JPS59101143A - Ultrasonic measuring apparatus - Google Patents

Abstract

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

Description

[Detailed Description of the Invention] (Field of the Invention) The present invention relates to a device that uses an ultrasonic beam to apply various types of effects to the inside of a medium, such as a living body, using h1 measurements, and particularly relates to a device that uses ultrasonic beams to apply various effects based on h1 measurements on the inside of a medium such as a living body. The present invention relates to a method of operation for each measurement pot that can be implemented for.

[Prior art to the invention]

Conventionally, devices are known that use ultrasonic waves to heat cancerous sites in living organisms, etc. 9, and devices that apply effects to living tissues such as generating cavitation and destroying cancer cells. Ultrasonic beams consisting of continuous waves (CW) or pulsed waves are used to measure the position of the area of interest on the body surface in advance using an X-ray or ultra-wave echo imaging device, and then irradiate the ultrasound beam to that area. In this case, the reference point on the body surface is set <<, and the relative position of the organ relative to the body surface shifts due to the time after meals, body position, breathing, pulse, etc., and the organ itself also shifts. The shape changes.For this reason, the relative position of the organ of interest on the body surface constantly changes.For this reason, the position of field cultivation becomes unclear, and for example, in the case of fin destruction, the cancer is not destroyed and the surrounding area is healthy cells are destroyed
This may cause some inconvenience.

In addition, we measured the dynamic dimensions of each part of the heart using a pulsed ultrasound beam (so-called M-mode meter B'll), measured the inner flow velocity of the heart chamber (I1T Doppler measurement), and
It is difficult to dynamically determine the blood flow velocity vector at a point of interest in a cardiac chamber using more than one beam at a fixed point of interest. The conventional methods used to counter this problem and their problems are described below.

First, set up the main beam for measurement such as M mode or Doppler so that it is within the scanning plane of the B mode echo beam using the reflection method.
This method is carried out while checking the position of the main beam for measurement and the position t of the point of interest on the B-mode cross-sectional image. In this case, as shown in Fig. 1, the B-mode image is produced using a mechanical or electronic method (linear, face array).

(e.g. sector) scanning transducer, and the main beam is mechanically fixed to the B-mode transducer in a specific geometrical position using another independent transducer, or 75J is connected by the link of the moving arm, and by detecting its relative position fi1t with the potentiometer of the joint joint, the position of the main beam and the region of interest is calculated by B.
It may be displayed on the mode cross-sectional image.

FIG. 1(a) shows an example in which a linear array electronic scanning probe 1 and a Doppler (M mode) probe 2 are integrally formed. Further, FIG. 1(b) shows an example in which a Doppler (M mode) probe 2 is integrated with a mechanical rotary sector scanning (B mode) probe 3. In both cases, the direction of Doppler probe 2 is 0.
It is a engineering change. Also, the first 1 (C) is a face array electronic sector scanning (B mode) search; 9'' electronic 4 43! ＞
It is connected to a Doppler (M-mode) probe 2 by an m-type link 5, and the hole array posture of both probes is detected by potentiometers located at each joint 51, 52, and 53 of the link.

Conventionally, in order to avoid the complication of using the two probe consonants mentioned above, the electronic system uses the fact that the scanning order of the scanning line can be freely set to perform B-mode scanning and Doppler (M-mode) scanning. It was devised that both parents could do this at different times. In FIG. 2(a), a part 11 of the linear array 1 is operated as a face array to form a main beam for Doppler (M mode) measurement in the direction M in the figure. FIG. 2(b) shows one of the scanning lines of the face array 4 as the measurement main beam M.
That is.

In the example shown in Fig. 2, for Doppler, M mode, etc. measurements, it is necessary to have a high number of scan line repetitions, so
A measurement raw beam scan is inserted between each scan of the mode scan line. That is, if the scanning line number is 1°2.3..., then 1
．． M, 2. M, 3. M.

. . - is scanned. Also, in the group shown in Fig. 1, for the same reason, both the B-mode and main measurement beam probes are scanned at ζ, and the respective scanning staffs are also scanned at a time interval of ζ to avoid mutual interference. .

The method described above is meaningful because it can be measured two-dimensionally on one cross section while continuously monitoring it in real time. Unfortunately, however, it has the drawback that it is not possible to fix parts in three dimensions. For this reason, the scanning repetition rate of the main measurement beam is halved when using 0 or B mode, which causes large errors in measurements of dynamic and unscrupulous instruments such as the heart. In the M mode 1 measurement, the time resolution deteriorates, and in the B mode (8), the number of scanning sets is halved or the number of frames per second is halved.

On the other hand, there are two ways to monitor the body part three-dimensionally.
Nine methods are listed in which two B-mode probes are positioned so that their respective scanning planes are perpendicular to each other. A probe for this purpose is one in which two sets of face array sector scanners are placed adjacent to the VC so that their scanning planes are perpendicular to each other,
``Misfire'' by Hyakutoshi tGJ 57 45395
r As in Japanese Patent Application No. 57-45394, concave, convex, and 1Il
There are ll-type IJ arrays that are orthogonal to each other, and face arrays that are stacked in multiple layers.

However, it is necessary to operate the two B-mode probes σ alternately for each field name, and it is difficult to add the measurement and field farming beams to this and operate the field fields sequentially by time switching.

In addition, in order to avoid the drawbacks such as a decrease in frame rate as described above, the present invention is designed to operate two or more ultrasonic beams at the same time, and to perform a full % characteristic such as making the total center frequency of each beam different. invented a method to prevent confusion by dividing received echoes according to their characteristics (Japanese Unexamined Patent Application Publication No. 1989-1999).
5-103837).

Although this method is effective, when applied to the actual human body, the frequencies that can be used are limited due to conflicting requirements such as the dependence on the mantissa, measurement depth, and idle resolution. The number is limited to about two.

For this reason, it is difficult to allocate a frequency of 34'' to each of the two orthogonal cross sections and the wave 1j constant king beam, for example.

[Purpose of the invention]

The purpose of the present invention is to connect the main ultrasonic beam for constant and different effects and the position of the region of interest three-dimensionally in real time, and to monitor the target 4Ke function of the main beam. We are providing revised sound equipment.

[Key points of the invention]

The present invention provides at least two reflected ultrasonic waves B that intersect with each other.
Introducing the mode cross-sectional image and the raw beam at a clear position relative to at least one of them, and assigning different frequencies to the main beam and the image system and operating them simultaneously, the 21tir plane of the image system is mutually 11 .1. By operating it on a rock between the rocks, etc., the main beam's essential pouring ability is not deteriorated.
These three beams can be operated simultaneously and continuously in real time to achieve the above objective.

[Embodiment 1] Hereinafter, 11 examples will be explained. For the 11i3 unit, there is one main beam, two beams are used for the image scanning, and the angles of the scanning pieces are right angles, but the invention is not limited to this.

The main beam is emitted into a medium such as a material, and is
It may also be possible to add a specific effect, such as heating a specific area of interest using waves, continuous waves, or pulse waves, or using cavitation to destroy cancer cells. In addition, it may also be used to measure Doppler dish velocity using reflections from streams or pulsed pumps, to measure temperature, or to measure tissue characteristic values.

75T Each fj of the pulse known as Ura M mode
:'It may also be possible to carry out all measurements of dimensions by utilizing the reflection of the glass. It may also be used in ultrasound-wave CT that utilizes all pulse transmission. The main purpose of this beam is to perform the original action and the 61+1 constant, and is hereinafter abbreviated as the king beam.

The image scanning surface is known as a B-mode image, which emits a pulse wave in one scanning line and scans a bright line in that direction on the CRT in synchronization with the emission. The reflected waves from each depth correspond to 1iJ1 at the time of reception,
It emits light on the f4 beam and then sequentially deflects the scanning line within a specific plane to obtain a cross-sectional image.
○Specifically, as mentioned above, there is a method that mechanically scans the Washi-wave transformer, and an all-electronic drive element group of an array consisting of a large number of divided water molecules. The direction of the combined beam is deflected by controlling the temporal phase of a linear array that forms the scanning direction with a group of parallel scanning lines and a drive stage element, and its deflection angle k l1fr4
Any system such as a sector array in which the scan surface is configured by a group of radial scan lines may be used. Figure 3(a)
is the first embodiment of the present invention, the probe 2 has a main beam M
are formed by the probes 4 and 6 on the image scanning plane BI+B2. They are each linked by a mechanical arm 5, and the nodes at the joints of the arms can freely rotate, and the intersection angles are detected by potentiometers 51 to 55 provided at the nodes. The probes 4 and 6 are attached to the arm so that their scanning directions are perpendicular to each other. FIG. 3(b) shows a second embodiment of Fi,
This is an example using a probe 7 in which probes 4 and 6 are integrally formed. The structure of the probe 7 can be approximated by integrating two transducers adjacent to each other so that the scanning direction is 90 different.
According to 7-45395 and %Kao 57-45394, a more complete version can be obtained. Figure 3 (a) + (b)
) is the main beam M at the image scanning plane B, and all the probes are attached to the arm link 5 as shown in FIG. Figure 4 (a) + (b) shows that the main beam M is on the intersection line of the image scanning planes B, B2. 8 is a main beam and an image scanning plane B using the same method as the probe 4 in FIG. 2(b).
Form into 2. As explained in FIG. 3, the probes 4 and 8 are attached to the arm link so that the probe B1 passes through the position B22t.

In the illustrated example, the intersection line and M are selected to coincide with the center scanning line of B2, but are not limited to the center.

FIG. 4(b) shows an example in which a main beam probe is further added to the probe 7 of FIG. 3(b) and integrated, and a specific example of the structure of the transducer will be explained with reference to FIG. 5. In FIG. 4(b), the cross lines of B+ and Bt and M coincide with the central scanning line of BI+B2, but they do not necessarily have to be the middle scanning line. A specific example of the construction of the probe 9 shown in FIG. 4(b) is shown in FIG. 5. FIG. I threw the child away and the smell mentioned above was 1μ Showa 5
Similarly to No. 7-45394, two sets of arrays 91.92 or 93.94 are arranged orthogonally on the back-facing absorber 95°96, and the counterfeits are made at the intersection. Furthermore, transducers 97 or 98 for the main beam of the present invention are laminated as a third layer, and when the main beam is used for measurement, the d transducers 97 and 98 may be of small diameter. For commercial purposes, a large diameter one is required. In that case, as shown in FIG. 5(c), two
Linear array ioo, iot &1 director of pair 9
, or a large-diameter transformer 1 as shown in Figure 5(d).
A window hole is provided in the center of 02 and the window hole is inserted into the hole as shown in Fig. 5(a).

Recesses 93, 94, 96 or 91, 92° 95 similar to those in (b) may be embedded.

The array shown in FIGS. 5(a), 5(b), and 5(d) may perform sector scanning using its own curvature, or may use the principle of a faced array to further widen the travel angle. Valley transducers can be made of PZT, organic piezoelectric materials, and the like.

Doppler blood flow velocity measurement using continuous waves, Doppler blood flow velocity measurement using Luss waves, M mode (11 mode, tissue characteristic measurement, etc.) where the main beam is mainly measured When the purpose of the main beam is heating or destruction of malignant tissue, etc., the 5th section 1 ((ri l ( A configuration such as a) is often used, and continuous waves or intermittent waves are often used.

When the main beam is a continuous wave or an intermittent wave, the time resolution becomes infinite, but the positional resolution in the depth direction disappears. However, since the frequency box has an extremely narrow band, it can be separated from the video frequency by a difference, and interference prevention means such as a filter can be easily installed to prevent mutual interference and interference.

In the case f3 where the main beam uses the reflected wave by the pulse wave, the spectrum of the main beam is at the center frequency fin.
It will be a wide band that spreads on both sides. Also, the pulse reciprocates to the maximum depth that the main beam can reach [ij cannot emit the next pulse, so if this reciprocating time is 2t, the maximum time resolution is 1'j2t. The spatial resolution in the depth direction is Cr, which is the product of the Noculus width r and the speed of sound C. When the main beam is operated at maximum time efficiency, the maximum opening arc minute is 1
- In order to obtain blood flow velocities and M-mode images that change to fJIU, it is necessary to operate at a return rate. This can be achieved by distinguishing the main beam M from the image scanning beams B, B2, by adding characteristics such as changing the center frequency, and separating them using interference prevention means such as a bandpass filter. It is possible to operate the beam M with maximum time utilization efficiency. Image n, B2 scanning line also fm
% at different center frequencies fl+f2 and different from each other.
Similarity, mixed aI with a bandpass filter as well! If /J is stopped, each can operate at maximum efficiency for the maximum time. However, when the live beam is used for measurements in human tissue,
fm+fnf2 is subject to practical limitations. That is, in order to improve the spatial depth resolution, each (+i
The castle must be spacious. Also, in order to prevent mutual interference, each band must not be M'fx. For this reason, assuming that fm>fl>f2, fm and f should not be significantly different from each other. On the other hand, since the resolution in the lateral direction perpendicular to the direction of removal is inversely proportional to the number of Jjj grains, there is a certain minimum slope wave number fL in order to make time-saving resolution a must. That is, f L < fm, f, il, &
:j: No. It is also known that in living tissue, the attenuation of ultrasonic waves changes exponentially with the depth (channel length), and that the attenuation coefficient α is proportional to the frequency (α−βf). Therefore, once the maximum depth for 11'' of the main beam is determined, the frequency must be less than a certain maximum value fH, that is, fH>fm1fHf2, in order to avoid attenuation. Therefore, in actual applications, there are cases where at most only about two frequencies can be taken between fL and fH. Therefore, it is not possible to randomly select three frequencies frnt f+ + f2. In this case, the present invention assigns fm to the main beam M and ll! Vif is assigned to BI+B2 for 11 images, and BITB2 is scanned by time share (time IN, switching). Furthermore, if the movement of the object is slow or if a long tube can be used to obtain the effect of the main beam, the 1i4J utilization rate for the main beam should be set to 100% or less, and the remaining time should be set to iif+i. Image river scanning may also be used. Even in this case, when the main beam is used, the 1'flJ utilization rate is different from the other ii! It is desirable that it be equal to or greater than the aThllJ4 utilization rate of the II image scan.

Furthermore, for image scanning, the time allocation rate can be halved by using the technology described in Japanese Patent Application Laid-Open No. 55-52746, which simultaneously receives multiple scanning lines in the vicinity of one scanning transmission. However, it is also possible to avoid reducing the number of scanning lines.

〔Effect of the invention〕

According to the present invention, when performing field farming or measuring a medium using an ultrasonic beam, the operation is performed while confirming the position of the beam and/or field farming river fish/measuring point in the three-dimensional medium. This makes it possible to perform accurate positioning and ensure that the medium is [i,
There is an effect that the movement can be performed following the target part even when the f181 is fluctuating.

[Brief explanation of the drawing]

FIGS. 1 and 2 are explanatory diagrams of the conventional system, and FIG. 3 is an explanatory diagram of the conventional method. FIG. 4 is a schematic diagram of the embodiment of the present invention, and FIG. 5 is a configuration diagram in which the main beam and the transducer for direct scanning of the direct plane 2b1 surface 1iiiI are integrated. (a) <b) Figure 3 %4 Figure (b) 7 (C), (d) Figure S

Claims (7)

[Claims] (1) In a device that uses ultrasonic sound to measure the inside of a medium or perform another action on the inside of the medium, a means for generating an ultrasonic beam (hereinafter referred to as the main beam) for the measurement or another action, and a non-zero beam. means for obtaining cross-sectional images by at least two reflected ultrasound waves intersecting at the father angle, and maintaining the positional relationship between the main beam and the at least two cross-sections at -2, or constantly detecting the positional relationship; 1. A device for measuring or acting on ultra-high waves, characterized in that it is provided with a means for measuring. (2) the main beam is driven by a continuous wave or a pulsed wave;
The special WFB ice range according to item 1, wherein the scanning lines of the at least two cross-sectional images are driven in a time-sharing manner with respect to each other and use a different hourglass shape or a different frequency from that for the main beam. Side legs or other acting devices that rely on sound waves. (3) The main beam is driven at the same frequency or the same waveform as the scanning line of one of the at least two -r-plane images and in a time-sharing manner with respect to the scanning line of the other cross-sectional image, and the scanning line of the other cross-sectional image is Ultrasonic measurement or other functional device according to claim 1, characterized in that it is driven at a different frequency or a different waveform than one scanning line. (4) Claims 1 to 3, characterized in that the time utilization rate of the main beam is greater than or equal to the time utilization rate of the scanning line of any of the above-mentioned cross-sectional images. Ultrasonic measurement or other action device according to any of the paragraphs. (5) The ultrasonic wave according to any one of claims 1 to 4, wherein the main beam is provided within the scanning plane of any one of the at least two cross-sectional images. Measuring or other acting devices. (6) Measurement by ultrasonic waves according to any one of paragraphs 1 to 4, characterized in that the main beam is located on the intersection line of the at least two cross-sectional images; Separate action device. (7) Ultrasonic measurement or other action device according to any one of claims 1 to 67U of the patent application, characterized in that the scanning planes of the at least two cross-sectional images are perpendicular to each other.