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WO2019187213A1 - Dispositif d'ablation - Google Patents

Dispositif d'ablation Download PDF

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Publication number
WO2019187213A1
WO2019187213A1 PCT/JP2018/033759 JP2018033759W WO2019187213A1 WO 2019187213 A1 WO2019187213 A1 WO 2019187213A1 JP 2018033759 W JP2018033759 W JP 2018033759W WO 2019187213 A1 WO2019187213 A1 WO 2019187213A1
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WIPO (PCT)
Prior art keywords
ablation
electrode needle
insulating tube
ablation device
along
Prior art date
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Ceased
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PCT/JP2018/033759
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English (en)
Japanese (ja)
Inventor
祐貴 児玉
謙二 森
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Japan Lifeline Co Ltd
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Japan Lifeline Co Ltd
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Filing date
Publication date
Application filed by Japan Lifeline Co Ltd filed Critical Japan Lifeline Co Ltd
Publication of WO2019187213A1 publication Critical patent/WO2019187213A1/fr
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    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
    • A61B18/04—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by heating
    • A61B18/12—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by heating by passing a current through the tissue to be heated, e.g. high-frequency current
    • A61B18/14—Probes or electrodes therefor

Definitions

  • the present invention relates to an ablation device provided with an electrode needle that is percutaneously punctured to an affected part in the body.
  • An ablation system that performs ablation (cauterization) on such an affected part has been proposed as one of medical devices for treating an affected part in a patient (for example, an affected part having a tumor such as cancer) (for example, Patent Document 1).
  • This ablation system includes an ablation device having an electrode needle that is punctured percutaneously into an affected part in the body, and a power supply device that supplies electric power for performing the ablation on the affected part.
  • the above-described ablation devices are generally required to improve convenience when used, for example. Therefore, it is desirable to provide an ablation device that can improve convenience.
  • An ablation device includes an electrode needle that is punctured percutaneously into an affected part of the body and that is supplied with electric power for ablation, and is positioned on the distal end side of the electrode needle.
  • An insulating tube that covers the periphery of the electrode needle along the axial direction of the electrode needle while exposing the electrode region to be exposed, and a handle attached to the proximal end side of the electrode needle.
  • the insulating tube has a high resistance region having a relatively high frictional resistance in a partial region along the axial direction.
  • the ablation device in the insulating tube that covers the periphery of the electrode needle while exposing the electrode region located on the tip side of the electrode needle, a partial region along the axial direction of the electrode needle In addition, a high resistance region having relatively high frictional resistance is provided.
  • the high resistance region may be provided in a region away from the tip of the insulating tube.
  • the insulating tube is punctured from the region other than the high resistance region (region where frictional resistance is relatively low). Therefore, the slipperiness of the insulating tube is ensured at the time of puncturing. As a result, the convenience when using the ablation device is further improved.
  • the insulating tube is configured to be slidable along the axial direction in response to a predetermined operation on the handle.
  • the high resistance region may be slidable along the axial direction.
  • the position of the high resistance region along the axial direction can be finely adjusted in a state where the electrode needle is percutaneously punctured from the distal end side.
  • the ablation range can be finely adjusted even after the electrode needle is punctured, the convenience when using the ablation device is further improved.
  • a plurality of the high resistance regions may be provided at positions separated from each other along the axial direction.
  • the displacement of the electrode needle along the axial direction is further suppressed, and the variation of the ablation range is further suppressed, so that more effective ablation can be performed.
  • the convenience when using the ablation device is further improved.
  • the frictional resistance may be increased stepwise from the proximal end to the distal end in the high resistance region. Also in this case, displacement of the electrode needle along the axial direction is further suppressed, and fluctuations in the ablation range are further suppressed, so that more effective ablation can be performed. As a result, the convenience when using the ablation device is further improved.
  • a high resistance region having a relatively high frictional resistance is provided in a partial region along the axial direction of the insulating tube. Ablation can be performed. Therefore, convenience when using the ablation device can be improved.
  • Embodiment an example of an insulating tube having a high resistance region in a part of a region away from the tip
  • Modified example Modified example 1 an example of an insulating tube having a plurality of high resistance regions at positions separated from each other
  • Modification 2 Example of an insulating tube in which frictional resistance increases stepwise in a high resistance region
  • FIG. 1 schematically shows a block diagram of an overall configuration example of an ablation system 5 including an ablation device (ablation device 1) according to an embodiment of the present invention.
  • the ablation system 5 is a system used when treating an affected part 90 in the body of a patient 9, and performs predetermined ablation (cauterization) on the affected part 90. It has become.
  • the above-mentioned affected part 90 includes, for example, an affected part having a tumor such as cancer (liver cancer, lung cancer, breast cancer, kidney cancer, thyroid cancer, etc.).
  • a tumor such as cancer (liver cancer, lung cancer, breast cancer, kidney cancer, thyroid cancer, etc.).
  • the ablation system 5 includes an ablation device 1, a liquid supply device 2, and a power supply device 3 as shown in FIG.
  • the counter electrode plate 4 shown in FIG. 1 is also used as appropriate.
  • the ablation device 1 is a device used in the above-described ablation, and includes an electrode needle 11 and an insulating tube 12 as will be described in detail later.
  • the electrode needle 11 is a needle that is punctured percutaneously into the affected part 90 in the body of the patient 9, for example, as indicated by an arrow P1 in FIG.
  • the liquid L supplied from the liquid supply apparatus 2 to be described later circulates in the electrode needle 11 (see FIG. 1).
  • the insulating tube 12 is a member that covers the periphery of the electrode needle 11 along the axial direction of the electrode needle 11 while exposing an electrode region (exposed region Ae described later) located on the distal end side of the electrode needle 11. .
  • the liquid supply apparatus 2 is an apparatus that supplies the cooling liquid L to the ablation device 1 (inside the electrode needle 11), and has a liquid supply section 21, for example, as shown in FIG.
  • Examples of the cooling liquid L include sterilized water and sterilized physiological saline.
  • the liquid supply unit 21 supplies the liquid L to the ablation device 1 as needed according to control by a control signal CTL2 described later. Specifically, for example, as illustrated in FIG. 1, the liquid supply unit 21 causes the liquid L to circulate between the inside of the liquid supply device 2 and the inside of the electrode needle 11 (in a predetermined flow path). Then, the supply operation of the liquid L is performed. Further, according to the control by the control signal CTL2, the liquid L supply operation is executed or stopped.
  • a liquid supply part 21 is comprised including the liquid pump etc., for example.
  • the power supply device 3 supplies power Pout (for example, power of radio frequency (RF)) for performing ablation between the electrode needle 11 and the counter electrode plate 4 and the liquid L in the liquid supply device 2 described above. It is a device for controlling the supply operation. As shown in FIG. 1, the power supply device 3 includes an input unit 31, a power supply unit 32, a control unit 33, and a display unit 34.
  • Pout for example, power of radio frequency (RF)
  • RF radio frequency
  • the input unit 31 is a part for inputting various set values and an instruction signal (operation signal Sm) for instructing a predetermined operation to be described later.
  • Such an operation signal Sm is input from the input unit 31 in response to an operation by an operator (for example, an engineer) of the power supply device 3.
  • these various setting values are not input in response to an operation by the operator, but may be set in the power supply device 3 in advance, for example, when the product is shipped.
  • the set value input by the input unit 31 is supplied to the control unit 33 described later.
  • Such an input unit 31 is configured using, for example, a predetermined dial, button, touch panel, or the like.
  • the power supply unit 32 is a part that supplies the power Pout described above between the electrode needle 11 and the counter electrode plate 4 in accordance with a control signal CTL1 described later.
  • a power supply part 32 is comprised using the predetermined power supply circuit (for example, switching regulator etc.).
  • the predetermined power supply circuit for example, switching regulator etc.
  • the frequency is, for example, about 450 kHz to 550 kHz (for example, 500 kHz).
  • the control unit 33 is a part that controls the entire power supply device 3 and performs predetermined arithmetic processing, and is configured using, for example, a microcomputer. Specifically, the control unit 33 first has a function (power supply control function) of controlling the supply operation of the power Pout in the power supply unit 32 using the control signal CTL1. In addition, the control unit 33 has a function (liquid supply control function) for controlling the supply operation of the liquid L in the liquid supply device 2 (liquid supply unit 21) using the control signal CTL2.
  • temperature information It measured in the ablation device 1 (a temperature sensor such as a thermocouple disposed inside the electrode needle 11) is supplied to the control unit 33 as needed. It has become so.
  • the measurement value of the impedance value Zm is supplied to the control unit 33 from the power supply unit 32 as needed.
  • the display unit 34 is a part (monitor) that displays various types of information and outputs the information to the outside. Examples of information to be displayed include the above-described various set values input from the input unit 31, various parameters supplied from the control unit 33, temperature information It supplied from the ablation device 1, and the like. However, the information to be displayed is not limited to these information, and other information may be displayed instead of or in addition to other information.
  • a display part 34 is comprised using the display (For example, a liquid crystal display, a CRT (Cathode * Ray * Tube) display, an organic EL (Electro * Luminescence) display, etc.) by various systems.
  • the counter electrode plate 4 is used while being attached to the body surface of the patient 9 during ablation. Although details will be described later, during ablation, high-frequency energization is performed (electric power Pout is supplied) between the electrode needle 11 (the electrode region described above) and the counter electrode plate 4 in the ablation device 1. ing. Although details will be described later, during such ablation, as shown in FIG. 1, the impedance value Zm between the electrode needle 11 and the counter electrode plate 4 is measured as needed, and the measured impedance value Zm is In the power supply device 3, power is supplied from the power supply unit 32 to the control unit 33.
  • FIG. 2 schematically shows a detailed configuration example of the ablation device 1 shown in FIG. 1 in a side view (YZ side view).
  • the portion indicated by the symbol P ⁇ b> 2 is enlarged and shown below in FIG. 2, as indicated by an arrow.
  • the electrode needle 11 is provided along the Z-axis direction as shown in FIG. 2, and the length (axial length) along the Z-axis direction is, for example, about 30 mm to 350 mm.
  • the electrode needle 11 has, along its axial direction (Z-axis direction), an exposed region Ae (electrode region that functions as an electrode during ablation) that is not covered with the insulating tube 12, and an insulating tube. 12 and the area
  • the electric power Pout for ablation is supplied between the exposed area Ae of the electrode needle 11 and the counter electrode plate 4.
  • hook 11 is comprised by metal materials, such as stainless steel, nickel titanium alloy, a titanium alloy, platinum, for example.
  • the insulating tube 12 is a member that covers the periphery of the electrode needle 11 along the Z-axis direction while partially exposing the distal end side (exposed region Ae) of the electrode needle 11.
  • the insulating tube 12 is attached to the electrode needle 11 along its axial direction (Z-axis direction), for example, as indicated by an arrow d2 in FIG.
  • Z-axis direction Z-axis direction
  • it is configured to be relatively slidable. Thereby, the length (axial direction length) along the Z-axis direction in the exposed region Ae of the electrode needle 11 can be adjusted.
  • the axial length (length along the Z-axis direction) of such an insulating tube 12 is, for example, about 30 mm to 347 mm. Further, the length (axial length) along the Z-axis direction in the exposed region Ae of the electrode needle 11 that can be adjusted by the insulating tube 12 is, for example, about 3 mm to 50 mm.
  • the insulating tube 12 has a high resistance region 12H having a relatively high frictional resistance in a partial region along the axial direction (Z-axis direction). is doing. Specifically, in the example of FIG. 2, the insulating tube 12 has such a high resistance region 12H and a low resistance region 12L having a relatively low frictional resistance. That is, as shown in FIG. 2, the frictional resistance RfH in the high resistance region 12H is higher than the frictional resistance RfL in the low resistance region 12L (RfH> RfL). The value of the frictional resistance RfH is preferably 1.5 times or more larger than the value of the frictional resistance RfL (RfH ⁇ (1.5 ⁇ RfL)).
  • such a high resistance region 12H is provided in a region away from the tip of the insulating tube 12, and the vicinity of the tip of the insulating tube 12 is a low resistance region 12L.
  • the low resistance region 12 ⁇ / b> L, the high resistance region 12 ⁇ / b> H, and the low resistance region 12 ⁇ / b> L are arranged in this order from the distal end to the proximal end side.
  • the axial length (the length along the Z-axis direction) of the low resistance region 12L located on the tip side is, for example, 1 mm to 250 mm, preferably 10 mm to 30 mm.
  • the axial length of the high resistance region 12H (the length along the Z-axis direction) is 3 mm to 230 mm, preferably 10 mm to 30 mm.
  • Such a high resistance region 12H has a function of suppressing (preventing) slipping of the insulating tube 12 during ablation, as will be described in detail later.
  • the high resistance region 12H can be formed, for example, by applying a film (coating film) having a relatively high frictional resistance around the base material in the insulating tube 12 constituting the low resistance region 12L. Is possible.
  • the base material (member constituting the low resistance region 12L) of the insulating tube 12 is, for example, PEEK (polyether ether ketone), PI (polyimide), fluorine resin, polyether block amide, It is made of a synthetic resin having a relatively high hardness.
  • the above-described coating film (member constituting the high resistance region 12H) is made of a synthetic resin having a relatively low hardness, such as polyurethane, silicone rubber, nylon elastomer, styrene elastomer, and the like. This is because as the hardness increases, the surface of the insulating tube 12 becomes slippery (friction resistance decreases), while as the hardness decreases, the surface of the insulating tube 12 becomes less slippery (friction resistance decreases). Because it becomes higher).
  • the handle 13 is a portion that is gripped (gripped) by an operator (doctor) when the ablation device 1 is used.
  • the handle 13 mainly includes a handle main body (handle member) 130 attached to the proximal end side of the electrode needle 11 and an operation unit 131.
  • the handle body 130 corresponds to a portion (gripping portion) that is actually gripped by the operator, and is a portion that also functions as an exterior of the handle 13.
  • the handle body 130 is made of synthetic resin such as polycarbonate, acrylonitrile-butadiene-styrene copolymer (ABS), acrylic, polyolefin, polyoxymethylene, and the like.
  • the operation part 131 is a part used for a predetermined operation (slide operation) for causing the insulating tube 12 to slide relative to the electrode needle 11 along the axial direction (Z-axis direction). Yes, and protrudes outside the handle body 130 (in the Y-axis direction).
  • the operation unit 131 is made of, for example, the same material (synthetic resin or the like) as the handle body 130 described above.
  • the operation unit 131 is configured to be slidable relative to the handle main body 130 along the axial direction (Z-axis direction) of the handle 13.
  • the insulating tube 12 moves along the Z-axis direction with respect to the electrode needle 11.
  • the sliding movement is relatively performed (see, for example, the arrow d2 in FIG. 2).
  • the length (axial direction length) along the Z-axis direction in the exposed region Ae of the electrode needle 11 can be adjusted.
  • the above-described high resistance region 12H is also slidable relative to the electrode needle 11 along the Z-axis direction (for example, FIG. 2 (see arrow d3 in 2).
  • the liquid supply device 2 in order that the cooling liquid L circulates between the inside of the liquid supply device 2 and the inside of the electrode needle 11 (within a predetermined flow path).
  • the liquid L is supplied from the liquid supply part 21) to the electrode needle 11 (see FIG. 1).
  • hook 11 is performed in the case of ablation.
  • the ablation is completed, after such cooling operation is also stopped, based on the temperature information It measured at the electrode needle 11, whether the tissue temperature of the affected area 90 is sufficiently increased, etc. The degree of shochu is confirmed.
  • FIG. 3 schematically shows an example of the condition of cauterization in the affected area 90 due to such ablation.
  • the initial rugby ball-shaped (elliptical spherical) thermal coagulation region Ah1 gradually expands.
  • a substantially spherical thermocoagulation region Ah2 is obtained (see the broken arrow in FIG. 3).
  • isotropic ablation of the entire affected area 90 is performed, and as a result, effective treatment of the affected area 90 is performed.
  • the above-described slide operation on the operation unit 131 is performed on the handle 13 of the ablation device 1. Done in advance. Specifically, when a slide operation along the Z-axis direction is performed on the operation unit 131 (see, for example, the arrow d1 in FIGS. 2 and 4B), the operation unit 131 is interlocked with the slide operation. Thus, the slide mechanism 132 in the handle main body 130 performs a sliding operation along the Z-axis direction (see FIGS. 4A and 4B).
  • the insulating tube 12 In conjunction with the sliding operation of the sliding mechanism 132, the insulating tube 12 also performs a sliding operation along the Z-axis direction (see, for example, the arrow d2 in FIGS. 2 and 4B).
  • the size (length along the Z-axis direction) of the exposed area Ae on the distal end side of the electrode needle 11 is arbitrarily adjusted,
  • the ablation range at the time of ablation is also arbitrarily adjusted.
  • the exposed area Ae (ablation range) is set small, and the tip of the electrode needle 11 is inserted to the affected area 90 to perform ablation.
  • the exposed area Ae cauterized selectively. That is, parts other than the affected part 90 are not cauterized, and the original function can be maintained.
  • the exposed area Ae cauterized together (collectively).
  • the slide operation on the operation unit 131 and the slide operation of the slide mechanism 132 and the insulating tube 12 in conjunction with the slide operation are stepwise along the axial direction (Z-axis direction) of the electrode needle 11. It may be adjustable (intermittently). In other words, the position when the operation unit 131, the slide mechanism 132, and the insulating tube 12 slide may be slightly fixed for each predetermined distance along the Z-axis direction.
  • FIG. 5 is a schematic diagram illustrating an operation example at the time of ablation using the ablation device (ablation device 101) according to the comparative example. Specifically, FIG. 5 shows a state where the electrode needle 11 in the ablation device 101 of the comparative example is punctured percutaneously (through the skin surface Sk) with respect to the affected part 90 during ablation. ing. This point is the same in FIG. 6, which will be described later, schematically showing an operation example in the ablation using the ablation device 1 of the present embodiment.
  • the ablation device 101 of the comparative example shown in FIG. 5 corresponds to the ablation device 1 of the present embodiment shown in FIGS. 2 and 4 in which an insulating tube 102 is provided instead of the insulating tube 12. is doing.
  • the insulating tube 102 corresponds to the insulating tube 12 in which the high resistance region 12H is not provided (omitted). That is, the insulating tube 102 is provided with only the low resistance region 12L (the base material of the insulating tube 12 described above) as shown in FIG.
  • the entire insulating tube 102 is slippery at the time of puncturing, it is easy to puncture the skin surface Sk.
  • the following problems may occur when ablation is performed with the electrode needle 11 being percutaneously punctured into the affected area 90.
  • the electrode needle 11 together with the insulating tube 102 slides along the axial direction (Z-axis direction) and is displaced in synchronization with the movement of the skin surface Sk due to respiration of the patient 9. (See arrow d101 in FIG. 5).
  • the ablation range corresponding to the exposed region Ae may vary along the Z-axis direction, making it difficult to perform effective ablation.
  • the ablation device 101 of the comparative example when used, it is difficult to perform effective ablation. As a result, the convenience in using the ablation device 101 may be impaired.
  • the ablation device 1 has the following configuration as shown in FIGS. That is, in the insulating tube 12 that covers the periphery of the electrode needle 11 while exposing the exposed area Ae (electrode area) located on the distal end side of the electrode needle 11, the axial direction (Z-axis direction) of the electrode needle 11 is aligned. A high resistance region 12H having a relatively high frictional resistance is provided in a partial region.
  • the ablation device 1 of the present embodiment is as follows, unlike the ablation device 101 of the comparative example described above.
  • the electrode needle 11 when ablation is performed with the electrode needle 11 percutaneously punctured on the affected part 90, the electrode needle 11 is axially moved together with the insulating tube 12. Displacement along the (Z-axis direction) is suppressed, and is preferably prevented (see “x (cross)” indicated by an arrow d101 in FIG. 6). Therefore, as a result of suppressing (preferably preventing) fluctuation of the ablation range corresponding to the exposed region Ae, effective ablation can be performed.
  • the electrode needle 11 when the electrode needle 11 is percutaneously punctured into the affected part 90, for example, as shown in FIG. 6, the high resistance region 12H is formed between the affected part 90 and the skin surface Sk. It is desirable to be located between them. This is because when the high resistance region 12H touches the skin surface Sk, as described above, the electrode needle 11 may be displaced under the influence of the respiration of the patient 9.
  • the high resistance region 12H is provided in a partial region along the axial direction of the insulating tube 12, effective ablation can be performed. it can. Therefore, in this ablation device 1, for example, convenience in use can be improved as compared with the ablation device 101 of the comparative example.
  • such a high resistance region 12 ⁇ / b> H is provided in a region away from the tip of the insulating tube 12. That is, the vicinity of the tip of the insulating tube 12 is a low resistance region 12L having a relatively low frictional resistance.
  • the insulating tube 12 is punctured from the side of the region other than the high resistance region 12H (low resistance region 12L). The slipperiness of the sex tube 12 is ensured. As a result, the convenience when using the ablation device 1 can be further improved.
  • the insulating tube is used in accordance with a predetermined operation (sliding operation described above: see arrow d1) with respect to the handle 13 (operation unit 131).
  • 12 is configured to be slidable along the axial direction (Z-axis direction) (see arrow d2).
  • the high resistance region 12H is also slidable along the axial direction (see arrow d3).
  • Adjustment can be performed (see arrows d2 and d3 in parentheses in FIG. 6). As a result, since the ablation range corresponding to the exposed region Ae can be finely adjusted even after the electrode needle 11 has been punctured in this way, the convenience when using the ablation device 1 is further improved. It becomes possible.
  • FIG. 7 schematically shows a configuration example of an ablation device according to Modifications 1 and 2 in a side view.
  • FIG. 7A schematically shows a configuration example of the distal end side of the electrode needle 11 and the like in the ablation device (ablation device 1A) according to Modification 1 in a side view.
  • FIG. 7B schematically shows a configuration example of the distal end side of the electrode needle 11 and the like in the ablation device (ablation device 1B) according to Modification 2 in a side view.
  • the ablation device 1A of Modification 1 shown in FIG. 7A corresponds to the ablation device 1 according to the embodiment in which an insulating tube 12A is provided instead of the insulating tube 12, and other configurations are provided. Is the same.
  • this insulating tube 12A unlike the insulating tube 12 in which only one high resistance region 12H is provided, a plurality (three in this example) are provided at positions separated from each other along the axial direction (Z-axis direction). ) High resistance region 12H.
  • the plurality of high resistance regions 12H are provided in regions away from the tip of the insulating tube 12A.
  • the plurality of high resistance regions 12H are provided at positions separated from each other along the axial direction of the insulating tube 12A. That is, the displacement along the axial direction (Z-axis direction) of the electrode needle 11 is further suppressed, and the above-described variation of the ablation range is further suppressed, so that more effective ablation can be performed. As a result, in the first modification, the convenience when using the ablation device can be further improved.
  • the ablation device 1B of Modification 2 shown in FIG. 7B corresponds to the ablation device 1 according to the embodiment in which the insulating tube 12B is provided instead of the insulating tube 12.
  • the structure of is the same.
  • the frictional resistance increases stepwise from the proximal end to the distal end in the high resistance region 12H.
  • the high resistance region 12H has three types of high resistance regions 12Ha, 12Hb, and 12Hc from the base end to the tip.
  • the frictional resistances RfHa, RfHb, and RfHc in the high resistance regions 12Ha, 12Hb, and 12Hc have the following stepwise magnitude relationship including the frictional resistance RfL in the low resistance region 12L. That is, as shown in FIG. 7B, there is a stepwise magnitude relationship of (RfHa>RfHb>RfHc> RfL).
  • the frictional resistance is increased stepwise from the proximal end to the distal end in the high resistance region 12H of the insulating tube 12B. become. That is, in this case as well, as in Modification 1 described above, the displacement of the electrode needle 11 along the axial direction (Z-axis direction) is further suppressed, and the above-described variation in the ablation range is further suppressed. Ablation can be performed. As a result, also in the second modification, it is possible to further improve the convenience when using the ablation device.
  • each member described in the above embodiment and the like are not limited and may be other materials.
  • the configuration of the ablation device and the like has been specifically described, but it is not always necessary to include all members, and other members may be further included.
  • the values, ranges, magnitude relationships, etc. of the various parameters described in the above embodiments are not limited to those described in the above embodiments, etc., and other values, ranges, magnitude relationships, etc. Good.
  • the configuration of the electrode needle, the insulating tube, the handle, etc. in the ablation device has been specifically described, but the configuration of each of these members has been described in the above-described embodiment, etc. It is not restricted to, It is good also as another structure.
  • the electrode needle may be a bipolar type instead of the monopolar type described in the above embodiments and the like.
  • the insulating tube and the high resistance region may not be slidable along the axial direction of the electrode needle.
  • the size, shape, and number of high resistance regions in the insulating tube, and the frictional resistance size (a fixed value or a value that varies depending on the region) in the high resistance region are described in the above embodiments.
  • the size, shape, number, etc. may be different.
  • the high resistance region is provided in a region away from the tip of the insulating tube as an example, but the present invention is not limited to this case. That is, for example, the high resistance region may be provided in the region at the tip of the insulating tube.
  • the block configurations of the liquid supply device 2 and the power supply device 3 have been specifically described, but it is not always necessary to include all the blocks described in the above-described embodiment and the like. Other blocks may be further provided.
  • the ablation system 5 as a whole may further include other devices in addition to the devices described in the above embodiments and the like.
  • the ablation device in which high-frequency conduction is performed between the electrode needle 11 and the counter electrode plate 4 at the time of ablation has been specifically described, but is not limited to the above-described embodiment and the like. Absent. Specifically, for example, an ablation device that performs ablation using other electromagnetic waves such as radio waves and microwaves may be used.
  • control operation (ablation method) in the control unit 33 including the power supply control function and the liquid supply control function has been specifically described.
  • the control method (ablation method) in the power supply control function and the liquid supply control function is not limited to the method described in the above embodiment.
  • the series of processing described in the above-described embodiment and the like may be performed by hardware (circuit) or may be performed by software (program).
  • the software is composed of a group of programs for causing each function to be executed by a computer.
  • Each program may be used by being incorporated in advance in the computer, for example, or may be used by being installed in the computer from a network or a recording medium.

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Abstract

La présente invention concerne un dispositif d'ablation qui peut améliorer la praticité. Un dispositif d'ablation 1 comprend : une aiguille d'électrode 11 qui perce par voie percutanée une partie affectée 90 à l'intérieur d'un corps et qui est alimentée en énergie électrique Pout pour réaliser une ablation ; un tube isolant 12 qui fait apparaître une zone d'électrode (zone apparente Ae) située sur le côté d'extrémité de pointe de l'aiguille d'électrode 11 tout en recouvrant la périphérie de l'aiguille d'électrode 11 le long de la direction axiale (direction d'axe Z) de l'aiguille d'électrode 11 ; et une poignée 13 montée sur le côté d'extrémité de base de l'aiguille d'électrode 11. Le tube isolant 12 possède, dans une région partielle le long de la direction axiale, une zone de résistance élevée 12H où la résistance à la friction est relativement élevée.
PCT/JP2018/033759 2018-03-27 2018-09-12 Dispositif d'ablation Ceased WO2019187213A1 (fr)

Applications Claiming Priority (2)

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JP2018-059921 2018-03-27
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JPH10243947A (ja) * 1997-03-04 1998-09-14 Olympus Optical Co Ltd 高周波装置
WO2006025366A1 (fr) * 2004-09-01 2006-03-09 Jms Co., Ltd. Système de traitement des varices
US20090118727A1 (en) * 2007-11-05 2009-05-07 Robert Pearson Ablation devices and methods of using the same

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JPH10243947A (ja) * 1997-03-04 1998-09-14 Olympus Optical Co Ltd 高周波装置
WO2006025366A1 (fr) * 2004-09-01 2006-03-09 Jms Co., Ltd. Système de traitement des varices
US20090118727A1 (en) * 2007-11-05 2009-05-07 Robert Pearson Ablation devices and methods of using the same

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