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WO2018138847A1 - Dispositif de traitement par ultrasons - Google Patents

Dispositif de traitement par ultrasons Download PDF

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Publication number
WO2018138847A1
WO2018138847A1 PCT/JP2017/002822 JP2017002822W WO2018138847A1 WO 2018138847 A1 WO2018138847 A1 WO 2018138847A1 JP 2017002822 W JP2017002822 W JP 2017002822W WO 2018138847 A1 WO2018138847 A1 WO 2018138847A1
Authority
WO
WIPO (PCT)
Prior art keywords
ultrasonic
support member
power cable
ultrasonic output
shield layer
Prior art date
Application number
PCT/JP2017/002822
Other languages
English (en)
Japanese (ja)
Inventor
定生 江幡
俊介 兼森
和夫 鎌田
Original Assignee
オリンパス株式会社
協同電子株式会社
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Application filed by オリンパス株式会社, 協同電子株式会社 filed Critical オリンパス株式会社
Priority to PCT/JP2017/002822 priority Critical patent/WO2018138847A1/fr
Publication of WO2018138847A1 publication Critical patent/WO2018138847A1/fr

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Classifications

    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
    • A61B8/12—Diagnosis using ultrasonic, sonic or infrasonic waves in body cavities or body tracts, e.g. by using catheters

Definitions

  • the present invention relates to an ultrasonic treatment apparatus.
  • an ultrasonic medical device having a plurality of vibration elements arranged one-dimensionally or two-dimensionally is known (see, for example, Patent Documents 1 and 2).
  • the ultrasonic medical device disclosed in Patent Document 1 is used for diagnosis to acquire an ultrasonic image for diagnosing a lesion or the like in the body by transmitting and receiving ultrasonic waves using a vibration element.
  • the ultrasonic medical device of Patent Document 2 is for treatment in which ultrasonic waves focused on a lesion in the body are irradiated from outside the body to cauterize the lesion.
  • Each vibration element is connected to a power supply cable, and the timing for driving each vibration element can be individually controlled.
  • the timing for driving each vibration element can be individually controlled.
  • ultrasonic waves that reinforce each other at one point (focusing position) are generated from the plurality of vibration elements, and strong energy is generated at the focusing position.
  • the focusing position can be changed by controlling the delay time.
  • a backing material made of a resin such as ferrite rubber is provided on the back surface of the vibration element for the purpose of absorbing unnecessary ultrasonic waves.
  • the cable penetrates the backing material and is joined to the vibration element, so that the cable is stably supported by the backing material.
  • a backing material it is difficult to provide a backing material, and cable support tends to be unstable.
  • strong ultrasonic energy is required for treatment such as cauterization of living tissue.
  • the vibration energy generated by the vibration element is absorbed by the backing material, so that the backing material is not suitable for an ultrasonic medical device for treatment.
  • the present invention has been made in view of the above-described circumstances, and an object thereof is to provide an ultrasonic treatment apparatus capable of reliably joining a vibration element and a power cable.
  • One embodiment of the present invention intersects the plane, an insertion section that is inserted into the body, an ultrasonic output section that has a plurality of vibration elements arranged on a plane, and that is provided at the distal end of the insertion section.
  • a support member having a plurality of through holes penetrating in a direction, and a plurality of power cables connected to the vibration elements through the through holes and supplying electric power to the vibration elements to vibrate the vibration elements.
  • the support member is disposed at a distance from the ultrasonic output unit in a direction intersecting the plane.
  • power is supplied to the vibration element via the power cable and ultrasonic waves are generated from the vibration element, so that the living tissue around the distal end portion of the insertion portion disposed in the body is super A sound wave is irradiated.
  • one power cable is connected to each vibration element, and the timing at which each vibration element is driven to vibrate can be individually controlled, so that ultrasonic waves that reinforce each other in the affected part of the living tissue can be generated. It can be generated from a plurality of vibration elements, and powerful ultrasonic energy can be given to the affected area.
  • each power cable is wired to the vibration element through the through hole of the support member, and is stably supported by the support member. Thereby, the joining operation of the power cable to the vibration element is facilitated, and the power cable can be reliably connected to the vibration element to be connected.
  • the support member is disposed at a position away from the ultrasonic output unit, the vibration energy generated by the vibration element is prevented from being absorbed by the support member, which is a powerful force required for treatment. Ultrasonic energy can be applied to living tissue.
  • the length in the direction which intersects the said plane of the said through hole is larger than the said distance between the said supporting member and the said ultrasonic output part.
  • the power cable is a coaxial cable having a core wire, an inner sheath, a shield layer, and an outer sheath arranged concentrically in order from the center side, and the through hole is provided on the ultrasonic output portion side.
  • a small-diameter portion having an inner diameter that is larger than the outer diameter of the core wire and smaller than the outer diameter of the inner coating or the shield layer, and larger than the inner diameter of the small-diameter portion provided on the opposite side of the ultrasonic output portion.
  • the through-hole has a two-stage structure having two inner diameters, and the power cable is inserted into the through-hole until the tip of the inner coating or shield layer abuts against the abutting surface.
  • the amount of protrusion at the tip of the can be controlled to a predetermined amount.
  • the power cable is a coaxial cable having a core wire, an inner coating, a shield layer, and an outer coating arranged concentrically in order from the center side, and the opposite side of the support member from the ultrasonic output unit And a ground layer electrically connected to the shield layer of the coaxial cable.
  • At least a part of the plurality of through holes located on the side close to the proximal end of the insertion portion may be bent toward the proximal end at a midway position in a direction intersecting the plane. It is preferable that the bend angle of the through hole is larger as it is closer to the base end side.
  • FIG. 1 It is a perspective view which shows the external appearance of the front-end
  • the ultrasonic treatment apparatus 1 As shown in FIGS. 1 and 2, the ultrasonic treatment apparatus 1 according to the present embodiment is provided with an elongated insertion portion 2 to be inserted into the body, and a diameter of the insertion portion 2 provided at the distal end portion of the insertion portion 2.
  • An ultrasonic output unit 3 that emits ultrasonic waves outward in the direction, a power cable 4 that is wired along the longitudinal direction inside the insertion unit 2 and supplies power to the ultrasonic output unit 3, and an ultrasonic output unit 3 and a support member 5 that is arranged to face the power cable 4 and supports the power cable 4.
  • the ultrasonic output section 3 includes a plurality of piezoelectric elements (vibration elements) 6 arranged in a matrix on a plane parallel to the longitudinal direction of the insertion section 2, and is formed in a rectangular flat plate shape as a whole.
  • Each piezoelectric element 6 has a quadrangular prism shape having a thickness direction and a width direction orthogonal to each other, and is arranged so that the thickness direction is along the radial direction of the insertion portion 2.
  • each piezoelectric element 6 The front surface on one side in the thickness direction of each piezoelectric element 6 is an emission surface that emits ultrasonic waves, and is exposed to the outside of the insertion portion 2. As shown in FIG. 4, a ground (GND) electrode 7 common to all the piezoelectric elements 6 is provided on the emission surface. A positive electrode 8 is provided on the back surface on the other side in the thickness direction of each piezoelectric element 6. In FIG. 3, the electrodes 7 and 8 are not shown in order to simplify the drawing.
  • GND ground
  • the power cable 4 is a coaxial cable having a core wire 4a, an inner coating 4b, a shield layer 4c, and an outer coating 4d arranged concentrically in order from the center side.
  • the core wire 4a and the shield layer 4c are made of a conductor, and the inner coating 4b and the outer coating 4d are made of an insulator.
  • the core wire 4 a, the inner coating 4 b, and the shield layer 4 c are exposed in order from the distal end side at the distal end portion of the power cable 4.
  • the number of power cables 4 is the same as the number of piezoelectric elements 6, and one power cable 4 is connected to the positive electrode 8 on the back surface of one piezoelectric element 6.
  • each power cable 4 is connected to a power source (not shown) arranged outside the insertion portion 2.
  • a power source not shown
  • ultrasonic waves are generated by stretching vibration in the thickness direction of the piezoelectric element 6, and the radial direction of the insertion portion 2 extends from the emission surface of the piezoelectric element 6. Ultrasonic waves are emitted outward.
  • each piezoelectric element 6 since one power cable 4 is connected to each piezoelectric element 6, the timing at which each piezoelectric element 6 generates ultrasonic waves by individually controlling the supply timing of high-frequency power to each piezoelectric element 6 and The phase of the ultrasonic wave can be controlled. Thereby, ultrasonic waves that reinforce each other at one point (focusing position) due to interference can be emitted from the plurality of piezoelectric elements 6. Furthermore, the focusing position can be changed by controlling the delay time between the supply timings of the high-frequency power.
  • the support member 5 is a flat plate member formed of an electrically insulating resin such as polyether ether ketone (PEEK), and has a front surface and a back surface that face each other in the thickness direction.
  • PEEK polyether ether ketone
  • the support member 5 is disposed so that the front surface of the support member 5 faces the back surface of the plurality of piezoelectric elements 6 and is parallel to the arrangement of the plurality of piezoelectric elements 6.
  • wall portions 5a projecting in the thickness direction from the front surface are provided on the side edges of the support member 5 on both sides in the longitudinal direction of the insertion portion 2, and the support member 5 in the thickness direction is provided.
  • the vertical cross section of is substantially U-shaped.
  • the tip of the wall 5a is fixed to the side surface of the ultrasonic output unit 3, and the thickness between the front surface of the support member 5 and the positive electrode 8 on the back surface of the piezoelectric element 6 is as shown in FIG.
  • a gap having a distance t1 in the vertical direction is formed.
  • the distance t1 may be of a size that allows the expansion of the piezoelectric element 6 when supplying high-frequency power.
  • the support member 5 is formed with a plurality of through-holes 9 from the front surface to the back surface that pass straight through in the thickness direction intersecting the plane on which the piezoelectric elements 6 are arranged and into which the power cable 4 is inserted.
  • the same number of through holes 9 as the number of piezoelectric elements 6 are formed such that one through hole 9 is positioned at a position facing one piezoelectric element 6 in the thickness direction.
  • the core wire 4a of the power cable 4 protruding from the through hole 9 is connected to the positive electrode 8 substantially perpendicularly with a conductive adhesive or solder.
  • a ground (GND) layer 10 made of a metal sheet such as copper and electrically connected to the GND electrode 7 of the ultrasonic output unit 3 is provided on the back and side surfaces of the support member 5.
  • the shield layer 4 c of each power cable 4 is joined to the GND layer 10 by the solder 12, and is thereby electrically connected to the GND electrode 7 of the ultrasonic output unit 3 via the GND layer 10.
  • the GND layer 10 is preferably provided only on both sides in the longitudinal direction of the insertion portion 2 or on one side surface among the four side surfaces of the support member 5. Thereby, the GND layer 10 can be provided on the side surface of the support member 5 without increasing the diameter of the insertion portion 2.
  • the through-hole 9 has a two-stage structure including a small-diameter portion 9a on the front surface side and a large-diameter portion 9b on the back surface side having a larger inner diameter than the small-diameter portion 9a, and includes a small-diameter portion 9a and a large-diameter portion 9b.
  • An annular abutment surface 9c is formed therebetween.
  • the small diameter portion 9a has an inner diameter that is larger than the outer diameter of the inner coating 4b and smaller than the outer diameter of the shield layer 4c.
  • the large diameter portion 9b has an inner diameter larger than the outer diameter of the shield layer 4c.
  • the tip surface of the shield layer 4c hits the abutting surface 9c, and the amount of insertion of the power cable 4 into the through hole 9 is such that the tip of the core wire 4a is the positive electrode 8.
  • it is controlled to a predetermined amount arranged at a position suitable for joining with the positive electrode 8.
  • the width dimension of each piezoelectric element 6 provided in the in-body ultrasonic treatment apparatus 1 is about 1 mm. Therefore, when connecting the tip of the power cable 4 to the positive electrode 8, it is necessary to control the position of the tip of the power cable 4 with high accuracy. If the position of the tip of the power cable 4 is shifted in the width direction of the piezoelectric element 6, the power cable 4 may be connected to the piezoelectric element 6 adjacent to the piezoelectric element 6 to be connected. In addition, if the position of the tip of the power cable 4 is shifted in the thickness direction of the piezoelectric element 6 and a gap is generated between the tip and the positive electrode 8, the electricity between the tip of the power cable 4 and the positive electrode 8 is generated. Connection may not be obtained.
  • the position of the tip of the power cable 4 is the connection target.
  • the piezoelectric element 6 is stably held at an appropriate position with respect to the positive electrode 8.
  • the support member 5 is arranged at a distance t1 from the ultrasonic output unit 3, the vibration energy of each piezoelectric element 6 is prevented from being absorbed by the support member 5. Accordingly, there is an advantage that powerful ultrasonic waves necessary for treatment such as cauterization of living tissue can be generated at the focusing position.
  • the distance t1 between the back surface of the piezoelectric element 6 and the front surface of the support member 5 is preferably smaller than the thickness of the support member 5 (that is, the length of the through hole 9 in the thickness direction) t2.
  • half t3 (see FIG. 4) of the width dimension of the piezoelectric element 6 is preferably larger than the distance t1.
  • the amount of insertion of the power cable 4 into the through hole 9 is controlled by abutting the tip surface of the shield layer 4c against the abutting surface 9c.
  • it may be formed so as to abut against the tip surface of the inner coating 4b. That is, the small diameter portion 9a has an inner diameter larger than the outer diameter of the core wire 4a and smaller than the outer diameter of the inner coating 4b, and the large diameter portion 9b has an inner diameter larger than the outer diameter of the inner coating 4b. Also good.
  • the inner diameter of the large diameter portion 9b is preferably slightly larger than the outer diameter of the inner coating 4b so that the inner coating 4b fits into the large diameter portion 9b. 6, the dimension may be such that play is formed between the inner surface of the large-diameter portion 9b and the outer surface of the inner coating 4b.
  • At least a part of the through hole 9 on the base end side may be bent toward the base end side in the middle of the thickness dimension of the support member 5 as shown in FIGS. 7 and 8. . 7 and 8, the right side of the drawing is the proximal end side of the insertion portion 2.
  • the distal end portion of the power cable 4 is bent by about 90 °.
  • the curvature of the power cable 4 becomes larger in the power cable 4 on the proximal end side as shown in FIG.
  • the mechanical load acting on the joint portion between 4c and the GND layer 10 is increased.
  • the curvature of the power cable 4 is reduced by bending the through hole 9 at an intermediate position and inclining the portion on the back surface side of the through hole 9 with respect to the longitudinal direction of the insertion portion 2.
  • the mechanical load acting on the joint portion between the layer 4c and the GND layer 10 can be reduced.
  • the through hole 9 may be bent at a bending angle ⁇ corresponding to the position of the through hole 9 in the longitudinal direction of the insertion portion 2.
  • the bending angle ⁇ of the through hole 9 is larger as it is closer to the base end side.
  • the through hole 9 on the front end side may be bent at an intermediate position, it is preferably straight as shown in FIGS. 7 and 8 from the viewpoint of ease of assembly.
  • the GND layer 10 formed uniformly on the back surface of the support member 5 is used.
  • the shape of the GND layer 10 is not limited to this, and an arbitrary shape that can electrically connect the GND electrode 7 and the shield layer 4c of each power cable 4 is adopted. Can do.
  • the GND layer 10 instead of a metal sheet, a substrate on which a wiring pattern extending from each through hole 9 is formed may be used.
  • the support member 5 has a substantially U-shaped longitudinal section and is fixed to the side surface of the ultrasonic output unit 3.
  • the shape of the support member 5 and the ultrasonic output unit 3 are not limited.
  • the fixing position is not limited to this, and can be changed as appropriate.
  • the ultrasonic output unit 3 has a fixing region 3 a made of an insulating material between the piezoelectric elements 6, and the support member 5 is located at a position corresponding to the region 3 a. You may have the wall part 5a fixed to 3a.
  • another ultrasonic output unit 11 that outputs diagnostic ultrasonic waves includes an insertion unit. 2 may be provided.
  • the ultrasonic output unit 11 is preferably provided on the distal end side with respect to the ultrasonic output unit 3.
  • the diagnostic ultrasonic output unit 11 includes an ultrasonic transducer (not shown) that transmits and receives ultrasonic waves, and generates an ultrasonic image based on the reflected waves (echoes) of the received ultrasonic waves.
  • the relative positions of the ultrasonic output unit 11 and the ultrasonic output unit 3 are arranged so that the focus position of the therapeutic ultrasonic wave from the ultrasonic output unit 3 is arranged in the observation field of view by the diagnostic ultrasonic output unit 11. The position is designed.

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  • Life Sciences & Earth Sciences (AREA)
  • Health & Medical Sciences (AREA)
  • Biomedical Technology (AREA)
  • Biophysics (AREA)
  • Nuclear Medicine, Radiotherapy & Molecular Imaging (AREA)
  • Pathology (AREA)
  • Radiology & Medical Imaging (AREA)
  • Engineering & Computer Science (AREA)
  • Physics & Mathematics (AREA)
  • Heart & Thoracic Surgery (AREA)
  • Medical Informatics (AREA)
  • Molecular Biology (AREA)
  • Surgery (AREA)
  • Animal Behavior & Ethology (AREA)
  • General Health & Medical Sciences (AREA)
  • Public Health (AREA)
  • Veterinary Medicine (AREA)
  • Surgical Instruments (AREA)

Abstract

Ce dispositif de traitement par ultrasons est pourvu : d'une partie d'insertion insérée dans un corps; d'une partie de sortie ultrasonore disposée sur une partie d'extrémité distale de la partie d'insertion, la partie de sortie ultrasonore ayant une pluralité d'éléments d'oscillation (6) disposés sur une surface plate; un élément de support (5) ayant une pluralité de trous traversants (9) pénétrant dans une direction croisant la surface plate; et une pluralité de câbles d'alimentation électrique (4) connectés à chacun des éléments d'oscillation (6) à travers les trous traversants (9); l'élément de support (5) étant disposé à une distance de la partie de sortie ultrasonore dans la direction croisant la surface plate.
PCT/JP2017/002822 2017-01-26 2017-01-26 Dispositif de traitement par ultrasons WO2018138847A1 (fr)

Priority Applications (1)

Application Number Priority Date Filing Date Title
PCT/JP2017/002822 WO2018138847A1 (fr) 2017-01-26 2017-01-26 Dispositif de traitement par ultrasons

Applications Claiming Priority (1)

Application Number Priority Date Filing Date Title
PCT/JP2017/002822 WO2018138847A1 (fr) 2017-01-26 2017-01-26 Dispositif de traitement par ultrasons

Publications (1)

Publication Number Publication Date
WO2018138847A1 true WO2018138847A1 (fr) 2018-08-02

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ID=62978184

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PCT/JP2017/002822 WO2018138847A1 (fr) 2017-01-26 2017-01-26 Dispositif de traitement par ultrasons

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Citations (5)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JPS5385982A (en) * 1977-01-10 1978-07-28 Tokyo Shibaura Electric Co Explorer for inspecting body cavity
JPS5596132A (en) * 1979-01-17 1980-07-22 Olympus Optical Co Endoscope
JPS5817359A (ja) * 1981-07-23 1983-02-01 Toshiba Corp アレイ形超音波探触子の製造方法
JPH07222743A (ja) * 1994-02-10 1995-08-22 Toshiba Corp 超音波プローブ
JPH0871078A (ja) * 1994-09-06 1996-03-19 Toshiba Ceramics Co Ltd 超音波発生装置

Patent Citations (5)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JPS5385982A (en) * 1977-01-10 1978-07-28 Tokyo Shibaura Electric Co Explorer for inspecting body cavity
JPS5596132A (en) * 1979-01-17 1980-07-22 Olympus Optical Co Endoscope
JPS5817359A (ja) * 1981-07-23 1983-02-01 Toshiba Corp アレイ形超音波探触子の製造方法
JPH07222743A (ja) * 1994-02-10 1995-08-22 Toshiba Corp 超音波プローブ
JPH0871078A (ja) * 1994-09-06 1996-03-19 Toshiba Ceramics Co Ltd 超音波発生装置

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