WO1994006380A1 - Ultrasonic irradiation apparatus and processor using the same - Google Patents
Ultrasonic irradiation apparatus and processor using the same Download PDFInfo
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- WO1994006380A1 WO1994006380A1 PCT/JP1993/001310 JP9301310W WO9406380A1 WO 1994006380 A1 WO1994006380 A1 WO 1994006380A1 JP 9301310 W JP9301310 W JP 9301310W WO 9406380 A1 WO9406380 A1 WO 9406380A1
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- ultrasonic
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- fundamental frequency
- wave
- piezoelectric
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
- A61N7/00—Ultrasound therapy
- A61N7/02—Localised ultrasound hyperthermia
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B17/00—Surgical instruments, devices or methods, e.g. tourniquets
- A61B17/22—Implements for squeezing-off ulcers or the like on the inside of inner organs of the body; Implements for scraping-out cavities of body organs, e.g. bones; Calculus removers; Calculus smashing apparatus; Apparatus for removing obstructions in blood vessels, not otherwise provided for
- A61B17/22004—Implements for squeezing-off ulcers or the like on the inside of inner organs of the body; Implements for scraping-out cavities of body organs, e.g. bones; Calculus removers; Calculus smashing apparatus; Apparatus for removing obstructions in blood vessels, not otherwise provided for using mechanical vibrations, e.g. ultrasonic shock waves
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
- A61N7/00—Ultrasound therapy
- A61N2007/0056—Beam shaping elements
- A61N2007/006—Lenses
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
- A61N7/00—Ultrasound therapy
- A61N2007/0078—Ultrasound therapy with multiple treatment transducers
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
- A61N7/00—Ultrasound therapy
- A61N2007/0086—Beam steering
- A61N2007/0095—Beam steering by modifying an excitation signal
Definitions
- the present invention relates to an ultrasonic treatment apparatus suitable for treating a malignant tumor, treating a thrombus or a calculus, and an ultrasonic wave having a function of generating an ultrasonic cavity for enhancing an ultrasonic echo image such as a blood flow. It relates to diagnostic equipment, ultrasonic chemical reaction accelerators, ultrasonic cleaners for solid surfaces, ultrasonic air bubble generators, and liquid sterilizers. Background art
- Treatment of malignant tumors and calculi using focused intense ultrasound is a non-invasive non-invasive treatment, and a treatment method that values the quality of life of patients (Quality of Life). It is expected that its social value will continue to increase in the future.
- Acoustic cavitation is considered to play an important role as a mechanism for generating therapeutic effects by such focused intense sound wave irradiation. It is also known that acoustic cavities play a significant role in promoting chemical reactions and cleaning by ultrasonic irradiation.
- Disinfection using chlorine has been performed for a relatively long time, but since the composition of the liquid to be treated is changed, neutralization or removal of residual chlorine is required for another purpose after disinfection. Operation is required, which is a problem in terms of safety and environmental costs.
- Sterilization using ultraviolet light does not use chemicals, so it is a simple sterilization method that can easily handle liquid after sterilization. It is widely used. However, since most organic compounds have a large absorption coefficient, ultraviolet rays cannot be expected to be very effective for liquids containing a large amount of organic compounds other than in the vicinity of the light source. It is known that irradiation of a liquid with ultrasonic waves produces acoustic cavitation, and sterilization can be performed by the action. Disclosure of the invention
- the present invention in view of the above-mentioned social demands and potential technical possibilities, provides an ultrasonic irradiation technology that generates acoustic cavities with significantly higher efficiency than conventional technologies. You It is intended to be This has the specific purpose of providing an ultrasonic therapy device that has virtually no side effects, or a highly efficient ultrasonic chemical reaction accelerating device, ultrasonic cleaning device, or ultrasonic sterilizing device ⁇ : I do.
- the ultrasonic therapy system can be given the function of preventing accidental firing, The purpose is to enhance which echo characteristics and improve the drawing power of the ultrasonic diagnostic apparatus.
- the ultrasonic cleaning device by having ultrasonic sources of multiple frequencies, not only can the cleaning capability be higher than that of a single frequency ultrasonic wave, but also the efficiency of the acoustic cavitation can be improved. It is an object of the present invention to provide a cleaning apparatus capable of obtaining a higher cleaning effect as a synergistic effect of a plurality of frequencies by setting a combination of frequencies that is generated in the same manner. .
- Bubbles involved in acoustic cavitation are almost inversely proportional to the frequency of the ultrasound used, so large bubbles collapse at lower frequencies.
- Semiconductor devices have become smaller in pattern size as their integration density has increased, and when ultrasonic waves of low frequency, such as 20 kHz, are used for cleaning, they become acoustic cavities.
- the size of the generated bubbles becomes approximately the same as the size of the pattern formed on the semiconductor element, which may have an adverse effect such as not entering the groove of the pattern of the semiconductor element and coming out. is there. Because of this high frequency It is necessary to use a number, but the problem is that acoustic cavities that are effective for cleaning are difficult to produce at high frequencies.
- An object of the present invention is to provide an ultrasonic irradiation method with a high generation efficiency of an acoustic cavity, which is a source of cleaning, and particularly to an acoustic wave effective for cleaning even at a high frequency of 500 kHz or more.
- An object of the present invention is to provide a cleaning apparatus having a higher cleaning capability than before by generating cavitation.
- the above-described collapse of the air bubble by the acoustic cavitation causes a region of high pressure and high temperature to be locally generated under specific conditions, and in a conventional ultrasonic cleaning apparatus, the acoustic cavitation of the acoustic cavitation is difficult.
- Figure 1 shows an example of a double frequency superimposed wave.
- Fig. 2B schematically shows the double-frequency waveform p2 and the states of generated and increasing bubbles on both the upper and lower sides.
- FIG. 2C is a diagram schematically showing a state in which the bubbles generated and increased by the waveform P 2 of the double frequency are further increased on the upper and lower sides of the waveform p 1 of the fundamental frequency.
- FIG. 3 is a block diagram showing the configuration of an embodiment of the ultrasonic irradiation apparatus according to the present invention.
- FIG. 4A is a top view showing a configuration of an example of an ultrasonic transducer section in the embodiment of FIG.
- FIG. 4B is a side view showing the configuration of an example of the ultrasonic transducer unit in the embodiment of FIG.
- FIG. 5 shows an ultrasonic transducer in the embodiment of FIG. The figure which shows the structure of another example of a part.
- Figure 6 shows the experimental results of a sonochemical reaction using a double-frequency superimposed wave.
- FIG. 8 is a cross-sectional view showing a configuration of a piezoelectric thickness vibrator of the ultrasonic transducer part in the embodiment of FIG.
- FIG. 9 is a diagram showing an example of a rectangular driving waveform of the piezoelectric thickness oscillator of FIG.
- FIG. 10 is a diagram showing an example of a step-like drive waveform of the piezoelectric thickness oscillator of FIG.
- FIG. 11 is a diagram showing a configuration of a piezoelectric vibrator peripheral circuit of the ultrasonic transducer section in the embodiment of FIG.
- FIG. 12 is a diagram illustrating an example of a configuration of a piezoelectric vibrating element drive circuit of the ultrasonic transducer in the embodiment of FIG. 7;
- FIG. 13 is a diagram illustrating an example of a push-pull switching circuit constituting a piezoelectric vibrating element drive circuit of the ultrasonic transducer in the embodiment of FIG. 7;
- FIG. 14B is a side view showing the configuration of an example of the ultrasonic transducer section in the embodiment of FIG.
- FIG. 15 is a diagram showing another configuration example of the ultrasonic transducer unit in the embodiment of FIG.
- FIG. 16 shows the ultrasonic transdues in the embodiment of FIG. The figure which shows another example of the piezoelectric vibration element drive circuit of a sa part.
- Fig. 17 is a timing chart for driving the stepped waveform of the piezoelectric thickness oscillator shown in Fig. 8.
- FIG. 19 is a cross-sectional view of an example of a non-focus type plane wave transducer employed in the present invention.
- FIG. 20 is a cross-sectional view of an example of an insertion needle-shaped transducer used in the present invention.
- FIG. 22 is a diagram showing another example of the configuration of the intraoperative ultrasonic therapy transducer of the present invention.
- FIG. 23 is a diagram showing an example of a reactor configuration of the ultrasonic chemical reaction device of the present invention.
- FIG. 24 is a diagram showing another example of the reactor configuration of the ultrasonic chemical reaction device of the present invention.
- FIG. 25 is a diagram showing an example of the configuration of the ultrasonic cleaning device of the present invention.
- FIG. 26 is a diagram showing another example of the configuration of the ultrasonic cleaning apparatus of the present invention.
- FIG. 27 is a view showing still another example of the configuration of the ultrasonic cleaning apparatus of the present invention.
- FIG. 29 is a diagram showing an example of the configuration of the sterilization apparatus of the present invention.
- FIG. 30 is a diagram showing another example of the configuration of the sterilization apparatus of the present invention.
- the pressure waveform changes from a sinusoidal wave to a so-called N-wave (the rise of the pressure falls). It is known that it is deformed into a steeper wave shape. This is due to the non-linearity that the sound pressure increases as the pressure of the medium increases.In the case of a pulsed ultrasonic wave, the positive pressure peak becomes negative as well as the propagation. It is known that the waveform is deformed into a waveform larger than that of the c.
- acoustic cavities are difficult to generate in a transmission or propagation type sound field without strong reflectors, but are likely to be generated in an ultrasonic sound field with strong reflectors. It has been known. The above results indicate that the pressure fall caused by the propagation of ultrasonic waves is slower than the rise, and waves where the negative pressure peak is smaller than the positive pressure peak are acoustic cavities. This is disadvantageous for generating sound, but it is considered that if the phase is inverted by the reflector and the waveform changes, it is considered to be advantageous for generating the acoustic cavities. it can.
- the present invention provides a configuration in which an ultrasonic wave having a frequency twice as high as that of the fundamental frequency can be combined with the ultrasonic wave at the irradiation target.
- an ultrasonic wave having a frequency twice as high as that of the fundamental frequency can be combined with the ultrasonic wave at the irradiation target.
- the fundamental frequency P1 and the double frequency p2 can be generated simultaneously from the same transmitting element or from separate transmitting elements, and transmitted so that they are combined at almost the same focal point.
- a wave filter can also be configured.
- the fundamental frequency p1 and the multiple frequency p2 that can generate the acoustic cavities more limited near the focal point are generated from a plurality of transmitting elements, respectively.
- a pulse wave having a frequency higher than the above-mentioned double frequency is transmitted so that the position where the acoustic cavitation is generated can be monitored as a position in the ultrasonic echo image.
- the fundamental frequency p1 and the double frequency p2 are devised to be simultaneously generated from the same transmitting element. I suggest an example.
- the same object is simultaneously irradiated with a plane wave having a fundamental frequency and a plane wave having a frequency twice that of the fundamental wave so that the wavefronts of both frequencies are substantially parallel to each other. Suggest a configuration.
- the generation of the acoustic cavities described above is performed using the same method as the cleaning using ammonia and hydrogen peroxide or hydrogen peroxide and sulfuric acid in the semiconductor device manufacturing process. It proposes effective use in a chemical process of oxidizing substances attached to the surface of semiconductor devices.
- the fifth embodiment proposes the use of liquid for sterilization.
- specific examples of the synthesis of the ultrasonic wave of the fundamental frequency p 1 and the ultrasonic wave of the double frequency p 2 and the ultrasonic wave, which can efficiently generate the acoustic cavities in the irradiation target, will be described first. I will tell.
- Figures 2A and 2B show that when the waveform pi of the ultrasonic wave at the fundamental frequency f is represented as sin (2 ft) at time t, the waveform of the double frequency P 2 is approximated to sin (47 ft). It shows the sound pressure waveform when such a phase relationship is set, and is synthesized. The fall is sharper than the rise of the sound pressure, which is extremely advantageous for generating acoustic cavities. This is a simple example. Taking this case as an example, the operation of generating the acoustic cavities will be schematically described.
- FIG. 9 is a diagram showing a waveform obtained by synthesizing a waveform p 2 of a frequency doubled with sin (4; rft).
- Fig. 2B schematically shows the waveform of the double frequency waveform P2 and the generated and increasing bubbles on the upper and lower sides.
- FIG. 2C schematically shows the waveform of the fundamental frequency P 1 and the upper and lower sides of the waveform P 2, which are generated and increased by the double frequency waveform p 2.
- the radius of the cavity bubble oscillates at the period of the double frequency, but at the beginning of bubble generation, as shown in the upper part of FIG. 2B, the radius is smaller than the radius of the resonant bubble. It is small, and becomes the maximum (for example, b1) at the negative pressure peak of the double frequency, and becomes the minimum (for example, b2) at the positive pressure peak. That is, expansion and contraction are repeated within the range of b 1 and b 2.
- the phase of the vibration of the bubble radius is delayed by 90 degrees, and the radius of the bubble increases.
- Is maximum eg, b 3
- the bubble corresponding to the positive pressure is substantially the same as at non-resonance (for example, b4).
- the cavity bubble grows further by receiving the energy of the fundamental frequency and reaches at least the size of the resonant bubble at the fundamental frequency (eg, c 2).
- the bubble corresponding to the positive pressure is substantially the same as the bubble corresponding to the initial positive pressure at the double frequency both at the time of resonance and at the time of non-resonance (for example, c3 and c4).
- the bubbles to be crushed When the grown bubbles are crushed, energy is locally generated by adiabatic compression of the gas inside. In order for this energy to be sufficient for triggering chemical reactions, etc., the bubbles to be crushed must have at least a certain size or more. . If the fundamental frequency is chosen somewhat lower, the resonant bubble can be set to a size greater than its required size. However, when irradiating the fundamental frequency alone, the problem arises that if the resonance bubble of the fundamental frequency is too large, then the generation of cavities cannot be started sufficiently. On the other hand, by using the method of the present invention and superimposing a double frequency having an appropriate phase relationship, the start of cavitation generation and the growth of cavitation bubbles to a sufficient size can be achieved. Can be efficiently performed in cooperation with the double frequency and the fundamental frequency, respectively.
- an ultrasonic echo image of the irradiation target is formed by transmitting and receiving a pulse wave having a frequency higher than the above-mentioned double frequency.
- the ultrasonic imaging unit it is possible to perform self-consistent monitoring using waves having substantially the same speed as the ultrasonic waves for applying the effect of the acoustic cavitation to the irradiation target.
- monitoring that is relatively unaffected by the sound velocity distribution of the intermediate medium can be realized.
- the ultrasonic imaging unit should receive an even-multiple frequency component of the ultrasonic multiple frequency for exerting the effect of the acoustic cavitation on the irradiation target. With such a configuration, it is possible to display the position where the acoustic cavitation is generated or the position where the generation is likely to be superimposed on the ultrasonic echo image.
- Information on the ultrasonic irradiation treatment strategy is input to the irradiation unit main control circuit 20 from the key input means 31 and the focal position and sound pressure distribution shape of each of the fundamental and double frequency irradiation sound fields are defined based on the information.
- the irradiation focus code signal to be applied is supplied from the irradiation section main control circuit 20 to the drive phase generation circuit I (11) and the drive phase generation circuit II (12), respectively.
- the driving phases of the generated fundamental and multiple frequency irradiation transducers are determined by the drive signal generation circuit 7 — 1 to 7 — N (where N is an independent transducer) Of the fundamental frequency) and the drive signal generation circuits 8-1 to 8 _ M (M is the total number of multiplicity of the transducer independent elements).
- the drive amplitudes of the fundamental frequency and the double frequency are given from the irradiation section main control circuit 20 to the respective drive signal generation circuits 7-1 to 7-N and 8-1 to 8-M.
- the generated driving signals of the fundamental frequency and the double frequency are respectively applied to the element driving circuits 3-1 to 3 -N and 4-1 to 41 M, and the irradiation transducer fundamental frequency element group 1-1 1 1 N and the double frequency element group 2 — 1 2 2 -M are driven respectively.
- the drive amplitude is configured to be controlled also by a signal directly applied from the irradiation section main control circuit 20 to the element drive circuits 3-1 to 3-N and 41-41-M. The emergency stop of ultrasonic irradiation when an abnormality occurs is ensured and easy.
- the receiving amplifiers 9 — 1 to 9 — N and 10 — 1 to 10 — M are variable gains, and the gains are controlled by signals directly supplied from the irradiation unit main control circuit 20. You. During times when a lot of unnecessary signal components are generated even at a frequency other than the irradiation ultrasonic center frequency, such as when switching the irradiation focus, this gain should be dropped to avoid amplifier saturation.
- the reception focus circuit I (13) and the reception focus circuit 11 (14) converge at a plurality of focal points arranged at intervals corresponding to the spatial resolution of the reception system within the irradiation focal area. Frequency f0 / 2.f with focus circuits in parallel and radiated by the cavities.
- Such as harmonic components and 3f. Z 2,5 fo no 2,7 f. / 2 Detects the generation and position of generation of ultrasonic waves of harmonic components of subharmonics.
- a signal indicating the position where the cavitation is generated and the intensity of the cavitation is supplied to the display circuit 30.
- the reception focus circuit I (13) and the reception focus circuit I (13) are configured by using a number of parallel processing focus circuits smaller than the above-mentioned number of focuses and scanning each focus. To reduce the cost of the signal focus circuit II (14) You can do it.
- 21 is an array type transmission / reception probe dedicated to ultrasonic imaging
- 2 2 is a rotation mechanism for rotating the probe around an axis perpendicular to the probe surface.
- the structure is such that multiple ultrasonic pulse echo tomographic images required for the squeezing can be obtained.
- Each element of the probe 22 is connected to a transmission control circuit 23 and a reception focus circuit 25 via a transmission / reception amplifier 24.
- the display circuit 30 displays, on the obtained echo tomographic image, the cavities detected by the reception focus circuit I (13) and the reception focus circuit ⁇ (14). It is configured such that a signal indicating the position and intensity of the generated signal is superimposed and displayed.
- the ultrasonic frequency band of the probe 21 is 4 f. Above. Also, frequency 4 f radiated by the cavity. , 6f. , 8f. Such as harmonic components and 9f.
- the harmonic components of the subharmonics such as Z 2 are detected by the probe 21 rather than the element group 1-1-1 to 1-N and the element group 2-1-1-2-M. It may be configured.
- the irradiation section main control circuit 20 controls the drive phase generation circuit I (11) and the drive phase generation circuit II (12), and the drive signal generation circuits 7-1 to 7—N and 8-1.
- ⁇ 8-M is controlled to transmit pulse ultrasonic waves in synchronism with the ultrasonic pulse transmission for imaging of the probe 21 for the ultrasonic imaging. 1 to 1 N and 2-1 to 2 — Obtained by transmission by M and reception by probe 21
- the strong ultrasonic focus position for generating the cavity can also be displayed so as to be superimposed on the echo tomographic image obtained by transmission and reception by the probe 21.
- the efficiency of the generation of cavities depends on the relative phase relationship between the fundamental frequency and the over-multiplied frequency, so that the harmonic components radiated by the cavities and the harmonics
- the drive signal generation circuits 7-1 to 7_N and 8-1 to 8-N are controlled to maximize the strength of the harmonic components of the wave, and the relative phase relationship is optimized. As a result, more efficient generation of cavities can be realized. If it is difficult to optimize the harmonic components or the harmonic components of the subharmonics based on the strength of the harmonic components, or if you want to omit the function, shift the relative phase relationship with respect to the multiple frequency; / 8/8 to ⁇ / 4.
- the reception focus circuit 25 sends the irradiation section main control circuit 2 Based on the signal given to 0, control is performed so that the irradiation focus moves in accordance with the movement of the target position.
- the movement of the target area is too large and exceeds the irradiation focus range.
- the ultrasonic irradiation timing is synchronized with the respiration based on the signal given from the respiration detection unit 32 to the irradiation unit main control circuit 20, and the respiration time phase is adjusted. Control so that ultrasonic irradiation is performed only within a certain range.
- the drawing power of the ultrasonic diagnostic apparatus of the present embodiment can be improved. That is, two-frequency superimposed ultrasonic irradiation is performed at a relatively small intensity using the element group 11 1 to 11 N and the element group 2 1 to 2 N, and the ultrasonic pulse echo using the probe 21 is performed. Acoustic cavitation is efficiently generated in the object to be drawn by the scanning method to emphasize the echo characteristics of the object to be drawn, such as blood flow, and the ultrasonic pulse echo method using the probe 21 alone does not It is possible to render blood flow in minute blood vessels and low-speed blood flow, which are difficult to draw even by the method.
- FIGS. 4A and 4B show, for example, a 16-sector X2 trap composed of ultrasonic element groups 1 — 1 to 1 — N and 2 — 1 to 2 — M.
- Fig. 1 shows an array-type high-intensity ultrasonic transducer.
- Figure 4A shows the transducer viewed from below, showing each element group and some of its peripheral circuits.
- Figure 4B shows the cross-sectional structure of the transducer.
- This focused high-intensity ultrasonic transducer has a minimum required number of elements, N + M, to enable the focal point to travel.
- the geometrical focus is obtained by arranging the ultrasonic element groups 11-1 to 1-N and 2-1 to 2-M on the light alloy spherical shell 33.
- the light-alloy spherical shell 33 mainly composed of magnesium or aluminum has a concave surface that forms a part of a spherical surface centered on the geometrical focus F on the ultrasonic irradiation surface side, and has a back surface.
- the side has a polished polyhedral shape for bonding ultrasonic elements made of piezoelectric ceramic.
- Light alloy sphere shell 33 has good thermal conductivity and is effective for cooling piezoelectric elements during irradiation with strong ultrasonic waves, and also works as a ground electrode for each piezoelectric element. I have. In addition, it forms part of a transducer housing, and is provided with a cooling fluid passageway 33 for removing heat generated during irradiation with high-intensity ultrasonic waves. A water bag 35 with degassed water is installed to facilitate the operation.
- the light alloy mainly composed of magnesium aluminum has an acoustic impedance between the piezoelectric ceramic and the degassed water for coupling, so that the spherical shell 33 is located between the two. Also works as an acoustic matching material.
- the thickness of the spherical shell 33 is selected so as to be a half wavelength at the fundamental frequency and one wavelength at the double frequency, but the fundamental frequency elements 1-1 to 11N
- the thickness is changed between the portion of the frequency band and the portion of the frequency multiplier 2 _ 1 to 2 — M, and the frequency is set to 1 Z 4 wavelength at each frequency, so that the transmission and reception characteristics of pulsed ultrasonic waves can be improved. You can also.
- a pulse echo transmission / reception probe 21 dedicated to ultrasonic imaging is placed in the circular hole at the center of the array shown in Figs. 4A and 4B.
- the basic structure of the probe 21 is the same as that of the sector scanning array probe used in the ultrasonic diagnostic apparatus.
- the probe 21 is used in place of the transducer 'nosing 33'. It is rotatable around the central axis, and its rotation is performed by a rotation mechanism 22.
- the geometrical focal length of the transducer is about 12 cm
- the outer diameter of the array is about 12 cm
- the inner diameter is about 4 cm
- the diameter of the circle separating the two tracks is about 12 cm. 8 cm. Since the diameter of the outer track that generates the fundamental frequency is approximately twice the diameter of the inner track that generates the harmonic, the diameter of the fundamental frequency spot at the focal plane and the diameter of the double-frequency spot The diameters of the birds are almost equal, and the generation of cavitation due to the synergistic effect of the two frequencies is performed efficiently.
- the outer diameter of the array is 12 cm
- the inner diameter is 3 cm
- the diameter of the circle separating the two tracks is 6 cm
- the outer side, the inner side, and the inner side Are almost exactly similar in wavelength ratio, so that the peak sound pressure distribution of the double frequency at the focal plane is almost the same as the fundamental frequency.
- the fundamental frequency and the double frequency are irradiated simultaneously. Since only the vicinity of the focal point is set, by setting the focal point on the irradiation target, the cavities can be efficiently generated locally only in the vicinity of the focal point.
- FIG. 5 is an example in which a rectangular array is used for the ultrasonic transducer part of the present embodiment.
- the ultrasonic transducer consisting of a rectangular piezoelectric ceramic with a short side of 4 c.m and a long side of 16 cm is divided into 2 N + M elements, with 2 N at both ends of the short side. These elements are electrically connected to each other, and are an array consisting of N electrically independent fundamental frequency generators 1 — 1 to 1 — N and M multiple frequency generators 2 — 1 to 2 — M.
- ⁇ Transducers are formed.
- the irradiation surface side of the acoustic matching layer 33 made of a light alloy mainly composed of magnesium or aluminum forms a part of a cylindrical surface, and the concave portion has a sound velocity similar to that of water. Filled with a slower polymer acoustic filler 36, the surface is shaped to be flat or convex, and the geometry converges on the line segment F'F '' as a whole. It forms a strategic focus.
- the ultrasonic transducer of the embodiment shown in Fig. 5 has a basic structure that also functions as a linear scanning or sector scanning array probe used in an ultrasonic diagnostic apparatus. have. Accordingly, of the basic configuration shown in FIG. 3, the probe 21 dedicated to ultrasonic imaging and its rotation mechanism 22, the transmission control circuit 23, the transmission / reception amplifier 24, and the reception focus circuit 2 5 None of the ultrasonic pulse echo cuts required to position the irradiation target A layer image can be obtained. However, like a normal linear scanning or sector scanning probe, the tomographic plane that can be imaged is only in the direction parallel to the long side.
- the width in the short side direction of the fundamental frequency generating element that is electrically connected in common is about twice as large as the width in the short side direction (direction orthogonal to the array arrangement direction) of the double frequency generating element.
- the spread of the fundamental frequency spot and the double frequency spot in the short side direction on the focal plane are almost equal, and the generation of cavities by the synergistic effect of the two frequencies is performed efficiently. It is.
- the fundamental frequency and the double frequency are synthesized in the medium, and the two frequencies are simultaneously irradiated only in the vicinity of the focal point. Cavitations can be efficiently generated locally only in the vicinity. This means that the potential for side effects at sites distant to the front or back of the irradiation target can be substantially eliminated when the sonication guided by the cavity is used for therapeutic purposes. This leads to the ability to do it.
- FIG. 6 shows the sonochemical reaction rates when the fundamental frequency of 75 kHz and the multiplied frequency of 1.5 MHz were simultaneously irradiated while keeping the sum of the ultrasonic waves of both constant.
- This is a plot of the ratio of the fundamental frequency to the frequency.
- the sum of the ultrasonic intensity of the fundamental frequency and the multiple frequency near the focal point was about 30 WZ square cm.
- the sonochemical reaction rate was 0 within the experimental error range when the fundamental frequency and the overtone were used alone, but the synergistic effect when both frequencies were irradiated simultaneously was remarkable.
- the transmitting element is composed of a piezoelectric material or a material having the same acoustic impedance as that of the piezoelectric element, and the entire thickness is set to a half wavelength for the fundamental frequency, and not the entire thickness.
- the drive waveform does not include a component of an even multiple of the fundamental frequency. Since it is not suitable for generating even-number-frequency ultrasonic waves, it is necessary to devise a drive circuit that uses a waveform containing the target frequency component as a drive waveform.
- the first contrivance is that when a square wave is used as the driving waveform, the ratio of the time to stay at two high and low potentials as usual is not a 1: 1 ratio but an asymmetric ratio Things.
- a second approach to the drive circuit is to use a sawtooth wave or a staircase wave simulating the sawtooth wave instead of a square wave as the drive waveform.
- the acoustic thickness (attention Consider a configuration in which the region corresponding to the ratio of ⁇ from the end is piezoelectrically driven in the case where the vibrator is not uniform with respect to the sound speed of the resonance mode in which it is not uniform).
- the piezoelectrically driven portion 71 of the piezoelectric body and the non-piezoelectrically driven portion 72 are acoustically integrated by means of sintering or a strong adhesive. .
- an electric field is applied between the electrode 74 and the electrode 73 covering the portion 72.
- the portion 72 covered with the electrode 74 is a portion that is not driven piezoelectrically.
- ⁇ i (F / 4) sin 2 2 ⁇ ⁇ (4).
- F is a constant determined by the difference between the two potentials, that is, the amplitude.
- ⁇ is obtained from (Equation 3) and (Equation 4).
- F, ⁇ ! 0, including the fundamental frequency component, but not the double frequency component.
- a sawtooth wave or a staircase wave simulating the sawtooth wave is used as the drive waveform instead of the rectangular wave.
- a sawtooth wave has a frequency component that is an even multiple of the fundamental frequency. Therefore, here, the case of a staircase wave that simulates this will be described in detail.
- the fundamental frequency included in a staircase wave with a ratio of the time to stay at two high and low potentials and the time to stay at an intermediate potential is 7: (1-r). Power of the component and its double frequency component 7? 0 and? ? 1 is
- a capacitor is connected in parallel to the piezoelectric vibrator, the total capacitance is C (43), and the inductors L (44), L (45) and
- capacity C (46) is added, when it can be considered that terminals 41 and 42 are connected to a drive circuit with sufficiently low output impedance, the terminal 41 side the electrical Yi down impedance as seen from the tail and the terminal 4 2 side Z, you and Z 2, when the angular velocity ⁇ rather far
- FIG. 7 shows the overall configuration of an embodiment of the ultrasonic irradiation apparatus of the present invention having an acoustic cavitation generation position monitoring function using the wave transmitting element devised as described above, and FIG.
- the configuration is shown in Figs. 12 and 13, and the configuration of the ultrasonic transducer is shown in Figs. 14 ⁇ and 14 4.
- This embodiment is the same as the embodiment in FIG. 3 except that the transmitting element is shared by the fundamental wave and the double frequency.
- Information on the ultrasonic irradiation treatment strategy is input from the key input means 31 to the irradiation unit main control circuit 20, and based on the information, the focus position •
- the driving phases of the generated fundamental frequency and double frequency irradiation transducers are determined by the drive signal generation circuits 7 — 1 to 7 — ⁇ (where ⁇ is the total number of transducers and independent elements). ).
- the control signals of the drive amplitudes of the fundamental frequency and the double frequency are supplied from the irradiation section main control circuit 20 to the drive signal generation circuits 7-1 to 7- ⁇ .
- the generated drive signal is supplied to the element drive circuits 3-1 to 3--, and the irradiation transducer element groups 11 1 to 1— ⁇ are driven. It is.
- the drive amplitude is also controlled by a signal directly applied from the irradiation section main control circuit 20 to the element drive circuits 3-1 to 3-N.
- Fig. 12 shows the circuit configuration of one element driving circuit 3-1 to 3-N
- Fig. 13 shows the push-pull switching circuit that constitutes a part of it. Is shown.
- the output units of the basic frequency drive unit 47 and the double frequency drive circuits 48 have the basic configuration shown in FIG. Is connected to each element through a circuit resonating at the frequency doubled 2 ⁇ 0 and.
- capacitance C and inductance L are the fundamental frequency f. It is a combination that resonates at. That is,
- the switching circuit shown in Fig. 13 consists of a constant potential source 49 on the low potential side (ground potential in this case) and a constant potential source 5 on the high potential side.
- the connection between 0 and the output terminal 52 is interrupted by switching elements 53 and 54, respectively.
- the output terminal 52 is connected via a capacitor 58 to output only the AC component.
- To stabilize the power supply potential connect a canon between the constant potential sources 49 and 50.
- System 58 connected.
- the input terminal 51 is connected directly to the gate of the switching element 53 on the ground potential side, but is connected directly to the gate of the switching element 54 on the high potential side. 5 is connected through.
- the direct current level of the gate is determined by the opening of the Zener diode 56 having a Zener potential of the gate drive signal amplitude (difference between the highest potential and the lowest potential).
- the potential is controlled so as to be equal to the potential of the high potential side constant potential source 50.
- a resistor 5 ⁇ ⁇ ⁇ is connected in parallel with the Zener diode 56.
- the irradiation transducer composed of the element groups 11 to 11N can be used as a reception transducer for detecting cavities generated in the irradiation target. Operate.
- the signals received by each element are converted into the reception amplifiers 9-1 to 9-1 after the components of the irradiation signal band are removed by the band rejection filters 5-1 to 5-N, respectively. It is guided to N, amplified, and supplied to the reception focus circuit 13.
- the element drive circuits 3-1 to 3-N output the frequency f. And 2 f. Since it is connected to a low impedance circuit via a resonant circuit that resonates at f, f. And 2 f. At frequencies outside of this range, the output impedance of the drive circuit does not shunt and hinder reception sensitivity.
- the display of the echo-one tomographic image by the array transmission / reception probe 21 dedicated to ultrasonic imaging and the response to the respiratory movement of the target site are the same as those in the embodiment of Fig. 3, so the description is omitted. I do.
- FIGS. 14A and 14B the difference between the ultrasonic transducer of this embodiment and the ultrasonic transducer shown in FIGS. 4A and 4B will be described. Will be described.
- Fig. 14 Transducer of 14A seen from below, each element group and its surroundings The diagram showing a part of the circuit is the same.
- This piezoelectric inactive plate may be made of a piezoelectric inactive material such as zinc or copper having an acoustic impedance almost equal to that of the piezoelectric ceramic. With such a configuration, a piezoelectric vibrator having piezoelectric activity at both the fundamental frequency and the multiple frequency is realized.
- the transmitting elements 111 and 112 are displayed with the same thickness.
- the spherical shell 33 that forms a part of the housing is made of zinc or copper instead of light alloy, giving a thickness of 1/6 wavelength at the fundamental frequency and 1/3 wavelength at the fundamental frequency. Even if a piezoelectric ceramic element with a wavelength thickness is attached, it can be made piezoelectrically active at both the fundamental frequency and the double frequency, as shown in Figs. 14A and 14B. The configuration is slightly better in acoustic separation between adjacent elements.
- FIG. 15 shows an example in which a rectangular array is used for the ultrasonic transducer portion of the present embodiment.
- FIGS. 4A and 4B correspond to FIGS. 14A and 14B.
- the drawing differs from FIG. 5 only in that the transmitting elements 11 1 and 11 2 are displayed with the same thickness.
- 1-1-1 to N 2-1 to 2-N, 3-1 to 3-N
- 1-1-1 to N and 3-1-1 to N correspond to Although the elements are electrically connected to each other, they can be driven in different phases with respect to the element groups 2-1 to 2—N, so that the focus on the short side is also deep.
- the focal point can be moved in the vertical direction.
- the ratio of the time to stay in each state is not 1: 1 but rather By controlling the unequal ratio, such as 1: 3, it is possible to simultaneously irradiate the ultrasonic wave of the fundamental frequency and the ultrasonic wave of twice the frequency.
- FIG. 10 shows a simple circuit configuration.
- This circuit drives one element per element, and drives the piezoelectric vibrator.
- the gate input terminals 66, 65, 68, and 67 of the drive circuit consisting of the grouping of the ring elements 54, 53, 63, and 64 are connected to the smaller timing circuit shown in Fig. 17.
- the input terminal 67 is directly connected to the gate of the tuning element 63, but other input
- the input terminals 65, 66, and 68 are connected to the gates of the switching elements 53, 54, and 64, respectively, and are connected to the gates of the switching elements 54 in FIG. They are connected via the same circuit as the circuit. Diodes 61 and 62 are connected in series to prevent backflow of the switching elements 63 and 64, respectively.
- FIG. 18 is a cross-sectional view showing an example of a single-focus manual scanning type transducer.
- the present invention is also applicable to a mechanical scanning type trans- ducer, a non-focus type plane wave transducer whose example is shown in a cross-sectional view in FIG.
- the electrode 73 is connected to a coaxial connector 76 by a lead wire 75.
- a housing 77 made of a metal having high thermal conductivity such as copper or aluminum is provided with a cooling water channel 78 so as to remove heat generated from the piezoelectric body during the operation of generating ultrasonic waves, and in some cases. In some cases, the ultrasonic irradiation target is cooled.
- the thickness of the central part of the acoustic lens 79 made of magnesium or a magnesium-based alloy is set to 1/4 or 1/2 wavelength at the fundamental frequency to achieve high efficiency. We are trying to secure it.
- the thickness of the flat plate 79 made of light metal such as magnesium or aluminum shall be 1/4 or 1/2 wavelength at the fundamental frequency. This ensures high efficiency.
- a therapeutic effect can be obtained by applying a plane wave transducer as shown in FIG. 19 to the body surface or by using it intraoperatively.
- a therapeutic effect can also be obtained by inserting a needle-shaped transducer, an example of which is shown in a cross-sectional view in FIG. .
- the ultrasonic wave is rather diffused by the conical portion 81 of the tip made of magnesium or a magnesium-based alloy.
- the conical portion 81 at the tip may be made of a material having a relatively low sound speed.
- This embodiment is similar to the embodiment of FIG.
- the phase rotation due to the diffraction effect can be ignored, so that the plane waves of both frequencies are combined so that the wavefronts of both frequencies are parallel to each other in each near field.
- the focus was on the fact that the phase relationship between the two frequencies over a wide area could be made an advantageous condition for the generation of acoustic cavities.
- FIG. 21 shows an example of the configuration of an intraoperative ultrasonic therapy transducer section of the ultrasonic therapy apparatus according to one embodiment of the present invention.
- the planar piezoelectric bodies 1 and 2 which generate a fundamental frequency and a double frequency, respectively, are mounted so as to face each other in parallel. Both piezoelectric bodies are acoustically bonded to the acoustic matching layers 79-1 and 79-2 made of a magnesium alloy with sufficient strength acoustically.
- the heat generated during the generation of ultrasonic waves is guided from these high thermal conductivity acoustic matching layers to the housings 77-1 and 77-2, which are made of metal with high thermal conductivity, and then cooled. Irrigation from the transducers by irrigation canals 7 8-1 and 7 8-2. In some cases, this cooling function can also be used for the purpose of cooling the vicinity of the surface of the affected part to be irradiated with ultrasonic waves.
- the affected area is sandwiched between the planar piezoelectric bodies 1 and 2 so that the fundamental frequency and the double frequency are superposed on both sides of the affected area. Irradiate sound waves at the same time.
- the distance between the planar piezoelectric bodies 1 and 2 can be adjusted by the parallel moving mechanism 90 while maintaining the parallelism.
- Acoustic matching layer of both piezoelectrics 7 9 1 1 and 7 9 In principle, the distance between the two surfaces is set to be an integral multiple of half the fundamental frequency.
- Fig. 22 shows an example of an intraoperative ultrasound therapy transducer configured to generate a fundamental frequency and a double frequency simultaneously from one piezoelectric body.
- planar piezoelectrics (71 and 72—this is the same as the configuration described in Figure 8), which simultaneously generates a fundamental frequency and a multiple frequency, the fundamental frequency is better than that of stainless steel.
- a reflector 92 having a thickness of an integral multiple of a half wavelength is attached so as to face in parallel.
- the flat piezoelectric body is acoustically bonded to a thickness diaphragm 79, which is made of a magnesium-based or aluminum-based alloy and has a thickness that is an integral multiple of half a wavelength at the fundamental frequency, with sufficient acoustically strong strength. I have.
- the standing wave sound field formed between the two acoustic matching layers 79-1 and 79-2 of the two-plane type piezoelectric bodies 1 and 2 in the embodiment of Fig. 21 is almost equivalent.
- This sound field can be formed between the thickness diaphragm 79 and the reflector 92.
- the reflector 92 can be designed to be much thinner than the housing 79-9-2 of the planar piezoelectric body 2, so that it is easy to use during surgery.
- the configuration shown in FIG. This is more advantageous than the configuration shown in FIG.
- the intraoperative ultrasonic therapy transducer shown in FIGS. 21 and 22 is placed on the transmitting element 1 or 2 or the transmitting element 1 in the configuration of the ultrasonic therapy apparatus of the embodiment shown in FIGS. 3 and 7, respectively. By interchanging, an intraoperative ultrasound therapy apparatus can be configured.
- the ultrasonic detector 21 in FIGS. 21 and 22 corresponds to the probe 21 in FIGS.
- the thickness shall be an integer multiple of that, but if it is made of stainless steel or quartz glass to ensure the required chemical stability, the thickness shall be an integral multiple of half a wavelength. .
- the distance between the inner walls of the reaction vessel is an integral multiple of a half wavelength of the fundamental frequency so as to satisfy the resonance condition. In the example shown in the figure, by selecting it at a distance of one wavelength in the fundamental frequency, not only the vicinity of the inner wall but also the central part of the vessel is affected by the sound pressure of the standing wave at both the fundamental frequency and the double frequency. It was designed to be belly.
- the configuration of FIG. 23, which is essentially superior in generating acoustic cavities, is also advantageous as a configuration of a bubble generator.
- Fig. 24 shows an example of the configuration of a reactor or bubble generator of an ultrasonic chemical reaction device that generates a fundamental frequency and a double frequency simultaneously from one piezoelectric body.
- a planar piezoelectric body that can simultaneously generate a fundamental frequency and a double frequency is made of stainless steel, quartz glass, or the like, and has a thickness that is an integral multiple of a half wavelength of the fundamental frequency.
- Reaction vessel 9 1 Attached with sufficient acoustic strength to thickness diaphragm 79, which forms part of the outer wall.
- the outer wall 92 on the opposite side parallel to the thickness vibrating plate 79 has a thickness which is an integral multiple of a half wavelength with respect to the fundamental frequency, and functions as a reflecting plate.
- a cleaning liquid 101 for example, pure water or a cleaning liquid for semiconductor substrates containing hydrogen peroxide and ammonia, is filled with a cleaning tank 102 and a piezoelectric element having a vibrating surface attached to the bottom of the cleaning tank 102.
- the acoustic thickness in the vibration direction is 103, which is composed of a solid body 103 and a solid substance having substantially the same acoustic impedance as 103 attached to the piezoelectric body 103.
- the resonance frequency f of a composite resonance type thickness vibrator composed of a flat plate 104 and 103 and 104.
- Waveform generators 105 and 106 which generate electrical signals and 2f0, respectively, and the electrical signals output from waveform generators 105 and 106, respectively.
- the diaphragm in which the piezoelectric body 103 and the flat plate 104 are bonded has substantially the same configuration as the piezoelectric thickness vibrator described above with reference to FIG.
- the fundamental frequency f in the region 108 is obtained by excitation by the waveform generators 105 and 106 and the amplifier circuit 100. And its double frequency 2f. Can coexist.
- the object to be cleaned 109 in this area 108 for example by placing a semiconductor substrate, produces an acoustic cavitation with high efficiency on the surface 1.09 of the object to be cleaned. Then, the surface of the object 109 to be cleaned by the acoustic cavities is cleaned.
- the electric signal output from the waveform generator 106 that generates the electric signal having the following components is amplified by amplifiers 107 ′ and 107 ′, respectively, and the piezoelectric bodies 103 ′ and 103 ′ are amplified.
- the object to be cleaned 109 in this area for example, by placing a semiconductor substrate, produces an acoustic cavitation with high efficiency on the surface of the object to be cleaned 109, and this acoustic cavitation occurs.
- the surface of the object 109 to be cleaned by the ion is cleaned.
- FIG. 27 shows an embodiment of the cleaning apparatus for performing the cleaning.
- a pipe 111 for conducting a cleaning liquid 101, for example, pure water, a nozzle 113 attached to the tip thereof, and a piezoelectric body held inside the nozzle 113 are provided.
- the resonance frequency f of the composite thickness oscillator constituted by 104 and 103 and 104.
- And amplifying circuit 107 that adds and amplifies the signals output from waveform generators 105 and 106 to each other and applies it to piezoelectric body 103. It is configured to include.
- the diaphragm bonded to the piezoelectric body 103 and the flat plate 104 has substantially the same configuration as the piezoelectric thickness vibrator described above with reference to FIG.
- its double frequency 2f. Can coexist.
- the cleaning liquid 101 from the nozzle 113 toward the rotating or stationary stage 119 By firing the cleaning liquid 101 from the nozzle 113 toward the rotating or stationary stage 119, the cleaning liquid in the area 120 is opened.
- the object to be cleaned 1 2 1 For example, on the surface of a semiconductor substrate, this results in a highly efficient acoustic cavitation, and the table of objects 1 2 1 to be cleaned by this acoustic cavitation. The surface is cleaned.
- cleaning was performed by oxidizing a semiconductor substrate using ammonia and hydrogen peroxide.However, the progress of oxidation in the semiconductor substrate stopped at a certain depth, and was quantified. Because it was difficult to convert the material, a substance that caused coloration due to the oxidation reaction was held at the position where the semiconductor substrate was held in the cleaning device, and the oxidation reaction rate of the substance due to ultrasonic irradiation was measured. The oxidation reaction rate was used as an index of washing efficiency. The experiment was conducted on a reaction in which triiodide ions 1, 3— were generated from iodide ions 2 I— by oxidation.
- aqueous solution obtained by adding chlorinated hydrate to potassium iodide is placed in a 0.03 mm-thick polyethylene bag, and held in a position for holding the semiconductor substrate.
- a sound wave was irradiated.
- the concentration of the generated triiodide ion was determined by the absorbance, and the oxidation reaction rate was determined from the value.
- the oxidation reaction rate when simultaneously irradiating a fundamental frequency of 75 kHz and a multiplied frequency of 1.5 MHz with the sum of the ultrasonic powers of both being constant is defined as the ratio of the fundamental frequency power to the total ultrasonic power.
- the oxidation reaction rate with the same characteristics as described above with reference to FIG. 6 was obtained.
- the sum of the ultrasonic intensity at the fundamental frequency and the double frequency at the place where the oxidation reaction occurred was about 30 WZ cm 2 .
- Oxidation at fundamental frequency and double frequency alone The reaction rate was 0 within the experimental error range, but the synergistic effect when both frequencies were irradiated simultaneously was remarkable.
- Figure 28 shows the results of plotting the oxidation reaction rate when the phase ratio between the fundamental frequency and the overtone frequency was changed while the acoustic ratio between the fundamental frequency and the overtone frequency was fixed at 1: 1. Again, the sum of the fundamental and multiple frequency ultrasonic intensity at the location where the oxidation reaction occurred was about 3 OWZ cm 2 .
- the horizontal axis shows the value of ⁇ ; when the fundamental wave is sin (2 ⁇ f) and the multiple frequency is sin ( ⁇ f + a.
- the ultrasonic cleaning device shown in this example was also effective for cleaning using hydrogen peroxide and sulfuric acid, cleaning using tri-acetic acid, and cleaning using hydrated chloral.
- a processing tank 201 a liquid inlet 202, A liquid discharge port 203, a valve 204, a bubble injection port 205, a piezoelectric body 206 with a vibrating surface adhered to the bottom of the processing tank 201, and a piezoelectric body 206 attached to the piezoelectric body 206
- a flat plate 207 of a piezoelectric body 206 having a thickness in the vibration direction consisting of a solid having a sound impedance substantially the same as that of 206, and 206 and 20. 7 is the resonance frequency f of the composite resonance thickness oscillator.
- Amplifier circuit 208 that adds and amplifies the waveform generators 208a and 208b that generate the electrical signals of the above and the electrical signals output from waveform generators 208a and 208b. It is more structured.
- the relationship between the piezoelectric body 206 and the flat plate 207 is configured as described in FIG. 8, as in the embodiment of FIG.
- the resonance frequency f is applied to the piezoelectric body 206.
- 2 f When the liquid in the processing tank 201 is irradiated with ultrasonic waves, the fundamental frequency f is applied to the liquid in the processing tank. Its double frequency 2 f. Can coexist. This effectively produces acoustic cavitation in the treatment tank and sterilizes the liquid.
- valve opening / closing degree and timing can change the liquid processing amount and processing time.
- the composition of the liquid uses the somatochemically active substances such as hematoporphyrin and chlorin.
- a fluorinated dye or a halogenated compound such as chloral hydrate or tetrachloroacetic acid to a liquid, the bactericidal effect per hour can be improved. .
- the overall configuration of the liquid treatment device is the same as in FIG.
- the vibrating surfaces of the ultrasonic vibrators 206 b that resonate with each other are independently adhered to the side walls of the processing tank 201, and each has a frequency f.
- a waveform generator 208 a that generates an electric signal having the components of Waveform generator 208b that generates an electric signal having a component of a frequency twice as high as the above, and the electric signal output from the waveform generators 208a and 208b is used as an amplifier 20
- AC voltage is applied to the ultrasonic transducers 206a and 206b by independently amplifying them by 9a and 209b.
- the fundamental frequency f enters the processing tank. And its frequency 2 f. Can coexist. This effectively produces acoustic cavitation in the treatment tank and sterilizes the liquid.
Description
Claims
Priority Applications (4)
Application Number | Priority Date | Filing Date | Title |
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EP93919658A EP0619104B1 (en) | 1992-09-16 | 1993-09-14 | Ultrasonic irradiation apparatus |
DE69331692T DE69331692T2 (de) | 1992-09-16 | 1993-09-14 | Ultraschallbestrahlungsgeraet |
JP50665494A JP3429761B2 (ja) | 1992-09-16 | 1993-09-14 | 超音波照射装置及びそれによる処理装置 |
US08/240,733 US5523058A (en) | 1992-09-16 | 1993-09-14 | Ultrasonic irradiation apparatus and processing apparatus based thereon |
Applications Claiming Priority (2)
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JP4/246179 | 1992-09-16 | ||
JP24617992 | 1992-09-16 |
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WO1994006380A1 true WO1994006380A1 (en) | 1994-03-31 |
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PCT/JP1993/001310 WO1994006380A1 (en) | 1992-09-16 | 1993-09-14 | Ultrasonic irradiation apparatus and processor using the same |
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US (1) | US5523058A (ja) |
EP (1) | EP0619104B1 (ja) |
JP (1) | JP3429761B2 (ja) |
DE (1) | DE69331692T2 (ja) |
WO (1) | WO1994006380A1 (ja) |
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Families Citing this family (196)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
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US7169123B2 (en) | 1997-01-22 | 2007-01-30 | Advanced Medical Optics, Inc. | Control of pulse duty cycle based upon footswitch displacement |
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US6231516B1 (en) * | 1997-10-14 | 2001-05-15 | Vacusense, Inc. | Endoluminal implant with therapeutic and diagnostic capability |
US6050943A (en) * | 1997-10-14 | 2000-04-18 | Guided Therapy Systems, Inc. | Imaging, therapy, and temperature monitoring ultrasonic system |
US5902242A (en) * | 1998-01-22 | 1999-05-11 | Acuson Corporation | System and method for forming a combined ultrasonic image |
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US7981368B2 (en) | 1998-10-28 | 2011-07-19 | Covaris, Inc. | Method and apparatus for acoustically controlling liquid solutions in microfluidic devices |
US7687039B2 (en) | 1998-10-28 | 2010-03-30 | Covaris, Inc. | Methods and systems for modulating acoustic energy delivery |
US20020134402A1 (en) * | 2000-01-21 | 2002-09-26 | Madanshetty Sameer I. | Article produced by acoustic cavitation in a liquid insonification medium |
US20020108631A1 (en) * | 1999-01-21 | 2002-08-15 | Madanshetty Sameer I. | Single-transducer ACIM method and apparatus |
US6395096B1 (en) * | 1999-01-21 | 2002-05-28 | Uncopiers, Inc. | Single transducer ACIM method and apparatus |
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US7448790B2 (en) * | 1999-11-24 | 2008-11-11 | Impulse Devices, Inc. | Cavitation fluid circulatory system for a cavitation chamber |
US7381241B2 (en) * | 1999-11-24 | 2008-06-03 | Impulse Devices, Inc. | Degassing procedure for a cavitation chamber |
US7387660B2 (en) * | 1999-11-24 | 2008-06-17 | Impulse Devices, Inc., | Degassing procedure for a cavitation chamber |
US8096700B2 (en) * | 1999-11-24 | 2012-01-17 | Impulse Devices Inc. | Heat exchange system for a cavitation chamber |
EP1128185B8 (en) * | 2000-02-25 | 2009-08-19 | Hitachi, Ltd. | Mixing device for automatic analyzer |
US20020157685A1 (en) * | 2000-09-11 | 2002-10-31 | Naoya Hayamizu | Washing method, method of manufacturing semiconductor device and method of manufacturing active matrix-type display device |
US7914453B2 (en) * | 2000-12-28 | 2011-03-29 | Ardent Sound, Inc. | Visual imaging system for ultrasonic probe |
US8235919B2 (en) | 2001-01-12 | 2012-08-07 | Celleration, Inc. | Ultrasonic method and device for wound treatment |
US7914470B2 (en) | 2001-01-12 | 2011-03-29 | Celleration, Inc. | Ultrasonic method and device for wound treatment |
ITSV20010030A1 (it) * | 2001-08-14 | 2003-02-14 | Esaote Spa | Metodo e dispositivo per la trasmissione di impulsi ad ultrasuoni e la ricezione dei segnali di eco ad una armonica della frequenza di trasm |
JP4157688B2 (ja) * | 2001-09-20 | 2008-10-01 | 株式会社日立メディコ | 超音波診断装置 |
US20040019318A1 (en) * | 2001-11-07 | 2004-01-29 | Wilson Richard R. | Ultrasound assembly for use with a catheter |
AU2002359576A1 (en) | 2001-12-03 | 2003-06-17 | Ekos Corporation | Catheter with multiple ultrasound radiating members |
GB0129139D0 (en) * | 2001-12-05 | 2002-01-23 | Sra Dev Ltd | Ultrasonic generator system |
JP4167178B2 (ja) * | 2001-12-14 | 2008-10-15 | イコス コーポレイション | 血液の流れの再開の判定 |
US6958040B2 (en) * | 2001-12-28 | 2005-10-25 | Ekos Corporation | Multi-resonant ultrasonic catheter |
JP3816809B2 (ja) * | 2002-01-30 | 2006-08-30 | 株式会社日立製作所 | 薬剤、薬剤キャリア、薬剤の製造方法及び腫瘍の治療方法 |
ITMI20020438A1 (it) * | 2002-03-04 | 2003-09-04 | Lorenzo Manzoni | Apparato ad ultrasuoni per il trattamento della sintomatologia della malattia da decompressione |
US20040028552A1 (en) * | 2002-03-20 | 2004-02-12 | Bhardwaj Mahesh C. | Gas contact ultrasound germicide and therapeutic treatment |
US6845778B2 (en) * | 2002-03-29 | 2005-01-25 | Lam Research Corporation | In-situ local heating using megasonic transducer resonator |
US8226629B1 (en) | 2002-04-01 | 2012-07-24 | Ekos Corporation | Ultrasonic catheter power control |
US7118852B2 (en) * | 2002-04-11 | 2006-10-10 | Throwleigh Technologies, L.L.C. | Methods and apparatus for decontaminating fluids |
US6716168B2 (en) | 2002-04-30 | 2004-04-06 | Siemens Medical Solutions Usa, Inc. | Ultrasound drug delivery enhancement and imaging systems and methods |
DE10234533A1 (de) * | 2002-07-30 | 2004-02-12 | Richard Wolf Gmbh | Gerät und Verfahren zur thermischen Gewebebehandlung unter gezielter Nutzung nichtlinearer Ultraschalleffekte |
US7316664B2 (en) | 2002-10-21 | 2008-01-08 | Advanced Medical Optics, Inc. | Modulated pulsed ultrasonic power delivery system and method |
ES2279178T3 (es) | 2002-11-04 | 2007-08-16 | Ashland Licensing And Intellectual Property Llc | Dispositivo y procedimiento para el tratamiento de un medio liquido por ultrasonido en la prevencion del crecimiento de celulas hiperproliferativas o infectadas. |
WO2004060448A2 (en) * | 2003-01-03 | 2004-07-22 | Ekos Corporation | Ultrasonic catheter with axial energy field |
US7104268B2 (en) * | 2003-01-10 | 2006-09-12 | Akrion Technologies, Inc. | Megasonic cleaning system with buffered cavitation method |
KR100516902B1 (ko) * | 2003-01-28 | 2005-09-27 | 주식회사 헬스피아 | 이동통신 단말기의 배터리 팩 장치 |
US20040230121A1 (en) * | 2003-02-20 | 2004-11-18 | Rune Hansen | Ultrasonic contrast agent imaging by dualband pulse transmission |
CA2830583C (en) * | 2003-03-12 | 2015-06-09 | Abbott Medical Optics Inc. | System and method for pulsed ultrasonic power delivery employing cavitation effects |
JP4244300B2 (ja) * | 2003-03-24 | 2009-03-25 | 富士フイルム株式会社 | 超音波送受信装置 |
US7048863B2 (en) * | 2003-07-08 | 2006-05-23 | Ashland Licensing And Intellectual Property Llc | Device and process for treating cutting fluids using ultrasound |
US20050070961A1 (en) * | 2003-07-15 | 2005-03-31 | Terumo Kabushiki Kaisha | Energy treatment apparatus |
CA2439667A1 (en) * | 2003-09-04 | 2005-03-04 | Andrew Kenneth Hoffmann | Low frequency vibration assisted blood perfusion system and apparatus |
US8721573B2 (en) | 2003-09-04 | 2014-05-13 | Simon Fraser University | Automatically adjusting contact node for multiple rib space engagement |
US8734368B2 (en) | 2003-09-04 | 2014-05-27 | Simon Fraser University | Percussion assisted angiogenesis |
US8870796B2 (en) | 2003-09-04 | 2014-10-28 | Ahof Biophysical Systems Inc. | Vibration method for clearing acute arterial thrombotic occlusions in the emergency treatment of heart attack and stroke |
US20060025683A1 (en) * | 2004-07-30 | 2006-02-02 | Ahof Biophysical Systems Inc. | Hand-held imaging probe for treatment of states of low blood perfusion |
US7393323B2 (en) | 2003-10-01 | 2008-07-01 | Robert Vago | Method and device for subaqueous ultrasonic irradiation of living tissue |
US7377905B2 (en) * | 2003-10-01 | 2008-05-27 | Robert Vago | Method and device for subaqueous ultrasonic irradiation of living tissue |
US7328628B2 (en) * | 2003-12-08 | 2008-02-12 | Covaris, Inc. | Apparatus and methods for sample preparation |
WO2005070299A1 (en) * | 2004-01-16 | 2005-08-04 | The University Of Houston System | Methods and apparatus for medical imaging |
US20050209578A1 (en) * | 2004-01-29 | 2005-09-22 | Christian Evans Edward A | Ultrasonic catheter with segmented fluid delivery |
US7201737B2 (en) * | 2004-01-29 | 2007-04-10 | Ekos Corporation | Treatment of vascular occlusions using elevated temperatures |
US9107590B2 (en) | 2004-01-29 | 2015-08-18 | Ekos Corporation | Method and apparatus for detecting vascular conditions with a catheter |
WO2005094701A1 (ja) * | 2004-03-31 | 2005-10-13 | Toudai Tlo, Ltd. | 超音波照射方法及び超音波照射装置 |
PT1761284E (pt) | 2004-06-23 | 2012-12-12 | Ashland Licensing & Intellectu | Dispositivo e método para tratamento de fluídos utilizados em processo de revestimento por electrodeposição com ultra-sons |
US7413552B2 (en) * | 2004-08-05 | 2008-08-19 | Robert Vago | Method for subaqueous ultrasonic catastrophic irradiation of living tissue |
US7824348B2 (en) * | 2004-09-16 | 2010-11-02 | Guided Therapy Systems, L.L.C. | System and method for variable depth ultrasound treatment |
US9011336B2 (en) * | 2004-09-16 | 2015-04-21 | Guided Therapy Systems, Llc | Method and system for combined energy therapy profile |
US7393325B2 (en) | 2004-09-16 | 2008-07-01 | Guided Therapy Systems, L.L.C. | Method and system for ultrasound treatment with a multi-directional transducer |
US8444562B2 (en) | 2004-10-06 | 2013-05-21 | Guided Therapy Systems, Llc | System and method for treating muscle, tendon, ligament and cartilage tissue |
US10864385B2 (en) | 2004-09-24 | 2020-12-15 | Guided Therapy Systems, Llc | Rejuvenating skin by heating tissue for cosmetic treatment of the face and body |
US8535228B2 (en) | 2004-10-06 | 2013-09-17 | Guided Therapy Systems, Llc | Method and system for noninvasive face lifts and deep tissue tightening |
US9827449B2 (en) | 2004-10-06 | 2017-11-28 | Guided Therapy Systems, L.L.C. | Systems for treating skin laxity |
US8133180B2 (en) | 2004-10-06 | 2012-03-13 | Guided Therapy Systems, L.L.C. | Method and system for treating cellulite |
US9694212B2 (en) | 2004-10-06 | 2017-07-04 | Guided Therapy Systems, Llc | Method and system for ultrasound treatment of skin |
EP2279696A3 (en) | 2004-10-06 | 2014-02-26 | Guided Therapy Systems, L.L.C. | Method and system for non-invasive mastopexy |
US11883688B2 (en) | 2004-10-06 | 2024-01-30 | Guided Therapy Systems, Llc | Energy based fat reduction |
US7758524B2 (en) | 2004-10-06 | 2010-07-20 | Guided Therapy Systems, L.L.C. | Method and system for ultra-high frequency ultrasound treatment |
KR101732144B1 (ko) | 2004-10-06 | 2017-05-02 | 가이디드 테라피 시스템스, 엘.엘.씨. | 초음파 치료 시스템 |
US20060111744A1 (en) | 2004-10-13 | 2006-05-25 | Guided Therapy Systems, L.L.C. | Method and system for treatment of sweat glands |
US11235179B2 (en) | 2004-10-06 | 2022-02-01 | Guided Therapy Systems, Llc | Energy based skin gland treatment |
US8690778B2 (en) | 2004-10-06 | 2014-04-08 | Guided Therapy Systems, Llc | Energy-based tissue tightening |
US11207548B2 (en) | 2004-10-07 | 2021-12-28 | Guided Therapy Systems, L.L.C. | Ultrasound probe for treating skin laxity |
US11724133B2 (en) | 2004-10-07 | 2023-08-15 | Guided Therapy Systems, Llc | Ultrasound probe for treatment of skin |
US20060184070A1 (en) * | 2004-11-12 | 2006-08-17 | Hansmann Douglas R | External ultrasonic therapy |
PL1828059T3 (pl) | 2004-11-17 | 2014-05-30 | Solenis Technologies Cayman Lp | Sposób obróbki płynów chłodniczych stosowanych w produkcji opon |
KR100714682B1 (ko) * | 2004-12-02 | 2007-05-04 | 삼성전자주식회사 | 파일 시스템 경로 처리 장치 및 방법 |
US20060173387A1 (en) * | 2004-12-10 | 2006-08-03 | Douglas Hansmann | Externally enhanced ultrasonic therapy |
US7624703B2 (en) * | 2005-01-25 | 2009-12-01 | Robert Edward Vago | Method and device for removal of ammonia and other contaminants from recirculating aquaculture tanks |
US8858805B2 (en) * | 2005-01-25 | 2014-10-14 | Robert Edward Vago | Method and device for removal of ammonia and related contaminants from water |
WO2006105616A1 (en) * | 2005-04-08 | 2006-10-12 | Commonwealth Scientific And Industrial Research Organisation | Method for microfluidic mixing and mixing device |
US7571336B2 (en) | 2005-04-25 | 2009-08-04 | Guided Therapy Systems, L.L.C. | Method and system for enhancing safety with medical peripheral device by monitoring if host computer is AC powered |
WO2006138438A2 (en) * | 2005-06-15 | 2006-12-28 | Akrion, Inc. | System and method of processing substrates using sonic energy having cavitation control |
JP4369907B2 (ja) * | 2005-07-01 | 2009-11-25 | 株式会社日立製作所 | 音響化学治療装置 |
US7757561B2 (en) * | 2005-08-01 | 2010-07-20 | Covaris, Inc. | Methods and systems for processing samples using acoustic energy |
US20070083120A1 (en) * | 2005-09-22 | 2007-04-12 | Cain Charles A | Pulsed cavitational ultrasound therapy |
US8057408B2 (en) * | 2005-09-22 | 2011-11-15 | The Regents Of The University Of Michigan | Pulsed cavitational ultrasound therapy |
US10219815B2 (en) * | 2005-09-22 | 2019-03-05 | The Regents Of The University Of Michigan | Histotripsy for thrombolysis |
US20070167798A1 (en) * | 2005-11-23 | 2007-07-19 | Cai Anming H | Contrast agent augmented ultrasound therapy system with ultrasound imaging guidance for thrombus treatment |
US20070149881A1 (en) * | 2005-12-22 | 2007-06-28 | Rabin Barry H | Ultrasonically Powered Medical Devices and Systems, and Methods and Uses Thereof |
WO2008016691A2 (en) * | 2006-08-01 | 2008-02-07 | Covaris, Inc. | Methods and apparatus for treating samples with acoustic energy |
EP2076179B1 (en) | 2006-08-01 | 2018-07-04 | Stichting voor de Technische Wetenschappen | Pulse inversion sequences for nonlinear imaging |
US8192363B2 (en) | 2006-10-27 | 2012-06-05 | Ekos Corporation | Catheter with multiple ultrasound radiating members |
EP1925359A1 (en) | 2006-11-22 | 2008-05-28 | Covaris, Inc. | Methods and apparatus for treating samples with acoustic energy to form particles and particulates |
US8327861B2 (en) * | 2006-12-19 | 2012-12-11 | Lam Research Corporation | Megasonic precision cleaning of semiconductor process equipment components and parts |
US8491521B2 (en) | 2007-01-04 | 2013-07-23 | Celleration, Inc. | Removable multi-channel applicator nozzle |
US9782608B2 (en) * | 2007-01-05 | 2017-10-10 | Angel Science & Technology (Canada) Inc. | High intensity focused ultrasound treatment head and system |
EP2111261B1 (en) | 2007-01-08 | 2015-04-15 | Ekos Corporation | Power parameters for ultrasonic catheter |
US10182833B2 (en) | 2007-01-08 | 2019-01-22 | Ekos Corporation | Power parameters for ultrasonic catheter |
DK2152167T3 (en) | 2007-05-07 | 2018-12-10 | Guided Therapy Systems Llc | Methods and systems for coupling and focusing acoustic energy using a coupling element |
US20150174388A1 (en) | 2007-05-07 | 2015-06-25 | Guided Therapy Systems, Llc | Methods and Systems for Ultrasound Assisted Delivery of a Medicant to Tissue |
TWI526233B (zh) | 2007-05-07 | 2016-03-21 | 指導治療系統股份有限公司 | 利用聲波能量調製藥劑輸送及效能之系統 |
US9044568B2 (en) | 2007-06-22 | 2015-06-02 | Ekos Corporation | Method and apparatus for treatment of intracranial hemorrhages |
DE102007030572A1 (de) * | 2007-07-02 | 2009-01-08 | Heidelberger Druckmaschinen Ag | Wascheinrichtung für einen Zylinder in einer Druckmaschine |
US8568339B2 (en) * | 2007-08-16 | 2013-10-29 | Ultrashape Ltd. | Single element ultrasound transducer with multiple driving circuits |
US20110301506A1 (en) * | 2007-12-14 | 2011-12-08 | Kim Volz | Ultrasound pulse shaping |
DK2282675T3 (en) | 2008-06-06 | 2016-05-17 | Ulthera Inc | Cosmetic treatment and imaging system |
CA2748362A1 (en) | 2008-12-24 | 2010-07-01 | Michael H. Slayton | Methods and systems for fat reduction and/or cellulite treatment |
PL2448636T3 (pl) | 2009-07-03 | 2014-11-28 | Ekos Corp | Parametry mocy dla cewnika ultradźwiękowego |
AU2010284313B2 (en) * | 2009-08-17 | 2016-01-28 | Histosonics, Inc. | Disposable acoustic coupling medium container |
JP5726191B2 (ja) | 2009-08-26 | 2015-05-27 | リージェンツ オブ ザ ユニバーシティー オブ ミシガン | 尿管結石の破砕の際に気泡混濁空洞現象の制御を使用する装置および方法 |
WO2011028603A2 (en) | 2009-08-26 | 2011-03-10 | The Regents Of The University Of Michigan | Micromanipulator control arm for therapeutic and imaging ultrasound transducers |
DE102009043014A1 (de) | 2009-09-04 | 2011-03-10 | Rodenbeck, Arno W., Dipl.-Ing. | Vorrichtung und Verfahren zum Reinigen von Keramikelementen |
US8539813B2 (en) | 2009-09-22 | 2013-09-24 | The Regents Of The University Of Michigan | Gel phantoms for testing cavitational ultrasound (histotripsy) transducers |
US8715186B2 (en) | 2009-11-24 | 2014-05-06 | Guided Therapy Systems, Llc | Methods and systems for generating thermal bubbles for improved ultrasound imaging and therapy |
KR20200004466A (ko) | 2010-08-02 | 2020-01-13 | 가이디드 테라피 시스템스, 엘.엘.씨. | 초음파 치료 시스템 및 방법 |
US9504446B2 (en) | 2010-08-02 | 2016-11-29 | Guided Therapy Systems, Llc | Systems and methods for coupling an ultrasound source to tissue |
US8459121B2 (en) | 2010-10-28 | 2013-06-11 | Covaris, Inc. | Method and system for acoustically treating material |
US8857438B2 (en) | 2010-11-08 | 2014-10-14 | Ulthera, Inc. | Devices and methods for acoustic shielding |
US8709359B2 (en) | 2011-01-05 | 2014-04-29 | Covaris, Inc. | Sample holder and method for treating sample material |
US11458290B2 (en) | 2011-05-11 | 2022-10-04 | Ekos Corporation | Ultrasound system |
WO2012156881A1 (en) * | 2011-05-18 | 2012-11-22 | Koninklijke Philips Electronics N.V. | Spherical ultrasonic hifu transducer with offset cavitation sense element |
WO2012156863A2 (en) * | 2011-05-18 | 2012-11-22 | Koninklijke Philips Electronics N.V. | Spherical ultrasonic hifu transducer with modular cavitation sense element |
JP5775751B2 (ja) * | 2011-06-15 | 2015-09-09 | オリンパス株式会社 | 超音波照射装置 |
JP5851127B2 (ja) * | 2011-06-24 | 2016-02-03 | オリンパス株式会社 | 超音波照射装置及び超音波照射装置の作動方法 |
US9452302B2 (en) | 2011-07-10 | 2016-09-27 | Guided Therapy Systems, Llc | Systems and methods for accelerating healing of implanted material and/or native tissue |
KR20140047709A (ko) | 2011-07-11 | 2014-04-22 | 가이디드 테라피 시스템스, 엘.엘.씨. | 조직에 초음파원을 연결하는 시스템 및 방법 |
US9144694B2 (en) | 2011-08-10 | 2015-09-29 | The Regents Of The University Of Michigan | Lesion generation through bone using histotripsy therapy without aberration correction |
US9049783B2 (en) | 2012-04-13 | 2015-06-02 | Histosonics, Inc. | Systems and methods for obtaining large creepage isolation on printed circuit boards |
US9263663B2 (en) | 2012-04-13 | 2016-02-16 | Ardent Sound, Inc. | Method of making thick film transducer arrays |
EP2844343B1 (en) | 2012-04-30 | 2018-11-21 | The Regents Of The University Of Michigan | Ultrasound transducer manufacturing using rapid-prototyping method |
US9510802B2 (en) | 2012-09-21 | 2016-12-06 | Guided Therapy Systems, Llc | Reflective ultrasound technology for dermatological treatments |
US20140100459A1 (en) | 2012-10-05 | 2014-04-10 | The Regents Of The University Of Michigan | Bubble-induced color doppler feedback during histotripsy |
WO2014124440A2 (en) * | 2013-02-11 | 2014-08-14 | Bloch Andrew E | Apparatus and method for providing asymmetric oscillations |
CN204637350U (zh) | 2013-03-08 | 2015-09-16 | 奥赛拉公司 | 美学成像与处理系统、多焦点处理系统和执行美容过程的系统 |
US20140271453A1 (en) | 2013-03-14 | 2014-09-18 | Abbott Laboratories | Methods for the early detection of lung cancer |
US10561862B2 (en) | 2013-03-15 | 2020-02-18 | Guided Therapy Systems, Llc | Ultrasound treatment device and methods of use |
US9675747B2 (en) | 2013-03-15 | 2017-06-13 | William L Puskas | Methods and systems for improved cavitation efficiency and density, cancer cell destruction, and/or causing a target object to be a cavitation nucleus |
NO2987005T3 (ja) * | 2013-06-13 | 2018-04-28 | ||
US11432900B2 (en) | 2013-07-03 | 2022-09-06 | Histosonics, Inc. | Articulating arm limiter for cavitational ultrasound therapy system |
JP6600304B2 (ja) | 2013-07-03 | 2019-10-30 | ヒストソニックス,インコーポレーテッド | 衝撃散乱を使用した気泡雲形成のために最適化されたヒストトリプシ励起シーケンス |
WO2015027164A1 (en) | 2013-08-22 | 2015-02-26 | The Regents Of The University Of Michigan | Histotripsy using very short ultrasound pulses |
GB2515134B (en) * | 2014-01-27 | 2017-05-17 | King Fahad Medical City (Kfmc) | Therapeutic ultrasound apparatus and method |
SG11201608691YA (en) | 2014-04-18 | 2016-11-29 | Ulthera Inc | Band transducer ultrasound therapy |
US10092742B2 (en) | 2014-09-22 | 2018-10-09 | Ekos Corporation | Catheter system |
US9884312B2 (en) | 2014-11-14 | 2018-02-06 | Rgf Environmental Group, Inc. | Device, system, and method for producing advanced oxidation products |
JP6244296B2 (ja) * | 2014-12-15 | 2017-12-06 | オリンパス株式会社 | 付着物の塗布方法 |
CN104622525B (zh) * | 2015-02-28 | 2017-01-04 | 西安交通大学 | 双倍频共焦叠加聚焦超声球面分裂阵及分裂焦点控制方法 |
EP3307388B1 (en) | 2015-06-10 | 2022-06-22 | Ekos Corporation | Ultrasound catheter |
JP6979882B2 (ja) | 2015-06-24 | 2021-12-15 | ザ リージェンツ オブ ザ ユニヴァシティ オブ ミシガン | 脳組織の治療のための組織破砕療法システムおよび方法 |
US10670341B2 (en) * | 2015-10-26 | 2020-06-02 | Georgia Tech Research Corporation | Ultra-compact, scalable, direct-contact vapor condensers using acoustic actuation |
KR101723163B1 (ko) * | 2015-12-10 | 2017-04-04 | 주식회사 코러스트 | 다중 주파수 출력이 가능한 초음파 생성 장치 |
KR102615327B1 (ko) | 2016-01-18 | 2023-12-18 | 얼테라, 인크 | 환형 초음파 어레이가 가요성 인쇄 회로 기판에 지엽적으로 전기적으로 연결된 컴팩트한 초음파 디바이스 및 그 조립 방법 |
CN107561157B (zh) * | 2016-06-30 | 2023-08-04 | 重庆医科大学 | 水质检测仪及其方法 |
KR102593310B1 (ko) | 2016-08-16 | 2023-10-25 | 얼테라, 인크 | 이미징 오정렬을 감소시키도록 구성된 초음파 이미징 시스템, 초음파 이미징 모듈 및 이미징 오정렬을 감소시키는 방법 |
WO2018102786A1 (en) | 2016-12-03 | 2018-06-07 | Juno Therapeutics, Inc. | Methods for modulation of car-t cells |
US10424278B2 (en) * | 2017-08-02 | 2019-09-24 | Applied Invention, Llc | Bell with subharmonic difference tone |
US11944849B2 (en) | 2018-02-20 | 2024-04-02 | Ulthera, Inc. | Systems and methods for combined cosmetic treatment of cellulite with ultrasound |
JP7024549B2 (ja) * | 2018-03-28 | 2022-02-24 | セイコーエプソン株式会社 | 超音波センサー、及び超音波装置 |
US11813484B2 (en) | 2018-11-28 | 2023-11-14 | Histosonics, Inc. | Histotripsy systems and methods |
EP3751558B1 (en) * | 2019-06-12 | 2022-12-28 | Esaote S.p.A. | Method for generating ultrasound transmission waves and ultrasound system for carrying out the method |
US11877953B2 (en) | 2019-12-26 | 2024-01-23 | Johnson & Johnson Surgical Vision, Inc. | Phacoemulsification apparatus |
EP4096782A4 (en) | 2020-01-28 | 2024-02-14 | Univ Michigan Regents | SYSTEMS AND METHODS FOR IMMUNOSENSITIZATION BY HISTOTRIPSY |
Citations (1)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
JPH02126848A (ja) * | 1988-07-01 | 1990-05-15 | Hitachi Ltd | 治療用超音波装置 |
Family Cites Families (12)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US3117768A (en) * | 1960-11-21 | 1964-01-14 | Branson Instr | Ultrasonic transducers |
GB1389291A (en) * | 1971-04-22 | 1975-04-03 | Telecommunications Ind | Waste treatment process and apparatus |
US3805596A (en) * | 1972-02-24 | 1974-04-23 | C Klahr | High resolution ultrasonic imaging scanner |
US3991933A (en) * | 1975-09-08 | 1976-11-16 | Blackstone Corporation | Methods and apparatus for soldering |
US4168295A (en) * | 1975-11-20 | 1979-09-18 | Vernon D. Beehler | Apparatus for enhancing chemical reactions |
US4375991A (en) * | 1978-11-24 | 1983-03-08 | The Johns Hopkins University | Ultrasonic cleaning method and apparatus |
US4249146A (en) * | 1979-02-23 | 1981-02-03 | Trw Inc. | Surface acoustic wave resonators utilizing harmonic frequencies |
US4556467A (en) * | 1981-06-22 | 1985-12-03 | Mineral Separation Corporation | Apparatus for ultrasonic processing of materials |
US4836684A (en) * | 1988-02-18 | 1989-06-06 | Ultrasonic Power Corporation | Ultrasonic cleaning apparatus with phase diversifier |
JP2832443B2 (ja) * | 1988-11-22 | 1998-12-09 | 本多電子株式会社 | マルチ周波数超音波洗浄方法及び洗浄装置 |
US5065066A (en) * | 1989-07-19 | 1991-11-12 | Murata Mfg. Co., Ltd. | Piezoelectric resonator |
US5259384A (en) * | 1992-07-30 | 1993-11-09 | Kaufman Jonathan J | Ultrasonic bone-assessment apparatus and method |
-
1993
- 1993-09-14 EP EP93919658A patent/EP0619104B1/en not_active Expired - Lifetime
- 1993-09-14 DE DE69331692T patent/DE69331692T2/de not_active Expired - Lifetime
- 1993-09-14 US US08/240,733 patent/US5523058A/en not_active Expired - Lifetime
- 1993-09-14 JP JP50665494A patent/JP3429761B2/ja not_active Expired - Lifetime
- 1993-09-14 WO PCT/JP1993/001310 patent/WO1994006380A1/ja active IP Right Grant
Patent Citations (1)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
JPH02126848A (ja) * | 1988-07-01 | 1990-05-15 | Hitachi Ltd | 治療用超音波装置 |
Cited By (32)
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JPH08140973A (ja) * | 1994-11-25 | 1996-06-04 | Toshiba Ceramics Co Ltd | 超音波発生装置 |
JPH09135842A (ja) * | 1995-09-29 | 1997-05-27 | Ethicon Endo Surgery Inc | 超音波装置 |
JP2007125554A (ja) * | 1996-07-04 | 2007-05-24 | Ashland Licensing & Intellectual Property Llc | 液状媒質を処理する装置及び方法 |
JP2000516522A (ja) * | 1996-07-04 | 2000-12-12 | ドゥ モイレナエル エリック コルデマンス | 液状媒質を処理する装置及び方法 |
JP2010158679A (ja) * | 1996-07-04 | 2010-07-22 | Ashland Licensing & Intellectual Property Llc | 液状媒質を処理する装置及び方法 |
JPH1127798A (ja) * | 1997-07-04 | 1999-01-29 | S C:Kk | 超音波振動の発生方法 |
JP2003533263A (ja) * | 1997-10-27 | 2003-11-11 | ロバート ダブリュー クリブス | 脂肪分解療法及び装置 |
JP2004538039A (ja) * | 2001-01-30 | 2004-12-24 | アドバンスト メディカル アプリケーションズ インコーポレーテッド | 定常波を用いる超音波創傷治療方法及び装置 |
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JP2008500136A (ja) * | 2004-05-18 | 2008-01-10 | ナノヴィブロニクス・インコーポレーテッド | 薄いピエゾ素子の複数の振動モードを用いた医療用具のためのナノ振動被膜工程 |
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JP2011206094A (ja) * | 2010-03-29 | 2011-10-20 | Akita Univ | 超音波照射装置 |
US9729252B2 (en) | 2011-10-21 | 2017-08-08 | Cerevast Medical, Inc. | Method and system for direct communication |
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US9282985B2 (en) | 2013-11-11 | 2016-03-15 | Gyrus Acmi, Inc. | Aiming beam detection for safe laser lithotripsy |
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JP2018529455A (ja) * | 2015-09-30 | 2018-10-11 | エシコン エルエルシーEthicon LLC | 超音波外科用器具のための複合電気信号波形をデジタル的に発生させる、発生器 |
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CN112912138A (zh) * | 2018-10-30 | 2021-06-04 | 京瓷株式会社 | 超声波辐射器具以及超声波装置 |
Also Published As
Publication number | Publication date |
---|---|
JP3429761B2 (ja) | 2003-07-22 |
EP0619104B1 (en) | 2002-03-13 |
DE69331692T2 (de) | 2002-10-24 |
EP0619104A1 (en) | 1994-10-12 |
EP0619104A4 (en) | 1996-05-08 |
DE69331692D1 (de) | 2002-04-18 |
US5523058A (en) | 1996-06-04 |
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