JP2010269018A - Ultrasonic diagnostic apparatus - Google Patents

Abstract

<P>PROBLEM TO BE SOLVED: To provide an ultrasonic diagnostic apparatus easily and accurately executing measurement using a plurality of ultrasonic images. <P>SOLUTION: The ultrasonic diagnostic apparatus generates an ultrasonic image representing information on the inside of a subject from an echo signal acquired through transmission/receiving of ultrasonic waves. The ultrasonic diagnostic apparatus includes; a display control means 14 for displaying a plurality of ultrasonic images on the screen of a prescribed display device 15; a first marker display means 20 for displaying a marker for specifying a range of measurement on one image of the plurality of ultrasonic images; a marker setting means 17 for allowing an operator to change the setting of the position, size or angle of the marker; a second marker display means 20 for displaying the same marker as the marker set by the marker setting means on the other image of the plurality of ultrasonic images; and a measuring means 16 for executing prescribed measurement in a range of measurement designated by the marker in the respective ultrasonic images. <P>COPYRIGHT: (C)2011,JPO&INPIT

Description

  The present invention relates to an ultrasonic diagnostic apparatus.

  When the elasticity of the blood vessels decreases, there is a high possibility of developing vascular diseases such as cerebral infarction and myocardial infarction through thickening of IMT (Intima-Media Thickness) and plaque development. Become. Therefore, it is desirable to periodically evaluate vascular elasticity for the prevention of vascular diseases.

  PWV (Pulse Wave Velocity) is known as one of such vascular elasticity evaluation indexes. This is to evaluate the elasticity of the blood vessel using the fact that the harder the blood vessel, the faster the propagation speed of the pulse wave (beat from the heart). The propagation speed of the pulse wave is attached to the limb of the subject. Observed using a blood pressure cuff. However, PWV is easily affected by blood pressure, so that comparison between patients is difficult, and if blood pressure fluctuates, follow-up observation in the same patient becomes difficult.

  Therefore, in recent years, Stiffness Parameter β (hereinafter abbreviated as “β value”) has been proposed and widely used as a blood vessel elasticity index that does not depend on blood pressure (see Non-Patent Document 1). The β value is expressed by the following formula, and it can be determined that the larger the value, the lower the vascular elastic function.

  Here, Dd is the diastolic blood vessel inner diameter, Ds is the systolic blood vessel inner diameter, Pd is the diastolic blood pressure, and Ps is the systolic blood pressure. Dd and Ds are generally measured in the carotid artery. The “diastolic phase” and “systolic phase” are based on the diastole and contraction of the heart, and the blood vessel diameter of the carotid artery decreases during the diastole and increases during the systole.

Cardiovascular Research, 1987, Volume 21, Issue 9, pp. 678-687

  As shown in the above formula (1), in order to derive the β value, it is necessary to measure the blood vessel diameters Dd and Ds in the diastole and the systole. These are measured by the following method using an ultrasonic diagnostic apparatus.

(1) Method Using M Mode FIG. 6 shows a screen display in so-called B / M display in which a tomographic image in the B mode and an M mode image are displayed side by side. The M mode image 102 on the right side in the figure represents depth in the vertical axis and time on the horizontal axis, and represents the time change of the echo signal at the position designated by the cursor 103 on the B mode image 101 on the left side in the figure in real time. Is. When the diastolic blood vessel inner diameter Dd and the systolic blood vessel inner diameter Ds are measured using such an M-mode image, the M-mode image 102 is frozen and is considered to correspond to the diastole and the systole in the M-mode image 102. The operator designates a portion to be measured as a measurement target using the caliper 104 for measurement, and measures the diameter of the blood vessel 200 in each.

  However, on the principle of the M mode of observing the temporal change of the echo signal obtained at a specific beam position, only the blood vessel diameter at one point on the blood vessel 200 can be measured at a time by this method.

(2) Method Using B / B Display FIG. 7 shows screen display in so-called B / B display in which two B-mode images are displayed side by side. When the diastolic blood vessel inner diameter Dd and the systolic blood vessel inner diameter Ds are measured using such B / B display, first, each B-mode image is frozen and the cine search function is used to store the B stored in the cine memory. Display the mode image retroactively. As a result, the image 105 corresponding to the diastole and the image 106 corresponding to the systole are searched for and displayed side by side. The measurement caliper 107 and the like are displayed on the images 105 and 106, and the operator adjusts the position and size of the caliper 107 on each of the images 105 and 106 to designate the measurement location. The diameter of the blood vessel 200 at the location is measured.

  According to such a method, since it is possible to measure blood vessel diameters at a plurality of locations on the blood vessel 200 at once, the reliability of the measurement results can be improved by taking the average of β values at the plurality of locations. Can do. However, as described above, the β value is calculated based on the rate of change of the blood vessel diameter in the diastole and the systole. Therefore, in order to obtain an accurate β value, the diastole blood vessel inner diameter Dd and the systolic blood vessel inner diameter Ds are set. It is necessary to measure at the same location on the blood vessel (for example, Dd1 and Ds1, Dd2 and Ds2, and Dd3 and Ds3 in the figure need to be measured at the same location on the blood vessel). Therefore, when the measurement location is designated, it is necessary for the operator to consider that the position of the caliper 107 is the same by comparing the left and right images. In addition, since the diastolic image 105 and the systolic image 106 used for measurement are visually searched by the operator using the cine search function as described above, there is a possibility that these images are not necessarily optimal images for the measurement of Dd and Ds. was there.

(3) Method Using Automatic Tracking Function FIG. 8 shows a screen display when the automatic tracking function is executed. The automatic tracking function is a function for tracking a location designated in advance in the image in real time. For example, the operator designates the position of the blood vessel wall 201 as the tracking location on the B-mode image 108 on the left side in the figure. Each time a new B-mode image 108 is generated and displayed by ultrasonic scanning, the tracking portion (that is, the blood vessel wall 201) in the image is automatically detected, and based on this, the blood vessel diameter in the image is measured. The As a result, it is possible to observe the temporal change of the blood vessel diameter as in the graph 110 shown on the analysis screen 109 on the right side of the figure, and on the graph 110, the diameter when the blood vessel diameter becomes maximum is shown as the systole. The β value can be obtained by setting the diameter when the blood vessel inner diameter Ds is minimized to the diastolic blood vessel inner diameter Dd.

  However, if the B-mode image is unclear, the tracking location may not be detected correctly, and automatic tracking is not always possible. In addition, in order to realize such an automatic tracking function, dedicated hardware is often required, which increases the cost.

  The present invention has been made in view of the above points, and the object of the present invention is to perform measurement using an ultrasonic image by solving the problems in measurement using the conventional B / B display. An object of the present invention is to provide an ultrasonic diagnostic apparatus that can be easily and accurately executed.

An ultrasonic diagnostic apparatus according to the present invention made to solve the above-described problem is an ultrasonic diagnostic apparatus that generates an ultrasonic image representing information inside a subject from an echo signal obtained by transmitting and receiving ultrasonic waves.
a) display control means for displaying a plurality of ultrasonic images on a screen of a predetermined display device;
b) first marker display means for displaying a marker for designating a measurement range on one of the plurality of ultrasonic images;
c) marker setting means for allowing an operator to change the position, size, or angle of the marker;
d) second marker display means for displaying the same marker as the marker set by the marker setting means on another image of the plurality of ultrasonic images;
e) In each of the plurality of ultrasonic images, a measurement unit that performs a predetermined measurement for a measurement range specified by the marker;
It is characterized by having.

  Here, the “marker” may be one that specifies a two-dimensional measurement range (for example, a frame representing a region of interest), or one that specifies a one-dimensional measurement range (for example, a caliper or a cursor). There may be.

  According to the above configuration, when an operator sets a measurement range on one image with a plurality of ultrasonic images displayed on the monitor, the same measurement range is automatically displayed on another image. Is set. For this reason, the same location can be reliably measured for a plurality of images. Thereby, for example, the diameter of the same location on the blood vessel can be measured in the diastolic image and the systolic image, and an accurate β value can be obtained. Moreover, since it is not necessary for the operator to individually set a measurement range for each image while comparing a plurality of images as in the prior art, the operation burden on the operator can be reduced.

  In the ultrasonic diagnostic apparatus according to the present invention, the measurement unit detects a position of a blood vessel wall included in an ultrasonic image within a measurement range specified by the marker, and a distance between a pair of blood vessel walls. It is desirable to measure the blood vessel diameter by obtaining the blood vessel diameter, and to measure the blood vessel diameter at the same plurality of positions on each ultrasonic image.

  According to such a configuration, when the operator designates a predetermined two-dimensional measurement range using the marker setting means, the position of the blood vessel wall included in the measurement range of each image is automatically detected. The blood vessel diameter is measured at a plurality of locations above. At this time, since each blood vessel diameter is measured at the same position for each of the plurality of ultrasonic images, for example, it is possible to easily measure a plurality of corresponding portions in the diastolic ultrasound image and the systolic ultrasound image. It becomes possible.

  In addition, the measurement range designated for measuring the blood vessel diameter includes the IMT measurement range (that is, the intima and media of the blood vessel). Therefore, in the ultrasonic diagnostic apparatus according to the present invention, the measurement unit detects the inner wall position of the vascular intima and the inner wall position of the vascular outer membrane included in the measurement range in addition to the measurement of the blood vessel diameter. The thickness of the intima-media complex may be measured by obtaining the interval between the two inner wall positions.

  According to the above configuration, the β value, which is an index of the blood vessel elastic function, and the IMT value, which is a blood vessel shape change index, can be measured at the same time, which is useful for early detection of arteriosclerosis. Further, if the β value and the IMT value can be measured simultaneously as described above, the burden on the subject and the operator in the diagnosis can be reduced.

The ultrasonic diagnostic apparatus according to the present invention further includes:
f) Timing signal generating means for acquiring a cardiac cycle signal of a subject, detecting a predetermined cardiac time phase from the cardiac cycle signal, and generating a timing signal corresponding to each
And the display control means displays ultrasonic images at different cardiac phases as the plurality of ultrasonic signals by causing the display device to display ultrasonic images in synchronization with the timing signal. It is good also as what is characterized by.

  The “cardiac cycle signal” is a signal corresponding to the movement of the subject's heart, for example, an electrocardiographic signal of the subject acquired by an existing electrocardiograph, a heart sound meter, a pulse wave meter, or the like. A heart sound signal, a pulse wave signal, or the like can be used.

  According to the above configuration, for example, an ultrasonic image corresponding to the diastole and an ultrasonic image corresponding to the systole can be easily and reliably displayed in the B / B display. Therefore, the diastolic blood vessel inner diameter Dd and the systolic blood vessel inner diameter Ds can be measured using appropriate images, and an accurate β value can be obtained. Further, unlike the prior art, it is not necessary for the operator to search for an image corresponding to the diastole or systole using the cine search function, so that the operator's workload can be reduced.

Still further, in the ultrasonic diagnostic apparatus according to the present invention, the timing signal generating means acquires an electrocardiographic signal of the subject and generates a timing signal corresponding to the appearance timing of the R wave and / or T wave. And
g) signal delay means for giving a predetermined time delay to the timing signal generated by the timing signal generating means;
It is preferable that the display control means display an ultrasonic image on the display device in synchronization with the delayed timing signal.

  The R wave of the ECG signal corresponds to the diastole and the T wave corresponds to the systole. According to the above configuration, for example, by giving a predetermined delay time to both the R-wave and T-wave timing signals, the time lag between the cardiac phase and the carotid artery change can be corrected. Further, without detecting the T wave, only the R wave that is steep and relatively easy to detect is detected, and a signal obtained by giving a predetermined delay time to the R wave timing signal is used as the T wave timing signal. You can also.

  As described above, according to the ultrasonic diagnostic apparatus of the present invention having the above-described configuration, the problems in the measurement using the conventional B / B display are solved, and the measurement using the ultrasonic image is easily and accurately performed. Can be performed.

The block diagram which shows the principal part structure of the ultrasonic diagnosing device which concerns on one Example of this invention. The figure explaining the phase of a cardiac cycle. The figure explaining the setting method of the measurement range in the ultrasound diagnosing device which concerns on one Example of this invention. The enlarged view showing the area | region of the blood-vessel wall periphery in an ultrasonic image. The figure explaining the other example of the setting method of a measurement range. The figure explaining the measurement of (beta) value using the conventional M mode. The figure explaining the measurement of (beta) value using the conventional B / B display. The figure explaining the measurement of (beta) value using the conventional automatic tracking function.

  Hereinafter, the form for implementing this invention is demonstrated using an Example.

  FIG. 1 is a block diagram showing the main configuration of the ultrasonic diagnostic apparatus according to the present embodiment. The probe 11 is brought into contact with the body surface of the subject and transmits an ultrasonic wave into the body of the subject, and receives an ultrasonic wave reflected from the body tissue to generate an electrical signal (echo signal). Convert. The transmission / reception unit 12 controls transmission / reception of ultrasonic waves by the probe 11, A / D-converts echo signals output from the respective ultrasonic transducers in the probe 11, and generates sound ray data by phasing and adding. To do. The image generation unit 13 performs predetermined processing on the sound ray data to generate ultrasonic image data for one frame, and converts it into a format that can be displayed on the monitor 15. The ultrasonic image data output from the image generation unit 13 is temporarily stored in a display image memory (not shown) provided in the display processing unit 14, read according to the scanning timing of the monitor 15, and sequentially to the monitor 15. Sent. By repeatedly executing the above steps, the image displayed on the screen of the monitor 15 is updated at a predetermined time interval and visually recognized as a moving image.

  The electrocardiographic sensor 22 detects the electrocardiogram of the subject and is attached to the body surface near the subject's heart. As the electrocardiographic sensor 22, an existing sensor for measuring an electrocardiogram can be used. The electrocardiogram detection signal output from the electrocardiogram sensor 22 is input to the timing signal generator 19 via the electrocardiogram signal acquisition unit 21.

  The timing signal generator 19 analyzes the electrocardiogram detection signal acquired by the electrocardiogram sensor 22 in real time, and generates a timing signal corresponding to each R wave or T wave detected.

  As shown in FIG. 2, the electrocardiogram detection signal includes peaks called P wave 31, Q wave 32, R wave 33, S wave 34, and T wave 35. In the diastole, the T wave 35 corresponds to the systole. Accordingly, if the vascular diameter is measured when the electrocardiographic sensor 22 detects the R wave 33 (symbol 36), the diastolic vascular inner diameter Dd can be measured, and the electrocardiographic sensor 22 detects the T wave 35 (symbol 37). ), The systolic blood vessel diameter Ds can be measured.

  The measurement unit 16 uses the image memory of the display processing unit 14 to store ultrasonic image data in the measurement target region designated by a frame (hereinafter referred to as “ROI frame”) representing a region of interest. And predetermined measurement is executed based on the image data (details will be described later).

  The graphic generation unit 20 generates a graphic such as a character or a figure, and includes a character representing a measurement result, a graph representing an electrocardiogram waveform, an ROI frame and a caliper for designating a part used for measurement on an ultrasonic image. And so on. The graphic generation unit 20 is provided with a graphic memory (not shown), and graphic data generated based on an instruction from the control unit 18 is temporarily stored in the graphic memory. Then, the data is read by the display processing unit 14 as appropriate, combined with the ultrasonic image data, and sent to the monitor 15. Thus, the various graphics are displayed on the screen of the monitor 15 side by side with the ultrasonic image or superimposed on the ultrasonic image.

  The operation of each unit is controlled by a control unit 18 including a CPU, a memory, and the like. Further, operator instructions are input to the control unit 18 via an operation unit 17 including a keyboard, various operation buttons, a trackball, and the like. The

  Note that the functions of the above-described units centering on the control unit 18 are performed in a so-called software manner by causing the CPU to execute a predetermined program except for input / output devices such as the ultrasonic probe 11, the operation unit 17, and the monitor 15. You may implement | achieve and you may comprise by hardware by a circuit etc. Moreover, the structure with which both were combined may be sufficient.

  In this embodiment, the display processing unit 14 corresponds to the display control unit in the present invention, and the operation unit 17 corresponds to the marker setting unit in the present invention. The graphic generation unit 20 functions as a first marker display unit and a second marker display unit in the present invention.

  Hereinafter, a procedure for measuring the β value using the ultrasonic diagnostic apparatus of the present embodiment will be described.

  First, the operator brings the probe 11 into contact with a predetermined position of the subject's neck and starts ultrasonic scanning in the B mode. As a result, an ultrasonic tomographic image (B-mode image) of the carotid artery is displayed in real time on the screen of the monitor 15 as a moving image.

  When the operator performs a predetermined operation on the operation unit 17 to instruct switching to B / B display, the screen of the monitor 15 is divided into left and right parts, and a B-mode image is displayed on each. At this time, the left and right images are the same real-time moving image.

  Subsequently, when the operator instructs display of the electrocardiogram waveform via the operation unit 17, a graphic representing the electrocardiogram waveform is generated by the graphic generation unit 20 based on the output signal of the electrocardiogram sensor 22. It is displayed on the screen of the monitor 15 together with the B-mode image. At this time, if the peak of the electrocardiogram waveform is low, it becomes difficult to detect the R wave and the T wave in the timing signal generator 19. Therefore, the operator adjusts the gain of the electrocardiogram signal by operating the operation unit 17 while confirming the electrocardiogram waveform on the monitor 15 so that each peak has a height that is easy to detect.

  After that, when the operator instructs the start of image display synchronized with the electrocardiogram signal on the operation unit 17, the two B-mode images displayed on the monitor 15 are updated at timings synchronized with the R wave and T wave of the electrocardiogram waveform, respectively. Will come to be.

  Specifically, the timing signal generator 19 analyzes the electrocardiogram detection signal output from the electrocardiogram sensor 22 in real time, and when the R wave is detected, the first timing signal is detected when the T wave is detected. A second timing signal is transmitted to the display processing unit 14. When the display processing unit 14 receives the first timing signal (corresponding to the R wave), the display processing unit 14 displays an image generated by the image generation unit 13 at that time on the left side of the screen of the monitor 15. When the second timing signal (corresponding to the T wave) is received, the image generated by the image generating unit 13 at that time is displayed on the right side of the screen of the monitor 15. Thereby, a B-mode image corresponding to the diastole (hereinafter referred to as “diastolic image”) is displayed on the left half of the screen of the monitor 15, and a B-mode image corresponding to the systole is displayed on the right half of the screen. (Hereinafter referred to as “systolic image”) will be displayed. These images are updated each time a new R wave or T wave is detected.

  A predetermined delay time may be given to each timing signal. For example, as shown in FIG. 2, the R wave is steep and easy to detect, whereas the T wave is gentle and relatively difficult to detect. Therefore, the timing signal generator 19 detects only the R wave, and when the R wave is detected, transmits the first timing signal (corresponding to the R wave) to the display processing unit 14 and the first timing. A delay time corresponding to the time difference Δt between the R wave appearance timing and the T wave appearance timing is given to the signal, and this delayed timing signal is used as a second timing signal (corresponding to the T wave) to the display processing unit 14. send. In this way, it is possible to reliably display the diastolic image and the systolic image even for a subject who has a weak electrocardiogram waveform and is difficult to detect a T wave. Further, by giving a predetermined delay time to both the first timing signal and the second timing signal, the timing shift between the cardiac phase and the change in the carotid artery blood vessel diameter may be corrected.

  The operator confirms the diastolic image and the systolic image sequentially displayed on the monitor 15 by the above processing, and operates the operation unit 17 to freeze each image at an appropriate time.

  Thereafter, the operator uses the operation unit 17 to select one of the left and right B-mode images as an operation target, and instructs the start of the measurement mode. As a result, a graphic of the ROI frame for designating the measurement range is generated in the graphic generation unit 20, and the correspondence on the diastolic image 41 and the systolic image 42 displayed on the screen of the monitor 15 as shown in FIG. The ROI frames 43 and 44 having the same shape and size are respectively displayed at the positions to be operated. At this time, the solid line ROI frame 44 is superimposed on the image selected as the operation target (the systolic image 42 in the figure) and the other image (the diastole image 41 in the figure). The ROI frame 43 of a broken line is superimposed and displayed.

  At this time, the ROI frames 43 and 44 are in an unconfirmed state, and the operator can arbitrarily move, rotate, and enlarge / reduce according to an instruction from the operation unit. These ROI frames 43 and 44 are interlocked. When the operator operates the operation unit 17 to move the ROI frame 44 on the operation target image 42, the ROI frame 43 on the other image 41 also moves. Move the same distance in the same direction. When the operator operates the operation unit 17 to enlarge / reduce the ROI frame 44 on the operation target image 42, the ROI frame 43 on the other image 41 is also enlarged / reduced at the same magnification.

  The operator adjusts the position and size of the ROI frame 44 so that the blood vessel 50 to be measured is included in the frame while checking the left and right images 41 and 42, and when an appropriate measurement range is determined, the operation unit 17. A predetermined operation is performed to instruct confirmation of the ROI frame. As a result, the ROI frame 44 on the operation target image 42 is determined, and at the same time, the ROI frame 43 on the other image 41 is also determined. Accordingly, the same measurement range is set for both the left and right images (diastolic image 41 and systolic image 42).

  When the setting of the measurement range is completed, the measurement unit 16 performs the following process.

  First, the measurement unit 16 acquires image data within the measurement range designated by the ROI frame 44 for the systolic image 42 and detects the position of the blood vessel wall based on the luminance distribution of each pixel.

  Specifically, the measurement unit 16 acquires the luminance values of the pixels at the left and right ends of the measurement range for one column in the vertical direction from the image memory of the display processing unit 14. Subsequently, all locations where the luminance value changes suddenly based on a predetermined reference are detected from this data. Then, a set of brightness value suddenly changing points satisfying a predetermined standard is recognized as the inner wall position of the vascular intima and the distance between the set of inner wall positions is measured as the blood vessel inner diameter.

  The measurement unit 16 sequentially performs the processing from the acquisition of the luminance value to the measurement of the blood vessel inner diameter in the horizontal direction of the measurement region, and measures the blood vessel inner diameter for all the pixel columns (vertical columns) in the measurement region.

  Further, similar processing is performed on the diastolic image 41 to measure the inner diameter of the blood vessel.

  Subsequently, the measurement unit 16 uses the blood vessel inner diameter measured for the diastolic image 41 as the diastolic blood vessel inner diameter Dd and the blood vessel inner diameter measured for the systolic image 42 as the systolic blood vessel inner diameter Ds from the above equation (1). The β value is calculated. For diastolic blood pressure Pd and systolic blood pressure Ps, values measured using a sphygmomanometer (not shown) are used.

  As described above, the diastolic blood vessel inner diameter Dd and the systolic blood vessel inner diameter Ds at many points on the blood vessel can be obtained. For example, by taking an average value thereof, a more reliable β value can be obtained. Can be calculated. Also, medically meaningful information can be obtained by calculating the β value using these minimum and maximum values.

  Here, the case where the diastolic blood vessel inner diameter Dd and the systolic blood vessel inner diameter Ds are measured for all pixel rows in the measurement range has been described as an example. However, the blood vessel inner diameter at the same position of the diastole image and the systolic image is described. It is not always necessary to measure all the pixel columns, for example, the blood vessel inner diameter is measured only for a predetermined pixel column within the measurement range (for example, the center column and the left and right end columns). It may be.

  It should be noted that the measurement range designated for measuring the blood vessel diameter as described above includes the IMT measurement range (that is, the intima and media of the blood vessel).

  Therefore, when performing the automatic measurement of the blood vessel inner diameter as described above, the automatic measurement of IMT may be performed simultaneously. FIG. 4 shows an enlarged view of the vicinity of the blood vessel wall 51 on the lower side (the side far from the probe) in the image 42 of FIG. Specifically, when the inner wall position 55 of the vascular intima 52 is detected from the luminance distribution of the image data within the measurement range as described above, the inner wall position 56 of the vascular outer membrane 54 (that is, the inner membrane 53 and the outer membrane) is detected. The distance between the inner wall position 55 of the inner membrane and the inner wall position 56 of the outer membrane is calculated as an IMT value. Thereby, the automatic measurement of the blood vessel inner diameter and the automatic measurement of IMT can be performed at a time. The IMT value may be measured using either a diastole image or a systole image. Further, the measurement range designated for measuring the blood vessel diameter includes two blood vessel walls 51 closer and far from the probe, but the IMT value may be measured for either blood vessel wall.

  IMT is an index of vascular morphological change, and it is useful for early detection of arteriosclerosis to evaluate this together with β value which is an index of the elastic function of blood vessels. Further, if the β value and the IMT value can be measured simultaneously as described above, the burden on the subject and the operator in the diagnosis can be reduced.

  As mentioned above, although the form for implementing this invention using an Example was demonstrated, this invention is not limited to the said Example, A change is accept | permitted suitably in the range of the meaning of this invention. It is.

  For example, in the above embodiment, a two-dimensional measurement range is specified by the ROI frame, and the blood vessel diameter is measured by automatically detecting the position of the blood vessel wall in the measurement range. As shown in FIG. 5, a one-dimensional measurement range is designated in each image by the calipers 45 and 46, and the length of the measurement range designated by the calipers 45 and 46 may be measured by the measurement unit 16. . Also in this case, first, calipers 45 and 46 having the same shape are displayed at the same positions in the left and right images 41 and 42, respectively, and when the operator changes the position and angle of the caliper on one image, Assume that the position and angle of the caliper on the other image change in conjunction with each other. However, in this case, the length of the calipers 45 and 46 on the images 41 and 42 needs to be changed by the operator individually.

DESCRIPTION OF SYMBOLS 11 ... Ultrasonic probe 12 ... Transmission / reception part 13 ... Image generation part 14 ... Display processing part 15 ... Monitor 16 ... Measurement part 17 ... Operation part 18 ... Control part 19 ... Timing signal generation part 20 ... Graphic generation part 21 ... Electrocardiogram signal Acquisition unit 22 ... electrocardiographic sensor 41 ... diastolic image 42 ... systolic image 43, 44 ... ROI frame 45, 46 ... caliper 50, 200 ... blood vessel 51, 201 ... blood vessel wall 52 ... intima 53 ... intima 54 ... outside film

Claims (5)

In an ultrasound diagnostic apparatus that generates an ultrasound image representing information inside a subject from an echo signal obtained by sending and receiving ultrasound,
a) display control means for displaying a plurality of ultrasonic images on a screen of a predetermined display device;
b) first marker display means for displaying a marker for designating a measurement range on one of the plurality of ultrasonic images;
c) marker setting means for allowing an operator to change the position, size, or angle of the marker;
d) second marker display means for displaying the same marker as the marker set by the marker setting means on another image of the plurality of ultrasonic images;
e) In each of the plurality of ultrasonic images, a measurement unit that performs a predetermined measurement for a measurement range specified by the marker;
An ultrasonic diagnostic apparatus comprising:   The measuring means detects a position of a blood vessel wall included in an ultrasonic image within a measurement range designated by the marker, and measures a blood vessel diameter by obtaining a distance between a pair of blood vessel walls; 2. The ultrasonic diagnostic apparatus according to claim 1, wherein the blood vessel diameter is measured at the same plurality of positions on each ultrasonic image.   In addition to the measurement of the blood vessel diameter, the measuring means detects the inner wall position of the vascular intima and the inner wall position of the vascular outer membrane included in the measurement range, and obtains an interval between these two inner wall positions. The ultrasonic diagnostic apparatus according to claim 2, wherein the thickness of the media complex is measured. Furthermore,
f) Timing signal generating means for acquiring a cardiac cycle signal of the subject, detecting a predetermined cardiac phase from the cardiac cycle signal, and generating a timing signal corresponding thereto
And the display control means displays ultrasonic images in different cardiac phases as the plurality of ultrasonic signals by causing the display device to display ultrasonic images in synchronization with the timing signal. The ultrasonic diagnostic apparatus according to claim 1, wherein the apparatus is an ultrasonic diagnostic apparatus. The timing signal generating means acquires an electrocardiographic signal of a subject and generates a timing signal corresponding to the appearance timing of an R wave and / or a T wave;
g) signal delay means for giving a predetermined time delay to the timing signal generated by the timing signal generating means;
The ultrasonic diagnostic apparatus according to claim 4, further comprising: the display control unit configured to display an ultrasonic image on the display device in synchronization with the delayed timing signal.

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