KR840002100B1 - Ultrasonic diagnosing apparatus - Google Patents

Abstract

A first set of transducers is arranged in an array to transmit an ultrasonic beam into human tissue and receive a reflected echo. A second set of transducers also transmits and receives ultrasonic pulses from human tissue and is arranged to transmit in a direction which is perpendicular to that of the first array, while forming an acute angle w.r.t. the first array along the direction of the beam transmitted by the latter. A first circuit processes the echo received by the first transducer array to produce a signal representative of tomogram information of the tissue.

Description

Ultrasonic Diagnostic Device

1 is a view showing a part of the transducer (tranoducer) of an embodiment of the present invention,

2 is a view showing the relationship between the ultrasonic beam, the scanning direction, the scanning line,

3 is a circuit configuration diagram of an embodiment of the present invention;

4 is a blood flow output curve.

5 is a view showing a change in the z-direction of FIG.

BACKGROUND OF THE INVENTION 1. Field of the Invention The present invention relates to a high-speed scanning ultrasound diagnostic apparatus capable of displaying ultrasonic realtime tomograms and accurately measuring blood flow or blood flow.

Conventionally, a device capable of measuring the blood flow velocity of a specific part in a heart tomography by combining a sector type ultrasound real-time tomography device and an ultrasonic pulse Doppler device has been reported. Lecture Papers p7, 1978). However, a linear scan type is suitable for abdominal diagnosis and the like, and clinically, it is often important to measure blood flow and blood flow, but blood flow or blood flow of the blood flowing through the sinus and vein is important. In addition, there is no device that can be measured accurately.

It is an object of the present invention to provide a device capable of measuring and outputting the flow rate of blood flow in a blood vessel, and furthermore, the two-dimensional blood flow distribution and blood flow simply and accurately.

In the present invention, a first vibrator array (real-time) depicts the longitudinal section of the blood vessel in real time, detects the state of travel of the vessel and the ultrasonic beam emitted by the second vibrator array and the angle formed of the vessel, The position of the beam for obtaining the Doppler blood flow signal is precisely determined by the vibrator array of 2, and the blood flow velocity and its distribution in the blood vessel are obtained from the obtained Doppler signal, and then integrated in the beam direction, and perpendicular to the aforementioned longitudinal section. If you add them together while injecting them, you can automatically calculate and output blood flow at every moment.

Next, the Example of this invention is described.

)한 프로우브이다. 제1및 제2의 진동자 어레이를 구성하는 진동자 엘레멘트는, 케이블(3)을 거쳐서 전자회로(멀티플렉서)에 접속되며 선택적으로 초음파 펄스의 송수파(送受波)를 행한다. 진동자어레이(1),(2) 및 케이블(3)은, 케이스(4)에 의해서 고정된 초음파탐촉자(探觸子((5)를 구성하고, 제1도(d)와 같이 진동자 어레이의면(1)(2)가 신체표면에 접촉하여 생체와 초음파펄스의 송수(送受)를 행한다. 송수파 되는 초음파비임의 방향은 이 예에서는 진동자 어레이의 면에 수직인 방향 즉, 제1위 진동자 어레이(1)에서는 제1도의 x방향, 제2의 진동자어레이(2)에서는 z에 수직인 면내의 xy방향(

방향)이며 서로가 예각(銳角)을 이루고 있다.1 is a view showing a first vibrator array 1 and a second vibrator array 2, (a) is a perspective view (b), a top view (c) is a front view, and (d) Joining the vibrator arrays (1) and (2)

It is a probe. The vibrator elements constituting the first and second vibrator arrays are connected to an electronic circuit (multiplexer) via a cable 3 and selectively transmit and receive ultrasonic pulses. The vibrator arrays 1, 2, and the cable 3 constitute an ultrasonic probe ((5) fixed by the case 4, and the surface of the vibrator array as shown in FIG. 1 (d). (1) (2) contacts the surface of the body to carry out the transmission of the living body and the ultrasonic pulse The direction of the ultrasonic wave to be transmitted is in this example perpendicular to the plane of the vibrator array, that is, the first-order vibrator array. In (1), the x-direction in FIG. 1 and in-plane xy-direction perpendicular to z in the second vibrator array (2)

Direction) and are acute with each other.

를 이룬 방향으로 방사된다. 이 방향을

방향이라 정한다.The direction of the ultrasonic beam is well shown in FIG. FIG. 2 (a) is a cross-sectional view of the xy plane, in which the ultrasonic beam is radiated from the first vibrator array 1 in a direction perpendicular to the vibrator surface, i. Inject. On the other hand, the ultrasonic wave radiated by the second vibrator array 2 is acute from the ultrasonic beam by the first vibrator array 1 in parallel in the xy plane.

Radiate in the direction of This direction

Direction.

The vibrator elements are, for example, width 1mm, length 10mm, resonant frequency 5MHZ, and 64 are arranged in the first vibrator array 1, 64 mm in array length, 32 in the second vibrator array 2, and array length 32 The dogs are arranged and the array is 32mm long.

방향단면은 제 2도(b)처럼 된다.When the ultrasonic transducer 5 is brought into contact with the body length such that the end face 6a of the blood vessel is in the scanning surface obtained by the first vibrator array 1, the scanning line by the second vibrator array 2 and

The direction cross section is as shown in FIG. 2 (b).

Next, the method of obtaining the tomographic and Doppler blood flow information by scanning the ultrasonic beam by the vibrator array (1), (2) is as follows.

3 is a circuit configuration diagram of the apparatus of the present invention.

The crystal oscillator 17 is a stable oscillator of a basic frequency, for example, 5 MHz, and the rate oscillator 16 divides the oscillator output and outputs a rate pulse of 5 KHz. Upon receiving the output of the rate oscillator 16, the pulser 13 registers with the rate pulses to generate an impulse, and through the multiplexers 11 and 12, the first and second vibrator arrays 1, ( Selectively drive the vibrator element of 2) and fire an ultrasonic pulse. The on / off control of the switches of the multiplexers 11 and 12 is performed by the scanning control circuit 18.

In general, the multiplexers 11 and 12 operate as follows. Either part of the multiplexer 11 (to write MPX ₁ ) is on, or multiplexer 12 (to write MPX ₂ ) is off, or MPX ₁ is off, or part of MPX ₂ is on. . Rate pulses if the first described for MPX ₁ in eight on-top of the MPX ₁ and FIG. 1 (d) the output of the pulse generator 13 to the eight transducer elements from above, through a cable 3 so added the Ultrasonic pulses are emitted and propagated in the second direction in the x direction to receive the reflected waves reflected from the tissue in vivo as the same eight vibrator elements through the same cable (3) and MPX ₁ . Input to preamplifier 20.

As a result, the first scanning line information for obtaining the B-mode image is obtained by the first vibrator array 1, and the scanning line is used as the first scanning line for obtaining the B-mode image by the first vibrator array. It means IB ₁ , which means scan line. The output of the preamplifier 20 is input to the amplitude detector 14, and the signal detected by the amplitude detector 14 is amplified by the video amplifier 15, and is a digital scan converter as a luminance modulation signal for a conventional B-mode. (Weak DSC) 21 is stored in the corresponding position. In the second rate pulse, the second to ninth eight of the MPX ₁ are turned on, and all of the information of the second scanning line IB ₂ is obtained in the same manner and stored in the DSC 21 in the same manner. Although the DSC 21 is controlled by the scanning control circuit 18, the luminance modulation signal is stored in the address corresponding to the position of the ultrasonic beam as in the conventional DSC method.

Third, fourth,... Similarly, the data pulses of the Tate pulses are obtained one by one, and the scanning line information of IB ₃ and IB ₄ is obtained and accumulated in the DSC 21, and the information is read out and displayed on the TV monitor as shown in FIG. The mode is displayed. This is all the same as what is commonly called linear electron scanning. In this case, as shown in FIG. 2A, a linear marker indicating the direction of the ultrasonic beam by the second vibrator array is displayed.

정보를 얻고, 전치증폭기(20), 진폭검파기(14)를 통해서 DSC(21)에 축적된다. MPX₂(12)의 동작에 따라 제2의 진동자어레이(2)에 의하여 얻어지는 단층상의 주사선을 순차적으로 IIB₁, IIB₂…라 부르는 것으로 한다. 이 단층상은, 제2도(b)에 나타낸 것이며 제2도(a)의 단면과 수직으로서 주사선이

방향의 단면선이다.Next, the MPX ₂ 12 will be described. The MPX ₂ (12) is also the same as the MPX ₁ (10), and is controlled by the scanning control circuit 18, and the B mode phase

The information is obtained and accumulated in the DSC 21 through the preamplifier 20 and the amplitude detector 14. In accordance with the operation of the MPX ₂ (12), the scan lines on the tomogram obtained by the second vibrator array (2) are sequentially added to IIB ₁ , IIB ₂ . It is called. This tomographic image is shown in Fig. 2 (b) and the scanning line is perpendicular to the cross section of Fig. 2 (a).

Section line in the direction.

Here, the number of scanning lines showing the ultrasonic beam direction for detecting the Doppler signal, which will be described later, is 64-8 + 1 = 57 in the tomographic phase (called the tomographic phase of I) by the first vibrator array 1 and the second vibrator. In the tomographic phase by the array 2 (it is called the tomographic phase of II), it is 32-8 + 1 = 25 pieces.

The MPX ₁ (11) and the MPX ₂ (12) are controlled by the scan control circuit 18 as described above, and the output signal of the amplitude detector 14 is accumulated in the DSC 21 through the video signal amplifier 15. As a result, a B-mode image displayed on the TV monitor 27 is obtained. Scanning to obtain a tomographic image of I has a scanning line obtained for each rate in order of IB ₁ , IB ₂ , IB ₂ ,. … , IB ₅₇ , IB ₁ ,. … Is a repetition of IIB, IIB ₁ , IIB ₂ , IIB ₃ ,... … IIB ₂₅ , IIB ₁ ,. … Of repetition.

Although the above is a description of the circuit for obtaining the B-mode image, the circuit for obtaining the blood flow signal by the pulse Doppler will be described as follows.

In this case, the scan control circuit 18 sends a control signal to turn on the i-th, (i + 1th, ...… (i + 8) th on the MPX ₂ (12), and turn off the others. The output of the pulser 13 generated by the rate pulse passes through the ON part of the MPX ₂ (12) and through the cable 3 the i- (i + 8) th vibrator of the second vibrator array 2 The reflected wave received by the same oscillator is input to the phase detector 19 via the cable 3, the MPX ₂ 11, and the preamplifier 20. Also in the rate pulses of the second, third, ... , MPX ₂ has the same position {i to (i + 8)} th) and the ultrasonic beam direction is fixed. The scan line in this case is referred to as IIDi. The reflected signal by each rate pulse is multiplied by the 5 MHz signal of the reference signal generator 17 in the phase detector 19, and phase detected. The output of the phase detector 19 is sampled only for a certain time (corresponding to a certain distance from the vibrator) between the following rare pulses at the timing at which each rate pulse occurs, and the signal is zero-crossed. ), The output of the zero-cross meter displays the blood flow velocity of a point at a certain distance from the vibrator in the direction of the ultrasonic beam, which is the same as an ultrasonic Doppler blood flow meter using a conventional zero-cross meter. In the embodiment of FIG. 3, the blood flow is simultaneously measured for each point added to the ultrasound beam, for example, 128 points, instead of only one point on the ultrasound beam. It is done by the blood flow velocity detection circuit 30 inside which is surrounded by the dotted line of FIG.

The phase detected output from the phase detector 19 is converted into a digital signal by the A / D converter 1. This is to have a zero crossing function, and may be a code bit added to 2 bits of 1,0.

That is, the output of the A / D converter 31 is three kinds of -1,0,1. The clock frequency of the A / D conversion is, for example, 128 times the rate frequency, and corresponds to dividing a signal in one rate into 128 sections.

)계수곱셈기(36)을 통해서 가산기(35)에 입력하고, 한쪽에서 D/A변환기(37)를 통해서 혈류속애널로그신호로서 출력된다. 가산기(35), RAM(II)(34), 계수곱셈기(36)의 조합은 애널로그신호로 말하면 콘덴서저항에 의한 적분회로에 상당하는 것이지만 이런 경우 각 레이트마다에 128의 데이터를 동기를 취하여 각각 독립적으로 적분하고 있는 것으로 되며, D/A변환기(37)의 출력에는 각 128점에 상당한 혈류속신호(영교차출력에 상당한 것)이 한꺼번에 출력된다. 제4도에, 이 D/A변환기(37)의 출력을 나타냄.RAM (Random Access Memory) (I) 33 has 128 addresses corresponding to the above 128 sections, and the values stored in each address are -1,0,1 as well. Is adopted. First, all of the inputs are "1", and the outputs of the RAM (I) 33 corresponding to the 128 outputs of the A / D converter 31 are compared as the comparators 32 for each rate. The comparator 32 is " 1 " only when the sign of the output of the A / D converter 31 and the output of the RAM (I) 33 is different from each other (that is, "1" or "-1" and "1"). And output the contents of the corresponding address of the RAM (I) 33. For example, 128 outputs of the A / D converter 31 are sequentially 1 (0), 2 (1). ), 3 (1), 4 (1), 5 (0) ... ... the contents of the third address of 128 (I) are changed from "1" to "-1". The signals output from the comparator 32 sequentially in this manner for each rate pulse are input to the corresponding address of the RAM (II) 34 through the adder 35 as well. Each address can store an 8-bit value. The output of RAM (II) 34 is K times on one side (e.g.

) Is inputted to the adder 35 through the coefficient multiplier 36, and outputted as a blood flow analog signal through the D / A converter 37 on one side. The combination of the adder 35, the RAM (II) 34, and the coefficient multiplier 36 corresponds to an integrating circuit by a capacitor resistor in terms of an analog signal, but in this case, 128 data are synchronized for each rate. Integrating independently, the output of the D / A converter 37 outputs a blood flow velocity signal (corresponding to zero crossing output) corresponding to 128 points at a time. 4, the output of this D / A converter 37 is shown.

방향의 제 2의 진동자어레이로부터의 거리를 표시하고 있으며, 혈관을 통과할때에 혈류에 의한 도플러신호가 얻어지며, 혈관내에서는 통상(通常) 중심부분은 단부(端部)에 비교해서 혈류속은 크므로 도면과 같은 파형이 얻어진다.The abscissa is time but the second degree

The distance from the second vibrator array in the direction is displayed, and the Doppler signal due to the blood flow is obtained when passing through the blood vessel. In the blood vessel, the central portion of the blood flow is compared with the end portion. Since it is large, a waveform as shown in the drawing is obtained.

Next, the MPX ₂ (12) is set to one difference and the scan line direction is fixed again to obtain a blood flow waveform in the next scan line direction in the z direction. In this case, the scan line is IID (i + 1). If the blood flow velocity parallel to the blood vessel at a certain scan line position IIDi in the z-direction of the blood vessel cross section is vi, the output of the D / A converter 37 becomes a value proportional to vicosθ. Θ is an angle formed between the ultrasonic beam and the blood vessel as shown in FIG. Integrating this value in the z direction by the integrator 22 results in vicosθdl. On the other hand, the flow rate Q is an integral of the radial blood flow velocity vi with respect to the cross section perpendicular to the blood vessel axis,

ΔZ is a scanning line interval in the direction. Passing the output of the integrator 22 through the adder 23, passing the coefficient multiplier 24 again, and again passing the coefficient multiplier 24, the output is,

It is equal to the blood flow Q of equation (2). Thus, the blood flow amount obtained at every moment is recorded and displayed on the recorder 26 or the digital display 25. FIG.

방향으로 적분하고, 적당한 계수를 걸어줌으로서 혈류량을 출력하는 것도 가능하다. 위상검파기(19)의 출력은 제2의 진동자 어레이(2)의 표면으로부터의 몇개의 지정된 거리에 있는 혈류신호를 얻기 위하여 레인지게이트(range gabe)회로(41)에 의하여 그 거리에 있어서의 반사신호가 샘플링 및 홀더되며, 실제시간 고속 푸우리에(Fourier)변환기(42)에 의해서 주파수분석되며, 레코오더(26)에 기록할 수도 있다.FIG. 5 shows FIG. 4 again in the Z direction. The output of the D / A converter 37 is once stored in the DSC 21 and displayed as shown in FIG. This notation is very convenient for examining blood flow distribution. In addition, only the blood flow on one scan line passing through the center of the blood vessel, for example, v ₃ cos θ

It is also possible to output the blood flow amount by integrating in the direction and applying an appropriate coefficient. The output of the phase detector 19 is reflected at that distance by a range gabe circuit 41 to obtain a blood flow signal at some specified distance from the surface of the second vibrator array 2. Is sampled and held, frequency analyzed by a real time fast Fourier converter 42, and recorded in recorder 26.

Although the method of obtaining the B-mode phase and the Doppler blood flow signal has been clarified, in practice, a combination thereof is used. All of these combinations are performed by the address control of the MPX ₁ (11), the MPX ₂ (12), the DSC (21) by the scan control circuit 18, and the like, by using a microcomputer in the scan control circuit 18. It is easy.

Next, examples of this combination will be described.

First, the transducer is applied to a living body to obtain a single-phase image of I and II. The order of the scan lines is for example IB ₁ , IB ₂ , IIB ₁ , IB ₃ , IB ₄ , IIB ₂ ,. … IB ₂₅ , IB ₅₁ , IB ₅₂ , (),.. … IB ₅₃ , IB ₅₄ , (), IB ₅₅ , IB ₅₆ , (), IB ₅₇ , (), (), IB ₁ , IB ₂ ,. … You can do

() Is arbitrary.

방향의 횡단면이 II의 단층상위에 제2도와 같이 표시된다.In this way, the longitudinal section of the blood vessel to measure blood flow is described above the tomography of I.

The cross section in the direction is shown in Figure 2 above the fault on II.

Next, it is assumed that the Flevi is also on the center of the cross section of the blood vessel above the tomogram of II, and the scan line for the Doppler signal of the II and the Doppler signal are alternately obtained. In this case, the order of the scanning lines is that when the j-th scanning line of the blood vessel center is placed, IIB ₁ , IIDj, IIB ₂ , IIDj,... … IIDj,… … IIB ₂₅ , IIDj, IIB ₁ ,... … Of repetition. At this time, of course, the output of the phase detection circuit 19 is used only when IIDj.

In this state, if the tomographic phase of II is also removed and only the plugler signal is used, a very good Doppler blood flow signal of S / N is obtained. The scanning lines at this time are IIDj, IIDj, ... for each rate. … It is fixed as one like.

If it is fixed in this way, only blood vessel center blood flow can be detected, and the blood flow content is approximately calculated by counting. On the other hand, by injecting the Doppler scanning line, blood flow distribution can be obtained over the entire blood vessel cross-section. … II D (j-10), IID (j-9), IID (j-9),... … IID (j-9), IID (j-8),... … IIDjJ, IIDj,… … IIDj,… … IID (j + 10), IID (j + 10)... … It becomes like IID (j + 10).

In other words, 64 scan lines in the same position and one staggered again 64 times. Since arterial blood flow is synchronized with the heart rate, the movement of the scan line is synchronized with the heart rate to obtain generally good reproducibility or data. Alternatively, each time the scanning line moves in synchronization with the heart rate, one frame of II or I and II can be obtained and frozen in the DSC to determine where the ultrasound beam is passing through the vessel. Blood flow measurement is performed.

As described above, in the present invention, the angle between the direction of the blood vessel and the direction of the Doppler signal detection ultrasonic beam can be accurately measured, and the position of the beam in the cross section can be checked in order to check the longitudinal section and the cross section of the blood vessel. Accurate blood flow can be measured.

In particular, since the straight line showing the direction of the ultrasonic doppler beam displayed simultaneously with the tomographic phase of II is driven by the same oscillator, the blood flow of the specified part within the cross section is measured correctly. If you use a completely different thing, no error occurs.

In the present invention, since the scanning line for scanning the Doppler signal can be scanned, when the doctor places the target tomogram on the display in real time, the blood flow is automatically calculated. It is displayed every time, and furthermore, the value is confirmed that there is actually a blood flow of the portion described on the real-time tomography, so that a very accurate blood flow measurement can be performed.

As a result, the measurement of blood flow rate or blood flow volume in the arteriovenous vein which has not been possible in the past can be performed easily clinically, and the value of medical diagnosis is very large.

Claims (1)

A first vibrator array formed by arranging a plurality of ultrasonic vibrators in a predetermined direction, and substantially perpendicular to the first vibrator array, wherein the ultrasonic wave direction is acute with the ultrasonic wave direction of the first vibrator array. And a second vibrator array formed by arranging ultrasonic vibrators of the first and second and second signal processing circuits respectively processing signals received by the first and second vibrator arrays. Diagnostic device.

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