JPH11197152A - Ultrasonographic device - Google Patents

Abstract

PROBLEM TO BE SOLVED: To provide an ultrasonogeaph capable of easily and accurately specifying plural measurement points on tomographic images. SOLUTION: In this ultrasonograph device provided with a probe 1 for scanning a cross section inside a testee body by ultrasonic waves, a transmission unit 2, a reception unit 3, a B/M mode processing unit 4 for generating the tomographic images relating to the cross section based on echo signals obtained by the scanning, a graphic computing element 6 for preparing a tool for specifying the measurement points, a display unit 5 for displaying the prepared tool together with the tomographic images, a track ball 7 for operating the tool and a calculator 8 for calculating a distance between the measurement points specified by the tool, the tool is provided with a reference line provided on the tomographic image at an optional position and an optional angle and the plural measurement points are successively specified on the reference line.

Description

DETAILED DESCRIPTION OF THE INVENTION

[0001]

BACKGROUND OF THE INVENTION 1. Field of the Invention The present invention relates to an ultrasonic diagnostic imaging apparatus capable of measuring a distance between two points on an ultrasonic image of B mode, M mode or the like.

[0002]

2. Description of the Related Art There are various medical applications of ultrasonic waves, and the mainstream is ultrasonic tomography of a soft tissue of a living body (B mode) using the ultrasonic pulse reflection method, and the tissue of one line. By arranging the images in parallel along the time axis, a so-called M-mode in which a morphological change over time of the heart, blood vessels, and the like can be observed in detail is generated.

[0003] Such ultrasonic image diagnosis is performed by an X-ray diagnostic apparatus, an X-ray computed tomography apparatus (X-ray CT scanner), a magnetic resonance imaging apparatus (MRI), SPECT or PE.
Compared to other imaging devices such as nuclear medicine diagnostic devices such as T, it is possible to observe the movement of the heart and fetus in real time with a simple operation just assigning an ultrasonic probe from the body surface, and it is possible to perform blood flow imaging Has superiority. In addition, there are various features such as harm to the living body is very small, and the test can be performed repeatedly. In addition, since the device is very small, the device can be moved to the bedside to perform the test. Therefore, it can be used in the heart, abdomen, mammary gland,
It is widely used in urology and obstetrics and gynecology.

[0004] By the way, many of such ultrasonic image diagnostic apparatuses measure structural dimensions such as distance, area, and volume from a B-mode image, and measure temporal changes from an M-mode image. The measurement software which can do it can be equipped as standard or option. Furthermore, recently, measurement software has been specialized for fetal and circulatory organs, etc.
More effective information can be provided for each clinical subject. For example, in the measurement software for the circulatory organ, the stroke volume (SV) and the cardiac output (C
O), an index (index) relating to cardiac function such as an ejection fraction (EF) can be calculated.

As described above, the diversification and specialization of the measurement items have been extremely advanced, but the development of the improvement of the efficiency of the operation of the operator has been lagging behind. For example, consider the case of measuring the blood vessel wall thickness and the blood vessel cavity diameter. When the measurement software is started, a cross pointer appears on the image as shown in FIG. The cross pointer can be freely moved up, down, left and right in the screen according to the output of a trackball or the like. The operator can move the cross pointer to the inner position P1 of the blood vessel front wall, the outer position P2 of the blood vessel front wall, Inner position P3 of posterior wall, outer position P of posterior wall of blood vessel
When a total of four measurement points P1 to P4 are specified in order in accordance with No. 4, the distance between the measurement points, that is, the blood vessel wall thickness and the blood vessel cavity diameter are calculated.

The work of designating these four measurement points P1 to P4 is very troublesome, and the four measurement points P1 to P4 are arranged diagonally and zigzag with respect to the blood vessel, and must be repeated many times. Often not.

Next, consider a case where an index of cardiac function such as stroke volume (SV) is measured. There are various methods for measuring the index of this cardiac function, and typical methods using the M-mode image include the TEICHHOLZ method, CUBE method, and GIBSON method, and typical methods using the B-mode image. Modified SIMPSON method and SINGLE PLANE ELLIPSE method are typical methods.

For example, in the M-mode TEICHHOLZ method, as shown in FIG. 12, four measurement points (P101 to P104, 4) are provided in each of the end diastolic (D) and end systolic (S) cardiac phases.
When P201 to P204) are specified, the interventricular septum thickness (IVST), left ventricular minor axis diameter (LVID), left ventricular posterior wall thickness (LVPW) is calculated from these, and one-time ejection is performed from the ventricular septum thickness and the like. The amount is to be calculated. As an operator's work necessary for this, four measurement points may be continuously specified in each cardiac phase, and the calculation result (cardiac output) can be obtained by a relatively simple operation. .

However, as is well known, there are patients who are difficult to take an M-mode image, so that the TEICHHOLZ method or the like often cannot be used. In that case, B mode SINGLE PLANE E
Switch to the LLIPSE method, etc. This B-mode SINGLE PLA
The NE ELLIPSE method can determine the cardiac output with relatively high accuracy, but has the disadvantage that the work of the operator is relatively complicated and time-consuming. In other words, this SINGL
In the PLANE ELLIPSE method, as shown in FIG. 13, the cardiac output is calculated by calculating the major left ventricular area (LVAL), the mitral valve level left ventricular area (LVAM), and the minor left ventricular axis (LVID). In order to further calculate the long axis left ventricular area (LVAL) and the like, the operator moves the cross pointer on the long axis tomographic image and moves the left indoor wall as shown in FIG. A trace line TL1 is drawn along
As shown in (b), by moving the cross pointer on the short-axis tomographic image, a trace line TL2 is drawn along the left ventricle wall, and two measurement points Pa, Pb for the left ventricular short-axis diameter are further drawn.
Must be specified. Moreover, the trace lines TL1 and TR2 and the measurement points Pa and Pb must be performed at both the end diastole (D) and the end systole (S).

[0010]

SUMMARY OF THE INVENTION An object of the present invention is to provide an ultrasonic diagnostic imaging apparatus capable of easily and accurately specifying a plurality of measurement points on a tomographic image.

[0011]

(1) The present invention provides a means for scanning a cross section in an object with an ultrasonic wave, and a means for generating a tomographic image on the cross section based on an echo signal obtained by the scanning. Means for creating a tool for designating measurement points, means for displaying the created tool together with the tomographic image, input means for operating the tool, and measurement points designated by the tool Means for calculating the distance between the ultrasound diagnostic imaging apparatus,
The tool includes a reference line provided at an arbitrary position and an arbitrary angle on the tomographic image, and a plurality of measurement points can be continuously designated on the reference line. I do. (2) The present invention provides a means for scanning a section in an object with an ultrasonic wave, a means for generating a tomographic image on the section based on an echo signal obtained by the scanning, and a tool for designating a measurement point Means for displaying the created tool together with the tomographic image, input means for operating the tool, and means for calculating the distance between measurement points specified by the tool. In the ultrasonic diagnostic imaging apparatus provided, the tool includes a first bar provided at an arbitrary position and an arbitrary angle on the tomographic image, and a second bar crossing the first bar at an arbitrary angle. The second bar is moved so that a plurality of measurement points can be continuously designated on the first bar. (3) The invention according to (1) or (2), further comprising means for calculating an index relating to cardiac function based on the distance between the measurement points.

[0012]

DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENTS The preferred embodiments of the present invention will be described below with reference to the drawings. FIG. 1 shows a configuration of an ultrasonic diagnostic imaging apparatus according to the present embodiment. The present invention relates to a technique for measuring a distance between a plurality of measurement points specified on an ultrasonic image, and this measurement is performed using a tissue tomographic image (B-mode image) relating to a cross section inside a subject. It can be applied to a color flow mapping image (color blood flow image) that provides a blood flow distribution of a cross section inside a subject in color. Here, a B-mode image typically used for measurement will be described as an example. It shall be.

First, the ultrasonic probe 1 has a plurality of transducers in which electrodes are formed on both surfaces of a piezoelectric material such as piezoelectric ceramics near the tip thereof. The electric signal (high-frequency voltage) is converted into an ultrasonic wave through the vibrator, and the ultrasonic wave is converted into an electric signal. A transmission / reception circuit 3 is provided to apply a high-frequency voltage to the vibrator during transmission and to generate an echo signal in which a specific directional component is emphasized from an electric signal during reception.

In the transmission system of the transmission / reception circuit 3, first, a rate pulse is generated at a frequency of, for example, 6 kHz by dividing the frequency of the clock from the clock generator 21 by a fraction pulse generator 22. As is well known, this frequency is called a pulse repetition frequency PRF, and the ultrasonic transmission / reception operation is repeated in synchronization with the pulse repetition frequency PRF. After the rate pulse is delayed by the transmission delay circuit 23,
4 The pulser 24 generates a high-frequency voltage having a frequency f0 in synchronization with the rate pulse and applies it to the vibrator. As a result, the probe 1 repeatedly transmits an ultrasonic beam having the center frequency f0 to the subject at the cycle of the reciprocal of the pulse repetition frequency PRF.

On the other hand, in the reception system of the transmission / reception circuit 3, the electric signal from the vibrator is first amplified by the preamplifier 31, then delayed by the reception delay circuit 32, and added by the adder 33. This makes it possible to generate an echo signal in which an echo component from a specific direction determined by an overall delay pattern of transmission and reception is enhanced.

The output of the transmitting / receiving circuit 3 is connected to a B / M mode processing unit 4. In the B / M mode processing unit 4, the echo signal generated by the transmission / reception circuit 3 is detected by a detection circuit 41, and the detected signal is subjected to logarithmic amplification by a logarithmic amplifier 42. By such processing,
A tissue structure (difference in acoustic impedance) on one beam line (also referred to as an ultrasonic scanning line) is represented by an amplitude change.

The detected signal is converted into a digital signal by an analog-to-digital converter (A / D) 43 and then sent to a display unit 5, where it is first converted to a rectangular coordinate system by a digital scan converter (DSC) 51. Mapping and digital-to-analog converter (D /
A) By returning the analog signal in 52 and displaying it on the display 53, the tissue structure is expressed in shades.

Here, while the overall delay pattern of transmission and reception is slightly changed for each transmission and reception, the digital scan converter 51 maps the vertical axis to the depth and the horizontal axis to the orthogonal coordinate system corresponding to the azimuth direction. , A cross-sectional tissue image (B-mode image) can be generated.
By extracting signals of the beam lines and mapping the signals to an orthogonal coordinate system in which the vertical axis corresponds to the depth and the horizontal axis corresponds to the time axis, a time-change image of a one-dimensional tissue structure on the beam line ( M-mode image) can be generated.

In the present ultrasonic diagnostic imaging apparatus, such a B
A measurement tool (measurement tool) for designating measurement points on an image is superimposed on a B-mode image so that indices related to the distance between two points and cardiac functions can be measured using the mode image. Calculator 6, a trackball 7 for allowing the operator to freely operate this measurement tool, and the actual size-converted distance between two designated points,
A calculator 8 is provided for calculating an index related to cardiac function such as cardiac output (CO) from the distance. What is important here is the display control of the measurement tool by the graphic calculator 6. The display control is generally realized by a program code that can be stored in a storage medium and that can be executed by a computer.

In FIG. 2, according to the display control,
The procedure for continuously designating a plurality of measurement points in a straight line on the B-mode image is shown. First, the measurement tool includes two intersecting bars (a first bar and a second bar). The display of these two bars is controlled by the graphic calculator 6 so that they can be individually moved on the B-mode image by an appropriate operation of the trackball 7 and its attached buttons. The intersection of these two bars represents a candidate for a measurement point. The operator moves the two bars appropriately, and when the intersection point matches the target position,
By giving a confirmation instruction, a measurement point can be designated at that position.

First, in step S1, a first reference line serving as a reference line is set.
The bar is displayed vertically at an initial angle (for example, 0 °) with respect to the vertical axis (depth) on the B-mode image (FIG. 3). At this time, the second bar may be displayed at the same time, but it is assumed here that the second bar has not been displayed for convenience of explanation. Next, in step S2, when the trackball 7 or the like is appropriately operated, the first bar is moved in parallel to the target position accordingly (FIG. 3). At this time, the vertical component (the vertical component of the screen) in the movement of the trackball 7 is ignored by the calculation unit 6, and only the horizontal component (the horizontal component of the screen) is recognized. Since the first bar is moved in the horizontal direction only according to the amount of movement of the track ball 7, the operation of the trackball 7 is simplified.

As shown in FIG. 4, the angle (inclination angle) of the first bar with respect to the vertical axis can be arbitrarily changed, and the operator operates the trackball 7 and the like as necessary. One bar can be appropriately inclined (steps S3 and S4). This tilting function is used when the blood vessel is displayed tilted with respect to the vertical axis,
It is also used to measure the interventricular septum thickness, left ventricular short axis diameter, and left ventricular posterior wall thickness by aligning the first bar with the long axis or short axis on the cardiac long axis or short axis tomogram. .

When the position and the angle of the first bar are determined, the second bar is displayed at an initial intersection angle (for example, 90 °) with respect to the first bar in step S5. The display control target is replaced by the two bars (FIG. 5).
The crossing angle can be arbitrarily changed, and the operator can operate the trackball 7 or the like as needed to appropriately tilt the second bar with respect to the first bar. (Steps S6, S
7). This function is used, for example, when making the second bar parallel to the blood vessel axis.

When the angle of the second bar is determined, next, in step S8, as shown in FIG. 6, according to an appropriate operation of the trackball 7 or the like, the second bar and the first bar have an initial intersection angle. Or, it is translated while maintaining the changed intersection angle. At this time, the horizontal component in the movement of the trackball 7 is ignored by the calculation unit 6, only the vertical component is recognized, and the second bar is moved in the vertical direction according to only the movement amount of the recognized vertical component. Therefore, the operation of the trackball 7 is simplified.

Then, as shown in FIG. 7, step S9
, When a predetermined determination operation is performed, the intersection of the first bar and the second bar at that time is determined as a measurement point, and further, the loop of steps S8 to S10 is repeated to initialize the first bar with the initial bar. While the second bar is being translated while maintaining the proper crossing angle or the changed crossing angle, for example, with respect to the outer edge of the front wall of the blood vessel, the inner edge of the front wall of the blood vessel, the inner edge of the rear wall of the blood vessel, and the outer edge of the rear wall of the blood vessel. A plurality of measurement points can be designated one after another in a straight line on the first bar. Simultaneously with this designation, in step 12, the calculator 8
Calculates the distance between adjacent measurement points in actual size conversion.

Further, the process proceeds to step S11 through step S11.
Returning to step 2, the measurement point can be specified separately for another part (multi-channel measurement function). At the same time as the specification of the measurement point, the calculator 8 determines the adjacent measurement point for each channel in step 12. The distance between them is calculated in actual size.

As described above, according to the present embodiment, once the reference line (first bar) is determined, the second bar is translated while maintaining a constant angle with respect to it. Thus, a plurality of measurement points can be arranged in a straight line and continuously specified one after another on a reference line.
After the distance calculation, the angle of the first bar and the intersection angle of the second bar are changed again, and the fixed first and second bars and the measurement point are moved in any direction as shown in FIG. Adding various supplementary functions that can be performed is considered to be very beneficial for the convenience of operation.

Next, a specific application example of the above-described simple designation method of a measurement point will be described. As described in the related art, the measurement of an index of cardiac function such as stroke volume (SV) can be obtained by using either an M-mode image or a B-mode image. The method using the M-mode image is relatively small and simple as the task imposed on the operator, but the measurement accuracy is relatively low. On the other hand, the method using the B-mode image is relatively small as the task imposed on the operator. Although it is complicated and cumbersome, it has advantages and disadvantages in that relatively high measurement accuracy can be obtained. Generally, the method of using the M-mode image is selected only when the index of cardiac function such as stroke volume (SV) is viewed for reference only, that is, the measurement accuracy may be low, but it is not so much. This is a time when you want to easily measure without taking time, but in reality, if there is a patient who is difficult to take an M-mode image, there is a case where you have to select a method that uses a troublesome B-mode image. May actually occur.

In order to cope with such a case, the measurement accuracy may be low using the B-mode image, but the index relating to the cardiac function such as the cardiac output can be easily measured without taking much time. There is a strong demand for such a method. This application technique has been made to meet such a demand.

FIG. 9 shows the procedure of this application example.
FIG. 10 is a supplementary diagram of the procedure of FIG. 9, and FIG. 10 (a) shows a B-mode image with respect to the long-axis section at the end diastole.
(B) shows a B-mode image related to a long-axis cross section at the end of systole. The B-mode image related to the long-axis section at the end diastole and the B-mode image related to the long-axis section at the end systole are collected beforehand using heart rate synchronization and stored in a frame memory (not shown) to specify a measurement point. It may be read out at a time and displayed in a frozen state, or may be collected and displayed in a frozen state using heart rate synchronization when a measurement point is designated.

First, in step S101, a first bar B1 serving as a reference line is displayed on a B-mode image related to a long-axis cross section of end diastole. Next, steps S102 to S104
In the above, the trackball 7 or the like is appropriately operated to
By moving the bar B1 and tilting it appropriately, the first bar B1 is aligned with the short axis of the heart.

When the position and angle of the first bar B1 are determined, in step S105, the second bar B2 is moved in parallel according to an appropriate operation of the trackball 7 or the like, and the position required for the measurement, that is, the present application example Now, the outer edge of the ventricular septum,
Four measurement points (P11 to P14) can be arranged in a straight line on the inner edge of the interventricular septum, the inner edge of the left ventricular posterior wall, and the outer edge of the left ventricular posterior wall, and can be successively designated one after another. Then, it is confirmed that the four measurement points (P11 to P14) are specified at appropriate positions, and the operation of specifying the measurement points on the end-diastolic image is completed in step S106.

Next, the display image is switched to a B-mode image related to the long-axis section of end-systole, and steps S101 to S10 are displayed on the B-mode image related to the long-axis section of end-systole.
In the same procedure as in 6, the outer edge of the ventricular septum, the inner edge of the ventricular septum,
Four measurement points (P on the inner edge of the rear wall of the left ventricle and on the outer edge of the rear wall of the left ventricle)
21 to P24) are specified (S107 to S112).

Next, the designated measurement points (P11 to P14,
From P21 to P24), an index relating to cardiac function such as cardiac output is obtained by the same calculation processing method as the TEICHHOLZ method for M mode, and an index relating to cardiac function such as cardiac output is determined during the calculation. End-diastolic ventricular septum thickness (IVST
D), left ventricular minor axis diameter (LVIDD), left ventricular rear wall thickness (LVP)
WD), the end-systolic ventricular septum thickness (IVSTS), left ventricular minor axis diameter (LVIDS), and left ventricular posterior wall thickness (LVPWS) are displayed on the same screen (S113).

As described above, indices relating to cardiac functions such as cardiac output can be easily measured using a B-mode image. In addition, the measurement points (P11 to P1
4, P21 to P24) can be easily specified in a straight line and continuously using a reference line. It is needless to say that the present invention is not limited to the above-described embodiment, and can be implemented with various modifications.

[0036]

According to the present invention, the measurement points can be arranged in a straight line on the first bar or the reference line and continuously specified, and the cross point can be moved in a completely free state as in the prior art. Rather than specifying a plurality of measurement points individually, it is possible to easily and accurately specify the target.

[Brief description of the drawings]

FIG. 1 is a block diagram showing a configuration of an ultrasonic diagnostic imaging apparatus according to an embodiment.

FIG. 2 is a flowchart illustrating a flow of a measurement point designation process according to the embodiment;

FIG. 3 is a view showing an example of a display screen corresponding to steps S1 and S2 in FIG. 2;

FIG. 4 is a view showing an example of a display screen corresponding to steps S3 and S4 in FIG. 2;

FIG. 5 is a view showing an example of a display screen corresponding to steps S5, S6, and S7 in FIG. 2;

FIG. 6 is a view showing an example of a display screen corresponding to step S8 in FIG. 2;

FIG. 7 is a view showing an example of a display screen corresponding to steps S9 and S10 in FIG. 2;

FIG. 8 is an explanatory diagram of additional functions provided by the graphic calculator of FIG. 1;

FIG. 9 is a flowchart showing a specific application example of the measurement point designation processing according to the embodiment.

10 is a supplementary diagram of FIG. 9, in which (a) shows measurement points specified on a tomographic image (B-mode image) at the end diastole;
(B) is a diagram showing measurement points designated on a tomographic image (B-mode image) at the end of systole.

FIG. 11 is an explanatory diagram of a conventional measurement point designating operation.

FIG. 12 is a diagram showing measurement points required to calculate a cardiac output from a conventional M-mode image.

FIG. 13 is a diagram showing trace lines and measurement points necessary for calculating a cardiac output from a conventional tomographic image (B-mode image).

[Explanation of symbols]

 DESCRIPTION OF SYMBOLS 1 ... Probe, 2 ... Transmission unit, 3 ... Receiving unit, 4 ... B / M mode processing unit, 5 ... Display unit, 6 ... Graphic calculator, 7 ... Trackball, 8 ... Calculator, 21 ... Clock generator, 22: Rate pulse generator, 23: Transmission delay circuit, 24: Pulser, 31: Preamplifier, 32: Reception delay circuit, 33: Adder, 41: Detection circuit, 42: Logarithmic amplifier, 43: Analog-to-digital converter, 51 ... Digital scan converter, 52 ... Digital / analog converter, 53 ... Display.

Claims (3)

[Claims] 1. A means for scanning a section in an object with an ultrasonic wave, a means for generating a tomographic image on the section based on an echo signal obtained by the scanning, and a tool for designating a measurement point Means for displaying the created tool together with the tomographic image; input means for operating the tool; and means for calculating the distance between measurement points designated by the tool. In the ultrasonic diagnostic imaging apparatus, the tool includes a reference line provided at an arbitrary position and an arbitrary angle on the tomographic image, and a plurality of measurement points can be continuously designated on the reference line. An ultrasonic diagnostic imaging apparatus, comprising: 2. A means for scanning a section in an object with an ultrasonic wave, a means for generating a tomographic image on the section based on an echo signal obtained by the scanning, and a tool for designating a measurement point Means for displaying the created tool together with the tomographic image; input means for operating the tool; and means for calculating the distance between measurement points designated by the tool. In the ultrasonic diagnostic imaging apparatus, the tool includes a first bar provided at an arbitrary position and an arbitrary angle on the tomographic image, and a second bar crossing the first bar at an arbitrary angle, An ultrasonic diagnostic imaging apparatus wherein a plurality of measurement points can be continuously designated on the first bar by moving the second bar. 3. The ultrasonic diagnostic imaging apparatus according to claim 1, further comprising: means for calculating an index related to cardiac function based on a distance between the measurement points.