JPS6379649A - Embryo vitiation treatment 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 (Industrial Application Field) The present invention relates to a medical ultrasound device, and more specifically, it extracts and identifies an embryo that has developed due to an unwanted pregnancy, and irradiates focused ultrasound toward the embryo. The present invention relates to a device for selectively disabling.

(Prior Art) Generally, when a woman has an unwanted pregnancy, an induced abortion is performed. In such artificial abortions, mechanical treatment using predetermined tools or treatment with medicine is usually used, but these methods are not preferred as they may damage the mother's body.

By the way, conventionally, a device that heats or incinerates living tissue at a desired location using focused ultrasonic waves is known as, for example, an ultrasonic surgical device. It is also known that in the ultrasound imaging apparatus, diagnosis of a desired region using B-mode display, presence or absence of a fetus, diagnosis of abnormalities thereof, etc. are performed using the Doppler method.

The present inventors have considered the possibility of applying a B-mode + pulsed Doppler type ultrasonic diagnostic device as a method of abortion when an unwanted pregnancy occurs.

That is, an attempt was made to consider whether or not the intended purpose could be achieved by using the g position to identify the target embryo and then annihilating the embryo with focused ultrasound. However, we came to the conclusion that this method is not the optimal method. One of the reasons for this is the problem of operability. B mode is
It is a tomographic scan (tomography) and is blind in the thickness direction (y direction) of the tomographic plane. Therefore, in B mode, G
Even if S (Gestation 5ack) is discovered and a "blinking object" or "Doppler signal source" within it can be identified as an embryo, it will not be easy to continue observing the fetal heart. After all, observation of the fetal mind is done while holding the probe and looking at the display. Moreover, B
mode, when you momentarily lose sight of the fetal Doppler, you cannot tell in which direction it has shifted in the y direction. For this reason, the trial and error method is used to search for fetal Doppler.
It is extremely difficult to perform this operation and each of the above operations in parallel. This is the biggest drawback of tomography. Ideally, three-dimensional understanding would be required for fetal Doppler tracking, but with the current 8-mode method, this can be solved by increasing the length of the sample volume in the Z direction (depth direction). . That is, the problem is θ (x direction) and φ (
y direction), and unless a method is used to view these two directions at the same time, it is of no use.

On the other hand, in the so-called cat's-eye beam pattern formed by the one-dimensional linear array transducer used for current phased array sector scans and switched array linear scans, the beam pattern of 0 (x direction) and φ (y direction) is It is not possible to focus in both directions at the same time. For this reason, it is not preferable to use the current array as a means for ultrasonically incinerating the embryonic heart, as this will also damage the surrounding tissue (on the mother's body side).

(Problems to be Solved by the Invention) The present invention has been made based on the above findings, and its purpose is to provide a device for disabling an embryo generated during pregnancy without invading the mother's body. There is a particular thing.

(Means for Solving the Problems) The embryo invalidation processing device of the present invention that achieves the above object selectively extracts and identifies echoes having a characteristic Doppler shift derived from the heartbeat of the embryo by ultrasonic irradiation. , is configured to apply aggressive, powerful ultrasound waves to the echo source.

(Example) Hereinafter, the present invention will be explained in detail with reference to the drawings.

FIG. 1 is a configuration diagram showing an embodiment of the present invention. In the figure, a probe 1 is connected to a B-mode drive unit 4 and a pulsed Doppler drive unit 5 through a transmission/reception unit 3 of an imager 2, and the B-mode output signal is sent to a CRT display 6. Further, the pulsed Doppler output signal is given to an envelope correlator 7, a speaker 8, headphones 9, etc. The transmitting/receiving section, each driving section, display, etc. are controlled by a control section 10. Each of the above-mentioned devices including the probe 1 etc.
: Ge5tation 5ack, 14 is embryonic heart)
coherent ultrasound energy (CW irradiation for CW Doppler) or pulsed coherent ultrasound energy (time between pulses for pulsed Doppler, whether or not B mode and M mode are used together) (PR
F) means for irradiating a specified transmission wave) for the purpose of exploration, receiving echoes from the embryo 11 in response to this irradiation, and detecting from among the echoes originating from the embryo's heartbeat. means for selectively extracting and identifying echoes having a Dobra shift. A sound ray 1a for pulsed Doppler operation in the probe 1 is fixed at the front. Further, the sampling point is fixed at the focal point of a probe 20, which will be described later. Furthermore, when the B-mode ecogram is displayed on the display 6, a mouth mark 15 indicating a sample point is displayed at a predetermined position on the screen. The probe 20 has θ,
It is a concave, large-diameter, wave-transmission-only element with sharp focuses on each of the φ and 2 surfaces, and is integrally fixed to the probe 1 and connected to the high-output oscillator 21. High output oscillator 21
(100W class CW output generator) is controlled on/off by a switch 22. The circuit consisting of the probe 20, high-power oscillator 21, etc. has a wavefront that focuses on the source of the echo (embryonic heart 13) identified by the probe 1 etc. It constitutes a means for generating coherent, pulse-like, burst-like (essentially intermittent), or continuous-wave strong ultrasonic waves.

The above-mentioned coherent strong ultrasound for attack purposes refers to pure CW, and the incoherent strong ultrasound for attack purposes refers to modulated waves (CW@FHL). It refers to sound waves).

Note that the probes 1 and 20 are normally used for the main purpose of thermally protecting the mother body 12 (also to ensure that the extremely concave surface of the probe 20 fits the belly of the mother body 12). Installed via bag or oil jelly standoffs 23.

In the above configuration, a B-mode echogram is displayed on the display 6, and a tick mark 15 is displayed at a predetermined location on the front, so search for the beating embryonic heart 14 within the tick mark 15. The relationship between the tentacle 1 and the target object (the belly of the mother body 12) is determined. Heartbeat can be detected using the 8-mode display shown above.

Next, confirm that it is the desired embryonic heart using the pulse analyzer. This is performed using headphones 9 or speakers 8 (you can hear the characteristic sound of thump, thump). Furthermore, in order to improve the accuracy of confirming heartbeat, it is preferable that the autocorrelator 7 also uses observation of the autocorrelation of the envelope of the Doppler signal. At this time, the integration time constant of the phase rA function is set to about 2 to 3 seconds. If periodicity is proven, a high correlation value will appear at a point on the time difference axis that corresponds to the period. Generally, the relative height of the first local maximum of the autocorrelation of the envelope of the Doppler signal of the embryonic heart to the origin is 70~
It is 80% or more. Therefore, if it is lower than that, it is suspicious. As described above, after the embryonic heart has been identified, the switch 22 is turned on and the probe 20 generates powerful ultrasonic waves. The focus of the probe 20 is set to be sharp in each of the θ, φ, and Z planes, and to coincide with the embryonic heart 14.
The embryonic heart 14 is reliably incinerated by the ultrasonic waves from the probe 20. The result of this ultrasonic irradiation can be confirmed on the display 7, headphones 9, speaker 8, etc.

In the above embodiment, the probes 1 and 20 are mechanically integrated, the sound ray 18 for the pulsed Doppler operation of the corresponding imager measurement is in front, and the sample point is at the focus formed by the probe 20. However, instead of these configurations, the attack focus of the probe 20 can be mechanically or electronically (phased array) two-dimensionally fixed in each of the 0, φ, and 2 planes. Alternatively, it may be varied three-dimensionally and the Doppler sample points may be linked. According to such a configuration, operability is further improved.

Furthermore, the probe 20 may have an annual phased array configuration. In this case, the configuration of the array surface can be made planar, and the contact with the base body 12 can be ensured, so there is no need for an ice bag, etc. (No problems will occur.)

FIG. 2 is a configuration diagram showing another embodiment of the present invention. Since each reference numeral in FIG. 2 has the same meaning as in FIG. 1, redundant explanation will be omitted here. In FIG. 2, the imager 31 has a transmitter/receiver section 3 and an 8-mode drive section 4 connected to the probe 1, and a CW Doppler drive section 32 is provided separately from these. Probe 33. and 33b are shaped like a donut vertically divided into two halves, and are connected to the CW Doppler drive unit 32 or 33b via the switch 34.
Connected to high output oscillator 21. Probes 338 and 33
．． When the probe 33a is connected to the CW Doppler drive section 32, the probe 33a operates as a transmitting probe, and the probe 338 operates as a receiving probe.

The focal points of these two transmitting and receiving probes sharply coincide with the θ, φ and 2 planes at the sample point (embryonic heart 14). On the other hand, when the probes 33a and 33b are connected to the high-power oscillator 21, both irradiate ultrasonic waves sharply focused on the θ, φ and 2 planes toward the target object (embryonic heart 14). The structure is as follows.

The switch 22 is configured to be switched in conjunction with the switch 34, and the probe 33. and 33. is high output oscillator 2
It is on when it is on the 1 side, and off when it is not.

In such a configuration, probes 1.33a and 33.
is installed on the mother body 12 in the same way as the embodiment shown in FIG. 1, and a B-mode echogram is displayed on the display 6. At this time, a mouth mark 15 indicating a sample point is displayed at a predetermined position on the screen.

Moreover, the probes 33a and 33. When the CW Doppler beam is on the side of the CW Doppler axillary section 32, the cross section of both the Doppler transmitting and receiving beams occurs at the focus of the probes 33a and 33b. Therefore,
The detected heartbeat is always at the above focus, and the target embryonic heart 14 can be reliably identified. embryonic heart 14
After identifying the probes 33 and 3, switch 34 is turned on.
3. A focused powerful ultrasound wave is directed toward the embryonic heart 14 Q4. As a result, the embryonic heart 14 is burned to death.

Note that in the above embodiment, the probe 33. is the sending side,
Furthermore, although the probe 33b is used as the receiving side, both may be used for both transmission and reception. Also, if you are an imager, use M mode.
You may also have one set.

At this time, in order to realize the coexistence of CW Doppler and this imager, it is necessary to devise ways to prevent the occupied frequency bands of both from overlapping. For example, a time division method may be used in which a time difference is provided between the two operations, or the probe 1 may be set at 3.5 HIIZ, and the probes 338 and 33b may be set at 28 IIZ.

FIG. 3 is a configuration diagram showing still another embodiment of the present invention. Since each reference numeral in FIG. 3 has the same meaning as in FIG. 1, a redundant explanation of this and the iron will be omitted. In FIG. 3, element 41. and 41b.
has a ring array configuration capable of two-dimensional beam forming, and the C-mode drive unit 43 of the imager 42
connected to. The probe 41, the C mode drive unit 43, etc.
The configuration is such that both the 0 and φ directions are combined, that is, the azimuth angle of the beam is directed to the space formed by both the θ and φ directions. The C-mode drive unit 43 includes a wave receiving amplifier, a range gate, a waveform memory for the extraction section, and an arithmetic processing unit (all of which are not shown) connected to each element of the probe 41, and is capable of performing C-mode exploration, In other words, the echo source distribution in the cross section perpendicular to the sound ray in depth (two directions) (it becomes a spherical slice, but can be approximately considered as a plane orthogonal to the center line) is mapped. There is. The range (depth) of the range game 1 to above coincides with the focus of the probe 20.

In such a configuration, the waveform memory stores a signal in a section where an echo is detected by the element 41b (a section regulated by the range gate) every time one wave is transmitted omnidirectionally from the element 41a. is stored at 8°, and then
An arithmetic processing unit reads the received signals of the elements from the waveform memory corresponding to the number of elements, and performs image reconstruction processing such as two-dimensional Fourier transform and Fresnel transform to obtain an image. This image coincides with the focus of the probe 20. Here, in order for the probe 41 side to focus on the central axis, the signals of all the elements need only be modified as they are, so such received beams are separately synthesized in the Doppler drive unit in the imager. You should always give it. Therefore, in this case, selectivity in one direction on the central axis is regulated by the waveform of the range gate that is applied. FIG. 4 shows an example of a C-mode image reconstructed by the above reconstruction process. Center marker 41 on the image
Alternatively, the intersection of the θ and φ axes is displayed, and the focus of the probe 20 (attack focus) is made to coincide with this. At this time, the depth of the range gate can be adjusted back and forth (up and down) using the control cage. Also, the length of the range gate (the thickness of the slice surface) is 1, which corresponds to the band width of the system (corresponds to the reciprocal of the band width)
It is possible to make it as narrow as possible, so you can make it as narrow as you like.

It goes without saying that in the present invention, the imager associated with the probe 1 of the embodiment shown in FIGS. 1 and 2 may be a phased array or a mechanical sector. or,
Depending on the case, it may be a near scan. just,
In the case of a mechanical sector, it is possible to focus in both the θ and φ directions like a pencil beam, so it is certainly more advantageous than a phased array. Furthermore, if a large-diameter annular array is used and equipped with a mechanical night sector that can be swung slowly and in both the θ and φ directions, the imaging and Doppler transducers can be burned out. It can also be used as a killing transmitter.

(Effects of the Invention) As explained above, according to the embryo invalidation processing device of the present invention, an echo having a characteristic Doppler shift derived from the heartbeat of the embryo is selectively extracted and identified by ultrasonic irradiation, and the echo By applying aggressive, powerful ultrasound waves to the source, it is possible to nullify the embryo generated during pregnancy without invading the mother's body.

[Brief explanation of the drawing]

FIG. 1 is a configuration diagram according to an embodiment of the present invention, and FIG.
FIG. 3 is a block diagram of still another embodiment of the present invention, and FIG. 4 is a diagram showing a display in the embodiment of FIG. 3. 1.20.33 and 41... probe, 2.31 and 4
2... Imager, 6... Display, 7...
Self-completion, 8...Speaker, 9...Headphones, 11...Candy bud, 12-ff1 body, 13-Gesta
t:on 5ack, 14...embryonic heart, 21...high output oscillator, 22 and 34...switch. M1 figure

Claims (5)

[Claims] (1) A means for irradiating a target embryo with coherent or pulsed coherent ultrasound energy for the purpose of exploration, and receiving echoes from the target embryo in response to the irradiation, and detecting the embryo from among the echoes. It has a means for selectively extracting and identifying echoes having a characteristic Doppler shift originating from heartbeats, and a wavefront focused on the source of the identified echoes, in particular for coherent or incoherent attack purposes. An embryo nullification processing device characterized by comprising: means for generating strong ultrasonic waves in the form of pulses, bursts, or continuous waves; and control means for controlling the operations of each of the means. (2) The embryo nullification processing device according to claim 1, wherein the powerful ultrasonic wave generating means is comprised of a fixed wavefront system and mechanical positioning or mechanical steering. (3) The embryo nullification processing device according to claim 1, wherein the powerful ultrasonic wave generation means is comprised of a variable phased array system. (4) The embryo invalidation process according to claim 1, wherein the means for selectively extracting and identifying echoes having a Doppler shift includes means for detecting pulsatility characteristic of the embryonic heart. Device. (5) The embryo invalidation processing device according to claim 4, wherein the pulsatility detection means includes a peak detection circuit for autocorrelation with respect to the envelope of the Doppler signal.