JP2006223558A - Ultrasonic diagnostic apparatus - Google Patents

Abstract

<P>PROBLEM TO BE SOLVED: To provide ultrasonic diagnostic apparatus shortening a diagnosis time in measuring the left ventricle on an M-mode image by automation and improving the efficiency of routine work. <P>SOLUTION: This ultrasonic diagnostic apparatus automates the measurement of the left ventricle of the heart on the M-mode image. In the measurement of the left ventricle, this apparatus is so formed as to automatically set measuring points for detecting the end-diastole, the end-systole, the left venticular posterior wall of the left ventricle, the left ventricle dimension and the interventricular septum. This apparatus is so formed that the automatically set measurement points, the end-diastole and the end-systole can be manually corrected. <P>COPYRIGHT: (C)2006,JPO&NCIPI

Description

  The present invention relates to an ultrasonic diagnostic apparatus that uses ultrasonic waves to display a temporal change as a so-called M-mode image for a diagnostic site in a subject.

  An organ that repeatedly expands and contracts, such as the heart, is examined by measuring its function with an ultrasonic diagnostic apparatus and an electrocardiogram. Here, as a measuring method, there is known a method in which a change with time of the heart is displayed as a so-called M-mode image and measured by this. In an ultrasonic diagnostic apparatus employing such a method, the volume (ventricular volume) is calculated from the diameters of the ventricle and the myocardium in the diastole and systole for the M-mode image. Specifically, in the M mode image, the left ventricular diameter, the left ventricular rear wall thickness, and the ventricular septal thickness in the diastole and the systole of the left ventricle are set, and for example, the ventricular volume is calculated.

By the way, the conventional measurement of the left ventricular diameter, the left ventricular posterior wall thickness, and the ventricular septum thickness in the left ventricular diastole and systole is, for example, a state in which an M mode image including the end diastole to the end systole is frozen. In this state, the measurement point for setting the left ventricular diameter, the left ventricular posterior wall thickness, and the ventricular septum thickness is set by the examiner. Specifically, in the setting of the end diastole and the end systole, the time phase of the R wave obtained from the electrocardiogram is designated as the end diastole, and the end systole position is designated by the time from the R wave (for example, Patent Document 1).
JP 2001-79006 A

  In the above prior art, the examiner himself has to specify the measurement point, and no consideration has been given to the examiner's burden and inspection time in routine work.

  The present invention has been made in view of the above-described circumstances, and performs ultrasonic diagnosis in left ventricle measurement on an M-mode image, thereby reducing the examination time and improving the efficiency of routine work. It is an object to provide an apparatus.

  The ultrasonic diagnostic apparatus according to the first aspect of the present invention, which has been made to solve the above problem, acquires a tomographic image or an M-mode image based on information from an ultrasonic probe in contact with a subject. In the ultrasonic diagnostic apparatus for displaying together with the electrocardiogram waveform of the subject, means for setting a line on the M-mode image based on the position coordinates of the feature points of the electrocardiogram waveform, and luminance information on the line It is characterized by comprising means for setting a plurality of measurement points and means for measuring the thickness or diameter based on the plurality of measurement points. According to the present invention having such a feature, since various measurement points are extracted on the ultrasonic diagnostic apparatus side, it becomes possible to reduce the work man-hours of the examiner. The work efficiency is improved.

  The ultrasonic diagnostic apparatus according to a second aspect of the present invention is the ultrasonic diagnostic apparatus according to the first aspect, further comprising means for enabling manual correction of the line and / or the plurality of measurement points. It is said. According to the present invention having such characteristics, erroneous measurement can be eliminated. Further, in the correction of the line, it is possible to appropriately cope with the case where the R wave as the feature point cannot be obtained from the electrocardiogram waveform.

  In addition, as an ultrasonic diagnostic apparatus for solving the above problems, (1) acquiring a tomogram of the subject based on information from an ultrasonic probe in contact with the subject, A function of displaying information obtained by imaging the passage of time by paying attention to a certain straight line as an M-mode image, and measuring an electrocardiogram, and obtaining the position of the R wave of the measured electrocardiogram as the position coordinates of the M-mode image. A function, a function of displaying an end diastole line as the end diastole of the subject on the M-mode image based on the position coordinates of the R wave, a left ventricular rear wall end diastole thickness, a ventricle on the end diastole line Setting the end-diastolic measurement point for measuring the septal end-diastolic thickness and the left ventricular end-diastolic diameter, and based on the set end-diastolic measurement point, the left ventricular posterior wall end-diastolic thickness, the ventricular septal end-diastolic thickness And the left ventricle A function for measuring the end-diastolic diameter, a function for tracing the left ventricular posterior wall and the ventricular septum based on the M-mode image, a trace of the end systolic line on the trace of the left ventricular posterior wall and the trace of the ventricular septum The end systolic measurement point is set based on the function of displaying as the end systole of the subject, the trace of the left ventricular posterior wall, the trace of the ventricular septum, and the end systolic line, and the set end systolic measurement point And a function of measuring the left ventricular posterior wall end-systolic thickness, the ventricular septal end-systolic thickness, and the left ventricular end-systolic diameter. According to the ultrasonic diagnostic apparatus having the feature (1) as described above, since various measurement points are extracted on the ultrasonic diagnostic apparatus side, it becomes possible to reduce the work man-hours of the examiner. The inspection time can be shortened and the efficiency of routine work can be improved.

  The ultrasonic diagnostic apparatus may be characterized in that, in the ultrasonic diagnostic apparatus described in (1) above, (2) the end diastole measurement point is set based on luminance information of the M-mode image. . According to the ultrasonic diagnostic apparatus having such a feature, it becomes possible to accurately set the end diastole measurement point.

  In the ultrasonic diagnostic apparatus according to (1) or (2), (3) the position of the end diastole measurement point and the end systole measurement point can be manually corrected. It can be. According to the ultrasonic diagnostic apparatus having such characteristics, erroneous measurement can be eliminated.

  The ultrasonic diagnostic apparatus is characterized in that, in the ultrasonic diagnostic apparatus according to any one of the above (1) to (3), (4) the position of the end diastole line and the end systole line can be manually corrected. can do. According to the ultrasonic diagnostic apparatus having such characteristics, it is possible to appropriately cope with the correction of the end diastole line when an R wave cannot be obtained from the electrocardiogram.

  According to the present invention, when left ventricle measurement is performed in an M-mode image, it is possible to shorten the inspection time and improve the efficiency of routine work. Further, the information desired by the examiner can be acquired by correcting the information acquired by automatic measurement.

  Hereinafter, description will be given with reference to the drawings. FIG. 1 is a block diagram showing an embodiment of the ultrasonic diagnostic apparatus of the present invention.

  The ultrasonic diagnostic apparatus of the present invention acquires a tomographic image related to an imaging region of a subject using ultrasonic waves, and focuses on a certain straight line on the acquired cross section to visualize information on the passage of time as M mode. While displaying as an image, it is possible to detect an electrocardiogram and to detect the position of the R wave on the M-mode image from the information of the detected electrocardiogram. Specifically, as shown in FIG. 1, the ultrasonic diagnostic apparatus of the present invention includes an ultrasonic probe 11, an ultrasonic transmission / reception unit 12, a value input unit 13, an electrocardiogram detection unit 14, and a calculation unit 15. The display unit 16 is provided. The ultrasonic diagnostic apparatus according to the present invention includes an M-mode image configuration unit, a digital scan converter, and an image storage unit, although not particularly illustrated. Each configuration will be described below.

  The ultrasonic probe 11 mechanically or electronically performs beam scanning to transmit and receive ultrasonic waves into the subject. Inside the ultrasonic probe 11 is a source of ultrasonic waves and from inside the living body. One or a plurality of transducers for receiving the reflected echo. As the ultrasonic probe 11, a known one is used.

  The ultrasonic transmission / reception unit 12 is configured to drive the connected ultrasonic probe 11 to generate ultrasonic waves from the vibrator and to process the received reflected echo signal. Specifically, the ultrasonic transmission / reception unit 12 includes a known transmission pulser and transmission delay circuit for forming an ultrasonic beam to be transmitted from the ultrasonic probe 11 into the subject, and the ultrasonic probe 11. A receiving amplifier that amplifies the reflected echo signal received by each transducer, and a receiving delay circuit and an adder that form a received ultrasonic beam by adding the phases of the received reflected echo signals together. And a phase circuit.

  Such an ultrasonic transmission / reception unit 12 is connected to and controlled by the calculation unit 15. In addition, the ultrasonic transmission / reception unit 12 is connected to an unillustrated M-mode image configuration unit so that an M-mode image is reconstructed. The reconstructed M-mode image is stored in an image storage unit (not shown) via a digital scan converter (not shown). Image data stored in an image storage unit (not shown) is read based on a control signal and displayed on the display unit 16.

  The electrocardiogram detection unit 14 is configured to detect the electrocardiogram information of the subject, that is, to detect the electrocardiogram (a known one is used. The description of the detailed configuration is omitted). The electrocardiogram detection unit 14 is connected to an R wave position detection unit 14a that acquires position coordinates of an R wave on an M mode image, which will be described later, from the electrocardiogram information. The R wave position detection unit 14a is connected to and controlled by the calculation unit 15. The electrocardiogram detected by the electrocardiogram detection unit 14 is also stored in an image storage unit (not shown) via a digital scan converter (not shown).

  The arithmetic unit 15 is a part that is incorporated as a part of a control unit (not shown) that controls the entire ultrasound diagnostic apparatus, or that is controlled by the control unit in an independent state. It is comprised so that the calculation for automatic measurement can be performed. The calculation unit 15 includes an end-diastolic setting unit 15a, an end-systolic setting unit 15b, a measurement point setting unit 15c, a left ventricular rear wall, a ventricular septum tracing unit 15d, and a measurement calculation unit 15e. ing. The calculation unit 15 has a function as a microcomputer.

  The end diastole setting unit 15a can automatically display the end diastole of the subject as an end diastole line 62 to be described later on the M mode image based on the position coordinates of the R wave acquired by the R wave position detection unit 14a. It is configured. In addition to the R wave position detection unit 14a, a value input unit 13 is also connected to the end diastole setting unit 15a from the outside of the calculation unit 15. The end diastole setting unit 15a is connected to the end systole setting unit 15b, the measurement point setting unit 15c, the left ventricular rear wall, and the ventricular septum tracing unit 15d.

  The end systole setting unit 15b is configured to automatically display the end systole of the subject as an end systole line 64 described later. Information from the end diastole setting unit 15a is input to the end systole setting unit 15b. The end systole setting unit 15b is connected to the measurement point setting unit 15c.

  The measurement point setting unit 15c is configured to automatically set four end diastole measurement points 63 on an end diastole line 62 described later. The measurement point setting unit 15c is configured to automatically set four end systole measurement points 65 on an end systole line 64 described later. Information from the end diastole setting unit 15a, the end systole setting unit 15b, the left ventricular rear wall, and the ventricular septum tracing unit 15d is input to the measurement point setting unit 15c. The measurement point setting unit 15c is connected to the measurement calculation unit 15e.

  The left ventricular posterior wall and ventricular septum tracing unit 15d is configured to trace the left ventricular posterior wall and ventricular septum based on an M-mode image described later. Information from the end diastole setting unit 15a is input to the left ventricular rear wall and the ventricular septum tracing unit 15d. The left ventricular rear wall and the ventricular septum tracing portion 15d are connected to the measurement point setting portion 15c.

  The measurement calculation unit 15e is configured to perform various measurement calculations based on information from the measurement point setting unit 15c, that is, four end-diastolic measurement points 63 and four end-systolic measurement points 65 described later. Yes. The measurement calculation unit 15 e is connected to the display unit 16 outside the calculation unit 15, and is configured to output various measurement calculation results to the display unit 16.

  The value input unit 13 is configured to be able to manually correct the end diastole position when the R wave is not detected by the R wave position detection unit 14a. The value input unit 13 is configured to be able to manually change and correct various measurement points, end diastole lines, and end systole lines after automatic measurement. Examples of manual correction by the value input unit 13 include a keyboard, a trackball, and a mouse. The value input unit 13 is connected to the end diastole setting unit 15a.

  The display unit 16 has a function as a so-called monitor, and is configured to display image information stored in an image storage unit (not shown). The display unit 16 is configured to be able to display various measurement calculation results from the measurement calculation unit 15e, a measurement result frame for displaying the measurement results, and an end-diastolic measurement point 63 and an end-systolic measurement point 65. Has been.

  Based on the above configuration, specific operations of the end diastole setting unit 15a, the end systole setting unit 15b, the measurement point setting unit 15c, the left ventricular rear wall, the ventricular septum tracing unit 15d, and the measurement calculation unit 15e in the calculation unit 15 are described. In addition, specific actions of the value input unit 13 and the display unit 16 will be described by taking an example of left ventricular automatic measurement processing executed by the ultrasonic diagnostic apparatus of the present invention. The left ventricular automatic measurement process will be described with reference to flowcharts and screen display explanatory diagrams.

  2 is a flowchart showing the flow of the left ventricular automatic measurement process, FIG. 3 is a flowchart showing the flow of the end diastole setting process, FIG. 4 is an explanatory diagram showing a display example of an M-mode image and an electrocardiogram, and FIG. FIG. 6 is an explanatory diagram showing the process of automatic measurement point measurement.

  In the ultrasonic diagnostic apparatus of the present invention, when the examiner selects automatic detection of the left ventricle via the value input unit 13, the ultrasonic diagnostic apparatus executes processing in order from step S31 in the left ventricular automatic measurement process. In FIG. 2, first, in step S31, a process related to left ventricular automatic measurement is started in earnest. When the process related to the left ventricular automatic measurement is started, the process proceeds to a process (subroutine) in step S32, and the end diastole of the subject is set.

  In FIG. 3, when a subroutine for setting the end diastole of the subject is executed, in steps S41 and S42, the R wave position detection unit 14a in the M mode image 17 from the electrocardiogram 18 (see FIG. 4) acquired by the electrocardiogram examination unit 14 is displayed. The process branches after confirming whether or not the position coordinates of the R wave 30 (here, the coordinates of the position of the R wave 30) can be obtained. If the position coordinates of the R wave 30 in the M-mode image 17 can be acquired, the process proceeds to step S43, and if not, the process proceeds to step S44.

  In step S43, since the position coordinates of the R wave 30 in the M-mode image 17 have already been detected from the electrocardiogram 18, the end diastole line 62 is displayed based on the position coordinates of the R wave 30 as shown in FIG. To do. The end diastole line 62 is displayed on the M mode image 17 of the display unit 16 as the end diastole of the subject. Here, reference numeral 61 in FIG. 5A indicates a measurement result frame.

  The position coordinates of the R wave 30 are set based on the latest R wave 30 displayed on the screen of the display unit 16 as the end of diastole. However, if the latest heartbeat does not include the end diastole and end systole, the next new R wave position is set as the end diastole.

  Since step S44 is a process when the position coordinates of the R wave 30 cannot be detected, the end diastole is set by the examiner himself setting the position of the R wave 30. In the position setting of the end diastole for the examiner himself, the value input unit 13 is operated to cause the end diastole setting unit 15a to function.

  When the process of the subroutine of FIG. 3 for setting the end diastole of the subject is completed, the processes of steps S33 to S36 of FIG. 2 are executed in order. In the processing of steps S33 to S36, automatic setting of the end diastole measurement point 63 and the end systole measurement point 65 and automatic measurement based on various measurement points (63, 65) are performed.

  In step S33, the left ventricular rear wall end-diastolic thickness 26, ventricular septal end-diastolic thickness 24 in the end diastole, ventricular septal end-diastolic thickness 24, and Four end diastole measurement points 63 for detecting the left ventricular end diastole diameter 25 are automatically set. The four end diastole measurement points 63 are extracted based on the luminance information of the M-mode image 17 and set automatically. Regarding the extraction of the luminance change of the M-mode image 17, the measurement point setting unit 15c is caused to function.

  The automatic setting of the four end diastole measurement points 63 is extracted by the change in the luminance of the portion overlapping the end diastole line 62. First, as shown in FIG. 6A, a process for removing noise from the M mode image as shown in FIG. 6B is performed. In the noise removal processing, first, averaging processing is executed in units of 3 × 3 pixels in the M mode image. After the averaging process, each pixel value of the M mode image is compared with a preset threshold value. If there is a luminance element equal to or lower than a preset threshold value, this luminance element is excluded (preprocessing for blackout is performed. Specifically, smoothing by moving average and deletion of low luminance information are performed. ). After excluding the luminance element, a labeling process is performed in which pixels connected in the image are considered as one block. In the labeling process, the area of each element block is calculated, and in the image excluding the luminance element of the M-mode image, the calculated area is compared with the threshold value, and elements below the threshold value are excluded (deletion of the low area region). ).

  After completion of the above processing, four end diastole measurement points 63 are automatically set on the end diastole line 62 based on the image from which noise is removed as shown in FIG. Hereinafter, automatic setting of the four end diastole measurement points 63 will be described.

  First, a search is performed from the center on the M-mode image from which noise has been removed to the left ventricular rear wall 21 side, and the position where the luminance value first appears is determined as the intima position of the left ventricular rear wall 21. Is set as a measurement point (the first end diastole measurement point 63. The luminance is displayed as, for example, 256 gradations, and the black drop is defined as 0 gradation. At the boundary, the luminance increases, for example, 1 gradation or more. Set a point). A further search is performed in the same direction as described above from the determined intima position of the left ventricular rear wall 21, and the position where the luminance value is maximized is determined as the outer membrane position of the left ventricular rear wall 21, and this is measured. Set as a point (second end diastole measurement point 63). On the other hand, a search is performed on the ventricular septum 19 side from the center of the M-mode image from which noise has been removed, and the position where the luminance value first appears is determined as the boundary on the left ventricular septum 19 side. Is set as a measurement point (third end diastole measurement point 63). Using the normal value (0.8 to 1.1 cm) of the ventricular septal end-diastolic thickness 24 from the left ventricular septum 19 side boundary of the ventricular septum 19, the ventricular septum 19 is determined as the right ventricular boundary, Is set as a measurement point (fourth end diastole measurement point 63).

  Here, once the above processing is summarized, the end diastole line 62 as shown in FIG. 5A is displayed on the display unit 16 at the end diastole of the subject. The four end diastole measurement points 63 on the end diastole line 62 are set at positions as shown in FIG. The four end diastole measurement points 63 are displayed as cross marks on the end diastole line 62.

  When four crossed diastole measurement points 63 with cross marks are displayed on the end diastole line 62, the measurement result frame 61 of the display unit 16 displays the left ventricular end wall diastole thickness 26 in the end diastole, the ventricular septal end diastole. The calculation results of the thickness 24 and the left ventricular end-diastolic diameter 25 are displayed as measured values.

  In step S34, the inner membrane of the left ventricular rear wall 21, the outer membrane of the left ventricular rear wall 21, the ventricle, and the information on the four end-diastolic measurement points 63 automatically set in step S33 and the luminance information of the M-mode image. The wall membrane on the left ventricle 20 side of the septum 19 and the wall membrane on the right ventricle side of the ventricular septum 19 are detected and traced. Regarding the trace, the left ventricular rear wall and the ventricular septum tracing portion 15d are assumed to function. Here, a method for tracing the inner membrane of the left ventricular rear wall 21, the outer membrane of the left ventricular rear wall 21, the wall membrane on the left ventricular septum 19 side of the ventricular septum 19, and the wall membrane on the right ventricular side of the ventricular septum 19 is traced. Assume that a method of comparing luminance information is used.

  A method for comparing the luminance information will be described. At the four end diastole measurement points 63 set in step S33, an average value is obtained for the vicinity of nine (in FIG. 11A, an average value for the vicinity of nine is obtained by “the end diastole measurement point + around It is assumed that “the value obtained by calculating the sum of 8 pixels and reducing the sum to 8/9” is acquired). Regarding the acquired average value, a difference in luminance value related to the vicinity of 5 of the next pixel is confirmed (in FIG. 11B, the difference of luminance value related to the vicinity of 5 of the next pixel is confirmed as “attention It is assumed that “the luminance difference between the pixel and the five neighboring pixels at the position moved by one pixel on the time axis is examined”). Then, a place where the difference in luminance value is minimized is set as a wall boundary. By sequentially performing the processing in the time direction, the inner membrane of the left ventricular rear wall 21, the outer membrane of the left ventricular rear wall 21, the wall membrane on the left ventricular septum 19 side of the ventricular septum 19, and the right ventricle of the ventricular septum 19 Detect side wall membrane.

  In the trace of the intima boundary of the left ventricular posterior wall 21, the wall membrane on the left ventricular side 20 of the ventricular septum 19, and the wall membrane on the right ventricular side of the ventricular septum 19, the position acquired by the above tracing method is used. When the brightness value is 0, the position where the brightness value changes is searched, and the position where the brightness value changes is the boundary of the intima of the left ventricular rear wall 21, the wall film on the left ventricle 20 side of the ventricular septum 19, And it detects as a wall film of the right ventricle side of the ventricular septum 19. The range to be detected is one heartbeat when one heartbeat is obtained, and when one heartbeat is not obtained, each boundary is detected from the end diastole line 62 to the right end of the M-mode image (see FIG. 5C).

  In step S35, the inner membrane of the left ventricular rear wall 21 detected in step S34, the outer membrane of the left ventricular rear wall 21, the wall membrane of the ventricular septum 19 on the left ventricle 20 side, and the right ventricular side of the ventricular septum 19 The end systole is set by detecting the left ventricular diameter and the left ventricular posterior wall thickness using the wall membrane. The setting of the end systole is performed by causing the end systole setting unit 15b to function. Specifically, as shown in FIG. 5D, the traveling direction is set to a new direction of time (see the arrow pointing to the right), and the left ventricular diameter and the left ventricular rear wall thickness at each time are calculated. Then, as shown in FIG. 5E, the minimum left ventricular diameter or the maximum left ventricular wall thickness is set as the end systole and the end systole line 64 is automatically displayed.

  In step S36, the inner membrane of the left ventricular rear wall 21 detected in step S34, the outer membrane of the left ventricular rear wall 21, the wall membrane on the left ventricular septum 19 side of the ventricular septum 19, and the right ventricular septum 19 on the right ventricular side Based on the wall membrane and the end systole (end systole line 64) set in step S35, the left ventricular rear wall end systolic thickness 29, the ventricular septal end systolic thickness 27, and the left ventricular end systolic diameter 28 at the end systole are obtained. Four end systolic measurement points 65 for detection are automatically set. When automatically setting the four end systolic measurement points 65, the measurement point calculation unit 15c is assumed to function.

  The measurement point setting unit 15c includes the intersection of the intima of the left ventricular rear wall 21 and the end systolic line 64, the intersection of the adventitia of the left ventricular rear wall 21 and the end systolic line 64, and the left ventricular septum 19 on the left ventricular 20 side. And the intersection of the wall membrane on the right ventricular side of the ventricular septum 19 and the end systolic line 64 are determined as the end systolic measurement point 65 and automatically set. The four end systolic measurement points 65 are displayed as cross marks on the display unit 16 as shown in FIG. Based on the set four end systolic measurement points 65, the left ventricular posterior wall end systolic thickness 29, the ventricular septal end systolic thickness 27, and the left ventricular end systolic diameter 28 are calculated. To display. Thus, a series of processing is completed.

  Next, an example in which manual correction is required will be described with reference to FIGS. FIG. 7 is a flowchart showing the flow of manual correction of measurement points, FIG. 8 is an explanatory diagram showing the operation and status of manual correction at the end diastole, and FIG. 9 is an explanatory diagram showing the operation and status of manual correction at the end systole, FIG. 10 is an explanatory diagram showing the operation and state of manual correction of measurement points.

  After a series of processing is completed as described above, processing starting from step S45 in FIG. 7 is executed in order. In step S45, the end of manual correction is confirmed. If the examiner chooses to end, the correction is completed and the result is fixed. If the examiner does not select the end, the process proceeds to one of steps S46, S52, and S55. Specifically, the process proceeds to step S46 when correcting the end diastole, to step S52 when correcting the end systole, and to step S55 when correcting the measurement point.

  Steps S46 to S51 show processing for correcting the end diastole. Hereinafter, manual correction at the end of diastole will be described with reference to FIGS. In step S46, the end diastole is designated. By operating the value input unit 13 from the state of FIG. 8A, when the cursor is moved to the end diastole (end diastole line 64) as shown in FIG. 8B, the cursor changes to the end diastole movement selection cursor 71. And execute in that state.

  In step S47, when this process is executed, the selectable R wave is displayed as an inverted triangle mark on the display unit 16 as shown in FIG. 8C, and the currently selected R wave 72 and the selectable R wave are displayed. 73 are displayed in a filled state and a hollow state, respectively. The selectable R-waves 73 are those included on the screen from the R-wave position to the end systolic position (when R-wave information can be acquired).

  In step S48, a point to be measured by the examiner is designated and moved to the selectable R wave 73. Note that the currently selected R wave 72 moves for each selectable R wave 73 so that the middle of the R wave 72 cannot be designated.

  In step S49, the R wave selected in step S48 is determined, and the end diastole position is corrected. In step S50, the process from step S31 is executed in order, and left ventricular automatic measurement is performed again. In step S51, the result calculated by the automatic measurement in step S50 is displayed on the measurement result frame 61 on the display unit 16. Note that the end diastole correction when it is impossible to correct the position of the R wave specifies the end diastole in step S46, and then proceeds to the process for manually setting the position of the R wave described with reference to FIG. Transition.

  Steps S <b> 52 to S <b> 54 and steps S <b> 50 to S <b> 51 that shift from step S <b> 54 show processing for correcting the end systole. Hereinafter, manual correction of the end systole will be described with reference to FIGS. In step S52, the end systole requiring correction is designated by operating the value input unit 13. The end systole is designated by designating a line representing the end systole (end systole line 64) on the M mode image in which the result is displayed as shown in FIG. 9A. When the designation is completed, a cursor 81 indicating horizontal movement is displayed as shown in FIG. When executed in the state of FIG. 9B, a cursor 82 indicating a horizontally movable state as shown in FIG. 9C is displayed.

  In step S53, the end systole designated in step S52 is moved in the horizontal direction. When the cursor 82 in a state in which horizontal movement is possible is displayed as shown in FIG. 9C, the examiner moves the end systole in the horizontal direction and corrects it. In step S54, a correction position is determined. By executing in the state of FIG. 9C, correction of the end systolic position becomes effective as shown in FIG. 9D. In step S50, automatic setting of the end systolic measurement point is performed again. In step S51, the result calculated by automatic measurement is displayed in the measurement result frame 61 as shown in FIG.

  Steps S55 to S58 show processing for correcting the end diastole and end systolic measurement points. Hereinafter, manual correction of measurement points will be described with reference to FIGS. In step S55, when the result is displayed as shown in FIG. 10A, the value input unit 13 is operated to move the cursor to the measurement point displayed by the cross mark. When the cursor is on the measurement point, a vertical movement cursor 91 as shown in FIG. 10B is displayed.

  When a measurement point is specified and executed in the state of FIG. 10B, a cursor 92 that can be moved in the vertical direction is displayed as shown in FIG. 10C. In step S56, the cursor 92 displayed in FIG. 10C moves in the vertical direction on the end diastole line or the end systole line. When the measurement point is moved using the cursor 92, the process proceeds to step S57. In step S57, each time the measurement point moves, recalculation is performed in the measurement calculation unit 15e, and the value of the measurement result frame 61 is updated. In step S58, the position of the measurement point is determined and executed again. After the manual correction is completed, the completion of the correction is confirmed again in step S45. Manual correction is possible unless the examiner specifies the end of the correction.

  As described above with reference to FIGS. 1 to 11, according to the present invention, when left ventricle measurement is performed in an M-mode image, it is possible to shorten the inspection time and improve the efficiency of routine work. it can. Moreover, information desired by the examiner can be acquired by correcting the information acquired by the automatic measurement.

  In addition, it goes without saying that the present invention can be variously modified without departing from the spirit of the present invention.

1 is a block diagram showing an embodiment of an ultrasonic diagnostic apparatus of the present invention. It is a flowchart which shows the flow of a left ventricular automatic measurement process. It is a flowchart which shows the flow of a setting process of the end diastole. It is explanatory drawing which shows the example of a display of an M mode image and an electrocardiogram. It is explanatory drawing which shows the operation | movement and state of a process of automatic measurement. It is explanatory drawing of the process of the automatic measurement of a measurement point. It is a flowchart which shows the flow of a process of manual correction of a measurement point. It is explanatory drawing which shows the operation | movement and state of manual correction of the end diastole. It is explanatory drawing which shows the operation | movement and state of manual correction of the end systole. It is explanatory drawing which shows the operation | movement and state of manual correction of a measurement point. It is explanatory drawing about 9 vicinity and 5 vicinity.

Explanation of symbols

DESCRIPTION OF SYMBOLS 11 Ultrasonic probe 12 Ultrasonic transmission / reception part 13 Value input part 14 Electrocardiogram detection part 14a R wave position detection part 15 Calculation part 15a End diastole setting part 15b End systole setting part 15c Measurement point setting part 15d Left ventricular rear wall, ventricle Septal trace section 15e Measurement calculation section 16 Display section 17 M mode image 18 ECG 19 Ventricular septum 20 Left ventricle 21 Left ventricular rear wall 24 Ventricular septal end diastolic thickness 25 Left ventricular end diastolic diameter 26 Left ventricular posterior wall end diastolic thickness 27 Ventricular septal end-systolic thickness 28 Left ventricular end-systolic diameter 29 Left ventricular posterior wall end-systolic thickness 30 R wave 61 Measurement result frame 62 End-diastolic line 63 End-diastolic measurement point 64 End-systolic line 65 End-systolic measurement point 71 Cursor 72 Present Selected R wave 73 Selectable R wave 81, 82, 91, 92 Cursor

Claims (2)

In an ultrasonic diagnostic apparatus that acquires a tomographic image or an M-mode image based on information from an ultrasonic probe in contact with a subject and displays it together with an electrocardiographic waveform of the subject.
Based on the plurality of measurement points, means for setting a line on the M-mode image based on the position coordinates of the feature points of the electrocardiogram waveform, means for setting a plurality of measurement points from luminance information on the line And a means for measuring a thickness or a diameter. The ultrasonic diagnostic apparatus according to claim 1,
The ultrasonic diagnostic apparatus further comprising means for enabling manual correction of the line and / or the plurality of measurement points.

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