JP3373399B2 - Ultrasound diagnostic equipment - Google Patents

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 apparatus for calculating an index for evaluating the function of an organ such as heart based on a plurality of Doppler waveforms.

[0002]

2. Description of the Related Art A conventional ultrasonic diagnostic apparatus has a Doppler waveform display mode. In this mode, first, an ultrasonic beam is formed so as to pass through a sample point designated by the user on the two-dimensional tomographic image (B-mode image). And
Doppler information at the sample points is extracted from the received signal, and the amplitude of the Doppler information is represented as a waveform on the time axis.

By the way, various indexes such as the tei index have been proposed as indexes for comprehensively evaluating the function of the heart, and are effectively used for evaluating the heart function of various heart diseases. Here, the tei index is, for example, mitral valve blood flow (left ventricular inflow blood flow) and aortic blood flow (left ventricular ejection blood flow).
Of the two Doppler waveforms, or two time values specified based on the two Doppler waveforms of the tricuspid blood flow (right ventricular inflow blood flow) and the pulmonary valve blood flow (right ventricular ejection blood flow) It is calculated by substituting in an arithmetic expression.

4A and 4B show Doppler waveforms of the left ventricular inflow blood flow and the left ventricular ejection blood flow. Here, a is defined as the period from the end point to the start point of the left ventricular inflow blood flow, and b is defined as the period from the start point to the end point of the left ventricular ejection blood flow. The tei index (T
I) is defined by, for example, TI = (ab) / b. It may be defined by a calculation formula other than this.

In any case, when calculating an index for evaluating the function of the moving organ as described above, Doppler waveforms at a plurality of sample points are required.

[0006]

However, the conventional ultrasonic diagnostic apparatus does not support observation of a plurality of Doppler waveforms. In particular, it was not possible to acquire Doppler waveforms at different sample points simultaneously or within the same heartbeat. Therefore, when the above-mentioned index is conventionally calculated, the sampling point is designated twice, and two Doppler waveforms acquired at different times (different heartbeat cycles) are thereby converted into an electrocardiographic signal or the like. The same heartbeat cycle was selected by matching as a reference, and the above-mentioned parameters were read on it. Therefore, since two parameters are not read at the same heartbeat, there is a problem that the reliability of measurement decreases. The above problem is similarly pointed out in the measurement in which there is a request to acquire the simultaneous phase or a plurality of Doppler waveforms that can be regarded as the simultaneous phase.

The present invention has been made in view of the above conventional problems, and an object thereof is to provide an ultrasonic diagnostic apparatus capable of acquiring a plurality of Doppler waveforms.

Another object of the present invention is to provide a device capable of highly accurately calculating an index for evaluating cardiac function.

[0009]

(1) In order to achieve the above object, the present invention provides a left ventricular inflow blood flow and a left ventricle in the heart.
Sump specifying multiple sample points for ventricular ejection flow
Point designating means, and a plurality of ultrasonic beams corresponding to the plurality of sample points are formed simultaneously or in time division within the same heartbeat, a transmission / reception control means for controlling transmission / reception of ultrasonic waves, A Doppler waveform forming unit that forms a Doppler waveform at the plurality of sample points based on a plurality of received signals corresponding to the plurality of ultrasonic beams, and the plurality of Doppler waveforms within the same heartbeat are displayed. display means to be the same
Can be read from the multiple Doppler waveforms within one heartbeat
Comprehensive evaluation of cardiac function based on multiple time values
Index calculation means for calculating an index for the calculation .

According to the above structure, the inflow of the left ventricle into the heart
When multiple sample points are specified for blood flow and left ventricular ejection blood flow , the same heart
A plurality of ultrasonic beams are set by, and transmission / reception for Doppler measurement is performed on the ultrasonic beams. A plurality of receiving signals obtained by this Doppler information corresponding to each sample point is extracted, it al is displayed on the time axis as a plurality of de-flops <br/> la waveform in the same heart beat. In this case, for example, a plurality of Doppler waveforms are displayed in upper and lower two stages on the screen. Therefore, it is possible to perform necessary measurement by using such a plurality of waveforms.

It is desirable that the plurality of ultrasonic beams are formed simultaneously or alternately in a time division manner.
If the time-division switching is performed at a higher speed than the movement of the heart, the Doppler waveform of the same time phase can be acquired.

A preferred aspect of the present invention is characterized in that it includes index calculating means for calculating a predetermined index for comprehensively evaluating the function of the heart based on a plurality of time values read from the plurality of Doppler waveforms. Here, the index is, for example, the above-mentioned Tay index. The present invention is particularly suitable for measurement of the heart, which is a moving body, and has a clinical advantage that the diagnostic accuracy of cardiac function evaluation of arrhythmia (atrial fibrillation, etc.) can be improved.

(2) In order to achieve the above object, the present invention provides an array transducer comprising a plurality of vibrating elements and a left part of a heart on a tomographic image formed by electronically scanning the array transducer. For ventricular inflow and left ventricular ejection
On the other hand , sample point designating means for designating a plurality of sample points and means for controlling the formation of a plurality of ultrasonic beams corresponding to the plurality of sample points within the same heartbeat, Divide into multiple groups,
A transmission / reception control unit that forms an ultrasonic beam for each group, and a Doppler waveform that forms Doppler waveforms at the plurality of sample points within the same heartbeat based on a plurality of received signals corresponding to the plurality of ultrasonic beams. Can be read within the same heartbeat from the waveform forming means and the plurality of Doppler waveforms
To comprehensively evaluate cardiac function based on multiple time values
Index calculating means for calculating the index of .

In forming a plurality of ultrasonic beams,
It is desirable to divide the array transducer into a plurality of pieces for use.
In this case, it is desirable to provide a plurality of transmitting / receiving circuits, Doppler processing circuits, etc. in parallel.

In a preferred aspect of the present invention, there is provided index calculation means for calculating an index for comprehensively evaluating the function of the heart based on a plurality of time values that can be read within the same heartbeat from the plurality of Doppler waveforms. To do.

[0016] In a preferred aspect of the present invention, the transmission / reception control means executes control for making frequencies different among the ultrasonic beams. By making the frequencies different in this way, it is possible to enhance the accuracy of separation of signals from each other and perform highly accurate measurement.

[0017]

DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENT A preferred embodiment of the present invention will be described below with reference to the drawings.

FIG. 1 shows a preferred embodiment of the ultrasonic diagnostic apparatus according to the present invention, and FIG. 1 is a block diagram showing the overall structure thereof. This ultrasonic diagnostic apparatus is an apparatus that transmits and receives ultrasonic waves to and from a living body to perform ultrasonic diagnosis of the living body. In particular, this ultrasonic diagnostic apparatus has a function suitable for measuring the heart. .

In FIG. 1, an ultrasonic probe 10 is used, for example, in contact with the chest of a living body, and the ultrasonic probe 10 in this embodiment is an array transducer 12.
have. The array transducer 12 is formed by arranging a plurality of ultrasonic transducers in a linear shape or an arc shape, and an ultrasonic beam is generated by electronically scanning the array transducer 12 (linear scanning or sector scanning). 101 is scanned. As a result, a two-dimensional data acquisition area is formed.

The transmission / reception control of the array transducer 12 is controlled by the transmission / reception control section 14. Under the control, the transmission signal from the transmission section 16 is supplied to the array transducer 12 and received from the array transducer 12. The signal is output to the receiving unit 22.

The ultrasonic diagnostic apparatus of this embodiment has a function of simultaneously forming two ultrasonic beams 102A and 102B. The ultrasonic beams 102A and 102B are respectively set so as to pass through two sample points set on the two-dimensional tomographic image, and so-called Doppler transmission / reception waves are generated on the ultrasonic beams 102A and 102B. Done. Generally, a wideband ultrasonic pulse is used in B-mode transmission / reception, and a narrowband ultrasonic pulse is used in Doppler measurement. The diagnostic depth on the ultrasonic beams 102A and 102B is defined by the depth of the designated sample point.

When the array transducer 12 is electronically scanned, the transmitter 16 supplies a transmission signal to one or a plurality of vibrating elements of the array transducer 12 as in the conventional case. On the other hand, when the two ultrasonic beams 102A and 102B are formed, the two transmission circuits 18 and 20 included in the transmission unit 16 function, and the respective transmission circuits 18 and 20 cause the respective ultrasonic beams 1 and
02A and 102B are formed. Those transmission circuits 1
Reference numerals 8 and 20 are circuits for performing beamforming by setting a predetermined delay amount in the transmission signal supplied to each vibrating element.

As shown in FIG. 1, when two ultrasonic beams 102A and 102B are formed, the array transducer 12 is divided into two groups, that is, an A group and a B group. The ultrasonic beam 102A is formed, and the ultrasonic beam 102B is formed by using the B group.
Is formed. Of course, two sample points are designated in the present embodiment, but when three or more sample points are designated, if the apparatus is configured so that a corresponding number of ultrasonic beams are formed. Good.

In the receiver 22, the array transducer 12
Is electronically scanned, the phasing addition processing is executed on the reception signals output from the respective vibrating elements as in the conventional case.
On the other hand, when the two ultrasonic beams 102A and 102B are formed, the phasing addition processing is executed in the receiving circuits 24 and 26 corresponding to the respective ultrasonic beams. That is, two transmitting beams are formed by the transmitting circuits 18 and 20, and correspondingly, two transmitting beams are formed by the receiving circuits 24 and 26.
Two receive beams are formed. Incidentally, the ultrasonic beams 101, 102A and 102B shown in FIG. 1 show the concept of an ultrasonic beam in which a transmission beam and a reception beam are integrated.

When the electronic scanning of the ultrasonic beam corresponding to the B mode is performed, the reception signal is output from the receiver 22 to the B mode processing circuit 30, and the B mode processing circuit 30 forms a so-called two-dimensional tomographic image. It The image data is output to the display processing circuit 32, the image data is output from the display processing circuit 32 to the display device 34, and a two-dimensional tomographic image is displayed on the display device 34. This is the same processing as the conventional one.

On the other hand, the two ultrasonic beams 102A, 10A
When 2B is formed, the two reception circuits 24 and 26 function together, the reception signals output from them are input to the Doppler detection circuits 36 and 38 provided in parallel, and the Doppler detection circuits 36 and 38 are provided. At, the Doppler information corresponding to each sample point is detected. That is, the blood flow velocity information at the location designated by the sample point is analyzed as a Doppler waveform. The data of the Doppler waveform output from the Doppler detection circuits 36 and 38 is the Doppler waveform storage circuit 4.
0, 42 and once stored in the Doppler waveform storage circuit 4
The Doppler waveforms read from 0 and 42 are the display processing circuit 3
It is output to the display device 34 via 2, so that the display device 34 simultaneously displays two Doppler waveforms corresponding to two sample points in an upper and lower two-stage arrangement on the screen.

The input device 43 is composed of, for example, a keyboard and a trackball.
The user uses 3 to specify two sample points and a predetermined section on the Doppler waveform to be described later. When a sample point is designated by the input device 43, the sample point designation signal 200 is output from the input device 43 to the transmission / reception control unit 14 so that the transmission / reception control unit 14 forms an ultrasonic beam on the sample point. Then, the transmitter 16 and the receiver 22 are controlled. Also, the transmission / reception control unit 1
4 controls the Doppler detection circuits 36 and 38 so that the Doppler information corresponding to the sample points is extracted.

In the input device 43, when the respective time phases L1 to L4 shown in FIG.
From 3, the start / end designation signal 202 is output to the index calculation circuit 44. The index calculation circuit 44 is a circuit for calculating the above-mentioned Tay index, and the start / end designation signal 2
Based on the parameters a and b indicated by 02, (a-
b) Calculate the Tay index by computing / b. The calculation result is output to the display device 34 via the display processing circuit 32, and the index is numerically displayed on the display device 34.

In the configuration example shown in FIG. 1, when forming two ultrasonic beams 102A and 102B at the same time, it is desirable to make the frequencies of the ultrasonic waves used for forming those beams different from each other. According to this, the accuracy of signal discrimination can be improved and more accurate Doppler extraction can be performed.
Also, in the embodiment shown in FIG.
Although 2A and 102B are formed at the same time, their formation may be switched in a time-sharing manner, for example. In this case,
Each circuit such as the transmission circuits 18 and 20 and the reception circuits 24 and 26 may be provided for only one channel. However, it is desirable to switch such ultrasonic beams at a high speed, and at least a high speed that is negligible with respect to the movement of the heart is required.

Electronic scanning of the B-mode ultrasonic beam 101 and two ultrasonic beams 10 for Doppler waveform observation are performed.
The formation of 2A and 102B may be performed at the same time, but in order to more smoothly express the two Doppler waveforms, it is desirable to interrupt the electronic scanning in the B mode when displaying the Doppler waveforms.

FIG. 2 shows a B-mode image 100 displayed on the display device 34. The example shown in FIG. 2 is a tomographic image of the left ventricle, and two sample points A and B are designated on the tomographic image using the input device 43. In this example, in order to calculate the Tay index, the sample point A is designated as the point of the left ventricular inflow blood flow, and the sample point B is designated as the observation point of the left ventricular ejection blood flow. When such designation is performed, the two Doppler beams 102A and 102B are automatically set so as to pass through the sample points A and B under the control of the transmission / reception control unit 14. The designation of the sample points A and B can be automatically performed on the basis of image recognition or the like.

As described above, FIGS. 4A and 4B show the Doppler waveform of the left ventricular inflow blood flow and the left ventricular ejection blood flow, respectively. In the present embodiment, these waveforms are displayed synchronously, and the input device 4 is displayed on the waveforms.
The user designates four points, that is, the end point L1 and the start point L2 of the left ventricular inflow blood flow, and the start point L3 and the end point L4 of the left ventricular ejection blood flow by using 3. By designating such points, the index calculation circuit 44 causes the parameters a and b which are time parameters.
Is calculated, and the Tay index is automatically calculated based on those parameters.

Of course, such recognition of the start point and the end point can be automatically performed by using, for example, image recognition. In this case, processing may be performed so that each point is automatically recognized based on the unique waveform forms of the Doppler waveform of the left ventricular inflow blood flow and the left ventricular ejection blood flow.

Next, the operation of the ultrasonic diagnostic apparatus of this embodiment will be described with reference to FIG.

First, in S101, transmission / reception for the B mode is performed as in the conventional case. That is, the ultrasonic beam 101 shown in FIG. 1 is electronically scanned, and thereby a two-dimensional tomographic image is displayed on the display device 34.

At S102, two sample points A and B are designated by the user on the B-mode image as shown in FIG. When such a designation is made,
In S103, the two Doppler beams 102 passing through those sample points are controlled by the transmission / reception control unit 14.
A and 102B are automatically formed. That is, transmission / reception for Doppler is performed. In this case, transmission / reception for B mode is stopped.

In S104, as shown in FIG. 4, a start point and an end point are designated on each Doppler waveform. Then, the parameter calculating circuit 44 causes the parameters a,
b is specified, the Tay index is further calculated, and the index is displayed on the display device 34 (S105).

In S106, it is judged whether or not such calculation is repeated, and if it is repeated, the Tay index is calculated in a plurality of heartbeat cycles, the average value thereof is calculated in S107, and the average value thereof is calculated. Is displayed on the display device 34.

The operation example shown in FIG. 3 is for the case where two ultrasonic beams are simultaneously formed. For example, when those ultrasonic beams are formed in a time division manner, S
At 103, transmission / reception control is performed so that the ultrasonic beams are alternately formed.

[0040]

As described above, according to the present invention,
An ultrasonic diagnostic apparatus that can acquire a plurality of Doppler waveforms can be provided. Further, according to the present invention, the heart function can be calculated with high accuracy.

[Brief description of drawings]

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

FIG. 2 is a conceptual diagram showing designation of two sample points on a B-mode image.

FIG. 3 is a flowchart showing the operation of the ultrasonic diagnostic apparatus.

FIG. 4 is an explanatory diagram showing a calculation principle of a Tay index based on two Doppler waveforms.

[Explanation of symbols]

10 ultrasonic probe, 12 array transducer, 14 transmission / reception control unit, 16 transmission unit, 22 reception unit, 36, 38
Doppler detection circuit, 40, 42 Doppler waveform storage circuit, 4
3 input device, 44 index calculation circuit.

─────────────────────────────────────────────────── ─── Continuation of the front page (72) Inventor Masafumi Ogasawara 6-22-1, Mure, Mitaka City, Tokyo Aloka Co., Ltd. (72) Takashi Shinobe, 6-22-1 Mure, Mitaka City, Tokyo Aro (56) References JP 58-83942 (JP, A) JP 8-191834 (JP, A) JP 3-170134 (JP, A) JP 56-18770 (JP , A) (58) Fields investigated (Int.Cl. ⁷ , DB name) A61B 8/00-8/15

Claims (5)

(57) [Claims] 1. Left ventricular inflow and left ventricular ejection in the heart
Sample point finger that specifies multiple sample points for blood flow
A constant section, a plurality of ultrasonic beams corresponding to the plurality of sample points
Based on a plurality of transmission / reception control means for controlling transmission / reception of ultrasonic waves and a plurality of reception signals corresponding to the plurality of ultrasonic beams, the plurality of the plurality of reception signals are formed so as to be formed simultaneously or in time division within the same heartbeat. a Doppler waveform forming means for forming a Doppler waveform sample points, and a display means for said plurality of Doppler waveforms in the same heart rate within appears, read from the plurality of Doppler waveforms in the same heart rate within
Comprehensive assessment of heart function based on multiple time values available
An ultrasonic diagnostic apparatus comprising: an index calculating unit that calculates an index for performing the operation . 2. The ultrasonic diagnostic apparatus according to claim 1, wherein the index is a Tay index . 3. An array transducer comprising a plurality of vibrating elements, and a left ventricular inflow blood flow and left ventricular drive in a heart on a tomographic image formed by electronically scanning the array transducer.
Sample point designating means for designating a plurality of sample points for the blood flow, and means for controlling the formation of a plurality of ultrasonic beams corresponding to the plurality of sample points within the same heartbeat. The vibration element is divided into a plurality of groups, a transmission / reception control means for forming an ultrasonic beam for each group, and a plurality of received signals corresponding to the plurality of ultrasonic beams, based on the same heartbeat, Doppler waveform forming means for forming Doppler waveforms at a plurality of sample points, and a plurality of Doppler waveforms that can be read within the same heartbeat from the plurality of Doppler waveforms
A finger for comprehensive evaluation of heart function based on the time value of
An ultrasonic diagnostic apparatus comprising: an index calculation unit that calculates a target . 4. The ultrasonic diagnostic apparatus according to claim 3, wherein the index is a Tay index . 5. The ultrasonic diagnostic apparatus according to claim 3, wherein the transmission / reception control unit executes control to make frequencies of the ultrasonic beams different from each other.