross section of the first volume data, and the four-chamber cross section and the dual-chamber cross section of the second volume data. The image processing apparatus further includes a trace processing unit that obtains contour data of the left ventricle by applying a trace process to the cross-sectional data.

  In a preferred embodiment, the ultrasonic diagnostic apparatus uses the left ventricular contour data obtained from the four-chamber cross section and the two-chamber cross section of the first volume data as the analysis result of the first time phase. The volume of the left ventricle in one time phase is calculated, and based on the left ventricular contour data obtained from the four-chamber cross section and the two-chamber cross section of the second volume data, as the analysis result of the second time phase, It further has a volume calculation part which calculates the volume of the left ventricle in the 2nd time phase.

  In a preferred embodiment, the ultrasonic diagnostic apparatus uses the first volume corresponding to the end diastole of the heart based on electrocardiographic waveform information of the heart from volume data obtained over a plurality of time phases. It further has a time phase selection unit for selecting data and the second volume data corresponding to the end systole of the heart.

  In a desirable specific example, the ultrasonic diagnostic apparatus may analyze the volume of the left ventricle of the heart at the end diastole obtained from the first volume data as the analysis result of the first time phase and the analysis result of the second time phase. The ejection rate of the left ventricle of the heart is calculated as the measured value based on the volume of the left ventricle of the heart at the end systole obtained from the second volume data.

  In addition, the function corresponding to each part with which the ultrasonic diagnostic apparatus demonstrated above is provided may be implement | achieved by computer. For example, at least a part of the functions of the cross-section specifying unit, the measurement processing unit, the trace processing unit, the volume calculation unit, and the time phase selection unit configured as described above are realized by a computer, and the computer is caused to function as an ultrasonic diagnostic apparatus. Also good.

  According to the present invention, an automated technique for measuring a heart by ultrasonic waves is provided.

It is a figure which shows the specific example of a suitable ultrasonic diagnostic apparatus in implementation of this invention. It is a figure which shows the specific example of a four-chamber cross section and a two-chamber cross section. It is a figure which shows the specific example of the display image displayed on a display part.

  FIG. 1 is a diagram showing a specific example of an ultrasonic diagnostic apparatus suitable for implementing the present invention. The ultrasonic diagnostic apparatus of FIG. 1 has a heart measurement function.

  The probe 10 is an ultrasonic probe that transmits and receives ultrasonic waves in a three-dimensional space including the heart in the living body. The probe 10 includes a plurality of vibration elements, and the plurality of vibration elements are electronically scanned and scanned with an ultrasonic beam in a space including the heart. The probe 10 is used, for example, by being held by a user such as a doctor or a laboratory technician and contacting the body surface of the subject. Note that the probe 10 may be a probe that combines electronic scanning and mechanical scanning.

  The transmission / reception unit 12 has functions of a transmission beam former and a reception beam former. That is, the transmission / reception unit 12 forms a transmission beam by outputting a transmission signal to each of the plurality of vibration elements included in the probe 10, and further receives a plurality of reception signals obtained from the plurality of vibration elements. A reception beam is formed by performing phasing addition processing or the like. As a result, the ultrasonic beam (transmission beam and reception beam) is scanned three-dimensionally in the three-dimensional space including the heart, and the reception signal (reception data) corresponding to the ultrasonic beam is collected from within the three-dimensional space including the heart. Is done. It should be noted that a technique such as transmission aperture synthesis may be used to obtain an ultrasonic reception signal.

  The image forming unit 20 forms volume data corresponding to a three-dimensional space including the heart based on an ultrasonic reception signal (reception data) obtained from the transmission / reception unit 12. The image forming unit 20 forms volume data for each time phase over a plurality of time phases. In addition, the image forming unit 20 may form image data of a three-dimensional ultrasonic image in which the heart is three-dimensionally displayed by, for example, rendering processing for volume data.

  The image storage unit 22 stores image files of a plurality of ultrasonic images. Each image file is three-dimensional moving image data composed of a plurality of time phase volume data formed in the image forming unit 20. The image storage unit 22 stores, for example, a plurality of image files corresponding to a plurality of dates and times relating to the same subject's heart, a plurality of image files relating to a plurality of subject's hearts, and the like.

  In addition, it is desirable that each image file stored in the image storage unit 22 is associated with electrocardiographic waveform information. In other words, it is desirable that the time phase of the volume data constituting each image file and the time phase of the electrocardiographic waveform are associated with each other. Thereby, for example, among the time data of a plurality of time phases constituting each image file, the time data corresponding to the characteristic time phase in the electrocardiogram waveform, for example, the timing of the R wave and the timing of the end of the T wave is obtained. Can be identified.

  The image selection unit 30 selects each image file used for heart measurement from a plurality of image files stored in the image storage unit 22. For example, display images (such as a list of thumbnail images based on typical volume data included in each image file) indicating the contents of a plurality of image files stored in the image storage unit 22 are displayed on the display unit 52, and doctors and A user such as a laboratory technician operates the operation device 60 while viewing the display image, thereby specifying at least one image file to be used for heart measurement. The image selection unit 30 selects at least one image file designated by the user.

  The measurement processing block 40 executes processing related to heart measurement based on each image file selected by the image selection unit 30. The measurement processing block 40 includes a time phase selection unit 41, a cross-section specifying unit 42, a site specifying unit 43, a trace processing unit 44, a volume calculation unit 45, a measurement processing unit 46, and a preset storage unit 47. Processing related to measurement executed in the measurement processing block 40 will be described in detail later.

  Based on the image data obtained from the image forming unit 20, the display processing unit 50 forms a display image that includes an ultrasonic image in which the heart is three-dimensionally projected. The display processing unit 50 also displays an image corresponding to each image file stored in the image storage unit 22 and a display image indicating the contents of a plurality of image files stored in the image storage unit 22 (for example, included in each image file). A list of thumbnail images based on representative volume data). Further, the display processing unit 50 forms a display image relating to the measurement of the heart based on each measurement image file selected by the image selection unit 30 and the measurement result obtained from the measurement processing block 40. The display image formed in the display processing unit 50 is displayed on the display unit 52.

  The control unit 100 generally controls the inside of the ultrasonic diagnostic apparatus in FIG. The overall control by the control unit 100 also reflects an instruction received from a user such as a doctor or a laboratory technician via the operation device 60.

  Among the configurations shown in FIG. 1 (respectively assigned parts), the transmitting / receiving unit 12, the image forming unit 20, the image selecting unit 30, the time phase selecting unit 41, the cross-section specifying unit 42, the site specifying unit 43, the trace processing unit 44, Each unit of the volume calculation unit 45, the measurement processing unit 46, and the display processing unit 50 can be realized using, for example, hardware such as an electric / electronic circuit or a processor. It may be used. Further, at least a part of the functions corresponding to the above-described units may be realized by a computer. That is, at least a part of the functions corresponding to the above-described units may be realized by cooperation between hardware such as a CPU, a processor, and a memory and software (program) that defines the operation of the CPU and the processor.

  The image storage unit 22 and the preset storage unit 47 can be realized by a storage device such as a semiconductor memory or a hard disk drive. A preferred specific example of the display unit 52 is a liquid crystal monitor or the like. The operation device 60 can be realized by at least one of a mouse, a keyboard, a trackball, a touch panel, and other switches, for example. And the control part 100 is realizable by cooperation with hardwares, such as CPU, a processor, a memory, and the software (program) which prescribes | regulates operation | movement of CPU, a processor, for example.

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

  The measurement processing block 40 performs a measurement process described in detail below on each image file selected by the image selection unit 30. A specific example of a measurement result obtained by the measurement process is a cardiac ejection fraction (EF: ejection fraction). Of course, other measurement values other than ejection ratio may be calculated. In the following description, processing relating to one image file (each image file) selected by the image selection unit 30 will be described in detail. When a plurality of image files are selected by the image selection unit 30, a process described in detail below may be executed for each image file.

  The time phase selection unit 41 selects time phase volume data used for measurement from volume data of a plurality of time phases constituting each image file to be measured selected by the image selection unit 30. For example, in the measurement of the ejection fraction of the heart, volume data corresponding to the end diastole of the heart and volume data corresponding to the end systole are selected as time phases used for the measurement. For example, based on the electrocardiogram waveform information associated with each image file to be measured, the time phase selection unit 41 and the end-diastolic volume data corresponding to the R wave of the electrocardiogram waveform and the T wave of the electrocardiogram waveform Select end systolic volume data corresponding to the end of the stroke.

  The cross section specifying unit 42 specifies at least one cross section data used for measuring the heart in the volume data corresponding to the end diastole and the end systole. For example, in the measurement of the ejection fraction of the heart, the cross-sectional data corresponding to the four-chamber cross section of the heart and the cross-sectional data corresponding to the two-chamber cross section are specified as at least one cross-sectional data used for the measurement.

  FIG. 2 is a view for explaining a four-chamber cross section and a two-chamber cross section of the heart. The four-chamber cross section (apical part four-chamber image: A4C) and the two-chamber cross section (apical part two-chamber image: A2C) are cross sections obtained by the apex approach, and the four-chamber cross section (A4C) has a left ventricle (LV). The four chambers of the right atrium (RV), left atrium (LA), and right atrium (RA) are projected. In addition, the left ventricle (LV) and the left atrium (LA) are projected on the two-chamber cross section (A2C). Various methods can be used to identify the cross-sectional data corresponding to the four-chamber cross section and the dual-chamber cross section in the volume data of each time phase, for example, in the volume data of the end diastole and the end systole, respectively. it can. A typical example is as follows.

"Specific example 1 (section identification using feature points in volume data)"
First, in the volume data of each time phase, three features consisting of a feature point corresponding to the heart apex of the heart, a feature point corresponding to the mitral annulus of the heart, and a feature point corresponding to the tricuspid annulus of the heart A point is searched. For the search for the three feature points, for example, it is desirable to use a learning-type technique such as random forest (Random Forest). For example, three feature points may be searched in the volume data of each time phase by pattern matching with reference volume data prepared in advance in a database or the like.

  A reference cross section including the searched three feature points is set in the volume data of each time phase, and the four-chamber cross section is specified based on the reference cross section. For example, the reference cross section is directly used as the four-chamber cross section. In addition, for example, a more appropriate four-chamber section is searched by pattern matching with a standard four-chamber section (four-chamber section template) prepared in advance in a database or the like in a space limited to the vicinity including the reference section. May be.

  Furthermore, in the volume data of each time phase, an orthogonal cross section that includes a feature point corresponding to the apex and a feature point corresponding to the mitral annulus and is orthogonal to the four-chamber cross section is defined as a two-chamber cross section. In addition, in a space limited to the vicinity including the orthogonal cross section, a two-chamber cross section intersecting the four-chamber cross section is searched by pattern matching with a standard two-chamber cross section (two-chamber cross-section template) prepared in advance in a database or the like. May be.

"Specific example 2 (section identification using image recognition processing)"
This method is described in detail in Patent Document 3 (International Publication No. WO2010 / 038848 pamphlet). For example, image data (signal pattern) of a four-chamber cross-section (apical part four-chamber image) serving as a reference (template) prepared in advance in a database or the like, and a cross-section (2 in a three-dimensional signal) in each time phase volume data The cross section with good matching (for example, most similar to the template) is set as the four-chamber cross section. Similarly, for example, image data (signal pattern) of a two-chamber cross section (apical portion two-chamber image) serving as a reference (template) prepared in advance in a database or the like, and volume data in each time phase (in a three-dimensional signal) Matching with a cross section (two-dimensional signal pattern) is performed, and a cross section with good matching (for example, most similar to the template) is defined as a two-chamber cross section.

  Further, as detailed in, for example, Patent Document 3, a two-dimensional signal pattern ranging from 0 to 180 degrees obtained by rotating the probe 10 (two-dimensional array probe) about the opening direction is used as an object of matching. Accordingly, it is desirable to reduce the amount of calculation of matching compared to the case where the entire region in the volume data (in the three-dimensional space) of each time phase is set as the object of matching.

  The specific examples 1 and 2 described above are only some of the preferred specific examples for specifying the four-chamber cross-section and the two-chamber cross-section, and the cross-section specifying unit 42 uses other techniques to determine the four-chamber cross-section. A two-chamber cross section may be specified.

  Thus, the cross-section specifying unit 42 specifies the cross-section data corresponding to the four-chamber cross section and the two-chamber cross section in the end diastole in the volume data corresponding to the end diastole, and the four chambers in the end systole in the volume data corresponding to the end systole. The cross-sectional data corresponding to the cross section and the two-chamber cross section are specified.

  The part specifying unit 43 specifies a measurement target part to be measured in the heart. The part specifying unit 43 specifies the measurement part in the cross-sectional data of the volume data of each time phase. For example, in the measurement of the ejection fraction of the heart, the cross-section specifying unit 42 specifies the four-chamber cross section and the two-chamber cross section at the end diastole, the four-chamber cross section and the two-chamber cross section at the end systole, Within each of these four cross sections, at least one of the left ventricle (LV) and the left atrium (LA) is specified as a measurement target region.

  The part specifying unit 43 specifies a measurement target part according to preset data stored in the preset storage unit 47 or according to an instruction from the user, for example. For example, if the left ventricle is preset as a measurement target part, the left ventricle is set as the measurement target part, and if the left atrium is preset, the left atrium is set as the measurement target part. Of course, both the left ventricle and the left atrium may be preset as measurement target parts. For example, the user may specify at least one of the left ventricle and the left atrium using the operation device 60, and the part specifying unit 43 may specify at least one of the left ventricle and the left atrium as a measurement target part according to the specification. Good.

  The trace processing unit 44 forms contour data of the measurement target part in the cross section specified in the volume data for each time phase. For example, when the left ventricle is the measurement target site in the measurement of the ejection fraction of the heart, the trace processing unit 44 performs each of the four-chamber section and the two-chamber section at the end diastole, the four-chamber section and the two-chamber section at the end systole. Every time, by applying a trace process to the cross-sectional data corresponding to each cross-section, the contour data of the left ventricle is formed in each cross-section. For example, a plurality of sample points are set along the contour of the left ventricle cavity, and contour data connecting the plurality of sample points is formed as contour data. The trace processing unit 44 desirably performs full auto trace (full auto trace) in which all of a plurality of sample points are set in the cross section data corresponding to each cross section.

  In the full auto trace, the trace processing unit 44 extracts an outline of a measurement target portion (for example, the left ventricle) included in the image (cross section) by analyzing an image in the cross section data corresponding to each cross section. For example, pattern matching, an active contour model (ACM), a dynamic shape model (ASM) using machine learning, or a dynamic appearance model (AAM) can be applied to the contour extraction. In the contour extraction, for example, an annulus portion (mitral annulus and tricuspid annulus) having relatively high brightness in the image is extracted as a representative point, and based on the extracted representative point, for example, The outline of the measurement target part (for example, the left ventricle) may be extracted using the technique of Patent Document 2 (Japanese Patent No. 5757944). Of course, for example, a learning method such as the AdaBoost method may be used for extracting the representative points.

  In the full auto trace, for example, if the measurement target site is the left ventricle, a plurality of sample points are set on the boundary of the left ventricular membrane. For example, when it is desired to measure the left ventricular epicardium, a plurality of sample points may be set on the boundary of the left ventricular epicardium.

  In the full auto trace, it is desirable that the trace processing unit 44 executes the trace processing using an algorithm selected according to the type of cross section to be processed, the time phase, and the measurement target portion. For example, when executing the trace processing for the left ventricle of the end-diastolic four-chamber section, an algorithm corresponding to the left ventricle of the end-diastolic four-chamber section is used, and the left-hand side of the two-chamber section of the end systole is used. When executing the trace processing on the chamber, an algorithm corresponding to the left chamber of the two-chamber cross section at the end systole is used.

  The user sets at least one representative point of the plurality of sample points in the cross-sectional data corresponding to each cross section, and the trace processing unit 44 sets the remaining plural points based on the at least one representative point set by the user. Semi-automatic tracing (semi-automatic tracing) for setting sample points may be performed.

  In the semi-automatic trace, a user such as a doctor or a laboratory technician operates the operation device 60 while confirming the display image of each cross section displayed on the display unit 52, and sets the position of each representative point in each cross section. Designate and set at least one representative point on the contour of the measurement target part. For example, if the measurement target region is the left ventricle, three representative points corresponding to three locations of two annulus parts (mitral annulus and tricuspid annulus) and one apex part are set. The trace processing unit 44 sets the remaining (other) sample points based on at least one representative point set by the user. The trace processing unit 44 may use any of various known processes. For example, the trace processing unit 44 uses a technique for extracting the contour of the target portion described in Patent Document 2 (Japanese Patent No. 575794). Thus, it is desirable to extract the contour of the measurement target part where a plurality of sample points are set.

  When contour data (contour data connecting a plurality of sample points) is formed in the cross-section data corresponding to each cross-section by the trace processing unit 44, the contour line is displayed on the tomographic image corresponding to each cross-section. An image is displayed on the display unit 52.

  FIG. 3 is a diagram illustrating a specific example of a display image displayed on the display unit 52. The display image illustrated in FIG. 3 includes an ultrasonic image display area 52A and a measurement result display area 52B. In the ultrasonic image display area 52A, tomographic images corresponding to a plurality of cross-sectional data used for measurement are displayed. For example, as illustrated in FIG. 3, the end-diastolic (ED) four-chamber section (A4C), the end-diastolic (ED) two-chamber section (A2C), and the end-systolic (ES) four-chamber section (A4C) and contraction Each tomographic image corresponding to the two-chamber cross section (A2C) at the end stage (ES) is displayed. In each tomographic image, a contour line set by the trace processing unit 44 (a trace line in the left ventricular cavity connecting a plurality of sample points) is also displayed. In FIG. 3, the outline is indicated by a broken line in each tomographic image.

  The user can confirm the contour line in each tomographic image displayed on the display unit 52 and can instruct re-execution of the trace processing using the operation device 60 as necessary. When an instruction to redo the trace process is given, the trace processing unit 44 executes the redo of the trace process (retrace process) in each cross section designated by the user. In the re-processing of the trace process, a manual trace (manual trace) in which the user specifies the positions of some sample points or all sample points may be performed.

  The volume calculation unit 45 calculates the volume of the measurement target part in the time phase based on the contour data of the measurement target part obtained for each time phase. For example, when the left ventricle is a measurement target site in the measurement of the ejection fraction of the heart and the contour data of the left ventricular cavity is obtained, the volume calculation unit 45 calculates the contour data in the four-chamber cross section at the end diastole. Based on the contour data in the cavity section, the volume (volume) of the left ventricular lumen at the end diastole is calculated. In addition, the volume calculation unit 45 calculates the volume (volume) of the left chamber in the end systole based on the contour data in the four-chamber cross section at the end systole and the contour data in the two-chamber cross section.

  In calculating the volume (volume), various known calculation methods can be used. A typical example of the calculation method is the Simpson method (disk method). When calculating the volume of the left ventricle (lumen volume) by the Simpson method, for example, the length of the left ventricle in the four-chamber cross-section (apex portion four-chamber image) and in the two-chamber cross-section (apex portion two-chamber image) A plurality of discs (virtual ellipses for calculation) perpendicular to the long axis by dividing the axis into a plurality of parts are set. Next, the inner diameters of the two minor axes perpendicular to the major axis in each disk, for example, the distance from the major axis to the contour of the four-chamber cross section and the distance from the major axis to the contour of the two-chamber cross section are derived. The cross-sectional area of each disk is calculated based on the short axis inner diameter. Then, the volume (volume) of the left chamber is calculated from the sum of the cross-sectional areas of the plurality of disks.

For example, the length of the long axis is L, the number of disks (total number) is N (N is a natural number), and the inner diameters of two short axes in each disk n (n is a natural number of 1 to N) are An and Bn. Then, the volume (volume) V of the left ventricular cavity is calculated by the following equation, for example. In the following equation, Σ is the sum of n = 1 to N.
“Equation 1” V = (π / 4) × Σ (AnBn) × (L / N)

  The volume calculation unit 45 applies, for example, Equation 1 to each of the left ventricle at the end diastole and the left ventricle at the end systole, thereby determining the volume of the left ventricle at the end diastole (end diastole volume) and the volume at the end systole. The left ventricular volume (end systolic volume) is calculated.

The measurement processing unit 46 measures the change in the measurement target part between the time phases based on the analysis result of the measurement target part obtained from the end-diastolic volume data and the analysis result of the measurement target part obtained from the end-systolic volume data. Deriving a value. A preferred specific example of the measured value is the ejection fraction (EF: ejection fraction) of the heart. When the measurement target site is the left ventricle, the ejection fraction (EF) of the left ventricle is calculated by the following equation, for example.
“Equation 2” ejection fraction (EF) = (end diastolic volume−end systolic volume) / end diastolic volume

  The measurement result obtained by the measurement processing unit 46 is displayed, for example, in the measurement result display area 52B shown in FIG. For example, the ejection rate (EF) and the like are displayed numerically in the measurement result display area 52B.

  As mentioned above, although preferred embodiment of this invention was described, embodiment mentioned above is only a mere illustration in all the points, and does not limit the scope of the present invention. The present invention includes various modifications without departing from the essence thereof.

  DESCRIPTION OF SYMBOLS 10 probe, 12 transmission / reception part, 20 image formation part, 22 image memory | storage part, 30 image selection part, 41 time phase selection part, 42 cross-section specific part, 43 site | part specific part, 44 trace processing part, 45 volume calculation part, 46 measurement Processing unit, 47 preset storage unit, 50 display processing unit, 52 display unit, 60 operation device, 100 control unit.

Claims (7)

Ri by the transmission and reception of ultrasonic for three-dimensional space including the heart, and means for obtaining a plurality of volume data including a second volume data corresponding to the first volume data and the second time phase corresponding to the first time phase,
Identifying a plurality of first time phase section data corresponding to a plurality of measurement section of Oite the heart within the first volume data by cross specifying processing based on the first volume data, cross-section based on the second volume data and a cross-sectional specifying unit configured to specify a plurality of second time phase section data corresponding to Oite the plurality of measuring section within the second volume data by a specific process,
A trace for generating a plurality of first time phase contour data by a tracing process for the plurality of first time phase cross section data, and generating a plurality of second time phase contour data by a tracing process for the plurality of second time phase cross section data. A processing unit;
Based on a first time phase volume obtained from the plurality of first time phase contour data and a second time phase volume obtained from the plurality of second time phase contour data, a measurement value indicating the function of the heart is calculated. A measurement processing unit;
A plurality of first time phase tomographic images representing the plurality of first time phase cross section data and the plurality of first time phase contour data, the plurality of second time phase cross section data, and the plurality of second time phase contour data. A display unit that displays an image including a plurality of second time-phase tomographic images representing the measurement values, and
Having
An ultrasonic diagnostic apparatus. The ultrasonic diagnostic apparatus according to claim 1,
The cross-section specifying unit specifies the plurality of first time phase cross-section data corresponding to the four-chamber cross section including the left ventricle of the heart and the two-chamber cross section in the first volume data, and in the second volume data Specifying the plurality of second time phase cross-sectional data corresponding to the four-chamber cross section including the left ventricle of the heart and the two-chamber cross section;
An ultrasonic diagnostic apparatus. The ultrasonic diagnostic apparatus according to claim 2,
The sectional identification unit searches the feature point corresponding to the apex tricuspid annulus feature points corresponding to the feature points and the mitral annulus corresponding to the heart within the first volume data, the three First phase cross-sectional data corresponding to the four-chamber cross-section is specified based on the feature points, and a feature point corresponding to the apex of the heart and a feature point corresponding to the mitral annulus in the second volume data are determined. It searches the feature point corresponding to the tricuspid annulus, identifies a second time phase section data corresponding to the four-chamber view plane on the basis of these three feature points,
An ultrasonic diagnostic apparatus. The ultrasonic diagnostic apparatus according to claim 3.
The cross section specifying unit includes a feature point corresponding to the apex of the heart and a feature point corresponding to the mitral valve annulus in the first volume data, and the cross section data corresponding to a cross section intersecting the four-chamber cross section. First phase cross section data corresponding to the cavity section is specified, and the second volume data includes a feature point corresponding to the heart apex of the heart and a feature point corresponding to the mitral annulus, and intersects the four-chamber section. Specifying the second time phase cross-sectional data corresponding to the two-chamber cross-section as cross-sectional data corresponding to the cross-section ,
An ultrasonic diagnostic apparatus. The ultrasonic diagnostic apparatus according to claim 2,
The cross section specifying unit specifies the plurality of first time phase cross section data corresponding to the four-chamber cross section and the two-chamber cross section of the first volume data by image recognition processing on the first volume data, and the second volume data Identifying the plurality of second time phase cross-section data corresponding to the four-chamber cross section and the two-chamber cross section of the second volume data by image recognition processing for
An ultrasonic diagnostic apparatus. The ultrasonic diagnostic apparatus according to claim 1 ,
From the Volume data of the multiple, based on the electrocardiographic waveform information of the heart, and the first volume data corresponding to end diastole of the heart, the second volume data corresponding to the telesystole of the heart And a time phase selector for selecting
An ultrasonic diagnostic apparatus. The ultrasonic diagnostic apparatus according to claim 1 ,
The measured value is ejection fraction,
An ultrasonic diagnostic apparatus.