JPS6331646A - Ultrasonic diagnostic apparatus - Google Patents

Abstract

(57) [Abstract] This bulletin contains application data before electronic filing, so abstract data is not recorded.

Description

DETAILED DESCRIPTION OF THE INVENTION [Objective of the Invention 1 (Industrial Application Field) The present invention relates to an ultrasonic diagnostic apparatus for diagnosing tissues within a subject using ultrasonic waves. below,
By measuring tissue characterization parameters such as sound velocity (sonic velocity) or degree of waveform disturbance, the tissue can be visualized, and tissue characterization parameters such as sound velocity or waveform disturbance degree can be measured and their display frozen for diagnosis. The present invention relates to an ultrasonic diagnostic apparatus equipped with the present invention.

(Prior Art) The ultrasonic propagation velocity in a subject is influenced to a large extent by the composition present in the ultrasonic propagation path in the subject.

In other words, this means that it is possible to detect lesions such as tumors in organs, liver cirrhosis, etc. in a living body based on the ultrasonic propagation velocity. Measuring propagation velocity has great clinical value.

Therefore, attempts have been made to utilize this fact to obtain information on the ultrasonic propagation velocity in the living body and use this information to inspect the composition at a target position.

Conventionally, as a practical ultrasonic measurement method for such examinations, a method as shown in FIG. 10 (hereinafter referred to as the cross-mode method) using an electronic scanning ultrasonic diagnostic device has been recently developed. ing.

In the figure, 1 is a probe for ultrasonic linear electronic scanning, and this probe 1 is used to enter the body from 9aA of the ultrasonic transmitting/receiving surface 2 that is in contact with the body surface (not shown).
Fires ultrasonic pulses in the direction.

Here, an electronic scanning type ultrasound diagnostic device uses a probe with an ultrasound sensor array in which a plurality of ultrasound pulses (hereinafter simply referred to as transducers) are arranged in parallel. Several adjacent image sensors are grouped together, and a driving pulse is applied to each group of image sensors with a predetermined delay time that is determined according to the direction of the transmitted ultrasonic beam and the position of the image sensors in the beam. The ultrasonic waves from each excited imager propagate radially and interfere with each other, canceling each other out in some areas and reinforcing each other in other areas. This method results in an ultrasonic beam. Wave reception is generally carried out at the above-mentioned (-) group used for wave transmission, and after aligning the time axis by delaying the detection signal of the H4H group by the delay time during wave transmission, They are synthesized to form a received signal.Then, by shifting the vibrators in the -group one pitch at a time, the position of the generated ultrasonic beam shifts, so the camera element to be excited is electrically selected. Furthermore, by controlling the excitation timing, linear scanning can be performed, and sector scanning can be performed at a desired position.

For example, if the ultrasonic pulse transmitted in the form of a beam in the θ direction is set in the liver tissue, it travels straight along the transmission path 1 in the liver tissue and is reflected at a point P. Here, among these reflected waves (echoes), the echoes arriving at the probe 1 following the wave receiving path 5 were used for transmission (not at the radial group, but at the incident position of the arriving echoes). The signal is received by the child group (the group of 6-pointed end B of the probe 1).

Since the distance y between A and B above is known, by measuring the propagation time of the ultrasonic wave propagating along path 4.5, the sound speed C in the liver tissue is c=y/ (t - sin θ) ・(11
It can be found by

This principle is used to measure the speed of sound.

Since the speed of sound is unknown, θ is strictly unknown, and
Since there is no reflection point such as point P in a living body, various measures must be taken to obtain the speed of sound from equation (1) above.

Standardly, the sound speed in living tissue is Co = 1530 [m/s]
Then, in order to radiate the ultrasonic beam in the θ0 direction, the delay time between adjacent elements τ0τo = (d/Co) ・s
inθo −(2), and each element is set to be driven with such a delay time difference.

If the sound velocity in the living tissue is Go, the ultrasonic beam will travel in the θ0 direction, but it is generally not limited to Co and will have a different value C. The propagation direction θ of the ultrasonic wave at this time is sinθ/Q=sinθo/C from Snell's law.
It becomes one shift shown as o-(3).

The peak point of the measured waveform indicates the reflected wave from point P,
By detecting the time (address) of the peak value, the propagation time t can be determined. Substituting the above equation (3) into equation (1), the sound speed C in the living body is C= yo t-s group 0) ... (4)
becomes. Furthermore, substituting equation (2) into equation (4) yields C=,7
7 cho cho 7Tτ17...(4゛). V
, d, and τ0 are known and are known, so using the propagation time t obtained by measurement, calculate the above equation (4゛) to find the sound speed C.
Find the value of.

(Problems to be Solved by the Invention) Incidentally, the scattering waveform display in a conventional ultrasonic diagnostic apparatus is performed by simply displaying one waveform with time as the horizontal axis. However, in such a scattering waveform display, the actual waveform pattern depends on the number of simultaneously driven elements in the ultrasound probe, the propagation distance of the ultrasound, etc., so it is difficult to compare it with a normal example. This poses a problem in that it is not possible to improve diagnostic performance based on the scattering waveform of the specimen.

This invention was made in view of the above circumstances, and its purpose is to easily compare the scattering waveform of a subject with that of a normal case, and to improve diagnostic ability based on the scattering waveform. Our goal is to provide an ultrasonic diagnostic device that can

[Structure 1 of the Invention (Means for Solving Problems) The present invention stores the scattering waveform of a phantom or a normal subject in a storage means as a standard scattering waveform, and stores the scattering waveform of a phantom or a normal subject as a standard scattering waveform. The display means displays scattered waveform information based on the scattered waveform.

(Function) Since the display means displays scattering waveform information based on the reference scattering waveform and the scattering waveform of the object, it is possible to easily compare the scattering waveform of the object with a normal example. It is possible to improve the diagnostic ability based on the scattered waveform.

(Example) Hereinafter, the present invention will be specifically explained with reference to Examples.

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

In the figure, reference numeral 1 denotes an ultrasonic probe, for example, a 128-element transducer Tl that transmits and receives ultrasonic waves.

~ T128 are arranged in parallel in a straight line. Oscillator T1゜～T
128 The parallel surface is the ultrasonic transmitting and receiving surface 2 of the probe 1 in Fig. 10.
becomes.

12 is a lead wire; 13 is a multiplexer with a circuit selection switch; 15 is a transmission delay circuit for obtaining the amount of delay to be given to each of the group of vibrators to be excited by the JUT;
14 is a pulser that generates pulses for ultrasonic excitation driving;
6 is a reception delay circuit for obtaining the echo delay amount necessary for aligning the time axis etc. according to the reception direction and element position for each of the group of transducers used for reception; 17 is a reception delay circuit for obtaining image and character information. It is a display (display means) used to display etc.

This display 17 displays tissue characterization parameters such as the speed of sound or the degree of disturbance of the waveform, as will be described in detail later. Scattered waveform information is displayed based on the waveform (this is referred to as a "standard scattered waveform") and the scattered waveform of the object. Specifically, simultaneous display of the standard scattering waveform and the scattering waveform of the object on the same screen,
Pseudo three-dimensional display of scattered waveforms obtained by scanning crossed beams, with time and scan direction as axes;
and numerical display of the spread ratio between the standard scattering waveform and the scattering waveform of the object, which is one of the features of the apparatus of this embodiment.

Incidentally, the phantom may be a scattered phantom or an agar graphite phantom, and the normal subject may be a living body diagnosed as normal.

18 is a meter sieve circuit that calculates the sonic velocity value, average value, etc. based on the output of the A/D converter 20, and 26 is a changeover switch that measures the cross mode sound velocity of the combined output of the receiving delay circuit 16. This is to switch the supply route selection between side X and side B of the ultrasonic device for obtaining an ultrasonic B-mode image. 27 is a receiving circuit on the ultrasonic device side, which performs amplification, detection, logarithmic conversion, etc. of the received signal. 28 is an A/D converter, which converts the output of the receiving circuit 27 into a digital signal. Reference numeral 29 denotes a marker generator, which displays image data for displaying the measurement route (beam path route) of the loss mode sound velocity measurement described above, and a time gate marker (hereinafter referred to as time gate marker) for measuring tissue characterization parameters. It generates image data for 30 is a digital scan converter, which has a frame memory and converts the digital signal output from the A/D converter 28.
The data is sequentially updated and stored in the address corresponding to the beam position where the data was collected, and readout is performed in accordance with the scanning timing of the display 17, thereby making a difference between the timing of collecting the ultrasound image and the display timing on the display 17. By interposing this frame memory, it is possible to convert the problem into a sea urchin.

Also, the output of the marker generator 29 is this digital signal.
It is written in the B-mode image on the frame memory of the scan converter 30 at a position corresponding to the route of the cross-mode sound velocity measurement.

Further, the memory 22 also hides updated data of the A-mode image. Furthermore, although not shown, the display 17 has a video RAM which is a display image memory, and displays the sound speed data, A-mode image, time gate marker, and changes in the average sound speed calculated by the calculation circuit 18. It is controlled by the system control means 25A to store graphs such as patterns in a predetermined layout and a predetermined format.

Then, an image is displayed based on the image data on the video RAM and the output of the digital scan converter 30.

Reference numeral 50 denotes external input means, which includes various switches, trackballs, etc. provided on the operation panel of the apparatus of this embodiment. This external input means 50 allows tissue characterization parameters and display methods to be selected as appropriate. Tissue characterization parameters include sound velocity, waveform disturbance, scattering coefficient, attenuation coefficient, nonlinear parameters, etc., and display methods include scattering waveform display of the subject, scattering waveform of the subject and standard scattering waveform display, and pseudo-display of these. Examples include three-dimensional display.

Next, the system control means 25A will be explained in detail.

The system moving means 25A includes a CPU (central processing unit), ROM (read only memory), RAM (random access memory), and the like. ROM
Inside, a table is formed with gate addresses for tissue parameter measurement calculated backward from the sound velocity value range required for each intersection depth, and each time an intersection is set for ultrasonic wave transmission/reception, the corresponding gate address is set. It is configured to be read out. Here, the necessary sound velocity value range is determined by taking into consideration whether the target region, for example, the liver, is normal or abnormal. And this system control means 25A
Unless there is an instruction to move the gate marker from the external input means 50, the gate address is output as is to the marker generator 29, and if there is an instruction to move the gate marker, the new gate address after the movement is output. is output to the marker 5 mold 29, and the ultrasonic reflection component within the time gate marker setting area is selected as tissue parameter training information. Roughly speaking, the system control means 25A controls the operation of the multiplexer 13, sets the delay times of the transmission delay circuit 15 and reception delay circuit 16, and writes and reads data into the memory 22, according to a predetermined program. Control and operation control of the calculation circuit 18, switching control of the changeover switch 26, marker output control of the marker generator 29, etc.
Normally, while performing ultrasound scans for B-mode, in between them (at predetermined timings), the ultrasound is controlled to be transmitted and received for cross-mode measurement, and the real-time display of B-mode and tissue characterization parameter measurements are performed. Calculate and display the results, and calculate and plot the average sound speed of the entire beam path.

If you want to display the averaged A-mode image, freeze the B-mode image at the end of the B-mode scan, then perform cross-mode measurement, calculate and display it, and perform cross-seed measurement. A frozen A-mode image, an average A-mode image, and an average sound speed change diagram or local sound speed change diagram of one selected beam path are displayed based on measurement data for each beam pass.

Further, regarding cross mode measurement, for example, the operation of the multi-brevener 13 is controlled as follows.

That is, as shown in Fig. 2, this device measures the tissue characterization parameters of the abnormal part included in the reflection point (measurement point) Pll and B12 at the upper boundary and the reflection point (measurement point) B00 at the lower boundary. In doing so, the ultrasonic beam transmission/reception path is changed from A-+POO to B, A-+P++-C, B-POO-
There are 4 routes: +A, B-PI2-D. That is, each of the A and B positions of the probe 1 is used as an ultrasonic beam transmitting position and also as a receiving position. Then, the wave is transmitted from position A, the wave reflected at Poo is received at position B, the wave is then transmitted from position 8, the wave reflected at Po is received at position C, and then the wave is transmitted from position 8. , the wave reflected by Poo is received at position A, and then transmitted from position B,
By switching the transmission and reception so that what is reflected at B12 is received at position C, symmetry is created in the measurement path.
Moreover, the directional directions of the ultrasonic beams in the transmission and reception directions are set at the same angle O. Furthermore, by making the measurement route symmetrical, it is possible to prevent statistically uneven averages, thereby reducing errors.

Next, the operation of the embodiment device configured as described above will be explained.

In this device, cross-mode sound velocity measurements are performed using four routes B1, B2, B3, and B4 as shown in FIG. Then, at a predetermined timing during the interval between ultrasonic electronic scans in B mode, the changeover switch 26
is temporarily switched from the terminal B side to the X side, and tissue characterization parameter measurements are performed.

Specifically, first, system 1: under the control of the control means 25A, the selector switch 26 is switched to the terminal B side, the multiplexer 13 is selected for linear electronic scanning, and the delay circuit is switched to the terminal B side. 1
5.16 is a delay time set for linear electronic scanning, and with these delay times, the multiplexer 13
Ultrasonic waves are transmitted and received by the selected transducer group. The combined output of the received signals is amplified and detected by the receiving circuit 27, converted into digital data by the A/D converter 28, and inputted to the digital scan converter 30. Then, the digital
An ultrasonic B-mode image is formed in the digital scan converter 30 by sequentially performing such ultrasonic scans while sequentially shifting the scan position of the scan converter 30. In addition, a marker of the beam path for cross mode measurement set by the marker generator 20 is output, and the marker is stored in a position corresponding to the cross mode measurement position in the frame memory of the digital scan converter 30. be done. Digital Ski 7
The image data on the frame memory of the pn converter 30 is read out in accordance with the scan of the display 17,
It is applied to the display 17 and displayed.

At a predetermined timing, the system control means 25A
Switch the J changeover switch 26 to the screw-to-wire X side to enter cross/toe measurement. This measurement is first performed on route B1.

That is, under the control of the system control means 25A.

The delay time of the transmission/reception delay circuit 15 is set. This delay time is determined by the delay time difference τ0 between adjacent fine oscillators.
The relationship is set to be o-(d/Co)sin θ (formula (2) above). Then, by the switching operation of the multiplexer 13, the imaging group T1 belonging to the point A of the probe is
~T32 and the output end of the pulser 14 are connected.

In addition, a rate pulse is generated from the clock generator 21 and input to the pulser 14 via the transmission delay circuit 15. The excitation (long pulse) is output at a shifted timing, and the pulse 4 is output on the back of the transducers T1 to T32
] is input to the corresponding transducer, and the transducer generates an ultrasonic wave.
An ultrasonic beam is transmitted to the

On the other hand, the system control means 25A flail (Elf
As a result, the delay time of the receiving delay circuit 16 is exclusively determined,
Due to the switching operation of multiplexer 13, probe 1
The transducer groups T97 to T128 belonging to point B are connected to the input terminal of the receiving delay circuit 16. As a result, in the ultrasonic beam transmitted toward the subject from the transducer group belonging to point A of the probe 1, the reflection valve at point Poo is received by the transducer group bending to point B of the probe 1, The echoes are combined and output after being given a time difference similar to that in the case of transmission by the reception delay circuit 16.

The reception echo synthesis output from this reception delay circuit 16 is
After being amplified and detected by the receiving circuit 19, it is converted into a digital signal by the A/D converter 20 and written into the memory 22. In the memory 22, the address is updated at a predetermined timing every time an ultrasound beam is transmitted by the clock signal output from the clock generator 20, and writing control is performed by the system control means 25A, so that the address is updated from the measurement point. echoes are stored in a form that corresponds to time. This is the data for A-mode Yuu.

When the above-mentioned ultrasonic transmission and reception is performed a plurality of times by one group of transducers belonging to each of points A and B of the probe 1, the processing circuit 23 performs averaging of the received echoes.

When this work is completed, the system control means 25A switches the selector switch 26 to the terminal B side again, and starts collecting B-mode images. Then, at a predetermined timing, the system control means 2
5A switches the selector switch 26 to the terminal X side again, and
Let's move on to the cross-mode measurement on route 2.

Then, the multiplexer 13 operates under the control of the system control means 25A, and this time, instead of the transducer group belonging to point B, the transducer group belonging to the 0 point of the probe 1 (the transducer group and the input terminal of the receiving delay circuit 16 are connected, and the reflected component of the ultrasonic wave transmitted from the transducer group belonging to the point A of the probe 1 at the point Pn is received by the transducer group belonging to the zero point of the probe 1.

The reception echoes are given the same time difference as in the case of transmission by the reception delay circuit 16, and then combined and output.

The combined output of the received echoes is amplified and detected by the receiving circuit 19 in the same way as in the case described above, and then used to measure the time t2 from transmitting and receiving the ultrasonic waves on the route B2 until the waves are received.

When this work is completed, the system control means 25A switches the selector switch 26 to the terminal B side again, and starts collecting B-mode images. Then, at a predetermined timing, the system control means 2
5A switches the selector switch 26 to the terminal X side and moves on to cross mode measurement on the route B3.

Then, the multiplexer 13 is operated under the control of the system control means 25A, and this time the pendulum vJ element group T 97 belonging to point A (instead of the oscillator group belonging to point B of probe 1)
~T128 and the output end of the pulser 14 are connected, and
Instead of the transducer group belonging to point 0, the transducer group belonging to point A of the probe 1 is connected to the receiving delay circuit 16. Then, an ultrasonic wave is transmitted from the transducer group belonging to point B of probe 1, and the reflected component of the transmitted ultrasonic wave at point Poo belongs to point A of probe 1 (received by the transducer group). The received echoes are given the same time difference as in the case of transmission by the reception delay circuit 16, and then synthesized and output.

The combined output of the received echoes is amplified and detected by the receiving circuit 19 in the same way as in the case described above, and is then used to measure the time t3 from transmitting the ultrasonic wave on the route B3 to receiving it.

When this work is completed, the system control means 25A switches the selector switch 26 to the terminal B side again, and starts collecting B-mode images. Then, at a predetermined timing, the system control means 2
5A switches the selector switch 26 to the terminal X side and moves on to cross mode measurement on the route B4.

The multiplexer 1 is controlled by the system control means 25A.
3 operates, and this time, instead of the transducer group belonging to point A, the transducer group belonging to point D of probe 1 and the receiving delay circuit 16 are activated.
is connected to the input terminal of

When an ultrasonic wave is transmitted from the transducer group belonging to point B of probe 1, the reflected component of the transmitted ultrasonic wave at point PI2 is received by the transducer group belonging to point D of probe 1. be waved. Then, the reception echoes are given a time difference similar to that for transmission by the reception delay circuit 16, and then synthesized and output.

The combined output of the received echoes is amplified and detected by the receiving circuit 19 in the same way as in the case described above, and then used to measure the time t4 from transmitting the ultrasonic wave to receiving the wave on the route B4.

When this work is completed, the system control means 25A switches the selector switch 26 to the terminal B side again, and starts collecting B-mode images. Then, at a predetermined timing, the system control means 2
5A switches the selector switch 26 to the terminal X side and moves on to cross mode measurement on the route B1. This operation is repeated to display a real-time B-mode image and average the cross-mode measurement data.

In this way, the data that has been averaged and recorded a predetermined number of times is read out from the memory 22, and the waveform analysis circuit 24 examines the data indicating the peak, and information on the address where the data is stored is read out from the memory 22. is sent to the itch meter circuit 18 as time information. Based on this, the calculation circuit 18 calculates B1. B2゜B3. IMIjl, j2. from the transmission of ultrasound to the above peak for each route of B4. j3.
t4 is calculated. After that, sound speed value V1 for each route
゜V2. V3. V4 and the average sound velocity (aV) over the entire beam path are calculated and the results are displayed on the display 17.

Therefore, in the normal state, only the B-mode image, the measured value of the sound velocity, and the graph of the average sound velocity over time are sequentially displayed.

Other items, such as A-mode images, are only displayed when frozen, except for those that are already displayed.

Examples of displays on the display 17 are shown in FIGS. 3 and 4.

FIG. 3 shows the display in the normal state, and FIG. 4 shows the display in the freeze state.

In FIG. 3, 60 is a B-mode image of the region of interest of the subject measured in real time, 61 is a beam path marker indicating the route of the set beam path for the cross mode measurement in this region of interest, and 62 is a B-mode image of the region of interest of the subject measured in real time. Real-time A-mode images for each beam path route determined by 1q by the cross mode measurement, 63 are sound speed values for each beam path route determined by 1q by the above cross mode measurement, and 64 are these beam path and route images. It is a change diagram of the average sound speed value of a target part calculated|required based on each sound speed value by route. Further, in FIG. 4, 71 is a B-mode image, 72 is a beam path marker indicating the route of the set beam path for the above-mentioned cross-mode measurement in this region of interest, and 73 is the beam obtained by the above-mentioned cross-mode measurement.・Freeze A mode image by path/route, 74 is 1q according to the above cross mode measurement
The sound speed values 75 for each beam path and route are a change diagram of the average sound speed value of the target region, which is obtained based on the sound speed values for each beam path and route. The beam path marker 72 indicates the routes (1) to (4) above,
Also, the sound speed (direction 63.74) is the sound speed value of the route (1) above among these routes, 1, the sound speed value of the route (2) above, V2, the sound speed value of the route (3) above. value 3
, the sound speed value of the route in (4) above is numerically displayed as ■4. Note that ■ is the average sound speed value of these four routes. Also, 75 is the variance value, 77 is the average of each route △
This shows the mode image. Further, the above-mentioned average sound speed value change diagram 75 shows the time change of this average sound speed value.

In addition, the A mode images 73 are those of roots (1) and (3) as 81, B3 as those of roots (2) and (4), and 82 as those of roots (2) and (4).
．． It is displayed as B4. In FIGS. 3 and 4, time gate markers 65, 66.67, 68.78, .
79.80.81 are displayed in a superimposed manner. 65.66 and 78.79 are gate markers for beam 1.3, and 67.68 and 80.81 are for beams 2 and 4.
There is a good marker.

This time gate marker is displayed under the control of the system control means 25A.

Next, the echo waveform and phase received in the device of this embodiment,
The relationship with the time gate for measuring similar characteristic parameters will be explained based on FIG.

In FIG. 5, 83 is the temporal waveform of an echo, and in addition to the image 84 from the intersection, @85 from other than the intersection (due to non-target echoes, for example, the abdominal wall layer, etc.) is included. There is. Note that the start address is shown from the zero point. 86 is a set of time gates for measuring time-decreasing parameters, and normally, R in the system control means 25A
It is set based on the information read from OM. Reference numeral 87 denotes a real-time A-mode image (ASA Nistart Address, ADL: Data Length), and this A-mode image is displayed on the display 17, and gate markers 88 and 89 are superimposed and displayed on this A-mode image. This marker 88.
89 correspond to the falling timing of the time gate 86, respectively. Then, the echo data within the setting area of the markers 88 and 89, that is, the echo data (indicated by DL: data length) corresponding to the high level of the time gate 86, is selected under the control of the system control means 25A (SA Nistart Address ), this is taken into the waveform analysis circuit 24 as an echo time waveform 90 for measuring the characterization parameters, and is used for peak value detection. As a result, non-target echoes existing outside the gate marker setting area are not subjected to peak value detection for measuring the sound speed h↑. Note that 91 is the average A-mode waveform displayed during freezing.

Therefore, the operator can accurately determine whether accurate sound speed measurement is being performed based on the relationship between the real-time A mode image 87 displayed on the display 17 and the time gates 88 and 89. Due to the thickness of the prototype layer of the object, etc., the image 85 due to the non-target echo becomes the gate marker 88.89.
In such a case, the gate marker 88.8 may be inputted via the external input means 50.
All you have to do is move 9.

In addition, when transmitting and receiving ultrasonic waves in cross mode measurement, this device uses the transducer group belonging to point A and the transducer group belonging to point D (the moving distance of the center position in the transducer array direction of each transducer group and the 8 points). The movement distance of the center position in the radial element arrangement direction of each of the transducer group belonging to the oscillator group belonging to the 0 point and the oscillator group belonging to the 0 point is the same distance Δy as shown in FIG.
The deflection angle θ of the ultrasonic beam is equal to θ° in both cases. Therefore, with this, point P++ and point P12 are
They are in a line-symmetrical positional relationship with respect to a line that passes through point Poo and is perpendicular to the ultrasound transmission/reception wave surface of the probe 1, and the distance therebetween is Δy.

Next, the algorithm in the calculation circuit 18 will be explained.

The calculation circuit 18 or performs the following calculation.

Δt=((tl-t2)+(t3-t4))/2=((
tl+t3)/2)-((t2+t4)/2)
...(101) Δt obtained by executing the calculation of equation (101) becomes an estimated propagation time value of the ultrasonic wave propagating along the path between point Pc→point Poo→point PI2.

Therefore, the average sound speed CA of the ultrasonic waves propagating along the path between point Pn→point Poo→point P+2 is determined by the following equation.

CA-(Δy-co)/(Δt-3inOQ>...
(11) The average sound velocity calculated by this equation (11) represents the sound velocity in a local area of the internal tissue of the subject (in this case, a region including points P111 and Poo and PI2).

In this way, it is possible to calculate the sound velocity locally in the internal tissue of the subject from the reflected components of the ultrasound waves at point P111 and point P123. By appropriately switching the multiplexer 13 and changing the position of the intersection of the directivity directions in the transmission and reception of ultrasonic waves, it is possible to obtain sound velocities at multiple locations in the internal tissue of the subject without changing the deflection angle θ.

FIG. 6 is a diagram showing a region where the local sound velocity can be measured by switching the camera. Generally, the delay time that determines the pointing direction is increased by 1q depending on the delay element, but this delay element has a limited range of delay times that can be set. Therefore, since the above-mentioned intersection point is specified, the marker generator 29 is configured to output a beam bus passing through this possible intersection position as a marker, and when a measurement route is set, Select and output the beam path as a marker.

In the figure, 97 is the measurable region of local sound velocity, and this region 9
7, the symbols "." with symbols Poo to P71 are the intersections (beam intersections) of the ultrasonic wave transmission/reception directional directions.

In this case, (Poo, Pt+) in the same way as Bota (above).

PI3), (Po, PZL, Pa), (P+2
．． Pzz.

P73), (PZL, P31.P32), (Pz, Pa
2゜P33), (PZ3.P33.P34),...
As shown in FIG. The second person in the relationship. By selecting a combination of the three reflection points at the third intersection, performing the above measurements on the reflected waves passing through the above-mentioned J: Una route at the three intersections, and calculating the average sound speed by calculating equation (11). , it is possible to obtain seven lines corresponding to the average sound speed of the desired local area within the measurable region 31.

Incidentally, the desired local combined speed value calculated in the S1 monument circuit 18 may be displayed on the display 17 as a color corresponding to the sound speed after being subjected to brightness modulation or color modulation. Further, if the average A-mode image is to be enlarged, a freeze command is given to the system control means 25A. Although not shown, a freeze command switch or the like is provided and operated by the operator. Upon receiving this command, the system control means 25△ collects data on all the ultrasonic beam transmission and reception paths to provide the ultrasonic propagation velocity information for measurement of 1q energy, and then
control to sequentially freeze the ultrasonic tomograms being displayed. Then, the measured sound speed values for each route are obtained and displayed on the display 17, and the average value is plotted and displayed. Further, an average seven-tone image is generated from the data stored in the memory 22, and an A-mode image using the average value from the same route is obtained in the calculation circuit 18, and each is given to the display 17 and displayed as a fourth image. As shown in the figure, the image is displayed frozen in a predetermined position and in a predetermined format.

The displayed images at this time, including the B mode, are almost the same in time, so if this is recorded and retained, it will be extremely useful as comprehensive measurement data at that point in time.

When the freeze command is dismantled, the measurement display returns to the normal mode described above, and the mode image display and the sound velocity measurement data are sequentially updated in real time.

Next, a pseudo three-dimensional display of the scattering waveform of the object and a marker) (
A case where a comparison display with a scattered waveform is performed will be explained. This display mode can be selected by external input means 50. FIG. 7 shows an example of a pseudo three-dimensional display of the scattered waveform. In the figure, 43 indicates a pseudo three-dimensional display of the scattered waveform, t indicates the time direction, and Z indicates the scan direction. When performing such a pseudo three-dimensional display, the intersecting beams are scanned in an oblique direction as shown at 41 under the control of the system control means 25A. In addition, parallel scanning is performed for each of the crossed beams as shown at 44 for the ultrasonic beam 1, thereby performing addition average speckle removal.

40 is a B-mode image, and 42 is a real-time A-mode image obtained every scan of the crossed beams. There is a gate marker 46 on this real-time △ mode image. =
17, 48, and 49 are set, and the data in the setting area of gate markers 46.47 and /18.49 are added to create a new pseudo three-dimensional display. Note that the data addition is executed by the processing circuit 23.

Further, FIG. 8 shows an example of a comparison display with the standard scattering waveform, and 50 in the same figure shows an example of a pseudo three-dimensional display of the standard scattering waveform, and 51 shows a pseudo three-dimensional display of the scattering waveform of the subject (living body). This is an example. Here, the standard scattering waveform is necessarily the scattering waveform of a predetermined fan 1 or a living body diagnosed as normal, and this waveform data is stored in the mailbox 22 in advance. This scattering waveform data may be obtained by measuring a predetermined phantom or a normal living body using the apparatus of this embodiment, or may be written into the memory 22 from outside. By displaying the standard scattering waveform on the same screen, it becomes possible to easily understand waveform disturbances.

Roughly speaking, FIG. 9 shows an example of the spread of the scattering waveform (1G display), and in the simplified version of mark 11 [scattered waveform 50, each mark 1M scattering waveform spread W○(1) ~ ~VO (7) is displayed numerically, and the spread of each scattered waveform W 0 (1) to W 0 (7) is displayed numerically near the scattered waveform 51 of the object. 7], the ratios R(1) to R(7) between the spread of the scattering waveform of the object and the spread of the standard scattering are numerically displayed.
(i) can be reduced to 1q by performing the calculation, where Wl(i) is the spread of the scattering waveform of the object and WO(i) is the spread of the standard scattering waveform. This calculation is performed by the calculation circuit 18.

In this way, in the device of this embodiment, the scattering waveform of the phantom or normal subject is stored as the standard scattering waveform.
Storage means) 22, and displays scattering waveform information based on this reference scattering waveform and the scattering waveform of the object, that is, simultaneous display of the scattering waveform of the object and the standard scattering waveform on the same screen, pseudo Since the three-dimensional display and the numerical display of the waveform spread ratio are performed on the display (display means) 17, the scattered waveform pattern of the subject can be easily compared with that of a normal example, and the diagnostic ability based on the scattered waveform is improved. You can improve your performance.

Further, the temporal waveform of the ultrasonic reflection component from the subject and a time gate marker movable on the time axis by the external input means 50 are displayed on the display means (display) 17,
The ultrasonic reflection component within this time gate marker setting #I region (corresponding to the high level period of the gate waveform 86 in FIG. 5) is selected as tissue characterization parameter measurement information under the control of the system control means 25A. Since the tissue characterization parameter information is calculated based on the selection result, the target element echo can be easily and reliably removed, and highly reliable tissue characterization parameter information can be obtained. can. Furthermore, by superimposing and displaying the time gate marker on the time waveform (real-time A mode image) of the foul component of the ultrasound, it is possible to determine whether only the echo waveform from the target area is within the gate. There is also an advantage that it can be easily performed and that the gate marker can be quickly moved by operating the external input means 50.

In addition, normally, a cross-mode sound velocity measurement for 1 hour is inserted between scans of B-mode images, and only the B-mode images and tissue characterization parameter measurements are updated.
Since the generation, display, calculation, and updating of other images and information such as other average A-mode images are not performed, the time required for this is no longer required, and therefore, the B-mode image can be displayed in real time, and
It becomes possible to successively measure and update the sound velocity values at multiple locations in the internal tissue of the subject. In addition, when you want to view tissue characterization parameter measurements or B-mode images at a certain point in time, including the average A-mode image, by giving a freeze command, you can immediately freeze the B-mode image after cross-mode measurement of 4 routes. is executed to calculate the sound velocity value and generate the average A-mode image, so that the B-mode image, the average A-mode image, and the sound velocity value for the same time phase can be displayed together.

Therefore, the ultrasonic diagnostic apparatus can obtain extremely useful information for diagnosis. In particular, this device performs real-time observation and freezes as necessary to obtain sound velocity information that reflects macroscopic changes in a predetermined part of the subject, such as the entire liver, and the average A of the sound velocity information measurement route. Comprehensive information including mode image etc. is packed into one image 12
It is particularly useful for diagnosing organs such as the liver, whose internal tissues are homogeneous under normal conditions.

Although the embodiments of the present invention have been described above, the present invention is not limited to the embodiments described above and shown in the drawings, and can be implemented with appropriate modifications within the scope of the gist thereof. .

[Effects of the Invention] As detailed above, according to the present invention, there is provided an ultrasonic diagnostic apparatus that can easily compare the scattered waveform of a subject with a normal example and can improve diagnostic performance based on the scattered waveform. can be provided.

[Brief explanation of the drawing]

Fig. 1 is a block diagram of an ultrasonic diagnostic apparatus according to an embodiment of the present invention, Fig. 2 is an explanatory diagram of the ultrasonic beam transmission and reception path in the apparatus of this embodiment, and Figs. 3 and 4 are diagrams of the apparatus of this embodiment. FIG. 5 is a waveform diagram for explaining the relationship between the echo waveform and the time gate. FIG. 6 is an explanatory diagram of the measurement point setting area in the probe of this embodiment.
figure. FIGS. 8 and 9 are explanatory diagrams showing an example of scattering waveform information display in the apparatus of this embodiment, and FIG. 10 is an explanatory diagram of the principle of cross-mode sound velocity measurement. DESCRIPTION OF SYMBOLS 1... Ultrasonic probe, 17... Display (display means), 22... Memory (storage means). Agent Patent Attorney Nori Chika Ken Shu
Norio Ogo Figure 2 Figure 3 Figure 4 Figure 5

Claims (4)

[Claims] (1) Equipped with an ultrasonic probe consisting of multiple ultrasonic transducers arranged in an array, and transmits and receives ultrasonic beams to the target area of the subject using multiple ultrasonic wave transmission and reception paths. In order to perform this, we selected a group of ultrasound transducers for transmitting and receiving different ultrasound beams, captured the reflected waves from the intersection of the ultrasound beams, and based on this, determined the tissue characterization parameters of the target area. In an ultrasonic diagnostic apparatus that obtains and uses for diagnosis, a storage means for storing a scattering waveform of a phantom or a normal object as a standard scattering waveform, and scattering waveform information based on the standard scattering waveform and the scattering waveform of the object in this storage means. 1. An ultrasonic diagnostic apparatus comprising: display means for performing display. (2) The ultrasound diagnostic apparatus according to claim 1, wherein the scattering waveform information display on the display means is simultaneous display of the standard scattering waveform and the scattering waveform of the subject on the same screen. (3) A patent claim in which the scattered waveform information display in the display means is a pseudo three-dimensional display of the scattered waveform obtained by scanning the ultrasonic beams intersecting at the intersection, with time and the scan direction as the axes. The ultrasonic diagnostic apparatus according to item 1. (4) The ultrasound diagnostic apparatus according to claim 1, wherein the scattering waveform information display on the display means is a numerical display of a spread ratio between the standard scattering waveform and the scattering waveform of the subject.