JP2000152929A - Ultrasonic diagnostic equipment - Google Patents

Abstract

PROBLEM TO BE SOLVED: To enable information for integrated backscatter(IB) values of many heartbeats to be stored in an ultrasonic diagnostic equipment capable of calculating the IB values and to facilitate designation of a region of interest. SOLUTION: On a B-mode image, a specific orientation is designated, an ultrasonic pulse on that orientation is transmitted, whereby a power M-mode image 100 is formed. In the power M-mode 100, power is represented by luminance or the like. In the image, a region of interest is set by an ROI marker 106, an IB value is calculated every hour and displayed as an IB value curve 102. Along with displays of these, an electrocardiographic waveform 104 is also displayed. Based on the electrocardiographic waveform, a time phase analysis of the IB value curve 102 can also be performed.

Description

DETAILED DESCRIPTION OF THE INVENTION

[0001]

BACKGROUND OF THE INVENTION 1. Field of the Invention The present invention relates to an ultrasonic diagnostic apparatus, and more particularly, to an integrated backscatter value (In).
The present invention relates to an ultrasonic device capable of measuring an integrated backscatter value.

[0002]

2. Description of the Related Art An iterated backscatter value (hereinafter referred to as "IB") is used to indicate the tissue characteristics of the myocardium.
Value ") is known. The IB value represents the total local power of the reflected ultrasonic waves, and corresponds to, for example, a value obtained by integrating the echo power over a predetermined area. When the disease causes a change in the structure of the myocardium, the change is reflected in a change in the ultrasonic echo intensity. Therefore, by observing the magnitude and change of the IB value, the tissue properties of the myocardium can be evaluated.

In the conventional apparatus, when measuring the IB value, for example, first, a B-mode image (two-dimensional tomographic image) is displayed, and a region of interest (one-dimensional region or spread along the ultrasonic beam) is displayed on the myocardium in the image. (A two-dimensional area with a). Then, an integrated value of the power in the region of interest is calculated for each frame, and is used as the IB value. Alternatively, the IB value is used as a value obtained by normalizing the IB value with an integrated value of the power calculated for a standard site (for example, a heart chamber site). There are various methods for defining the IB value, but in any case, the IB value is an index value corresponding to the integration of the instantaneous power.

[0004] In the conventional apparatus, an IB value graph showing a temporal change of the IB value is displayed on a display together with a B-mode image. In creating the graph, a plurality of B-mode images stored in a memory are used, data corresponding to the region of interest of each frame is sequentially read from the memory, and an operation such as data integration is performed for each frame. This is executed to obtain the IB value. Then, by connecting the IB values of each frame and expressing them as a curve, the IB value graph is formed.

[0005]

However, in a conventional ultrasonic diagnostic apparatus, a B-mode image that can be stored in a memory having a general size is, for example, about two heartbeats. On the other hand, when measuring an IB value for a patient having an arrhythmia, for example, an IB value graph of at least about five heartbeats is required. Therefore, in the related art, when diagnosing a patient having such arrhythmia, for example, processing such as performing measurement a plurality of times and manually connecting IB value graphs obtained in each measurement has been performed. . For this reason, it is complicated and there is a problem that continuity of data cannot be ensured. On the other hand, if the memory is increased, the IB value graph can be displayed at a time for a longer time.
In that case, there is a problem that the cost of the apparatus increases.

In the conventional apparatus, an electrocardiogram can be displayed together with the B-mode image. However, the observation direction (data acquisition timing) and the electrocardiogram (waveform display timing) specified on the B-mode image are synchronized. Therefore, there is a problem that synchronization is not ensured even when the electrocardiogram is displayed together with the IB value graph.

[0007] The present invention has been made in view of the above-mentioned conventional problems, and has as its object the purpose of increasing the I
An object of the present invention is to store information for calculating a B value.

Another object of the present invention is to make it possible to easily specify a region of interest.

[0009]

In order to achieve the above object, the present invention provides a transmitting / receiving means for transmitting / receiving ultrasonic waves, and a power calculation for calculating power based on a signal received from the transmitting / receiving means. Means, a horizontal axis is a time axis, a vertical axis is a depth axis, a power M mode image forming means for forming a power M mode image representing power at each depth or a value corresponding thereto, and the power or the power M mode image forming means. Index value calculating means for calculating an index value for evaluating tissue properties from corresponding values, index value graph creating means for creating an index value graph representing a change over time of the index value, the power M mode image and Display means for displaying an index value graph.

According to the above configuration, a power M mode image is displayed. The horizontal axis is a time axis, and the vertical axis is a depth axis, similar to a known M-mode image, but the displayed information is not the echo intensity but the power or a value corresponding thereto. If data corresponding to the power M mode image is stored in the memory, power for calculating the index value or a value corresponding thereto can be stored in a finite memory capacity over many heartbeats. Preferably, the index value is an integrated backscatter value.

Preferably, the apparatus further includes a region of interest setting means for setting a region of interest on the power M mode image, wherein the index value calculating means calculates the index value by integrating power within the region of interest. I do. Here, the region of interest is a one-dimensional region or a two-dimensional region along the beam.
The one-dimensional area may be shifted in the time axis direction to form a two-dimensional area.

Preferably, the power M mode image and the index value graph are simultaneously displayed in two upper and lower stages with the time axes parallel to each other. According to this display, the time variation of the index value can be evaluated while confirming the integration range and the like.

Preferably, the apparatus further includes a biological signal measuring means for measuring a biological signal, and the waveform of the biological signal is displayed together with the power M mode image and the index value graph.

Preferably, a memory for storing the power is provided, and the index value calculation means reads the power in the region of interest from the memory and calculates the index value.

Preferably, the waveform of the biological signal is an electrocardiographic waveform, and the apparatus further includes an analyzing means for analyzing the index value graph based on the electrocardiographic waveform. Preferably, the analysis means performs a time phase analysis.

[0016]

DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENTS Preferred embodiments of the present invention will be described below with reference to the drawings.

FIG. 1 shows a preferred embodiment of an ultrasonic diagnostic apparatus according to the present invention, and FIG. 1 is a block diagram showing the overall configuration.

In FIG. 1, a probe 10 is an ultrasonic probe used in contact with the surface of a living body or inserted into a body cavity. The probe 10 has an array vibrator composed of a plurality of vibrating elements, and an ultrasonic beam is scanned by electronically scanning the array vibrator to form a two-dimensional data capturing area. The transceiver 12 includes the probe 1
This is a well-known circuit that supplies a transmission signal to 0 and processes a reception signal output from the probe 10.

The control unit 14 performs overall control and timing control of the present apparatus.
The (region of interest) setting device 18 and the direction specifying device 16 are connected. The ROI setting device 18 and the direction designation device 16
Is composed of an input device such as a trackball or a keyboard.

The azimuth designator 16 is a device for designating a azimuth, ie, a beam address, for forming a power M mode image described later on a B mode image, as will be described later. M
This is an apparatus for setting an ROI on a mode image.

The detector 20 is a circuit for detecting the received signal output from the transceiver 12, and the detected received signal B is input to the display processing unit 22. The display processing unit 22 forms a B-mode image based on the received signal B after detection, and outputs it to the display unit 24.

The received signal output from the transceiver 12 is
The signal is input to the quadrature detector 26. This quadrature detector 26 has 2
Two mixers, in each of which 90
Reference signals having different degrees of phase are mixed with the received signal.
As a result, the received signal is converted into a complex signal. The power calculator 28 is a circuit that calculates the power by squaring each of the real part signal and the imaginary part signal constituting the complex signal and adding them. The power P is stored in the memory 30.

That is, as will be described later, transmission of an ultrasonic pulse is repeatedly performed in a designated direction, and a received signal obtained thereby is converted into a complex signal as described above, and power is calculated from the complex signal. It is stored in the memory 30. The power M read from the memory 30 is input to the display processing unit 22 and the display processing unit 2
2, a power M mode image is actually formed and is output to the display unit 24.

The IB value calculator 32 is a circuit for calculating the above-mentioned integrated backscatter (IB) value, and substantially corresponds to a power integrator. The integration is performed within the ROI set on the power M mode image. Therefore, integration is performed at each time, and as a result, the IB value at each time is calculated. Incidentally, when calculating the IB value, the power integrated value is normalized by a predetermined reference value. In this case, the predetermined reference value is, for example, a predetermined value obtained in advance or a reference value calculated in the same B-mode image. It may be a power integrated value within the region.

In the display processing unit 22, an IB value curve (IB value graph) representing the time change of the IB value is created and output to the display unit 24.

The electrocardiograph 34 is a device for measuring an electrocardiographic waveform of a living body. A signal output from the electrocardiograph 34 is input to the display processing unit 22, and the electrocardiographic waveform is displayed on the display unit 24. FIG. 2 shows a B-mode image (two-dimensional tomographic image) displayed on the display unit 24. On this B-mode image 40, the power M
The azimuth θ for creating the mode image is designated. When the azimuth θ is specified in this manner, the transmission of the ultrasonic pulse is repeatedly performed in the azimuth. Of course, at the same time as the formation of the B-mode image, the power M
Transmission of the ultrasonic pulse for the mode image may be performed intermittently.

FIG. 3 shows an image displayed on the display unit 24. In the figure, reference numeral 100 represents a power M mode image. Here, the horizontal axis is the time axis, and the vertical axis corresponds to the depth in the θ direction shown in FIG. Incidentally, the luminance in the power M mode image 100 corresponds to the power, and of course, the hue may be changed according to the magnitude of the power together with the luminance. For example, a color change that changes from yellow to red may be used.

On the power M mode image 100, a region of interest is set along a predetermined tissue or a tissue boundary using the ROI marker 106. In the example shown in FIG. 3, an I-shaped ROI marker 106 is used, and is scanned in a time axis direction along a predetermined tissue by manual operation of a trackball or the like. As a result, an IB value curve indicated by reference numeral 102 is created within the scan range. This IB value curve 102 is
It shows a temporal change of the IB value based on the power integrated value in the ROI calculated by the IB value calculator 32 described above.

The horizontal axis of the IB value curve 102 is the time axis, which coincides with the time axis of the power M mode image 100. The vertical axis of the IB value curve 102 represents the magnitude of the IB value.

An electrocardiographic waveform 104 is shown in the lower part of the power M mode image 100, and the horizontal axis thereof corresponds to the time axis of the power M mode image 100.

Therefore, according to the display form as shown in FIG. 3, there is an advantage that the properties of the tissue can be diagnosed while comparing the three pieces of information with each other. Particularly, since the horizontal axes are synchronized with each other, there is an advantage that more accurate diagnosis can be performed.

The time phase analysis setting unit 19 and the time phase analysis unit 23 shown in FIG.
This is a means for analyzing the time phase of the time period 02, for example, and will be described later.

Further, according to the embodiment shown in FIG. 1, power information for creating the power M mode image 100 is stored in the memory 30, that is, when a relatively small memory 30 is used. Also, there is an advantage that information for calculating the IB value can be stored over many cardiac cycles.

FIG. 4 shows the operation of the ultrasonic diagnostic apparatus according to this embodiment.

In step S101, the probe 10 transmits an ultrasonic pulse for a B-mode image. That is, an ultrasonic pulse is transmitted for each beam address on the B-mode image. In S102, the display unit 2
4 displays a B-mode image. In S103, the azimuth designator 16 is used, and the azimuth for creating the power M mode image on the B mode image is designated by the user.

At S104, the power M
Transmission of an ultrasonic pulse for forming a mode image is repeatedly executed. In S105, the power M mode image is displayed on the display unit 24. In S106, the ROI setting unit 18 shown in FIG.
The ROI is specified on the mode image as shown in FIG. In S107, the IB is calculated based on the ROI thus set, and in S108, the IB value curve 102 shown in FIG. In S109, it is determined whether or not to observe another azimuth.

Next, the operation of the phase analysis unit 23 will be described. FIG. 5 is a flowchart showing a processing procedure for analyzing the IB value curve. FIG.
A state is shown in which the B value curve 102 and the electrocardiographic waveform 104 are simultaneously displayed in synchronization with each other.

In S201 of FIG. 5, first, the time phase analysis setting unit 19 (see FIG. 1) is used, and on the display screen,
Based on the electrocardiographic waveform 104, for example, the time phase of the reference R wave is designated by the user through the line 200. next,
One or more points (points A and B) to be analyzed on the IB value curve 102 are designated by the user through lines 201 and 202. These points are points corresponding to, for example, end-diastole and end-systole. When such setting is completed, in step S202, the phase analysis unit 23 outputs
The analysis of the B value curve 102 is performed. For example, the time from the R wave to the point A and the point B (time phase difference) 204, 205, A
The time (phase difference) 203 between the point and the point B is calculated. Further, the IB value of the point A and the IB value of the point B are read as necessary, and the difference IB value 206 between the points is read.
Is calculated. Note that another analysis can be performed. In S203, those analysis results are displayed on the screen. If the analysis is to be continued, S204 to S20
1 is executed, and the above steps are repeatedly executed. For example, since temporal phase delay occurs in transient myocardial ischemia, the disease or the like can be determined using the above analysis results.

It should be noted that the above time phase analysis is based on the IB value curve 10
2 and the ECG waveform 104 are displayed synchronously, the power M
This can be performed even when the mode image 100 is not displayed.

[0040]

As described above, according to the present invention,
In an ultrasonic diagnostic apparatus having a function of calculating an integrated backscatter (IB) value, more information for calculating an IB value can be stored in a memory, and a region of interest can be easily specified. .

[Brief description of the drawings]

FIG. 1 is a block diagram showing a preferred embodiment of an ultrasonic diagnostic apparatus according to the present invention.

FIG. 2 is a diagram showing designation of an azimuth on a B-mode image.

FIG. 3 is a diagram illustrating an example of a display screen displayed on a display unit.

FIG. 4 is a flowchart for explaining the operation of the ultrasonic diagnostic apparatus.

FIG. 5 is a flowchart for explaining an operation in the time phase analysis.

FIG. 6 is a diagram for explaining a phase analysis.

[Explanation of symbols]

10 probe, 12 transceiver, 14 control unit, 16
Orientation designator, 18 ROI (region of interest) setting device, 19
Time phase analysis setting device, 20 detector, 22 display processing unit, 2
3 Time phase analysis unit, 24 display unit, 26 quadrature detector, 2
8 Power calculator, 30 memory, 32 IB value calculator.

 ──────────────────────────────────────────────────続 き Continued on the front page F term (reference) 4C301 AA02 BB22 CC04 DD07 DD16 EE11 EE13 FF28 HH17 HH54 JB21 JB30 KK09 KK13 KK26 KK27 KK30 KK31 KK34 KK40 LL02

Claims (8)

[Claims] A transmitting / receiving means for transmitting / receiving ultrasonic waves; a power calculating means for calculating power based on a signal received from the transmitting / receiving means; a horizontal axis as a time axis, and a vertical axis as a depth axis And a power M-mode image forming means for forming a power M-mode image representing power at each depth or a value corresponding thereto, and an index value for evaluating tissue properties is calculated from the power or a value corresponding thereto. An index value calculating unit; an index value graph creating unit that creates an index value graph representing a change over time of the index value; and a display unit that displays the power M mode image and the index value graph. Ultrasound diagnostic device. 2. The apparatus according to claim 1, further comprising a region of interest setting unit for setting a region of interest on the power M mode image, wherein the index value calculating unit integrates power in the region of interest. An ultrasonic diagnostic apparatus, wherein the index value is calculated by the following. 3. The ultrasonic diagnostic apparatus according to claim 2, wherein the index value is an integrated backscatter value. 4. The ultrasonic diagnostic apparatus according to claim 1, wherein the power M mode image and the index value graph are simultaneously displayed in two vertical stages with the time axis parallel to each other. 5. The apparatus according to claim 1, further comprising a biological signal measuring unit that measures a biological signal, wherein the power M mode image and the index value graph are provided.
An ultrasonic diagnostic apparatus, wherein a waveform of the biological signal is displayed. 6. The apparatus according to claim 2, further comprising a memory for storing the power, wherein the index value calculation means reads the power in the region of interest from the memory and calculates the index value. Ultrasound diagnostic device characterized by the following. 7. The ultrasonic wave according to claim 5, wherein the waveform of the biological signal is an electrocardiographic waveform, and further comprising an analyzing unit that analyzes the index value graph based on the electrocardiographic waveform. Diagnostic device. 8. An ultrasonic diagnostic apparatus according to claim 7, wherein said analysis means analyzes a time phase of said index value graph.