JPH09122139A - Ultrasonic treatment device - Google Patents

Abstract

PROBLEM TO BE SOLVED: To provide a small-sized ultrasonic treatment device capable of being used through a rectum as well and varying the focus point of ultrasonic impulse waves and to improve the convergence efficiency of the ultrasonic impulse waves at a treatment object part. SOLUTION: An ultrasonic vibrator 1 and a reflector probe 5 provided with a mirror part 4 on a tip are provided so as to hold the treatment object part 6 therebetween. An ultrasonic treatment device 2 is inserted through the rectum and the reflector probe 5 is inserted through an urethra. By positioning the mirror for ultrasonic wave reflection of the reflector probe 5 in an area where the ultrasonic impulse waves are radiated, the ultrasonic impulse waves are converged at the position closer to the focus point (f1) provided in the single plate type ultrasonic vibrator 1. Further, when the mirror part 4 is rotated, finer focus point control is made possible. By using a reflector, the propagation of the ultrasonic impulse waves to the back side part of the reflector is eliminated and the treatment object part 6 is efficiently cauterized.

Description

Detailed Description of the Invention

[0001]

BACKGROUND OF THE INVENTION 1. Field of the Invention The present invention relates to an ultrasonic therapeutic apparatus, and more particularly to an ultrasonic therapeutic device suitable for concentrating an ultrasonic shock wave on a treatment target site and performing treatment.

[0002]

2. Description of the Related Art Japanese Patent Application Laid-Open No. 63-1
No. 11852 (Reference 1) and Japanese Patent Publication No. 42-14379.
A device according to the proposal of Japanese Patent Publication (Reference 2) is known. In this type of device, as shown in, for example, Document 1, generally one or more ultrasonic transducers including piezoelectric elements are used, and ultrasonic shock waves emitted by the ultrasonic transducers are concentrated to The stone is destroyed and the tumor site is cauterized. On the other hand, in recent years, as a treatment method for benign prostatic hyperplasia (hereinafter, also abbreviated as BPH), a treatment method in which an ultrasonic treatment device is inserted transrectally and cauterize BPH is being established.

[0003]

However, the conventional apparatus can be used to perform treatment by concentrating ultrasonic shock waves on the treatment target site, but when viewed from the following points, There is still room for improvement. For example, Document 1 discloses a technique for changing the position of the focal point where the ultrasonic wave converges at one point, but the device becomes large in scale because the focus point of the ultrasonic shock wave is variable. So also
As a result of such a large scale, it is difficult to use it rectally, and in particular, for example, BPH rectally as described above.
It is difficult to respond to the use and application such as treatment of. In addition, the ultrasonic shock wave is not efficiently converted into thermal energy at the treatment target site. In this respect, in the treatment using therapeutic ultrasonic waves, the ability has not been sufficiently drawn out, so there is room for improvement in terms of the improvement of the convergence efficiency of ultrasonic shock waves.

The present invention realizes a small-sized ultrasonic therapy apparatus which can be used transrectally and which can change the focus point of an ultrasonic shock wave, and the efficiency of focusing the ultrasonic shock wave. The aim is to obtain an ultrasonic therapy device that can be improved.

[0005]

The ultrasonic treatment apparatus of the present invention is characterized in that an ultrasonic treatment oscillator and an ultrasonic reflection reflector are provided so as to sandwich a treatment target region. In the present invention, it has an ultrasonic treatment oscillator and an ultrasonic reflection reflector so as to sandwich the treatment target region, and is suitable for performing treatment by concentrating ultrasonic shock waves from the body to the treatment target region. Can be used. This ultrasonic treatment device is equipped with an ultrasonic treatment transducer and an ultrasonic reflection reflector so as to sandwich the treatment target region. If possible, realize a device that can. In addition, by using the ultrasonic reflection reflector so as to face (or nearly face) the ultrasonic treatment oscillator so as to sandwich the treatment target region, the ultrasonic wave to the back side region of the ultrasonic reflection reflector is used. Propagation of shock waves is eliminated, and it is possible to improve the convergence efficiency of ultrasonic shock waves at the treatment target site.

[0006]

Embodiments of the present invention will be described below with reference to the drawings. FIG. 1 shows an embodiment of the present invention. The present embodiment exemplifies a case where the present invention is applied to, for example, a single-plate ultrasonic treatment apparatus, in which 1 is a fixed-focus single-plate ultrasonic transducer and 2 is a fixed-focus single-plate ultrasonic wave. An ultrasonic treatment device (apparatus) in which the vibrator 1 is incorporated at the tip is shown. Here, the ultrasonic therapeutic device 2 is driven by the drive unit 3. The drive unit 3 is capable of various outputs such as continuous wave and burst wave. A preferred use example of these will be described later.

In this example, a reflector probe having a mirror portion as a reflector for ultrasonic wave reflection, which is used in combination with the ultrasonic treatment device 2 at the tip, is also provided. In the figure, 5 indicates a reflector probe having a mirror portion 4 for reflecting ultrasonic waves at its tip. Here, the reflector probe 5 has a mirror portion 4 and a shaft 7 connected to the mirror portion 4, and these are inserted and arranged in the body together with the ultrasonic treatment device 2 during ultrasonic treatment. The figure shows
An example of the mode of use during ultrasonic treatment is also shown,
The mirror section 4 is positioned so as to sandwich the treatment target portion 6 with the single-plate ultrasonic transducer 1.

FIG. 2 shows an enlarged detail of an example of the mirror portion 4 of the reflector probe 5 arranged so as to face the single plate type ultrasonic transducer 1. In a preferred example, the mirror portion 4 can be provided with at least two curved surfaces having different curvatures (R). In the case of the example shown,
As shown in the figure, the mirror section 4 has peripheral surfaces (here, four surfaces).
Are concave mirrors having different curvature surfaces. That is, the four surfaces are concave mirrors 4-1 (curvature R
1), 4-2 (curvature R2), 4-3 (curvature R3), 4-
4 (curvature R4) (R1 ≠ R2 ≠ R3 ≠ R4) (the concave mirrors 4-3 and 4-4 on the back side of the paper surface are shown in this perspective view). Absent).

Further, the shaft 7 of the reflector probe 5 connects the mirror section 4 and a hand operation section (not shown) operated by an operator (operator). The diameter of the shaft is such that the surface of the shaft has fine irregularities so as to diffusely reflect ultrasonic shock waves. The shaft 7 and the mirror unit 4 are advanced and retracted by an operation from the hand side, and the mirror unit 4 can be rotated by rotating the shaft 7. In the case of the configuration in which the single-plate ultrasonic transducer 1 and the mirror portion 4 are provided so as to sandwich the treatment target portion 6, when the mirror portion 4 is rotated, the mirror will face the ultrasonic treatment device 2 side. Selective switching of the concave mirror (4-1 to 4-4) surfaces of the section is performed along with the rotation thereof.

The ultrasonic therapeutic device 2 and the reflector probe 5 using the single-plate ultrasonic vibrator 1 as the ultrasonic therapeutic vibrator according to this example are inserted into the subject by transrectal insertion of the ultrasonic therapeutic device 2. Then, the reflector probe 5 is inserted transurethrally. In FIG. 1, f1 is a focus position corresponding to the single-plate ultrasonic transducer 1 having a fixed focus,
f2 represents an example of the changed focus position when the mirror unit 4 is positioned as illustrated. The position of f1 is
It means the position of the focal point which the single-plate ultrasonic transducer 1 originally has, and the sound pressure becomes maximum there.

The above-mentioned configuration according to this embodiment is
By using this as described below, the operator can appropriately change the focus point with the single-plate type ultrasonic treatment apparatus, and can easily realize the improvement of the convergence efficiency of ultrasonic shock waves. The operation, function, and the like will be described below with reference to the usage example of FIG.

In the ultrasonic treatment, as described above, the ultrasonic treatment device 2 inserts it as a probe transrectally, and the reflector probe 5 inserts it transurethrally. In this device, ultrasonic shock waves are concentrated from the inside of the body to a target site to be treated for treatment. In this case, the ultrasonic shock wave generated from the single-plate ultrasonic transducer 1 of the ultrasonic therapeutic device 2 proceeds so as to be converged on the focus point (f1) of the single-plate ultrasonic transducer 1 having the fixed focus. However, when the mirror portion 4 of the reflector probe 5 faces the single-plate ultrasonic transducer 1 behind the treatment target portion 6 in the ultrasonic beam radiation direction as shown in FIG. 1, the ultrasonic shock wave is The light is reflected by the mirror unit 4 at a position in front of the focus point (f1) and converges on the treatment target site 6 at a position (f2) closer to the focus point (f1).

Therefore, even when the site at such a position is a target as an ablation site, the ultrasonic shock wave can be concentrated from the inside of the body to the treatment target site 6 and cauterization can be performed. In this case, the ultrasonic shock wave does not propagate to the back side portion of the mirror portion 4, and the target treatment target portion 6 can be cauterized efficiently. The improvement (higher efficiency) of the convergence efficiency of ultrasonic shock waves at the relevant treatment target site contributes to the full extraction and exertion of the ability of the treatment using the treatment ultrasonic waves.

On the other hand, when it is desired to converge on the original focus point (f1), this can be done as follows. For example, the reflector probe 5 is moved forward and backward (downward in the figure) or back (upward in the figure), and the ultrasonic reflection mirror of the reflector probe 5 is positioned outside the region where the ultrasonic shock waves are emitted. That is, the surgeon
The mirror unit 4 may be operated by the hand operation unit so as to move to a position deviated from the ultrasonic shock wave, and it is of course possible to use in this way. Ultrasonic treatment for the cauterization position) can also be performed.

In this way, when the single-plate ultrasonic transducer 1 and the mirror portion 4 are provided so as to sandwich the treatment target region 6, even in the single-plate ultrasonic transducer 1 having a fixed focus, the convergence position is set to the unique focus point (f1). ) Can be changed to a position other than. According to this, it is possible to avoid making the device bulky because the focus point of the ultrasonic shock wave is variable, and it becomes difficult to use it transrectally, and even when the BHP is directly treated, the focus point And a device capable of controlling the ablation range with a simple configuration can be realized.

Further, when it is desired to change the focus point,
By rotating the hand operation part of the reflector probe 5, the shaft 7 can be rotated and the mirror part 4 can be rotated so as to switch to an optimum one of the plurality of concave mirror surfaces set in advance. This allows
Here, four concave mirrors 4-1 and 4 having different curvatures are used.
It is possible to reflect the ultrasonic shock wave by the concave mirror selected from any of −2, 4-3, and 4-4, and thus the focus point can be made variable. Further, in that case, the cauterization site can be variously changed by changing the curved surface shape of the ultrasonic reflection mirror serving as the reflector, but this is not accompanied by replacement of the once inserted reflector probe 5 or the like. It is also possible to control the focus point more freely, and it is also easier to control the ablation range more freely. Even in this respect, the ablation range can be controlled with a simple configuration, and it is small, It is possible to realize an ultrasonic therapeutic apparatus that can be used transrectally and that can change the focus point of an ultrasonic shock wave.

(1) According to the present embodiment, the ultrasonic treatment can be satisfactorily performed as described above, and in particular, it is suitable for performing the treatment by concentrating the ultrasonic shock waves from the body to the treatment target site. Will be things. In this example, the ultrasonic reflection mirror of the reflector probe 5 is positioned in the area where the ultrasonic shock waves are radiated, so that the ultrasonic shock waves are closer to the focus point (f1) of the single-plate ultrasonic vibrator 1. Can be converged and the focus point can be changed. (2) Further, by rotating the mirror unit 4, finer focus point control becomes possible. (3) Further, even when the reflector probe 5 is moved to the front side (downward in FIG. 1), the shaft 7 is positioned in the ultrasonic shock wave at this time, but the shaft 7 has a small diameter and the ultrasonic wave Since the ultrasonic shock wave is diffusely reflected on the surface of the structure having fine unevenness so as to diffusely reflect the shock wave, the influence of the shaft is hardly generated. (4) Further, if the drive unit 3 drives with a burst wave, a standing wave may be generated between the reflector probe 5 and the ultrasonic therapy device 2 by radiating the burst wave from the ultrasonic therapy device 2. It can be prevented. (5) Further, the focusing efficiency of ultrasonic shock waves at the treatment target site can be improved (increased in efficiency), and the use of the reflector eliminates the propagation of the ultrasonic shock waves to the back side region of the reflector, and the treatment target can be efficiently treated. Can cauterize part 6.

In addition to the above, the present embodiment can be variously modified and changed. [Modification 1 of First Embodiment] For example, the present invention is not limited to the above-described first embodiment, but a single-plate type ultrasonic transducer used in an ultrasonic treatment apparatus is used as a therapeutic transducer. It is needless to say that the same action and effect can be obtained by changing from the array type to the array type. Further, the application site is not limited to BPH, and can be used for treating tumors of other organs.

Next, another embodiment (second embodiment) will be described. The present embodiment is an example of a case in which a curved portion that changes the direction and direction of the mirror provided in the ultrasonic reflection reflector is further provided, and is described in the above-described embodiment (first embodiment). In addition to the above-mentioned aim similar to that described above, further, even if there is a portion that is relatively sensitive to ultrasonic shock waves as a normal portion between the treatment device and the treatment target portion, it does not stimulate the target treatment target. It aims to efficiently focus ultrasonic shock waves on a part.

FIG. 3 shows the present embodiment and also shows an example of a usage mode. The basic configuration is the same as that of the first embodiment, and the main differences from the first embodiment and the main parts of the present embodiment will be described below. Also in this embodiment, the ultrasonic therapeutic device 2 is the same as that of the first embodiment. Similarly, the tip portion of the reflector probe 5 is a concave mirror (4-1, 4-2, 4-3, 4-4) having different curvatures, and has a mirror portion 4 having four surfaces. Has become. Therefore, the same applies to the case where the reflector for ultrasonic wave reflection is provided with concave mirrors having different curvatures.

On the other hand, a hand operation portion (not shown) has a bending operation knob having the same structure as that used in a known endoscope or the like. Then, in the present embodiment, as shown in the figure, a bending portion 8 that is operated by the knob is provided between the mirror portion 4 and the shaft 7, and an operator operates the bending operation knob. As a result, the bending portion 8 bends as shown, and the direction of the mirror portion 4 can be freely changed. Other components may be the same as those in the first embodiment.

The device according to this embodiment can be used as follows. The usage example of FIG. 3 shows a converged state of the ultrasonic shock waves when the treatment target region 6 and the normal region 9 relatively sensitive to the ultrasonic shock waves are close to each other.
In the case of such a positional relationship, according to the conventional device of the above-mentioned document, if there is a normal region relatively sensitive to ultrasonic shock waves between the treatment device and the treatment target region, it will be stimulated. However, in the case of the configuration of this example, as shown in the drawing, the operable bending portion 8 can be bent, and the direction and direction of the mirror can be changed. Therefore, here, it is also possible to radiate the ultrasonic shock wave from the ultrasonic therapeutic device 2 so as to avoid the normal region 9, and to limit the ultrasonic shock wave to the treatment target region only by the ultrasonic reflection mirror. It is possible to deal with this even with the ultrasonic treatment in the above cases.

In this case, the control of the converging position of the ultrasonic shock wave is performed by rotating the mirror portion 4 as described in the first embodiment and operating the bending knob of the hand operation portion to adjust the direction of the mirror portion 4. It is done more effectively by changing.
In this way, even if the portion sensitive to ultrasonic energy (normal portion 9) interferes with the target, the ultrasonic energy can be converged by avoiding the sensitive portion by the reflector, and also in this respect. It is possible to improve the convergence efficiency of ultrasonic shock waves. The other functions, functions, and the like are the same as those described in the first embodiment.

According to the present embodiment, in addition to the same operational effects (1) to (5) as those of the first embodiment, the ultrasonic shock wave is concentrated from the body to the treatment target site 6 for treatment. As the device according to the present invention, the treatment target region 6 to be applied
The target of can be expanded and becomes more suitable. (11) That is, even in the case of the positional relationship as shown in FIG. 3, the target treatment is performed without stimulating the normal region 9 between the ultrasonic therapeutic device 2 and the treatment target region 6 which is relatively sensitive to ultrasonic shock waves. The ultrasonic shock wave can be efficiently focused on the target region 6. Also,
Also in this case, as in the first embodiment, by using the reflector probe 5, the ultrasonic shock wave does not propagate to the back side portion of the mirror portion 4, the treatment target portion 6 can be cauterized efficiently, and the ultrasonic shock wave The convergence efficiency of
Needless to say, high efficiency can be realized.

The present embodiment (second embodiment) can also be modified or changed in various ways, including the matters already mentioned. [Modification 1 of Second Embodiment] For example, it can be implemented in the same manner as in the case of [Modification 1 of the first embodiment] described above, and the invention is not limited to the configuration example of the second embodiment. Similar effects can be obtained even if the acoustic wave transducer is changed from a single plate to an array type, and the application site is not limited to BPH but can be used for treatment of tumors of other organs.

Next, still another embodiment (third embodiment)
This will be described with reference to FIGS. 4 and 5. This embodiment also
The aim is the same as that described in the first embodiment, and further, in addition to this, the same aim as that described in the second embodiment is realized. FIG. 4 shows an example of the configuration of the mirror part, which is a main part of the ultrasonic therapy apparatus according to this embodiment.

The main part of this embodiment will be described below.
Also in this embodiment, as shown in FIG. 1 or FIG. 3, the configuration is such that an ultrasonic treatment device and an ultrasonic reflection mirror are provided so as to sandwich the treatment target region 6, and they are provided so as to face each other. The ultrasonic treatment device 2 is basically the same as that of the embodiment, and the ultrasonic treatment device 2 (not shown in FIG. 4) to be used is the same as that of the first and second embodiments. However, in this embodiment, the configuration of the mirror portion 4 at the tip of the reflector probe 5 is different as shown in FIG.
That is, in the present embodiment, the mirror section 4 has a configuration in which two mirrors 10-a and 10-b are paired, and the opening angle formed by the mirrors 10-a and 10-b is not shown. It is variable on the operation unit (hand operation unit). Even if the mirrors 10-a and 10-b here are flat surfaces,
It may be a concave surface having a relatively large curvature. Other components may be the same as those in the first embodiment.

In the present embodiment, the control of the convergent position of the ultrasonic shock wave is performed by adjusting the opening angles of the mirrors 10-a and 10-b. Other operations, functions, etc. are the same as those described in the first embodiment. According to this embodiment as well, the same effects (1) to (5) as those of the first embodiment can be obtained, and the convergence of the ultrasonic shock wave to the treatment target site can be controlled more finely.

The present embodiment (third embodiment) can also be modified or changed in various ways, including the matters already mentioned. [Modification 1 of the third embodiment] For example, a mirror 10-a,
The opening direction of 10-b may be parallel to the insertion axis (the axis of the shaft 7 of the reflector probe 5) as shown in FIG. The present invention can also be implemented in this manner.

[Modification 2 of Third Embodiment] Also in this embodiment, as shown in the second embodiment, a curved portion (8) may be provided between the mirror portion 4 and the shaft 7. Good. In this case, the same effect (11) as that of the second embodiment can be further obtained. [Modification 3 of Third Embodiment] Further, the same modification as in the case of [Modification 1 of the first embodiment] can be carried out.

Next, the examples shown in FIG.
Similarly, it uses an ultrasonic therapeutic transducer, but it can be advantageously applied in the case of an ultrasonic therapeutic apparatus that confirms the state inside the subject on an image and performs treatment by the biological action of ultrasonic waves. The purpose of this is to realize an ultrasonic treatment device that has been developed. This is based on the following considerations.

For example, in the treatment of the enlarged part of the prostate gland, which is the target site, it has already been described that a method of radiating and concentrating therapeutic ultrasonic waves to perform treatment is being established. As an apparatus configuration used in this case, an ultrasonic treatment apparatus is known which employs a configuration in which a probe of an ultrasonic diagnostic apparatus is provided with an ultrasonic transducer for treatment. Then, the acoustic emission surface of the ultrasonic transducer for treatment has a concave spherical shell shape, and thus, as already seen, the position of the focal point is a fixed focal point. The same applies to the fixed-focus single-plate ultrasonic transducer 1 illustrated in FIGS. 1 and 2), which is unique to the therapeutic ultrasonic transducer to be provided in the probe of the ultrasonic diagnostic apparatus. is there.

Therefore, the basic diagnosis and treatment procedure in this case is as follows. That is, by observing an ultrasonic tomographic image of the subject, the operator (operator) adjusts the positional relationship so that the treatment position determined by the concave shape of the therapeutic transducer and the affected area match. After that, for example, a continuous wave voltage is applied to the therapeutic oscillator to emit strong ultrasonic waves.
Then, in this case, the ultrasonic waves converge at the original focus position of the therapeutic transducer, causing protein denaturation at that position. In this way, the degenerated parts are necrotic and eventually absorbed. In this way, the enlarged prostate region, tumor, etc. are treated.

As described above, when an ultrasonic transducer for radiating therapeutic ultrasonic waves is used, the distance to the position where the sound pressure of the therapeutic transducer becomes maximum, that is, the focal length is basically Is determined by the shape of the treatment oscillator. But,
When actually used in a living body, the focal length (actual focal length) slightly changes depending on the attenuation amount of the ultrasonic waves in the living tissue. Furthermore, the amount of attenuation also differs depending on the type of tissue and individual differences among patients. Japanese Patent Laying-Open No. 4-338462 (Reference 3) discloses an ultrasonic treatment apparatus, but no such consideration is taken into consideration. Therefore, the focus position predicted in advance from the geometrical shape of the therapeutic oscillator may differ from the actual focus position. Then, in such a situation, if the treatment position is determined by relying on the focal length predicted from the geometrical shape of the treatment oscillator, the required position cannot be treated accurately, and as a result, sufficient treatment is achieved. There are cases where the effect cannot be obtained. What is desirable is to provide accurate and appropriate treatment, regardless of the amount of attenuation of ultrasonic waves in the living tissue when actually used in the living body during treatment, and also depending on the type of tissue and the patient. It is possible to detect which position (actual focus point) the therapeutic ultrasonic wave actually converges to, regardless of individual differences or the like.

Therefore, in some of the embodiments described below, improvements have been made in this respect, and the focal length (actual focal length) according to the environment in which the therapeutic oscillator is intended to be used.
The present invention aims to provide an ultrasonic therapeutic apparatus having excellent adaptability, which enables to detect an error and to treat the position appropriately and appropriately.

6 to 12 show an example of the embodiment (fourth embodiment) of the improved ultrasonic therapeutic apparatus.
The present embodiment is a preferred configuration example in the case of an ultrasonic therapeutic apparatus that visualizes information inside the subject and irradiates the subject with strong ultrasonic waves to perform treatment. Ultrasonic waves of a level that does not produce a therapeutic effect are transmitted as burst waves, the echoes reflected by the burst waves inside the subject are received, and the convergence position of the therapeutic ultrasonic waves is determined from the echoes The information is superimposed and displayed.

FIG. 6 shows an example of the configuration of an ultrasonic probe applicable to this embodiment, and corresponds to a sectional equivalent view of the ultrasonic probe 30 of FIG. In FIG. 6, reference numeral 20 denotes a rotary shaft that rotates the ultrasonic probe. In the illustrated example, the therapeutic oscillator 21 (ultrasonic therapeutic oscillator) and the diagnostic oscillator are sandwiched by the rotary shaft 1. (Diagnostic ultrasonic transducer) 22 is back-to-back. Here, the therapeutic oscillator 21 is formed of a therapeutic piezoelectric element 23 and a protective layer 24 provided on the acoustic radiation surface thereof. The acoustic emission surface has a concave shape, and the back surface of the therapeutic piezoelectric element 23 is hollow.

Further, the diagnostic oscillator 22 is formed with an acoustic lens 26 made of a filler-containing epoxy resin on the acoustic radiation surface side of the diagnostic piezoelectric element 25 and an epoxy resin mixed with a tungsten powder on the opposite side. Back braking layer 27
Have respectively. Further, although not shown in FIG. 6, a cable (coaxial cable) described later is electrically connected to each of the therapeutic piezoelectric element 23 and the diagnostic piezoelectric element 25.

FIG. 7 exemplifies the external structure of a therapeutic probe having the ultrasonic probe 30, and FIG. 8 mainly shows the outline of the components inside the main body of the therapeutic probe (of the drive system). (Outline of elements) is an example. As shown in FIG. 7, the ultrasonic probe 30 having the structure shown in FIG. 6 is fixed to the rigid shaft 31. Ultrasonic probe 30 and rigid shaft 31
Are housed in a cap 32 that also serves as an acoustic window for passing ultrasonic waves. The cap 32 is made of, for example, hard polyethylene. The inside of the cap 32 is filled with an acoustic medium. Water can be used as the acoustic medium. A valve 34 is provided at the connecting portion between the cap 32 and the main body 33 to prevent the acoustic medium filling the cap 32 from flowing out.

As shown in FIG. 8 showing the internal construction of the main body 33 of the therapeutic probe, the ultrasonic probe 30 in the cap 32 is moved forward and backward in the axial direction (movement in the left-right direction in the figure) and is rotationally driven. As for the mechanism itself, that in a known ultrasonic diagnostic apparatus may be adopted. Here, the rigid shaft 31 is fixed to the slip ring 35. Cables 36 respectively connected to the therapeutic piezoelectric element 23 and the diagnostic piezoelectric element 25 (FIG. 6) are connected to a control device (not shown in FIG. 8) via the slip ring 35.

The slip ring 35 is fixed so as to rotate together with the radial motor 37.
Then, the slip ring 35 and the radial motor 37
The base 38 holding the above is integrally inserted into the ball screw 39. The ball screw 16 is fixed to the drive shaft of the linear motor 40.

FIG. 9 shows an outline of an example of the configuration of a circuit system according to the ultrasonic therapy apparatus of this embodiment. The control device can be configured to include all or part of the circuit portion of this circuit system. As shown in FIG.
The cables 36 are electrically connected to the piezoelectric elements 23 and 25 inside the diagnostic oscillator 22, respectively, as described above. In this example, the therapeutic oscillator 21 is connected to the demultiplexing circuit 51 (first demultiplexing circuit) via the cable 36, and further passes through the demultiplexing circuit 51, and on the other hand, a therapeutic vibration for supplying a driving voltage. The child drive circuit 52 is connected, and on the other hand, it is connected to the detection circuit 53 (first detection circuit). The therapeutic oscillator drive circuit 52 is connected to the control circuit 54. Further, the first detection circuit 53 is also connected to the control circuit 54 via the focus position detection circuit 55. Here, the above-mentioned drive circuit 5 related to the therapeutic oscillator 21.
2, demultiplexing circuit 51, detection circuit 53, focus position detection circuit 5
Under the control of the control circuit 54, the system of No. 5 has the therapeutic oscillator 21.
When an ultrasonic wave of a level that does not produce a therapeutic effect is transmitted as a burst wave, the echo signal obtained by being reflected in the subject based on the burst wave is extracted, and the focus position of the therapeutic ultrasonic wave (actual focus A circuit system for detecting (position) is configured. The position information obtained thereby is used by the control circuit 54 to be displayed by being superimposed on the information inside the subject by a display device described later.

On the other hand, the cable 36 connected to the diagnostic oscillator 22 is connected to the diagnostic oscillator drive circuit 57 and the detector circuit 58 (second detector circuit) via the splitter circuit 56 (second splitter circuit). )It is connected to the. The therapeutic oscillator drive circuit 57 that supplies a drive voltage is connected to the control circuit 54.
Further, the second detection circuit 53 is also connected to the control circuit 54.

A display device 59 is connected to the control circuit 54, and in the present example, while the information inside the subject is obtained as an ultrasonic image based on the scanning of the diagnostic transducer 22, the above-mentioned information is obtained. Based on the detection information from the detection system on the therapeutic oscillator 21 side, the ultrasonic wave for treatment is always used regardless of the attenuation amount of the ultrasonic wave in the biological tissue, the type of tissue, individual difference, or the like. The control circuit 54 also controls the display of the display device 59 so as to superimpose and display on the ultrasonic image the exact position that will actually converge.

The therapeutic oscillator 21 according to the present embodiment
The determination of the actual focal length, etc. can be carried out on the basis of the following contents as its basics, and the basics will be described below. First, in the case of transmitting a burst wave of ultrasonic waves at a level that does not produce a therapeutic effect from the therapeutic oscillator 21, in a preferred example, this is applied to the extent that the therapeutic oscillator 21 does not affect the subject. It is possible to perform a method in which intense burst ultrasonic waves, that is, for example, waves of several tens of waves are radiated, and then ultrasonic waves of a shape that rests for several hundred waves or more are radiated to the subject. Here, the ultrasonic waves are reflected at discontinuous portions of acoustic impedance, which are everywhere in the subject. The reflected echo is received by a therapeutic transducer or another ultrasonic transducer adjacent to the therapeutic transducer. In this example, the reception of the burst wave is performed by the system on the therapeutic oscillator 21 side as shown in FIG.

Now, the reflected echoes come back from many places in the range where the burst waves of the ultrasonic waves pass inside the subject. However, the echoes having different phases overlap each other, so that the amplitude of the echo signal becomes small. However, at the position where the ultrasonic waves are sufficiently converged, the amplitude of the ultrasonic echo returning from that position is also large. Further, if the echoes are from the same position, the phases are the same, so the received echo signal becomes large. Thus, the focal length of the therapeutic transducer 21 can be obtained from the time from the transmission of the burst wave to the reception of a large echo signal and the speed of sound in the subject (FIG. 1).
0,11). In this case, when ultrasonic waves are used for observing the inside of the subject, it is desirable that the speed of sound used here matches the speed of sound used when generating the diagnostic image in order to further improve accuracy. Becomes

More specifically, referring to FIGS. 10, 11 and 12, the linear motor 46 shown in FIG. 8 is driven to move the base 16 on the ball screw 39. Therefore, as described above, the ultrasonic probe 30 has the structure shown in FIG.
(Fig. 8) Moves to the left and right. On the other hand, while rotating the radial motor 37, ultrasonic pulses are transmitted and received by the diagnostic transducer 22 to generate an ultrasonic image during sector scanning.

When the user (operator) finds a portion to be treated on the basis of the image, the therapeutic transducer 21 is used to perform the process for detecting the focus of the therapeutic ultrasonic wave.
A burst wave ultrasonic wave having a strength that does not produce a therapeutic effect is transmitted. In this example, the diagnostic oscillator 22 and the therapeutic oscillator 21 are back-to-back, so that the transmission is performed after the surface on the therapeutic oscillator 21 side faces the treatment site. Here, at this time, the drive circuit 5
An example of the waveform of the ultrasonic wave that is transmitted by driving the therapeutic transducer 21 with 2 is shown in the upper part (a) of FIG.

The ultrasonic wave of the above-mentioned burst wave can be transmitted by the therapeutic oscillator 21 in this way, and when such transmission is performed, an echo from the inside of the subject is detected in the therapeutic oscillator 21. The therapeutic piezoelectric element 23 converts the electric echo signal. In this example, the therapeutic piezoelectric element 2
The demultiplexing circuit 51 connected to 3 extracts the echo signal.
Here, an example of the extracted echo signal is shown on the lower side (b) of FIG.

As described in the above description of the principle, and as can be seen from these, the echo from the focus position is shown in FIG.
The amplitude is large as shown in 0 (b). Therefore, in this example, the focus position detection circuit 45 divides the time Δt from the transmission of the burst wave to the return of the echo from the focus position by twice the speed of sound, and the The focal length L in the treatment case is obtained. Here, referring to FIG. 11, the line connecting the geometric center of the spherical shell of the therapeutic piezoelectric element 23 in the therapeutic oscillator 21 and the center of gravity of the therapeutic piezoelectric element 23 indicates the sound of the therapeutic oscillator 21. It becomes an axis. Then, on the sound axis, a point distant from the piezoelectric element 23 by the value L calculated above is a position where the intensity of the therapeutic ultrasonic wave is maximum (actual focus position), that is, a position where the therapeutic effect appears. Becomes

Further, in this example, the value of the sound velocity as a divisor when applied to the calculation for obtaining the focal length L value is
From the viewpoint described above, the speed of sound is matched with the speed of sound used when the diagnostic image is generated. Focal length L obtained in this way
The position on the sound axis of the therapeutic oscillator 21 away from the therapeutic oscillator 21 is displayed superimposed on the diagnostic image. Then, the user (operator, operator) can clearly know which position on the diagnostic image is the focal point of the therapeutic transducer 21.
Therefore, the target site can be treated accurately. Therefore, in this example, the display device 59 of the control circuit 54 is used.
12 is displayed by superimposing the convergent position of the therapeutic ultrasonic wave obtained by the above-described method on the ultrasonic image obtained by the sector scan of the diagnostic transducer 22 by the display control for. .

According to this embodiment, as described above,
The focal length L according to the environment where the therapeutic oscillator 21 is to be used can be detected to treat an accurate position, and the internal state of the subject can be confirmed on the image to detect a strong ultrasonic living body. It is possible to realize an ultrasonic therapy apparatus that is suitable and suitable for the case of performing treatment.

The present embodiment (fourth embodiment) can also be modified or changed in various ways. [Modification 1 of Fourth Embodiment] For example, in the above configuration example, information ultrasonic waves inside the subject are acquired, but instead of acquiring diagnostic images by ultrasonic waves, they are acquired by a nuclear magnetic resonance apparatus (MRI). Good. In this case, in addition to the above-described effects, the MRI image is not affected by strong therapeutic ultrasonic waves, so that the progress of the treatment can be observed in real time while performing the treatment. Play.

[Modification 2 of Fourth Embodiment] An example in which an ultrasonic probe 30 'of a modification shown in FIG. 13 is used instead of the structure of the ultrasonic probe 30 shown in FIG. But it's okay. Explaining only the points different from the configuration example shown in FIGS. 6 to 12, in this example, the therapeutic oscillator 21 and the diagnostic oscillator 22 are arranged on the same surface as shown in FIG. The entire shape of the probe 30 'is an ellipse. Other configurations, operations, and the like are the same as the above-described configuration example according to FIGS. In this example, in addition to the effects described above,
Since it is not necessary to turn over the ultrasonic probe when obtaining the convergent position of the therapeutic ultrasonic wave after acquiring the diagnostic image, it is possible to reduce the total time required to acquire the image and detect the convergent position. Therefore, the processing speed can be increased. Further, since it is elliptical, it is possible to reduce the diameter of the probe while increasing the surface area of the element.

[Modification 3 of Fourth Embodiment] Further, in the above-mentioned [Modification 2 of the fourth embodiment], the shape of the ultrasonic probe 30 'may be an ellipse or a rectangle instead of an ellipse. Good. You may implement with such a structure.

[Modification 4 of Fourth Embodiment] FIG.
An embodiment using an ultrasonic probe 30 'according to another modification shown in FIG. This example also corresponds to a modified example of [Modification 2 of the fourth embodiment] described above, and in the case of this example, as shown in FIG. The therapeutic oscillator 21 and the diagnostic oscillator 22 are arranged on the same surface as in the above [Modification 2 of the fourth embodiment], but an electronic scanning linear array is used as the therapeutic oscillator 22. It is a thing. Other configurations, operations, and the like are also basically the same as those of the configuration examples shown in FIGS. In the case of this example, in addition to the effects described above,
Since an image for diagnosis is obtained by electronic linear scanning,
Compared with the mechanical sector scanning of the above configuration example, an image having a high resolution can be obtained at a position distant from the ultrasonic probe, and the operational effects such as the improvement of the resolution in the distance of the diagnostic image can be further obtained. To be

[Fifth Modification of Fourth Embodiment] As the therapeutic oscillator 22, a convex type may be used.
It can also be implemented in this way.

Next, another embodiment (fifth embodiment) will be described. The present embodiment is intended to realize simplification of a circuit system and cost reduction accompanying it, and a configuration in which a diagnostic ultrasonic probe for obtaining information inside a subject receives a burst wave It is also an example of the case. In the present embodiment, as an example, the same ultrasonic probe as that shown in FIG. 13 is used (therefore, this example also corresponds to a modification of [Modification 2 of the fourth embodiment] described above. ).

Further, regarding the circuit system, the circuit system having the configuration of FIG. 9 in the fourth embodiment is used, but in the present embodiment, the one having the configuration of FIG. 15 described below is used. Note that other configurations are basically the same as those in the case of the fourth embodiment, and hereinafter, a main part of the present embodiment will be described with reference to FIG. 15. In the figure showing the outline of the circuit system, the therapeutic transducer 2 of the ultrasonic probe 30 'is shown.
Cables 36 are electrically connected to the piezoelectric elements inside each of 1 and the diagnostic vibrator 22 (FIG. 13) in the same manner as described above. In this example, the cable 36 connected to the therapeutic oscillator 21 is connected to the therapeutic oscillator drive circuit 52, and the therapeutic oscillator drive circuit 52 controls the same as the control circuit of FIG. It is connected to the circuit 54.
Therefore, here, the circuit unit side of the therapeutic oscillator 21 has the drive unit system of the therapeutic oscillator 21, but the first branching circuit (51) and the first detecting circuit (53) in the case of FIG. ),
The focus position detection circuit (55) is not provided.

On the other hand, the diagnostic oscillator 22 includes a cable 36.
Is connected to the demultiplexing circuit 56 via the
It is connected to the diagnostic oscillator drive circuit 57 and the detection circuit 58 through. The diagnostic oscillator drive circuit 57 is connected to the control circuit 54, and the detection circuit 58 detects the actual focus position by the same method as the focus position detection circuit of FIG. 9 described above. The circuit 55 is connected to the control circuit 54. Therefore, in the present example, when ultrasonic waves of a level at which a therapeutic effect is not generated by the circuit system of the therapeutic transducer 21 are transmitted as burst waves (see FIG. 1).
0 (a)), a system including such a focus position detection circuit 55 also constitutes a reception system of an echo signal obtained by being reflected in the subject based on the burst wave thereof, which is the same as the above-mentioned method. In this way, the focal position L of the ultrasonic wave for treatment is detected and displayed on the information inside the subject as shown in FIG. 12 by the display device 59 connected to the control circuit 54. The present example is configured as described above, and the basic operation, function, etc. of the other components are the same as in the case of the fourth embodiment.

As described above, the present embodiment uses, for example, the ultrasonic probe 30 'shown in FIG. 13 and a circuit system as shown in FIG. The echo from the weak burst wave radiated from the child 21 may be received by the diagnostic transducer 22. Therefore, according to the present embodiment as well, in addition to the effects and advantages described in the case of the fourth embodiment, in comparison with the configuration of FIG. Since it is not necessary to provide a demultiplexing circuit and a detection circuit for the above, the circuit system can be simplified, the cost can be reduced and the operational effects can be further obtained.

The present embodiment (fifth embodiment) can be modified and changed in various ways. [Modification 1 of Fifth Embodiment] For example, also in the present embodiment,
It is also possible to carry out in the same manner as in the case of [Modification 3 of the fourth embodiment], [Modification 4 of the fourth embodiment], and [Modification 5 of the fourth embodiment].

Next, still another embodiment (sixth embodiment)
This will be described with reference to FIGS. In the present embodiment, when the converged position of the therapeutic ultrasonic wave is displayed by being superimposed on the information inside the subject, a display mode is provided so that the operator (operator) can more easily understand the treatable position. Devise,
From this point, further improvements will be made.
In this embodiment, the basic configuration is the same as that of the fifth embodiment. Therefore, as the ultrasonic probe, for example, the ultrasonic probe 30 'of FIG. 13 is used, and It is assumed that the circuit system having the configuration shown in FIG. 15 is used. Therefore, the present embodiment is also a modification of the fifth embodiment.

The main part of this embodiment will be described below.
In this embodiment, the ultrasonic probe 30 'is rotated to perform sector scanning. Here, as shown in the upper side (a) of FIG. 16, an ultrasonic pulse train is transmitted from the diagnostic transducer 22 and a diagnostic image is generated from the echo of each pulse. In this case, however, in detecting the position of the focal point of the therapeutic ultrasonic wave, the diagnostic ultrasonic pulse is paused once every several pulses as shown in FIG. 16
As shown in the lower side (b), the therapeutic oscillator 21 radiates a burst wave of a level that does not show a therapeutic effect. These are performed under the control of the diagnostic oscillator 22 and the therapeutic oscillator 21 of the control circuit 59 of FIG.

Thus, similarly to the case of the fifth embodiment, the echo of the burst wave is also received by the system of the diagnostic oscillator 22, and the focal length of the therapeutic oscillator 21 is obtained in the same manner. Then, on the display device 59, as shown in FIG. 17, the line 60 in which the therapeutic transducer 21 is focused is displayed as a treatable line on the diagnostic image by superimposing it on the ultrasonic image. Also according to the present embodiment, the operation and effect described in the case of the fourth embodiment can be obtained, and in addition to the operation and effect described in the case of the fourth embodiment, the operator can treat. Since it is possible to grasp different positions as lines instead of points, the operability is further improved, and the effects such as ultrasonic treatment for a more accurate position can be obtained.

The present embodiment (sixth embodiment) can also be modified and changed in various ways. [Modification 1 of Sixth Embodiment] For example, also in the present embodiment,
It is also possible to carry out in the same manner as in the case of [Modification 3 of the fourth embodiment], [Modification 4 of the fourth embodiment], and [Modification 5 of the fourth embodiment].

The fourth to sixth embodiments (including their modified examples) may be combined with any of the first to third embodiments (including their modified examples). If so, a better ultrasonic therapy device can be realized.

Next, with reference to FIG. 18 and subsequent drawings, an example of the configuration of the improved ultrasonic probe and its driving method and driving device will be described. This is, for example, in an ultrasonic therapy device that performs treatment by transmitting strong ultrasonic waves from inside the body cavity,
It can be advantageously used for driving an ultrasonic probe that transmits or transmits a continuous wave or a burst wave in a subject. More specifically, it is suitable for carrying out an ultrasonic probe including a piezoelectric element and a coaxial cable electrically connected to the piezoelectric element and having a length that cannot be treated as a lumped constant. It is based on the following considerations.

In an ultrasonic probe using an ultrasonic transducer composed of a piezoelectric element, for example, a structure in which a protective layer is provided on the surface of the piezoelectric element inside the ultrasonic probe and a cavity is provided on the back surface is adopted. (Eg, FIG. 6 above). A coaxial cable is electrically connected to the piezoelectric element, and the other end of the coaxial cable is connected to a drive circuit. The drive circuit is connected to a control circuit to supply a drive voltage. (Eg, FIGS. 9 and 15).
Here, focusing on the electrical impedance of the ultrasonic probe and the characteristic impedance of the coaxial cable for connection,
The tip of the ultrasonic probe is designed so that the electrical impedance near the resonance frequency matches the characteristic impedance of the coaxial cable in order to effectively convert the voltage supplied from the drive circuit into ultrasonic energy. It is desirable to do so.

In such a configuration, the drive circuit
For example, when a burst wave voltage is applied to the piezoelectric element through the coaxial cable, a burst wave ultrasonic wave is transmitted from the piezoelectric element into the subject through the protective layer. Here, the present applicant has previously made a proposal regarding the impedance characteristic measurement of an ultrasonic probe by Japanese Patent Laid-Open No. 62-144646 (reference 4), and when driving the ultrasonic probe, such an ultrasonic wave is used. A combination with drive control based on measurement of the frequency-impedance characteristic of the probe is conceivable. When adopting such a drive control technology, the drive circuit measures the electrical impedance of the ultrasonic probe while changing the frequency of the burst wave transmitted from the drive circuit, and the drive frequency is It is possible to adopt a method of adjusting so as to match the resonance frequency of the acoustic probe. Then, at this time, the phase difference between the current and the voltage of the drive signal becomes zero. By adjusting the drive frequency in this way, the power factor of the electric energy supplied from the drive circuit is increased, and the electric energy can be efficiently supplied to the ultrasonic probe.

On the other hand, paying attention to the cable to be used, in the case of an ultrasonic therapeutic apparatus for cauterizing a tumor or the like at a focal position by transmitting a strong continuous wave or burst wave from the body cavity, or recently, , An ultrasonic diagnostic apparatus with a color Doppler system has been developed, which introduces an ultrasonic probe into the body cavity, transmits and receives continuous waves or burst waves, detects the Doppler effect, and displays the blood flow. However, including these devices, in the case of these devices, between the ultrasonic probe to be introduced into the body cavity and the drive circuit on the drive unit side fixed to, for example, the bedside or the like. It is usual to have a device configuration that requires a coaxial cable of a few meters in length. The resonance frequency of the ultrasonic probe seen from the tip of the coaxial cable is that the length of the coaxial cable is a length that cannot be ignored compared to the wavelength of the electric signal for driving in the coaxial cable. , It depends on the length of the cable used.

And again, this "cable length"
Varies depending on the application, that is, the position (location) at which the ultrasonic probe is introduced. For example, it may be relatively short when targeting the rectum, but when targeting the duodenum or ascending colon, it needs to be, for example, 1 meter to several meters longer than when targeting the rectum. Therefore, in order to support the ultrasonic probe of various application sites, the drive circuit needs to support a wide range of excitation frequencies. However, even if the ultrasonic probe is driven at the resonance frequency of the coaxial cable, if the driving frequency deviates from the resonance frequency of the piezoelectric element, the electric energy cannot be efficiently converted into ultrasonic energy. Especially,
When the treatment is performed by generating strong ultrasonic waves, if the supplied electric energy cannot be efficiently converted into ultrasonic energy, the focus position of the therapeutic ultrasonic wave is set to the convergence position during the treatment ( Even if it can be set to the actual focus position), it may not be possible to obtain a sufficient therapeutic effect by the amount that cannot be efficiently converted, and it is not possible to fully exert its ability.

Therefore, in the embodiment described below, under such consideration, even if a long coaxial cable is added, electric energy is efficiently applied to the ultrasonic probe,
Moreover, it is intended to efficiently convert the ultrasonic energy. The embodiment (seventh embodiment) shown in FIGS. 18 to 20 includes a piezoelectric element and a coaxial cable electrically connected to the piezoelectric element and having a length that cannot be treated as a lumped constant and transmits ultrasonic waves. Alternatively, when driving the ultrasonic probe for transmission / reception, an ultrasonic probe driving method is adopted in which the ultrasonic probe is driven by a continuous wave or a burst wave having a frequency near the anti-resonance frequency of the piezoelectric element. Preferably, in this case, the device is configured so that the driving frequency of the piezoelectric element changes following the anti-resonance frequency of the piezoelectric element.

FIG. 18 is a sectional view showing an example of the structure of an improved ultrasonic probe applicable to this embodiment.
9 shows the outline of an example of the circuit system. In this example, a probe that can perform both ultrasonic diagnosis and ultrasonic treatment is taken as an example, and in that case, a therapeutic oscillator (a therapeutic ultrasonic oscillator) and a diagnostic oscillator (a diagnostic oscillator) are used. In the point that it is arranged on the same side as the ultrasonic transducer, it also corresponds to a modification such as the above-mentioned [Modification 2 of the fourth embodiment].

As shown in FIG. 18, in this example, the ultrasonic probe 30A is provided with a spherical shell-shaped piezoelectric element 71, and the entire upper surface (upper surface in the drawing) of the piezoelectric element 71 is grounded. A (GND) electrode 72 is formed. Further, on the lower surface (lower surface in the figure) of the piezoelectric element 71, there is a circular diagnostic electrode 73 at the center and an annular therapeutic electrode 74 around it. The diagnostic electrode 73 and the therapeutic electrode 74 are not electrically connected to each other. Here, there is one piezoelectric element 71, and therefore, the diagnostic piezoelectric element and the therapeutic piezoelectric element are formed on the same single piezoelectric element 71, and in this example, such a configuration is followed. (The details of such improvements and other features will be described in other embodiments (the ninth embodiment and subsequent embodiments)).

An acoustic matching layer 5 is formed on the acoustic emission surface side of the portion of the piezoelectric element 71 corresponding to the diagnostic electrode 73. Further, the back braking layer 6 is formed on the lower surface of the diagnostic electrode 73. The back braking layer 6 may be formed of epoxy resin mixed with tungsten powder and cured, as in the case of FIG. The piezoelectric element 71 is adhered and held by a resin insulating layer 77. A metal housing 78 is provided outside the insulating layer 77. And GND
The electrode 72 and the housing 78 are electrically connected by a conductor wire 79.

The ultrasonic probe 30A further includes a piezoelectric element 7
1 has a cable used for transmission of an electric signal to and from 1.
In this example, a cable 80 that contains two coaxial cables
Through the holes formed in the housing 78 and the insulating layer 77. The other end of the cable 80 thus drawn out is shown in FIG.
At 8, an ultrasonic observation device (not shown) is connected. Here, the ultrasonic observation device can be configured to include a control device, a display device, and the like, and the cable leads to, for example, a drive circuit in the control device.

Each shield wire of the two coaxial cables in the cable 80 is electrically connected to the housing 78. Further, each of the core wires is electrically connected to the diagnostic electrode 73 and the therapeutic electrode 74, respectively, as shown in the figure. Further, here, the space formed by the insulating layer 77, the therapeutic electrode 74, and the back braking layer 76 is a space. The lower surface of the housing 77 is watertightly sealed with a back cover 81. Further, the surface of the ultrasonic probe of FIG. 18 is covered with a film of polyparaxylylene (not shown) having a film thickness of 10 μm, for example.

In the above structure, the portion related to the diagnostic electrode 73 functions as a diagnostic vibrator, while the portion related to the therapeutic electrode 74 functions as a therapeutic vibrator.

In FIG. 19 showing the outline of the circuit system of this example, the system of the diagnostic part may be the same as that according to, for example, a known ultrasonic diagnostic apparatus, and is not shown. (Note that when combined with the fourth embodiment, the circuit portion of the system related to the diagnostic oscillator includes the branching, diagnostic oscillator driving, detection, and control circuits (5
4, 56 to 58) and the display device (59), or the structure shown in FIG. 15 may be employed). FIG. 19 therefore shows the system of the therapeutic part, in which the part of the piezoelectric element 71 with the therapeutic electrode 74, ie the therapeutic oscillator 91, is connected to the coaxial cable by the coaxial cable. It is electrically connected to the impedance measurement circuit 93 together with the drive circuit 92 which supplies the drive voltage via the. The drive circuit 92 and the impedance measurement circuit 93 are connected to the control circuit 94, respectively. The control circuit 94 can be a control circuit common to the circuit system of the diagnostic oscillator (see the control circuit 54 described above).

The drive circuit 92, here, is a control circuit 94.
Under the control of 1., a continuous wave voltage is applied to the therapeutic oscillator 91. On the other hand, the impedance measuring circuit 92 is a circuit having a function of monitoring a voltage and a current applied to the therapeutic oscillator 91 and measuring an electrical impedance of the therapeutic oscillator 91, and the measurement information is control information. The circuit 94 is used for automatic frequency control of the output of the drive circuit 92 as described later. The control circuit 94 is also adapted to receive ON / OFF operation data from a switch (not shown) operated by a user (operator, operator) to emit a continuous wave ultrasonic wave, Further, a display device (see the above-mentioned display device 59) for generating an ultrasonic image is also connected.

The apparatus according to the ultrasonic probe driving method according to the present embodiment can be used as follows, and will be further described below with reference to FIG. [During Ultrasound Diagnosis] The operations and processes related to the diagnostic part are basically handled in the same manner as in the case of ultrasonic diagnosis by the conventional ultrasonic diagnostic apparatus in this ultrasonic probe 30A. Therefore, it is omitted here. In addition,
In this case, the preferred usage mode of the device part of the diagnostic system, the function thereof, and the like will be further described in relation to the structure using the single piezoelectric element 71 in other embodiments (the ninth and subsequent embodiments). Described in.

[During Ultrasonic Treatment] After ultrasonic diagnosis, a powerful ultrasonic wave is radiated to the subject for treatment, as follows. When performing ultrasonic treatment, the user operates the switch for emitting the continuous wave ultrasonic wave. By operating the switch, the drive circuit 9 is controlled by the control circuit 94.
2 applies a continuous wave voltage to the therapeutic oscillator 91.

In this example, the impedance measuring circuit 14 is provided, and when the continuous wave voltage is applied to the therapeutic oscillator 91, the impedance measuring circuit 92 applies the voltage to the therapeutic oscillator 91. And the electric current are sequentially monitored to measure the electrical impedance of the therapeutic oscillator 91. Then, the information on the thus-measured electrical impedance is sent to the control circuit 94 as input data for controlling the driving frequency, and the control circuit 94 is based on this, the phase of the electrical impedance is 0, and the absolute value is The output frequency of the drive circuit 92 is controlled so as to be maximized, that is, to be driven at the anti-resonance frequency of the therapeutic oscillator 91.

In this way, even the therapeutic oscillator 9
Even if the coaxial cable used between 1 and its drive circuit 92 is long (several meters), the electric energy is efficiently applied to the ultrasonic probe 30A during the ultrasonic treatment, and the efficient ultrasonic wave is obtained. Energy conversion is realized. this is,
It can be explained as follows.

20A to 20C show the electric impedance characteristics of the ultrasonic probe seen from the end of the coaxial cable when the length of the coaxial cable to be applied is changed. In each figure, the solid line and the broken line are the frequency characteristics of the absolute value | Z | of the impedance and the phase θ, respectively. When the length of the coaxial cable changes, for example, the cable length is 20 mm, 10
As shown in FIGS. (A), (b) and (c) showing the case of 00 mm (= 1 m) and 3000 mm (= 3 m), the frequency at which the absolute value of impedance | Z |
The value of r varies greatly. However, the figures (a), (b),
As shown in (c), the frequency at which the absolute value of impedance | Z | becomes maximum, that is, the value of the anti-resonance frequency Fa hardly changes. Further, like the resonance frequency Fr, the impedance phase θ is 0 at the anti-resonance frequency Fa as well.

Therefore, when driving the ultrasonic probe,
When a continuous wave or burst wave voltage having the anti-resonance frequency Fa is applied to the ultrasonic probe, the power factor of the voltage applied from the drive circuit is increased, and the electric energy can be efficiently input. Furthermore, since the characteristic impedance of the coaxial cable and the electrical impedance of the tip of the ultrasonic probe at the anti-resonance frequency Fa match, the reflection of electric power does not occur even at the joint between the coaxial cable and the piezoelectric element. , Can efficiently convert electric energy into ultrasonic energy.

In this example, when performing ultrasonic treatment, as described above, the control circuit 94 uses the impedance measured by the impedance measurement circuit 93 to determine the phase θ of the electrical impedance and set the absolute value | The control is performed so that the therapeutic oscillator 92 is driven at the anti-resonance frequency Fa at which Z | is maximized. Therefore, as described in the above principle, the continuous wave voltage of the anti-resonance frequency Fa can always be applied to the ultrasonic probe 30A regardless of the coaxial cable length, and the voltage applied from the drive circuit 92 can be changed. The efficiency is increased, and the electric energy can be efficiently input. Furthermore, since the characteristic impedance of the coaxial cable and the electrical impedance of the tip portion of the ultrasonic probe 30A at the anti-resonance frequency Fa match, the electric power is reflected at the joint portion between the coaxial cable and the piezoelectric element 71. Electric energy can be efficiently converted into ultrasonic energy without wakeup.

As described above, according to this embodiment,
Effective driving can be realized in the case of an ultrasonic probe that transmits continuous wave ultrasonic waves into the subject, and even if a long coaxial cable is added, electric energy can be efficiently applied to the ultrasonic probe 30A. And can be efficiently converted into ultrasonic energy. Therefore, even in the ultrasonic treatment in which a powerful ultrasonic wave is generated to perform the treatment, the more efficient conversion of the ultrasonic energy can be realized, so that the therapeutic effect can be easily enhanced.

The present embodiment (seventh embodiment) can also be modified and changed in various ways. [Modification 1 of Seventh Embodiment] For example, although a continuous wave ultrasonic wave is used in the above example, the present invention is not limited to the continuous wave. So, for example, instead of also sending a continuous wave,
It can also be applied to a probe that visualizes blood flow by transmitting and receiving burst waves and detecting Doppler signals.

Next, another embodiment (eighth embodiment) will be described. The present embodiment is intended to realize simplification of a circuit system and cost reduction. In this embodiment,
As the probe to be used, as an example, an ultrasonic probe 30A similar to that shown in FIG. 18 is used, but as for the circuit system, the one shown in FIG. 21 showing an example of the outline of the circuit system of the present embodiment is used. To use. Here, as shown in FIG. 21, the portion of the piezoelectric element 71 of the ultrasonic probe 30A with the treatment electrode 73, that is, the treatment oscillator 92, is electrically connected to the drive circuit 92 by a coaxial cable. ing. The drive circuit 92 is connected to the control circuit 94.
Therefore, in the case of this example, the impedance measuring circuit (93) of FIG. 19 is not provided. Regarding the diagnostic part,
In this example as well, similar to the case of the seventh embodiment, it may be the same as a known conventional ultrasonic diagnostic apparatus, and therefore, illustration is omitted here. Other configurations are basically the same as in the case of the seventh embodiment, and the main part of the present embodiment will be described below.

[During Ultrasonic Treatment] In this example, when performing ultrasonic treatment, the user operates the above-mentioned switch for emitting continuous wave ultrasonic waves, as in the case of the seventh embodiment ( As for the diagnostic part, this is also the seventh
The description is omitted because it is similar to the case of the embodiment). In response to the switch operation, the drive circuit 92 applies a continuous wave voltage to the therapeutic oscillator 91 under the control of the control circuit 94. When the continuous wave voltage of the anti-resonance frequency Fa is applied to the ultrasonic probe 30A, the power factor of the voltage applied from the drive circuit 92 becomes large, and the electric energy can be efficiently input. Furthermore, since the characteristic impedance of the coaxial cable and the electrical impedance of the tip portion of the ultrasonic probe 30A at the anti-resonance frequency Fa match, the reflection of electric power also occurs at the joint portion between the coaxial cable and the piezoelectric element 71. Electric energy can be efficiently converted into ultrasonic energy without waking up.

According to this embodiment, as in the seventh embodiment, even if a long coaxial cable is added, it is possible to efficiently apply electric energy to the ultrasonic probe 30A and efficiently convert it into ultrasonic energy. In addition, the impedance measurement circuit (93) is compared with the configuration of FIG.
By omitting, the circuit system can be made inexpensive. In this embodiment, the value of the anti-resonance frequency of the probe used must be constant regardless of the type of probe, but the length of the cable can be any length depending on the application.

The present embodiment (eighth embodiment) can also be modified and changed in various ways. [Modification 1 of Eighth Embodiment] For example, in order to enable the use of probes of various frequencies, the following drive system may be used. That is, a code according to the frequency is attached to the probe used. On the other hand, for example, a code reader is provided in the controller including the control circuit 94 and the drive circuit 92 shown in FIG. In this case, the control device controls the barcode read in advance on each probe according to the ultrasonic probe to be applied by the code reading device and supplies a drive voltage having a frequency corresponding to the barcode to the probe to be used. To do. According to this, the anti-resonance frequency of the probe can be selected according to the application. Thus, it allows the use of probes of different frequencies. The present example may be implemented in this manner.

[Modification 2 of Eighth Embodiment] Also, this embodiment can be implemented in the same manner as in [Modification 1 of the seventh embodiment].

Further, the seventh embodiment and the eighth embodiment (including their modified examples and the like) are implemented in combination with any of the first to third embodiments (including their modified examples and the like). be able to. Further, in driving the ultrasonic probe in the fourth to sixth embodiments (including their modified examples), the ultrasonic probe of the seventh embodiment and the eighth embodiment (including their modified examples) is used. Any driving method or device can be applied.

The ultrasonic probe 30 having the structure shown in FIG.
A is applicable to both ultrasonic diagnosis and ultrasonic therapy. Furthermore, this is the sound of both when viewed from the viewpoint of the sound axis of the diagnostic oscillator and the therapeutic oscillator. It is possible to provide an ultrasonic probe that is excellent in that the axes can be easily matched. The embodiment described below (the ninth embodiment and below) is mainly related to the improvement from such a side, and emits ultrasonic waves to the subject,
It can be advantageously used for an ultrasonic probe in the case of obtaining its internal information or performing treatment by the action of ultrasonic waves.

Ultrasonic treatment for irradiating a living body with a burst wave or continuous wave of high sound pressure to cauterize a lesion such as a tumor is
It can be done with the ultrasonic treatment device as already mentioned,
In particular, as generally used in the past, by using a combination of an ultrasonic diagnostic device and such an ultrasonic therapeutic device, the position and size of the lesion to be treated can be accurately confirmed, It has already been described that it can greatly contribute to ensuring reliable ultrasonic treatment.

FIG. 29 is a sectional view of an ultrasonic probe of a comparative example for performing both ultrasonic diagnosis and ultrasonic treatment, which is shown in comparison with FIG. As shown in FIG. 29, in this ultrasonic probe, a spherical shell-shaped piezoelectric element 1 for diagnosis is provided in the central portion.
01, and there is a therapeutic piezoelectric element 102 in the shape of an annular spherical shell. The diagnostic piezoelectric element 101 and the therapeutic piezoelectric element 102 are joined by an adhesive 103 to form a part of a spherical shell. The GND electrode 112 is continuously formed on the upper surfaces of the therapeutic piezoelectric element 102 and the diagnostic piezoelectric element 101.
Are formed. Although diagnostic electrodes 113 and therapeutic electrodes 114 are formed on the lower surfaces of the diagnostic piezoelectric device 101 and the therapeutic piezoelectric device 102, respectively, they are not electrically connected to each other.

An acoustic matching layer 104 is formed on the acoustic radiation surface side of the diagnostic piezoelectric element 101. Further, the backside braking layer 1 is provided on the side opposite to the acoustic radiation surface of the diagnostic piezoelectric element 101.
05 is formed. The back braking layer 105 is formed of epoxy resin mixed with tungsten powder and cured. The diagnostic piezoelectric element 101 and the therapeutic piezoelectric element 102, which are separate from each other, are bonded and held to a resin insulating layer 106. A metal housing 10 is provided outside the insulating layer 106.
7 and the electrode portion (GND electrode portion) on the upper surface of the therapeutic piezoelectric element 102 and the housing 107 are the lead wires 1
It is electrically connected at 08.

Cable 1 with two coaxial cables built-in
09 is pulled out through a hole formed in the housing 107 and the insulating layer 106, and the other end of the cable 109 is connected to an ultrasonic observation device (not shown).
The point that the shield wires of the two coaxial cables in 09 are electrically connected to the housing 107 is the same as in the case of FIG. On the other hand, the respective core wires are electrically connected to the diagnostic electrode 113 and the therapeutic electrode 114 of the individual piezoelectric element parts assembled by joining with the adhesive 103, respectively. The space formed by the insulating layer 106, the therapeutic piezoelectric element 102, and the back braking layer 105 is filled with the filling material 110. The filler 110 is a resin containing a large number of minute closed cells.

The ultrasonic probe shown in FIG. 29 can be used, for example, by directly contacting it with a subject or through a transmission medium such as a water bag. At the time of ultrasonic diagnosis, a drive pulse is applied from an ultrasonic observation device (not shown) to the diagnostic piezoelectric element 101 via the cable 109. The diagnostic piezoelectric element 101 vibrates by a drive pulse and generates an ultrasonic wave. The acoustic matching layer 104 acts on the acoustic radiation surface side to efficiently radiate the acoustic radiation into the subject. On the other hand, the ultrasonic waves emitted to the back side are absorbed by the action of the back braking layer 105. Due to the action of the acoustic matching layer 104 and the back damping layer 105, a short ultrasonic pulse is emitted.

The ultrasonic wave radiated into the subject is reflected by the acoustic impedance discontinuity. The reflected ultrasonic echo is transmitted through the acoustic matching layer 104 to the diagnostic piezoelectric element 1.
01, and converted into an electrical echo signal. The echo signal is processed in the ultrasonic observation device (not shown) via the cable 109. When the above operation is repeated while changing the emitting direction of the ultrasonic wave and scanning, an ultrasonic image showing the internal information of the subject is generated. The shorter the ultrasonic pulse radiated, the more ultrasonic image with high distance resolution is generated. The user can grasp the position and size of the affected area by looking at the ultrasonic image.

At the time of treatment, a continuous wave is applied to the therapeutic oscillator consisting of the therapeutic piezoelectric element 102 and the electrodes 112 and 114 via the cable 109, and this emits a continuous wave ultrasonic wave. The filling material 110 on the back surface of the therapeutic oscillator contains a large number of closed cells, and the acoustic impedance is much lower than that of the piezoelectric element. Therefore, the ultrasonic waves are efficiently radiated to the acoustic radiation surface side. Since ultrasonic waves are emitted from a spherical shell-shaped acoustic emission surface that is larger than the wavelength, the ultrasonic waves converge at the focal point. When a continuous wave with a high sound pressure is applied, the temperature near the focus rises, causing degeneration in the living tissue, and the affected area such as a tumor can be treated.

However, focusing on the points of the sound axis during such ultrasonic diagnosis and ultrasonic treatment, in the ultrasonic probe shown in FIG. 29, the diagnostic piezoelectric element 101 and the therapeutic piezoelectric element 10 are used.
2 and 2 are joined by an adhesive 103. Therefore, it is difficult to completely match the geometric center axes of the two.
Although both axes are aligned during assembly, nonetheless,
Causes axis misalignment. When the central axes of the diagnostic piezoelectric element 101 and the therapeutic piezoelectric element 102 do not match, the sound axes of both transducers, that is, the emission directions of ultrasonic waves, are displaced as shown by the sound axis illustrated by the broken line in FIG. Will end up. Then, the ultrasonic wave emitted from the therapeutic oscillator by the therapeutic piezoelectric element 102 converges with the position intended to be treated by observing the diagnostic piezoelectric element 101 and the electrodes 112, 113 on the diagnostic oscillator side. The position is out of alignment. As a result, the intended therapeutic effect may not be obtained, or normal tissue may be damaged.

Some of the embodiments described below have been improved from this point, and the acoustic axes of the diagnostic oscillator and the therapeutic oscillator were easily matched and observed. An ultrasonic probe capable of reliably treating a site can be provided, and the ultrasonic probe 30A in FIG. 18 is also an example of this. First, with reference to FIG. 18, the ultrasonic probe according to the present embodiment will be described with supplementary explanations.

The ultrasonic probe 30A (FIG. 18) according to the present embodiment is used for an apparatus that performs both ultrasonic diagnosis and treatment using ultrasonic waves, and has the configuration of the comparative example of FIG. On the other hand, a GND electrode 72 is formed on the entire upper surface of one spherical shell-shaped piezoelectric element 71, and a circular diagnostic electrode 73 is provided in the center of the lower surface of the one piezoelectric element 71. In addition, an annular therapeutic electrode 74 is provided around it. The diagnostic electrode 73 and the therapeutic electrode 74 are not electrically connected to each other. In this example, furthermore, as shown in FIG. 18, the one piezoelectric element 71 used is of a single and uniform thickness.

The portion of such one piezoelectric element 71 corresponding to the diagnostic electrode 73 is a portion (diagnosis portion) which is vibrated by a drive pulse and emits ultrasonic waves, which will be described later. The therapeutic electrode 74 of the piezoelectric element 71
The portion corresponding to is a portion for radiating continuous wave ultrasonic waves (treatment portion) as described later, these two portions are present, and they are formed on the same piezoelectric element 71. ing.

An acoustic matching layer 75 is formed on the acoustic emission surface side of the portion of the piezoelectric element 71 corresponding to the diagnostic electrode 73, and on the lower surface of the diagnostic electrode 73, that is, on the opposite side of the acoustic emission surface. Has a backside braking layer 76 (formed of epoxy resin mixed with tungsten powder and cured), which absorbs and attenuates ultrasonic waves during pulse ultrasonic wave transmission by the diagnostic portion. Become a layer.

The structure of the insulating layer 77, the housing 78, the conducting wire 79, the cable 80, etc. of FIG. 18 is the same as that described in the description of FIG. Are incorporated into this example and are fully referenced. The space formed by the insulating layer 77, the therapeutic electrode 74, and the back braking layer 76 is a space in the ultrasonic probe 30A as compared with the comparative example of FIG.
The lower surface of the housing 78 is watertightly sealed with a back cover 81. Furthermore, the ultrasonic probe surface has a film thickness of 10 μm (not shown).
Covered with a film of polyparaxylylene.

In the present embodiment, the structure is assembled as described above, and it is not necessary to align both the diagnostic piezoelectric element and the therapeutic piezoelectric element as in the case of FIG. 29 in the assembly during manufacturing. The sound axes are also the same.
Then, by the ultrasonic probe 30A having the sound axis thus obtained, ultrasonic diagnosis is performed by the portion corresponding to the diagnostic electrode 73 of the piezoelectric element 71, and the therapeutic electrode 74 of the piezoelectric element 71 is changed. The ultrasonic treatment can be appropriately performed by the corresponding portion. Here, for example,
Similar to the use example in the case of the comparative example of FIG. 29, a case where the present ultrasonic probe 30A is used by being brought into contact with a subject directly or through a transmission medium such as a water bag will be described as an example.

[During Ultrasound Diagnosis] First, at the time of ultrasonic diagnosis will be described. A drive pulse is applied from an ultrasonic observation device (not shown) to the diagnostic electrode 73 of the present ultrasonic probe via the cable 80. Here, in this example, the frequency band of the drive pulse can be the frequency band of FIG. 22A described later. When the drive pulse is applied, as a result, the portion of the single piezoelectric element 71 corresponding to the diagnostic electrode 73 vibrates due to the drive pulse and generates an ultrasonic wave. In this way, when a drive pulse is applied to the portion with the diagnostic electrode 73, that is, the diagnostic vibrator, the portion vibrates by the drive pulse and generates an ultrasonic pulse.

When the acoustic matching layer and the backside damping layer are added to the portion that radiates the ultrasonic pulse in this manner, the acoustic matching layer serves to efficiently radiate into the subject on the acoustic radiation surface side. It In this example, the acoustic matching layer 75 and the back damping layer 76 are provided, and the acoustic matching layer 75 acts on the acoustic radiation surface side to efficiently radiate the acoustic radiation into the subject. On the other hand, the ultrasonic waves radiated to the back side are absorbed by the action of the back braking layer 76. As a result of the action of the acoustic matching layer 75 and the backside damping layer 76, a shorter ultrasonic pulse is emitted.

The ultrasonic wave radiated into the subject is the fourth ultrasonic wave.
As mentioned in the embodiments and the like, the acoustic impedance is reflected at the discontinuous portion. In this example, the part that emits the ultrasonic pulse can also be received, and the reflected ultrasonic echo is
It is received by the piezoelectric element 71 (here, a diagnostic transducer) via the acoustic matching layer 75 and converted into an electrical echo signal. In this example, the echo signal is processed in the ultrasonic observation device (not shown) via the diagnostic electrode 73 and the cable 80. When the above operation is repeated while changing the emitting direction of the ultrasonic wave and scanning, an ultrasonic image showing the internal information of the subject is generated. In this case, the ultrasonic image is displayed
For example, the configuration of the display device (59) shown in FIGS. 9 and 15 can be applied. The user (operator) can grasp the position and size of the affected area by looking at the ultrasonic image.

[During Ultrasonic Treatment] Next, the time of treatment will be described. After ultrasonic diagnosis, ultrasonic waves are emitted to the subject to be treated as follows. Also in this example, the seventh
As described in the embodiment, for example, a configuration including a switch operated by a user to emit a continuous wave ultrasonic wave is adopted. When the user turns on such an operation switch (not shown), a continuous wave is applied to the treatment electrode 74 of the ultrasonic probe via the cable 80, and at this time, the treatment of the single piezoelectric element 71 is performed. The portion corresponding to the working electrode 74, that is, the portion of the therapeutic oscillator radiates continuous wave ultrasonic waves.

Here, the acoustic impedance on the back surface of the therapeutic oscillator is set to be much lower than that of the piezoelectric element. Then
Ultrasonic waves are efficiently radiated to the acoustic radiation surface side. In this example, the back surface of the therapeutic oscillator is air, and the acoustic impedance is much lower than that of the piezoelectric element. Therefore, the ultrasonic waves are efficiently radiated to the acoustic radiation surface side. Since ultrasonic waves are emitted from a spherical shell-shaped acoustic emission surface that is larger than the wavelength, the ultrasonic waves converge at the focal point. When a continuous wave with high sound pressure is emitted, the temperature near the focus rises,
Causes degeneration in living tissues. Therefore, the affected part of the tumor can be treated.

In this way, ultrasonic diagnosis and ultrasonic treatment can be performed, and in that case, since the sound axis of the vibrator for vibration and the sound axis for therapy are the same, the observed site can be treated surely. As in the case of the comparative example of FIG. 29, due to the mismatch of the sound axes, the position intended to be observed and treated and the ultrasonic wave actually emitted for ultrasonic treatment converge. There is no case where the position is displaced and, as a result, the intended therapeutic effect is not obtained.
Therefore, in the manufacturing process, it is possible to accurately and surely treat the site observed by the diagnostic oscillator during use without the need for labor such as axis alignment during assembly. As described below, in the diagnosis and treatment, it is possible to obtain a clear image with a high distance resolution, and it is also possible to emit a therapeutic ultrasonic wave having a high sound pressure.

22 (a) and 22 (b) show the frequency characteristics of the diagnostic portion and the therapeutic portion in the present ultrasonic probe having the above configuration. Since the acoustic impedance of the back surface of both the diagnostic portion of the piezoelectric element 71 corresponding to the diagnostic electrode 73 and the therapeutic portion of the piezoelectric element 71 corresponding to the therapeutic electrode 73 is lower than the acoustic impedance of the piezoelectric element 71, The piezoelectric element 71 resonates at 1/2 wavelength. Therefore, the center frequencies of both parts match.

Since the acoustic matching layer 75 and the backside damping layer 76 are added to the diagnostic portion, the bandwidth becomes wide as shown in the upper side (a) of FIG. Therefore, when a pulsed electric signal is applied, a very short ultrasonic pulse is emitted. As described above, the reflected ultrasonic echo is received by the diagnostic transducer of the ultrasonic probe, the echo signal is processed by the observation device via the cable 80, and the ultrasonic image showing the internal information of the subject is obtained. In generating, the shorter the emitted ultrasonic pulse, the higher the distance resolution of the ultrasonic image is generated. However, as shown in FIG. 22A, the frequency band is wide and short pulses can be transmitted and received. Can easily respond.

On the other hand, the therapeutic portion has no acoustic matching layer and the back surface is air. Therefore, although the bandwidth is narrow as shown in the lower side (b) of FIG. 22, very high efficiency can be obtained at the center frequency. Therefore, when a continuous wave having the same frequency as the center frequency is applied, electric energy is converted into ultrasonic energy with high efficiency, and high sound pressure is obtained.

As described above, according to this embodiment, the sound axes of the diagnostic oscillator and the therapeutic oscillator can be easily matched,
The observed site can be treated surely. Further, since the diagnostic portion has a wide frequency band and can transmit and receive short pulses, a clear image with high distance resolution can be obtained. On the other hand, since the treatment portion has high efficiency at the center frequency, unnecessary heat generation and the like can be reduced, and treatment ultrasonic waves with high sound pressure can be emitted.

The present embodiment (ninth embodiment) can also be modified and changed in various ways. [Modification 1 of Ninth Embodiment] For example, an embodiment using the ultrasonic probe 30A shown in FIG. 23 may be used. A configuration example of the ultrasonic probe 30A according to the ninth embodiment (FIG. 18,
Explaining only the points different from 22), in this example, as shown in FIG. 23, the lower surface of the therapeutic electrode 74 is filled with a filler 82 containing a large amount of minute closed cells. In this example, expanded polystyrene was used as the material of the filler 82. Other configurations, operations, and the like are similar to those of the above configuration example.

In this example, in addition to the above-described effects, since the back surface of the piezoelectric element 71 is not a space, it is possible to prevent liquid such as water or body fluid from entering. Therefore,
Since there is no possibility that liquid such as water or body fluid will enter the space behind the piezoelectric element to short-circuit or corrode the electrode, the reliability and durability of the ultrasonic probe are improved.

[Modification 2 of Ninth Embodiment] In addition, in the above-mentioned [Modification 1 of the ninth embodiment], as the filler 82, in addition to the foaming stethole, for example, urethane, silicone, resin or the like may be used. Resin can be used. Further, as the filler 82, a resin such as low density polyethylene having a low acoustic impedance and containing no minute closed cells can be used. Furthermore, an air layer having a thickness of several hundreds of μm or more may be provided on the back surface of the therapeutic electrode 74, and the lower surface thereof may be filled with an arbitrary resin such as epoxy or silicon.

[Modification 3 of Ninth Embodiment] FIG.
High-speed scanning and the like may be realized by the embodiment using the ultrasonic probe having the configuration shown in FIG. This example also corresponds to the modification of [Modification 4 of the fourth embodiment] (FIG. 14). Explaining only the points different from the configuration example of the ultrasonic probe 30A of the ninth embodiment, in this example, as shown in FIG. 24, the piezoelectric elements 71a used are strip-shaped small piezoelectric elements arranged in a line. It is a linear array type piezoelectric element. A diagnostic electrode (not shown) is formed at the center of each element, and a therapeutic electrode (not shown) is formed at the end thereof. Further, cables are laid for each element by using a method similar to that of the conventional general array type probe.

As shown in the figure, an acoustic matching layer 75a is provided on the upper surface of the diagnostic electrode, and a rear damping layer 76a is provided on the lower surface thereof. In order to prevent a short circuit between the electrodes on the lower surface of the adjacent element, the backside braking layer 76a is made of epoxy mixed with zirconia powder. Other configurations and the like may be basically the same as those in the ninth embodiment.

In this example, the individual elements are driven with a slight time difference under the control of an ultrasonic observation device (not shown). As a result, the emission direction and focal length of ultrasonic waves change. The operation of each element is similar to that of the ninth embodiment.

Also in this example, in addition to the operational effects of the ninth embodiment, electronic scanning can be realized for diagnosis as in the case of the conventional electronic scanning type probe. For this reason,
It is possible to focus on an arbitrary position and observe it in detail. In the case of treatment, the focal length can be changed by the observation device as in the case of diagnosis, so that the treatment position can be easily selected.

[Modification 4 of Ninth Embodiment] As a modification, a vibrator of another type such as a convex type or a sector type may be used instead of the electronic linear type for diagnosis according to the application site. . Further, the diagnosis side may be an electronic scanning type, and the treatment side may be one wiring, and may be a fixed focus type similar to the case of the ultrasonic probe of the ninth embodiment. It can also be implemented in this way.

[Fifth Modification of Ninth Embodiment] In the above example, the continuous wave is used as the therapeutic ultrasonic wave. However, a burst ultrasonic wave may be used, or a continuous wave or a burst wave may be used. The part that transmits the ultrasonic waves may also be capable of receiving the ultrasonic waves.

Next, another embodiment (tenth embodiment) will be described. This embodiment is intended to improve the therapeutic effect. In the case of the ninth embodiment, the common piezoelectric element used has a uniform thickness in both the diagnostic portion and the therapeutic portion, but in the present embodiment, the acoustic portion is used in these portions. FIG. 25 shows a modification in which the thickness of the surface opposite to the radiation surface is made different, and the surface of the acoustic radiation surface has a continuous shape.
The cross section of the ultrasonic probe 30B of the example is shown.

Basically, the present ultrasonic probe 30B may be the same as the configuration example of the ultrasonic probe 30A of the ninth embodiment, and the main differences and the main parts of this example will be described below. about,
explain. As shown in FIG. 25, the piezoelectric element 71b used in this example has a central circular portion (diagnostic portion) here.
Is twice the thickness of the peripheral portion (treatment portion). On the acoustic emission surface side of the piezoelectric element 71b, an acoustic matching layer 75b having a thickness of a quarter wavelength of the frequency of the diagnostic portion of the piezoelectric element 71b is added to the entire surface. Even in the case of adopting such a configuration with one piezoelectric element 71b having a different thickness, the GND electrode 72, the diagnostic electrode 73, and the therapeutic electrode 74 are formed at the positions as shown in the figure.

FIGS. 26 (a) and 26 (b) show frequency characteristics of a diagnostic portion and a therapeutic portion by the ultrasonic probe 30B having the above configuration. Since the acoustic impedance of the back surface of both the diagnostic portion and the therapeutic portion is lower than the acoustic impedance of the piezoelectric element 71b, the piezoelectric element resonates at 1/2 wavelength. Therefore, the center frequency of the therapeutic portion is twice (f × 2) the center frequency of the diagnostic portion.

Since the acoustic matching layer 75b having a thickness of ¼ wavelength and the back damping layer 76 are added to the diagnostic portion, the bandwidth is wide as shown in the upper part (a) of FIG. Become. Therefore, when a pulsed electrical signal is applied, it emits a very short ultrasonic pulse. The shorter the ultrasonic pulse radiated, the more ultrasonic image with high distance resolution is generated.

On the other hand, a ½ wavelength acoustic matching layer 75b is added to the treatment portion, and the back surface is air.
Therefore, as shown in the lower side (b) of FIG. 26, the bandwidth is narrow, but very high efficiency is obtained at the center frequency. Therefore, if a continuous wave with the same frequency as the center frequency is applied,
Electric energy is converted into ultrasonic energy with high efficiency, and high sound pressure is obtained.

According to this embodiment, the same effects as those of the above-described ninth embodiment can be obtained, and the piezoelectric element 71b can be obtained.
Since the entire surface of is covered with the acoustic matching layer 75b, the electrodes on the surface are less likely to be damaged by corrosion and the durability is improved. In addition, when a high frequency is used for treatment, the efficiency of focusing ultrasonic waves at the focal point is increased, and the therapeutic effect is enhanced.

The present embodiment (tenth embodiment) is also
Various modifications and changes are possible. [Modification 1 of Tenth Embodiment] For example, an example using an ultrasonic probe 30C shown in FIG. 27 may be used. Also in this example, the surface of the sound emitting surface is a continuous shape, the surface opposite to the sound emitting surface is a discontinuous shape, and the thickness of the diagnostic portion and the therapeutic portion is different. However, instead of the piezoelectric element 71b of FIG. 25, a piezoelectric element 71c as shown in FIG. 27 is used. Here, the thickness of the peripheral portion of the piezoelectric element 71c is 1.5 times the thickness of the central portion. On the acoustic emission surface side of the piezoelectric element 71c, an acoustic matching layer 75c having a thickness of a quarter wavelength of the frequency of the diagnostic portion of the piezoelectric element 71c is added to the entire surface.

FIGS. 28 (a) and 28 (b) show frequency characteristics of a diagnostic portion and a therapeutic portion by the ultrasonic probe 30C of this example. Since the acoustic impedance of the back surface of both the diagnostic portion and the therapeutic portion is lower than the acoustic impedance of the piezoelectric element 71c, the piezoelectric element resonates at a half wavelength. Therefore, the center frequency of the therapeutic portion is ⅔ times (f × (2/3)) the center frequency of the diagnostic portion.
An acoustic matching layer 75 having a thickness of 1/4 wavelength is provided for the diagnostic portion.
Since c and the back damping layer 76 are added, the bandwidth becomes wider as shown in the upper side (a) of FIG. 28. Therefore, when a pulsed electric signal is applied, a very short ultrasonic pulse is emitted. The shorter the ultrasonic pulse radiated, the more ultrasonic image with high distance resolution is generated.

On the other hand, a 1/6 wavelength acoustic matching layer 75c is added to the therapeutic portion, and the back surface is air.
If the acoustic matching layer 75c has such a thickness, it rather acts only as a protective layer that protects the piezoelectric element 71c and the electrodes on the surface thereof. Therefore, although the bandwidth is narrow as shown in the lower side (b) of FIG. 28, very high efficiency can be obtained at the center frequency. Therefore, when a continuous wave having the same frequency as the center frequency is applied, electric energy is converted into ultrasonic energy with high efficiency, and high sound pressure is obtained.

This example also exhibits the same operational effect, is particularly effective for improving the diagnostic ability, and since the frequency of the ultrasonic wave for diagnosis is increased, the distance resolution of the ultrasonic image is improved and the affected area can be more accurately measured. It can be diagnosed and treated in detail.

[Modification 2 of Tenth Embodiment] Further, also in the present embodiment, the above-mentioned [Modification 1 of the ninth embodiment] to [Ninth Embodiment].
Modification 5 of the embodiment] can be carried out in the same mode.

[Modification 3 of Tenth Embodiment] Further, the ratio of the frequencies of the therapeutic ultrasonic waves and the diagnostic ultrasonic waves is not limited to the numerical values given here, and an arbitrary value is selected according to the application site or the like. it can.

The ninth embodiment and the tenth embodiment (including their modified examples) are the same as the first embodiment to the third embodiment.
It can be implemented in combination with any of the embodiments (including their modifications). Also, for example, the fourth
It can be implemented in combination with any of the embodiments to the sixth embodiments (including their modified examples).

The contents described in each of the above embodiments and modifications can be understood as the following inventions. [1] Ultrasonic treatment oscillator and ultrasonic reflection reflector so as to sandwich a treatment target region. And a concave mirror having a different curvature on the reflector for ultrasonic wave reflection. [2] An ultrasonic treatment oscillator and an ultrasonic reflection reflector are provided so as to sandwich the treatment target region, and a curved portion is provided to change the direction and direction of the mirror provided on the ultrasonic reflection reflector. Ultrasonic therapy device.

[3] In an ultrasonic therapy apparatus that visualizes information inside a subject and irradiates the subject with strong ultrasonic waves for treatment, an ultrasonic transducer that emits ultrasonic waves for treatment is used. , Transmitting an ultrasonic wave of a level that does not produce a therapeutic effect in a burst wave, receiving the echo reflected by the burst wave in the subject and obtaining the convergence position of the ultrasonic wave for treatment from the echo An ultrasonic therapy device characterized by being capable of being superimposed and displayed on information, or an ultrasonic therapy device in which this is combined with any one of the above-mentioned additional items [1] and [2]. [4] The ultrasonic therapeutic apparatus according to the above-mentioned additional item [3], wherein the ultrasonic wave for treatment receives the burst wave. [5] The ultrasonic treatment apparatus according to the above-mentioned additional item [3] or [4], wherein the information inside the subject is acquired by ultrasonic waves.

[6] The ultrasonic therapeutic apparatus according to the above-mentioned additional item [5], wherein the reception of the burst wave is performed by a diagnostic ultrasonic probe for obtaining information inside the subject. [7] Information on the inside of the subject is analyzed by a nuclear magnetic resonance apparatus (MRI)
The ultrasonic treatment apparatus according to the above-mentioned additional item [3] or [4].

[8] When driving an ultrasonic probe that transmits or receives ultrasonic waves including a piezoelectric element and a coaxial cable that is electrically connected to the piezoelectric element and has a length that cannot be treated as a lumped constant In addition, an ultrasonic probe driving method or device characterized by driving with a continuous wave or a burst wave having a frequency near the anti-resonance frequency of the piezoelectric element, or this and the above-mentioned additional items [1] to [7]. Combination with either.

[9] The ultrasonic probe driving method or device according to the above-mentioned additional item [8], wherein the electric impedance of the piezoelectric element matches the characteristic impedance of the coaxial cable in the vicinity of the antiresonance frequency.

[10] The drive frequency of the piezoelectric element changes following the anti-resonance frequency of the piezoelectric element, [8] or

[9] The ultrasonic probe driving method or apparatus according to [9]. [11] The above-mentioned item [8] or [8], wherein the driving frequency of the piezoelectric element is a constant value in the vicinity of the anti-resonance frequency of the piezoelectric element.

[9] The ultrasonic probe driving method or apparatus according to [9].

[12] A piezoelectric element and a cable for transmitting an electric signal to the piezoelectric element are provided. The piezoelectric element has a portion for transmitting pulsed ultrasonic waves and a portion for transmitting continuous wave or burst wave ultrasonic waves. In an ultrasonic probe having at least two parts, one part for transmitting the pulsed ultrasonic wave and one part for transmitting / receiving ultrasonic waves of continuous wave or burst wave are formed on the same piezoelectric element. An ultrasonic probe characterized by the above, or the above-mentioned additional items [1] to
Combination with any of [11]. [13] The part for transmitting pulsed ultrasonic waves is capable of receiving ultrasonic waves as well, [12] above.
The described ultrasonic probe. [14] The ultrasonic probe according to the above-mentioned additional item [12] or [13], wherein the portion for transmitting the continuous wave or burst wave ultrasonic wave is for ultrasonic therapy. [15] The ultrasonic probe according to the above-mentioned additional item [12] or [13], wherein the portion that transmits the continuous wave or burst wave ultrasonic wave can also receive the ultrasonic wave.

[16] A supplementary item [12] to [1] characterized in that a damping layer that absorbs and attenuates ultrasonic waves is provided on the opposite side of the acoustic emission surface of the portion that transmits and receives pulses.
5] The ultrasonic probe according to any one of 5). [17] On the acoustic emission surface of the part that transmits and receives pulses,
It has an acoustic matching layer.
2] The ultrasonic probe according to any one of [16]. [18] The portion for transmitting / receiving a pulse and the portion for transmitting a continuous wave or a burst wave have a continuous acoustic emission surface, and a surface opposite to the acoustic emission surface has a discontinuous shape. The ultrasonic probe according to any one of the above-mentioned additional items [12] to [17], characterized in that the thickness of the portion transmitting the pulse wave and the thickness of the portion radiating the burst wave or the continuous wave are different. [19] The ultrasonic probe according to any one of the additional items [12] to [17], characterized in that a piezoelectric element having a uniform thickness is used.

[20] The ultrasonic probe according to any one of [12] to [19] above, which is used for treatment using ultrasonic waves. [20] The ultrasonic probe according to the above-mentioned additional item [16], wherein the acoustic impedance of the acoustic damping layer is smaller than the acoustic impedance of the piezoelectric element.

[0152]

EFFECTS OF THE INVENTION According to the present invention, the ultrasonic treatment oscillator and the ultrasonic reflection reflector are provided so as to sandwich the treatment target region, and the ultrasonic shock waves are concentrated from the body to the treatment target region for treatment. It is possible to provide an ultrasonic therapeutic apparatus that can be suitably used for performing a treatment, is small, can be used transrectally, and can change the focus point of an ultrasonic shock wave. Further, it is possible to improve the convergence efficiency of ultrasonic shock waves at the treatment target site.

[Brief description of the drawings]

FIG. 1 is a diagram showing an embodiment of an ultrasonic treatment apparatus of the present invention.

FIG. 2 is a diagram showing an example of details of a mirror unit in the same example.

FIG. 3 is a diagram showing another embodiment.

FIG. 4 is a diagram showing an example of a mirror portion of a main portion, showing still another embodiment.

FIG. 5 is a diagram showing an example of a modification of the mirror unit in the same example.

FIG. 6 is a diagram showing an ultrasonic probe according to an embodiment of the improved ultrasonic treatment apparatus.

FIG. 7 is a diagram showing a therapeutic probe in the same example.

FIG. 8 is a diagram for explaining the internal structure of the probe body.

FIG. 9 is a diagram showing an outline of a circuit system in the same example.

FIG. 10 is a waveform chart for explaining the same example.

FIG. 11 is also a diagram for explaining a focal length.

FIG. 12 is also a diagram for explaining a display mode.

FIG. 13 shows an essential part of an example of a modified example of the same example, and is a diagram showing an ultrasonic probe.

FIG. 14 is a diagram showing an ultrasonic probe according to another example of the modification.

FIG. 15 is a diagram for explaining an ultrasonic therapy apparatus according to another embodiment and is a diagram showing an outline of a circuit system of a main part thereof.

FIG. 16 is a diagram provided for explaining yet another embodiment,
It is a figure which shows an example of a drive of a diagnostic oscillator and a therapeutic oscillator.

FIG. 17 is a diagram for explaining a display mode in the example.

FIG. 18 is a cross-sectional view showing a configuration of an ultrasonic probe, which is a diagram used for explaining an embodiment of an improved ultrasonic probe, a driving method, and an apparatus.

FIG. 19 is a diagram showing an outline of a circuit system in the same example.

FIG. 20 is used for explaining the ultrasonic probe driving in the same example.
It is an electric impedance-frequency characteristic view.

FIG. 21 is a diagram for use in explaining another embodiment and is a diagram showing an outline of a circuit system of a main part thereof.

FIG. 22 is a diagram for explaining the embodiment of the improved ultrasonic probe, and is an efficiency-frequency characteristic diagram of a diagnostic portion and a therapeutic portion when performing ultrasonic diagnosis and treatment.

FIG. 23 is a cross-sectional view of an ultrasonic probe according to a modified example of the same example.

FIG. 24 is a diagram showing a main part of another example of the modified example.

FIG. 25 is a cross-sectional view for explaining the configuration of an ultrasonic probe of another embodiment.

FIG. 26 is an efficiency-frequency characteristic diagram of a diagnostic portion and a therapeutic portion in the ultrasonic probe.

FIG. 27 is a sectional view for explaining the configuration of an ultrasonic probe according to a modified example of the same example.

FIG. 28 is an efficiency-frequency characteristic diagram of a diagnostic portion and a therapeutic portion in the ultrasonic probe.

FIG. 29 is a cross-sectional view of an ultrasonic probe shown as a comparative example.

[Explanation of symbols]

 DESCRIPTION OF SYMBOLS 1 Ultrasonic transducer 2 Ultrasonic treatment device 3 Driving unit 4 Mirror part 4-1,4-2,4-3,4-4 Concave mirror 5 Reflector probe 6 Treatment target part 7 Shaft 8 Bending part 9 Normal part 10- a, 10-b Mirror 20 Rotational axis 21 Ultrasonic wave oscillator for treatment 22 Ultrasonic wave oscillator for diagnosis 23 Piezoelectric element for treatment 24 Protective layer 25 Piezoelectric element for diagnosis 26 Acoustic lens 27 Back braking layer 30, 30 'Ultrasonic probe Tactiles 30A, 30B, 30C Ultrasonic probe 31 Hard shaft 32 Cap 33 Main body 34 Valve 35 Slip ring 36 Cable 37 Radial motor 38 units 39 Ball screw 40 Linear motor 51, 56 Divergence circuit 52 Treatment transducer drive Circuit 53, 58 Detection circuit 54, 94 Control circuit 55 Focus detection circuit 57 Diagnosis vibrator drive circuit 59 display device 60 line 71, 71a, 71b, 71c piezoelectric element 72 GND electrode 73 diagnostic electrode 74 therapeutic electrode 75, 75a, 75b, 76c acoustic matching layer 76, 76a back damping layer 77 insulating layer 78 housing 79 conductor 80 cable 81 Back Cover 82 Filling Material 91 Treatment Oscillator 92 Treatment Oscillator Drive Circuit 93 Impedance Measurement Circuit

Claims (1)

[Claims] 1. An ultrasonic treatment apparatus comprising an ultrasonic treatment oscillator and an ultrasonic reflection reflector so as to sandwich a treatment target region.