WO2021066479A2

WO2021066479A2 - Magnetic induction-type surgical instrument

Info

Publication number: WO2021066479A2
Application number: PCT/KR2020/013266
Authority: WO
Inventors: 최준호
Original assignee: (주)나노맥
Priority date: 2019-10-02
Filing date: 2020-09-28
Publication date: 2021-04-08
Also published as: WO2021066479A3

Abstract

The present invention relates to a magnetic induction-type surgical instrument. The surgical instrument comprises: a base electrode (11); a magnetic layer (12) formed on the base electrode (11); and a current induction pattern layer (13) for inducing a magnetic field in the magnetic layer (12).

Description

Magnetic induction surgical device

The present invention relates to a magnetic induction type surgical device, and specifically relates to a magnetic induction type surgical device capable of cutting by coagulating a surgical site with heat due to hysteresis resistance due to induction of a magnetic field.

In the process of surgery, human tissues, such as blood vessels, need to be cut, and after coagulation for hemostasis, a designated area can be cut by an appropriate cutter. For example, in the process of laparoscopic surgery, a part of a blood vessel or similar human body needs to be cut, and for this purpose, a surgical tool such as an ultrasonic cutting machine or a high frequency cutting machine may be used. For example, International Publication No. WO 2011/097469 discloses an electrosurgical device for dissecting tissue by applying high-frequency energy. In addition, WO 2010/120944 discloses a thermally adjustable surgical instrument made of an electric conductor coated with a ferromagnetic coating. The magnetic induction method in which a magnetic field is induced and heat is generated by hysteresis loss has the advantage that the response is fast and power efficiency is high due to a method in which high-frequency energy is directly applied. It is necessary to form an appropriate current induction structure for generating a magnetic field for solidification and cutting by transferring heat to human tissues by such a magnetic induction method. In addition, there is a need to create a heat transfer structure that conducts heat in a predetermined direction by a magnetic field generated by current induction. However, the prior art does not disclose such a current inducing structure and a heat transfer structure.

The present invention has the following objects to solve the problems of the prior art.

An object of the present invention is to provide a magnetic induction type surgical device that induces a magnetic field generated by a current induced by a current induction pattern by a ferromagnetic cutter so that solidification and cutting are effectively performed.

Another object of the present invention is to provide a surgical device having a ferromagnetic structure that operates in a hybrid manner in which a portion of a tissue solidified by heat generated from a ferromagnetic electrode according to a magnetic induction method is cut by an ultrasonic blade.

According to a preferred embodiment of the present invention, a surgical device for cutting body tissue by generating heat includes a base electrode; A magnetic layer formed on the base electrode; And a current induction pattern layer for inducing a magnetic field in the magnetic layer, wherein the current induction pattern layers are arranged in parallel with each other or consist of a plurality of linear induction paths extending in a spiral shape.

According to another suitable embodiment of the present invention, the current induction pattern becomes a printed electrode.

According to another suitable embodiment of the present invention, it further comprises vibration generating means for operating the functional tool.

According to another preferred embodiment of the present invention, a surgical device for cutting human tissue includes a current control unit for controlling an amount of current; A magnetic induction current pattern for generating a magnetic field by a current induced by the current control unit; A magnetic induction heat generating unit generating heat by a magnetic field generated by the magnetic induction current pattern; And a functional tool for coagulating and cutting human tissues with the generated heat.

According to another suitable embodiment of the present invention, a surgical device for cutting human tissue includes first and second sub-jaws coupled to enable engagement with each other; A cutting electrode formed in the first sub-jaw; A ferromagnetic layer formed on at least a portion of the cutting electrode; And a current pattern layer for inducing a magnetic field in the ferromagnetic layer.

According to another suitable embodiment of the present invention, it further comprises a temperature detection unit and a switch operation unit that cuts off the electrical connection according to a signal transmitted from the temperature detection unit.

According to another suitable embodiment of the present invention, a surgical device includes a ferromagnetic induction electrode module that generates heat according to the flow of current; An ultrasonic cutter module for cutting a portion solidified by heat generated from the ferromagnetic induction electrode module; And a timing module for determining an operating time of the ferromagnetic induction electrode module and the ultrasonic cutter module.

According to still another suitable embodiment of the present invention, a switch module is further included that is operated according to the operation of the timing module to block a current flowing to the ferromagnetic induction electrode module.

According to another suitable embodiment of the present invention, a surgical device for cutting a human tissue portion includes a first sub-jaw in which a ferromagnetic induction electrode is disposed; A second sub-jaw in which an ultrasonic blade is disposed; And a transducer for controlling the operation of the ultrasonic blade.

According to another suitable embodiment of the present invention, the ultrasonic blade is operated with a vibration frequency of 10 to 50 kHz while vibrating back and forth or left and right.

The magnetic induction type surgical device according to the present invention allows a cutting tool portion for coagulation and cutting to be operated by magnetic induction, thereby reducing a procedure time. The surgical device according to the present invention forms an appropriate current induction pattern according to the surgical site so that heat is generated in the area for cutting, so that the influence of the surrounding area according to the procedure is reduced. In addition, the surgical device having a ferromagnetic structure according to the present invention prevents damage to the tissue surrounding the surgery by cutting the coagulated portion with an ultrasonic blade while rapidly coagulating the tissue portion with a ferromagnetic induction electrode. In the surgical device according to the present invention, the conductor for the flow of current is sealed to prevent the current from flowing to the human body. The surgical device according to the present invention can be applied to various areas including laparoscopic surgery.

1 shows an embodiment of a magnetic electrode structure of a magnetic induction type surgical device according to the present invention.

2 shows an embodiment of a current induction pattern applied to the magnetic electrode of the surgical device according to the present invention.

Figure 3 shows an embodiment of the operation structure of the magnetic electrode in the surgical device according to the present invention.

4 shows an embodiment of a surgical device according to the present invention.

5 shows an embodiment of a cutting process by the surgical device according to the present invention.

6 shows another embodiment of a surgical device having a ferromagnetic structure according to the present invention.

7 and 8 show another embodiment to which the surgical device according to the present invention is applied.

9 shows another embodiment of the operating structure of the surgical device according to the present invention.

In the following, the present invention will be described in detail with reference to the embodiments shown in the accompanying drawings, but the embodiments are for a clear understanding of the present invention, and the present invention is not limited thereto. In the following description, components having the same reference numerals in different drawings have similar functions, so if they are not necessary for the understanding of the invention, they will not be described repeatedly, and well-known components will be briefly described or omitted, but the present invention It should not be understood as being excluded from the embodiment of.

Referring to FIG. 1, a surgical device for cutting body tissue by generating heat includes a base electrode 11; A magnetic layer 12 formed on the base electrode 11; And a current induction pattern layer 13 for inducing a magnetic field in the magnetic layer 12.

The base electrode 11 may have a function of cutting by coagulating a cutting portion by contacting a blood vessel or similar body tissue, for example. The base electrode 11 may be made in various structures depending on the surgical site or the cutting area, and some may be made in a cutter structure. At least a portion of the base electrode 11 may be made of a material having a high heat transfer coefficient or may include a magnetic material. The base electrode 11 may be made of various structures suitable for solidification and cutting of a cutting portion, and may include various materials capable of generating heat in a predetermined portion, and is not limited to the presented embodiment. A magnetic layer 12 may be formed under the base electrode 11, and the magnetic layer 12 is, for example, iron (Fe), cobalt (Co), nickel (Ni), or iron oxide (FeO ₄ ). It may contain a ferromagnetic material. The magnetic layer 12 is formed as a layer independent from the base electrode 11. It can be formed integrally. Specifically, a magnetic layer 12 made of a magnetic material having a thickness of 1 to 10,000 μm may be formed on a lower portion of the base electrode 11. Alternatively, the magnetic layer 12 may be formed on at least a part of the inside of the base electrode 11. Alternatively, the magnetic layer 12 may be formed in a manner in which a magnetic strip is inserted into the base electrode 11. The magnetic layer 12 may be formed in various ways, for example, coated on the base electrode 11, printed with magnetic ink, attached in a film form, or formed by inserting a magnetic strip. I can. The magnetic layer 12 may be formed on a part of the base electrode 11 and may be formed based on a portion to which a body tissue to be solidified and cut is fixed. The magnetic layer 12 may be formed in various ways and is not limited to the presented embodiment.

As the magnetic field is induced in the magnetic layer 12, a current induction pattern layer 13 may be disposed to generate hysteresis loss and thereby generate heat due to an eddy current. The current induction pattern layer 13 may be formed in various ways, for example, may be formed under the magnetic layer 12. The current induction pattern layer 13 may have a function of inducing a current in a predetermined direction to generate a change in a magnetic field, and is formed by being coupled to the base electrode 11 or the magnetic layer 12, or depending on the structure of the surgical device. It may be formed separately on the base electrode 11 or the magnetic layer 12. The current induction pattern layer 13 may have a function of generating a magnetic field according to the flow of current and inducing the generated magnetic field to the magnetic layer 12. The current pattern layer 13 may be made in various shapes such as a coil pattern, a spiral pattern, or a parallel linear pattern. When the current induction pattern layer 13 is combined with the magnetic layer 12, the current pattern layer 13 may be formed inside the insulating layer or may be separated from the magnetic layer 12 by the insulating layer. As shown in the plan view and cross-sectional view of (A) of FIG. 1, when the base electrode 11, the magnetic layer 12, and the current induction pattern layer 13 are formed in a combined structure, the current induction pattern layer 13 A protective layer 14 may be formed on the underside of. The protective layer 14 may be made of an electromagnetic shielding material or may be made of an insulating material. Alternatively, the protective layer 14 may be made of a heat-dissipating structure or a heat-dissipating material, whereby heat generated from the current induction pattern layer 13 may be quickly discharged to the outside. The protective layer 14 may be formed in various ways according to the structure of the current induction pattern layer 13 and is not limited to the exemplary embodiment presented.

As shown in (B) of FIG. 1, the magnetic layer 12a or the current induction pattern layer 13a may be made in various shapes according to the structure of the cutting tool. For example, the cutting tool may include an induction body 15 and an electrode tip 11a protruding from the induction body 15 and having a cutting function. The electrode tip 11a may be made of a triangular cone or a similar structure having a sharp side at the lower end as a whole. The magnetic layer 12a may be formed inside the cutter at a sharp portion corresponding to the solidification and cutting portion, and the current pattern inducing layer 13a may be formed inside the electrode tip 11a. A pair of

inductors

16a and 16b for inducing the flow of current to the current pattern induction layer 13a are connected to one end and the other end of the current induction pattern layer 13a to induce current to the current pattern induction layer 13a. can do. The current may be, for example, an alternating current having a predetermined frequency, and electric fields in different directions may be generated in the current pattern inducing layer 13a by induction of the alternating current. In addition, as magnetic fields in different directions are induced in the magnetic layer 12a, heat according to the flow of the induced current may be generated. In addition, the generated heat may be transferred to the base electrode 11 or the electrode tip 11a so that the body tissue in contact with the base electrode 11 or the electrode tip 11a is solidified and can be cut. The solidified body tissue can be cut by the base electrode 11 or the electrode tip 11a or by other suitable cutting means. The base electrode 11 or the electrode tip 11a may have various structures and is not limited to the exemplary embodiments presented.

Referring to FIG. 2, the current induction pattern layers 13 may be arranged in parallel with each other, or may be formed of a plurality of linear induction paths extending in a spiral shape. The current induction pattern layer 13 may include a base layer 21 made of an insulator material and

induction patterns

22a and 22b formed on the base layer 21. The base layer 21 may have a plate shape, may be made in the form of a thin film, or may be made in a shape having a predetermined thickness. When the base layer 21 is made in the form of a thin film,

induction patterns

22a and 22b may be formed on one or both sides, and the

induction patterns

22a and 22b are a plurality of induction paths that allow current to flow in the same direction. It may include (22_1 to 22_N). The guide paths 22_1 to 22_N may be formed by printing with a conductive ink or by bonding a conductive film having a plurality of conductive paths. Both ends of the plurality of guide paths 22_1 to 22_N arranged parallel to each other may be connected to each other by

connection paths

221a and 221b, and guide

tabs

23a and 23b are provided in each of the

connection paths

221a and 221b. Can be connected. The

induction tabs

23a and 23b may be connected to the current control module to induce a current through the

induction patterns

22a and 22b to generate a magnetic field. The guide paths 22_1 to 22_N may have a structure extending in the width direction of the base 21 or may have a structure extending in the length direction, and may be formed at various positions of the base 11. Referring to the lower part of FIG. 2, an induction pattern 22 may be formed above the base 21, and a magnetic layer 12 may be coupled above the induction pattern 22. The protective layer 25 may be formed under the base 21, and the magnetic induction module thus formed may be coupled to the base and the electrode described above. Optionally, the base layer 21 may have a plate shape having a thickness, and the interior may be an empty space or may be filled with a ferrite material having a high permeability. When made into a plate shape having a thickness of the base layer 21, the guide paths 22_1 to 22_N may be formed in a shape surrounding the base layer 21 while forming a coil shape with one end connected to each other. In this case, the

induction patterns

22a and 22b may extend in a spiral shape. The

induction patterns

22a and 22b may be formed in various structures and are not limited to the presented embodiments.

3, a surgical device for cutting human tissue includes a current control unit 32 for controlling an amount of current; A magnetic induction current pattern 33 for generating a magnetic field by a current induced by the current control unit 32; A magnetic induction heat generating unit 34 for generating heat by a magnetic field generated by the magnetic induction current pattern 33; And a functional tool 35 for coagulating and cutting human tissues with the generated heat.

The entire operation of the surgical instrument may be controlled by the control module 31, for example, the operation of the current control unit 32 may be controlled. The current control unit 32 may have a function of adjusting the amount of current flowing into the current induction pattern, the cycle or time of the alternating current. By the current control unit 32, the current can be induced to the magnetic induction current pattern unit 33, and the magnetic induction current pattern unit 33 includes a current induction pattern, and has a function of inducing a magnetic field to the magnetic layer. I can. The self-inducing current pattern unit 33 may have a function of detecting an internal temperature according to the flow of current while detecting the amount of current flowing in the current inducing pattern. The magnetic induction heat generating unit 34 may have a function of detecting heat generated by an induced current induced in the magnetic layer by the magnetic induction current pattern unit 33. The magnetic induction heat generating unit 34 may detect the flow of current induced in the magnetic layer, and detect a heat transfer direction with this. In addition, it is possible to detect whether the temperature of the magnetic layer or the functional tool 35 is out of a predetermined temperature range while detecting a temperature difference between the magnetic layer or the functional tool 35 by detecting the temperature of the magnetic layer and the functional tool 35. The magnetic induction heat generating unit 34 can detect and monitor various heat generating effects according to the induction and flow of electric current, and is not limited to the presented embodiment. Heat generated in the magnetic layer may be transferred to the functional tool 35, and the functional tool 35 may have a function of fixing and coagulating a body tissue to be cut, such as a blood vessel, to make it a cuttingable state. The functional tool 35 can be actuated by the actuating means 36, and the actuating means 36 can have a function of regulating the operation of the functional tool 35. The functional tool 35 may have a structure in which the coagulated body tissue is cut together with coagulation, or may have a structure in which the cutter is moved and cut in a solidified state in a fixed state. The operating means 36 may include a driving means such as a motor for applying vibration or moving the cutter for cutting the solidified body tissue. The actuating means 36 may include various additional means to allow the cutting to be performed efficiently and is not limited to the embodiment presented. The functional tool 35 may have a jaw or clamp structure that can be engaged with each other.

4 shows an embodiment of a surgical device according to the present invention.

Referring to FIG. 4, the surgical device 40 for cutting human tissue includes first and second sub-jaws 42 and 43 coupled to enable engagement with each other; A cutting electrode 422 formed in the first sub-jaw 42; A ferromagnetic layer 423 formed on at least a portion of the cutting electrode 422; And a current pattern layer 424 for inducing a magnetic field in the ferromagnetic layer 423. The surgical device 40 may be composed of an induction module 41 and a jaw module 42, and the induction module 41 may be connected to an operation module (not shown) for operating the jaw module 42. The actuation module can operate the jaw module 42 via the induction module 41, for example, it can operate the jaw module. The first and second sub-jaws 42 and 43 may have a structure that can be interlocked with each other, and for example, one end of the first sub-jaw 42 with respect to the first sub-jaw 42 maintained in a fixed state The second sub-jaws 43 coupled to are rotatably coupled so that the first and second sub-jaws 42 and 43 may be engaged with each other.

Connectors

413 and 414 are coupled to one end of the first and second sub-jaws 42 and 43, respectively, and each of the

connectors

413 and 414 may be connected to the operation member 412. The operation member 412 may be disposed inside the induction tube 411 extending in a cylindrical shape. The wiring unit 415 may be disposed inside the induction tube 411, and current may be supplied to the current induction pattern layer 424 through the wiring unit 415. The first and second sub-jaws 42 and 43 may be composed of first and

second jaw bodies

421 and 422 and first and second engaging

units

422 and 432, respectively, and the first and second jaw bodies 421, 422) is engaged with each other so that the body tissue can be fixed. Article 1 A current pattern layer 424 may be disposed on the body 421, and a ferromagnetic layer 423 may be disposed above the current pattern layer 424. The ferromagnetic layer 423 may be disposed below the first engaging unit 422, and the ferromagnetic layer 423 may be disposed based on a position where the body tissue is fixed. In order to fix the body tissue, the first and second sub-jaws 42 and 43 may be opened, and the body tissue may be fixed in a region in which the ferromagnetic layer 423 of the first engaging unit 422 is disposed. The body tissue may be fixed to the jaw module while the first and

second sub jaws

42 and 43 are engaged with each other by the operation of the operation module. In addition, current is induced to the current pattern layer 424 so that the crude module can be operated.

5, the coarse module may be operated by the trigger unit 51 installed in the operation module, and the power setting unit 52 and the temperature setting unit 53 may be operated before the operation of the coarse module is started. have. The current delivered to the current induction pattern layer by the power setting unit 52 may be set, and the temperature of the crude module may be set by the temperature setting unit 53. When the power and temperature are set in this way, the bath module may be operated by the bath operation unit 54. A contact connection unit 55 and a switch operation unit 56 may be installed in the jaw module, and in the contact connection unit 55, when the first and second sub-jaws are engaged with each other, the wiring for power supply and the current induction pattern layer are electrically connected to each other. Make sure to connect. In addition, when the first and second sub-jaws are opened, the contact connection unit 55 is opened, thereby preventing electrical connection. The switch operation unit 56 may function as a switch for supplying current in a current induction pattern by detecting an operation to the contact connection unit 55. In addition, it may have a function of stopping current supply to the current pattern layer by detecting a connection by the contact connection unit 55. The temperature of the crude module may be detected by the temperature detection unit 57, and when a predetermined temperature is reached, a cutting signal may be transmitted to the cutting unit 58. The temperature detection unit 58 may stop supplying current by controlling the operation of the switch operation unit 56 when the temperature does not fall within the preset temperature range or is out of the temperature range, and may transmit this to the control module 31. In addition, when the cutting process is completed by the operation of the cutting unit 58, the trigger unit 51 is operated by the control module 31 to open the jaw module. The surgical instrument may be operated in various ways and is not limited to the presented embodiments.

Referring to FIG. 6, a surgical device having a ferromagnetic structure includes a ferromagnetic induction electrode module 63 that generates heat according to the flow of current; An ultrasonic cutter module 64 for cutting a portion solidified by heat generated from the ferromagnetic induction electrode module 63; And a timing module 62 for determining the operating time of the ferromagnetic induction electrode module 63 and the ultrasonic cutter module 64.

The ferromagnetic induction electrode module 63 may include a magnetic induction electrode having various structures capable of generating eddy current due to a change in a magnetic field according to the flow of current, and thus generating heat. The ferromagnetic induction electrode module 63 may include, for example, a ferromagnetic material such as iron (Fe), cobalt (Co), nickel (Ni), or iron oxide (FeO ₄ ), and apply a magnetic field to the ferromagnetic material. It may include an inducible current induction path. The flow of current to the ferromagnetic module 63 can be generated by the control of the control module 61, for example, the flow of AC current can be generated, and the timing and start of current application by the timing module 62 The time can be set. When a current is applied to the ferromagnetic induction electrode module 63, heat is generated, and accordingly, a portion of a human body tissue in contact with the electrode module 63 may be solidified by heat. In this way, when a tissue portion such as a blood vessel to be cut is coagulated, the coagulated portion may be cut by the ultrasonic cutter module 64. The ultrasonic cutter module 64 has a function of vibrating by, for example, 5 to 50 kHz of ultrasonic waves, and generating vibrations in the left-right direction or the front-rear direction of the solidified part to cut the solidified part. In general, ultrasonic waves mean sound waves having a frequency of 20 kHz or more, but in this specification, ultrasonic waves are _{generated by piezoelectric vibration elements such as PZT(Pb(ZrTi)O 3} ), ceramic elements, crystals, and barium titanate. It includes various frequencies, and preferably refers to a frequency band of 1 MHz or less. The ultrasonic cutter module 64 includes, for example, a transducer for converting electrical vibration into mechanical vibration, a fixing unit fixing the transducer at a predetermined position; An acoustic lens or horn for guiding the generated sound waves in a predetermined direction; And an ultrasonic blade vibrating so as to vibrate at the end of the horn. The ultrasonic cutter module 14 may have various structures capable of generating vibrations for a predetermined time, such as 0.01 to 5 seconds at the coagulation site, and is not limited to the presented embodiment.

The ferromagnetic induction electrode module 63 and the ultrasonic cutter module 64 may be in contact with each other during the solidification and cutting process, and the solidification and cutting process needs to be started or terminated at a predetermined time while proceeding for as short a time as possible. The operating time or time of the ferromagnetic induction electrode module 63 or the ultrasonic cutter module 64 may be set by the timing module 62. The timing module 62 may have a function of determining a start time, a duration time, and a cutoff time of the ferromagnetic induction electrode module 63 and the ultrasonic cutter module 64. Specifically, it is necessary to apply vibration to the cut part by the ultrasonic cutter module 64 while the cut part is solidified by the ferromagnetic induction electrode module 63 or at the same time as the solidification is performed. The timing module 62 may have a function of matching the solidification time by the ferromagnetic induction electrode module 63 and the cutting time by the ultrasonic cutter module 64 as described above. Additionally, the timing module 62 may have a function of stopping the operation of the ferromagnetic induction electrode module 63 or the ultrasonic cutter module 64 after solidification or cutting is completed. The operating states of the ferromagnetic induction electrode module 63 and the ultrasonic cutter module 64 may be detected by the detection module 65. For example, the relative position, temperature, or operating state of the ferromagnetic induction electrode module 63 and the ultrasonic cutter module 64 may be detected by the detection module 65. The detection module 65 may also detect a leakage current that may be generated in the ferromagnetic induction electrode module 63 or the ultrasonic cutter module 64. The ferromagnetic induction electrode module 63 may induce a magnetic field by the flow of current and detect a leakage current due to various causes. The information detected by the detection module 65 may be transmitted to the operation check module 66, and the operation check module 66 may check whether a predetermined operation has been completed. In addition, a confirmation signal according to the completion of the operation check module 66 may be transmitted to the switch module 67. The switching module 67 may determine switching by checking the completion signal transmitted from the operation check module 66 while being operated according to the setting of the timing module 62. The switch module 67 may be various switches such as, for example, a semiconductor switch or a program switch, and the present invention is not limited thereby.

Referring to FIG. 7, a surgical device for cutting a human tissue portion includes a first sub jaw 71 in which a ferromagnetic induction electrode 713 is disposed; A second sub-jaw 22 in which an ultrasonic blade 722 is disposed; And a transducer 25 for controlling the operation of the ultrasonic blade 222. The first sub-jaw 71 and the second sub-jaw 72 may have a structure that can be engaged with each other, and for example, one end is connected to the actuating connector 23, and the operation of the actuating connector 23 is It can be operated by means of an operation module (not shown). For example, the surgical instrument may have a handpiece structure connected to a control computer, but is not limited thereto. The first and second sub-jaws (71, 72) are engaged by rotating the first sub-jaw (71) in the direction of the second sub-jaw (72) or the opposite direction with one end connected to the actuating connector (73). Can be removed or separated. The first sub jaw 71 includes a first body 711; A groove-shaped electrode guide 712 formed on the inner surface of the first body 711; And a ferromagnetic induction electrode 713 disposed inside the electrode guide 712. The electrode guide 712 may have a shape extending linearly to the inner surface of the first body 711, and the ferromagnetic induction electrode 713 may have a structure extending along the center of the electrode guide 712. Optionally, the end portion of the ferromagnetic induction electrode 713 may have a blade structure having a relatively thin thickness. The second sub-jaw 72 meshed with the first sub-jaw 71 may be formed of an ultrasonic blade 722 formed to partially protrude toward the upper surface of the second body 721 and the second body 721. . The first sub-jaw 21 may have an overall inverted U-shape, and a cross section in a direction perpendicular to the length direction of the second sub-jaw 72 may be a polygon whose width becomes narrower as it goes upward. In this structure, the first sub-jaw 71 may be engaged in a shape covering at least a part of the upper portion of the second sub-jaw 72. Optionally, the current inductor 76 inside the first sub-jaw 71 may be separated by the ferromagnetic induction electrode 713 and the insulating material. In such a structure, the current derivative 76 may be formed of copper, brass, bronze, platinum or similar conductive material, and the ferromagnetic induction electrode 713 may be a ferromagnetic material. The current inductor 76 may be a linear plate shape, a linear wire shape, or a similar shape. Optionally, the ferromagnetic induction electrode 713 may be a current derivative. The transducer 75 that generates ultrasonic waves by power supply may be installed inside the second sub-jaw 72 or in another suitable position, and convert electrical vibration into mechanical vibration so that the ultrasonic blade 722 vibrates back and forth. do. The lower portion of the ultrasonic blade 722 may be supported by a spring or similar elastic unit 74, and the elastic unit 74 may have a coil shape or a pad shape. Human tissue to be cut may be located on the upper surface of the second sub-jaw 72, and the first sub-jaw 71 may be moved in the direction of the first sub-jaw 72. When the first sub-jaw 71 and the second sub-jaw 72 are approached, heat may be generated in the ferromagnetic induction electrode 713, and when the tissue portion in contact with the ferromagnetic induction electrode 713 solidifies, the ultrasonic blade The solidified portion may be cut by the vibration of 722. Thereafter, when the first sub-jaw 71 is rotated and restored to its original position, the solidification and cutting process is completed.

Referring to FIG. 8, the magnetic induction surgical tool includes a first sub-jaw 71 in which an ultrasonic blade 722 is disposed; A second sub-jaw 72 in which the ferromagnetic induction electrode 713 is disposed; And a connector 73 for engaging the first sub-jaw 71 and the second sub-jaw 72 with each other, and the ferromagnetic induction electrode 713 has a linear tube structure. As described above, the first and second sub-jaws 71 and 72 may be coupled by an actuating connector 73 so as to be engaged with each other. The ferromagnetic induction electrode 713 disposed on the second body 721 of the second sub-jaw 72 may have a linearly extending tube or wire shape. Referring to the cross-sectional view perpendicular to the extension direction shown on the right side of FIG. 3, a part of the first ferromagnetic induction electrode 713a may be exposed to the outside of the upper surface of the second body 721, and the first ferromagnetic The second ferromagnetic induction electrode 713b for inducing the current of the induction electrode 713a to the current supply module may be disposed inside the second body 721. The first ferromagnetic induction electrode 713a and the second ferromagnetic The induction path of the current may be set so that magnetic fields induced by the current flowing through the induction electrode 713b do not cancel each other. The first body 711 may be provided with a linear receiving guide 711a in which the exposed portion of the first ferromagnetic induction electrode 713a can be accommodated, and the ultrasonic blade 722 may be disposed in the receiving guide 711a. I can. The ultrasonic blade 722 may be vibrated in the front-rear direction by the ultrasonic generating module 81. The ferromagnetic induction electrode 713a includes, for example, a hollow tube-shaped induction path 84; A current inducing layer 83 disposed outside the induction path; An insulating layer 82 disposed outside the current inducing layer 33; And a magnetic induction layer 81 including a ferromagnetic component disposed outside the insulating layer 82. Optionally, the magnetic induction layer 81 may include a protective layer made of a thermally conductive material. The surgical device having such a structure has an advantage that the coagulation portion can be cut by the ultrasonic blade 722 while coagulation is performed. In addition, the cooling component of the gas or liquid component is guided through the guide path 84. The cooling fluid can be guided by various fluid induction modules, and the area around the cutting or the area that has been cut can be quickly cooled.

Referring to Figure 9, the surgical tool is a control module 61; An induced current module 91 whose operation is controlled by the control module 61; A ferromagnetic induction electrode 713 generating heat by a magnetic field by a current controlled by the induction current module 91; And a cooling unit 84 for removing heat generated from the ferromagnetic induction electrode 713. The entire operation of the surgical tool may be controlled by the control module 61, and the control module 61 may be disposed in a computer, for example. And a part including a jaw unit having a hand piece structure can be connected to the computer. A current having a predetermined frequency is induced by the induction current module 91 to the ferromagnetic induction electrode 713, and heat may be generated in the ferromagnetic induction electrode 713 due to hysteria loss. As described above, an induction path may be formed in the ferromagnetic induction electrode 713, and a cooling fluid may be guided through the induction path. Supply and discharge of the cooling fluid through the induction path may be performed by the cooling control module 92. Optionally, a cooling unit 94 such as a thermoelectric element may be disposed in the induction path, and the current flowing through the ferromagnetic induction electrode 713 and the current flow of the cooling unit 94 may be switched by the switch unit 93. have. Specifically, after the current is supplied to the ferromagnetic unit 713, when the human tissue is solidified and cut, the current is supplied to the cooling unit 94 by the switch unit 92 to perform cooling. As described above, the solidified portion may be cut by vibration of the ultrasonic blade. The cooling unit 94 can be an electrical element or component having various operating structures, and as described above, a cooling fluid can also be directed to the cooling unit 94.

The present invention has been described in detail above with reference to the presented embodiments, but those of ordinary skill in this field will be able to make various modifications and modifications without departing from the technical spirit of the present invention with reference to the presented embodiments. . The present invention is not limited by such modifications and modifications, but is limited by the claims appended below.

The surgical device according to the present invention can be applied to a laparoscopic surgical device manufacturing industry or a variety of medical industries similar thereto.

Claims

In a surgical device for cutting body tissue by generating heat,

A base electrode 11;

A magnetic layer 12 formed on the base electrode 11; And

Including a current induction pattern layer 13 for inducing a magnetic field in the magnetic layer 12,

The current induction pattern layer 13 is a magnetic induction type surgical device consisting of a plurality of linear induction paths arranged in parallel with each other or extending in a spiral shape.
The magnetic induction type surgical device according to claim 1, wherein the current induction pattern 13 becomes a printed electrode.
The surgical instrument according to claim 1, further comprising vibration generating means for operating the functional tool (35).
In a surgical device for cutting human tissue,

A current control unit 32 that controls the amount of current;

A magnetic induction current pattern 33 for generating a magnetic field by a current induced by the current control unit 32;

A magnetic induction heat generating unit 34 for generating heat by a magnetic field generated by the magnetic induction current pattern 33; And

Surgical device comprising a functional tool 35 for coagulating and cutting human tissues with the generated heat.
In a surgical device for cutting human tissue,

First and second sub-jaws 42 and 43 coupled to enable engagement with each other;

A cutting electrode 422 formed in the first sub-jaw 42;

A ferromagnetic layer 423 formed on at least a portion of the cutting electrode 422; And

A surgical instrument for cutting comprising a current pattern layer 424 for inducing a magnetic field in the ferromagnetic layer 423.
The surgical instrument for cutting according to claim 7, further comprising a temperature detection unit (57) and a switch operation unit (56) that cuts off the electrical connection according to a signal transmitted from the temperature detection unit (55).
In the surgical device,

A ferromagnetic induction electrode module 63 for generating heat according to the flow of current;

An ultrasonic cutter module 64 for cutting a portion solidified by heat generated from the ferromagnetic induction electrode module 63; And

A surgical instrument having a ferromagnetic characteristic structure comprising a ferromagnetic induction electrode module 63 and a timing module 62 for determining an operation time of the ultrasonic cutter module 64.
The surgical device of claim 7, further comprising a switch module (67) that is operated according to the operation of the timing module (64) to block a current flowing to the ferromagnetic induction electrode module (63).
In the surgical device for cutting human tissue parts,

A first sub-jaw 71 in which a ferromagnetic induction electrode 713 is disposed;

A second sub-jaw 72 in which the ultrasonic blade 722 is disposed; And

Surgical device of a ferromagnetic structure comprising a transducer (75) for controlling the operation of the ultrasonic blade (722).
The surgical device of claim 9, wherein the ultrasonic blade 722 is operated at a vibration frequency of 10 to 50 kHz while vibrating back and forth or left and right.