WO2021139017A1 - 一种微波消融针头及微波消融针 - Google Patents

一种微波消融针头及微波消融针 Download PDF

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Publication number
WO2021139017A1
WO2021139017A1 PCT/CN2020/083723 CN2020083723W WO2021139017A1 WO 2021139017 A1 WO2021139017 A1 WO 2021139017A1 CN 2020083723 W CN2020083723 W CN 2020083723W WO 2021139017 A1 WO2021139017 A1 WO 2021139017A1
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Prior art keywords
branch
microwave ablation
distal end
ablation needle
tube
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PCT/CN2020/083723
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English (en)
French (fr)
Inventor
王卫中
郑锐
陈翠华
江荣华
隆龙
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南京康友医疗科技有限公司
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Priority to US17/642,941 priority Critical patent/US20220361947A1/en
Priority to EP20912960.0A priority patent/EP3988043B1/en
Priority to JP2022504071A priority patent/JP2022541817A/ja
Publication of WO2021139017A1 publication Critical patent/WO2021139017A1/zh

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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
    • A61B18/18—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by applying electromagnetic radiation, e.g. microwaves
    • A61B18/1815—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by applying electromagnetic radiation, e.g. microwaves using microwaves
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B17/00—Surgical instruments, devices or methods, e.g. tourniquets
    • A61B2017/00831—Material properties
    • A61B2017/00867—Material properties shape memory effect
    • A61B2017/00871—Material properties shape memory effect polymeric
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B17/00—Surgical instruments, devices or methods, e.g. tourniquets
    • A61B2017/00831—Material properties
    • A61B2017/0088—Material properties ceramic
    • 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
    • A61B2018/00005—Cooling or heating of the probe or tissue immediately surrounding the probe
    • A61B2018/00011—Cooling or heating of the probe or tissue immediately surrounding the probe with fluids
    • A61B2018/00023—Cooling or heating of the probe or tissue immediately surrounding the probe with fluids closed, i.e. without wound contact by the fluid
    • 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
    • A61B2018/00053—Mechanical features of the instrument of device
    • A61B2018/00059—Material properties
    • A61B2018/00071—Electrical conductivity
    • A61B2018/00083—Electrical conductivity low, i.e. electrically insulating
    • 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
    • A61B2018/00053—Mechanical features of the instrument of device
    • A61B2018/00107—Coatings on the energy applicator
    • 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
    • A61B2018/00053—Mechanical features of the instrument of device
    • A61B2018/00107—Coatings on the energy applicator
    • A61B2018/00148—Coatings on the energy applicator with metal
    • 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
    • A61B2018/00571—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body for achieving a particular surgical effect
    • A61B2018/00577—Ablation
    • 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
    • A61B2018/00636—Sensing and controlling the application of energy
    • A61B2018/00773—Sensed parameters
    • A61B2018/00827—Current
    • 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
    • A61B18/18—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by applying electromagnetic radiation, e.g. microwaves
    • A61B18/1815—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by applying electromagnetic radiation, e.g. microwaves using microwaves
    • A61B2018/183—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by applying electromagnetic radiation, e.g. microwaves using microwaves characterised by the type of antenna
    • A61B2018/1853—Monopole antennas
    • 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
    • A61B18/18—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by applying electromagnetic radiation, e.g. microwaves
    • A61B18/1815—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by applying electromagnetic radiation, e.g. microwaves using microwaves
    • A61B2018/1869—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by applying electromagnetic radiation, e.g. microwaves using microwaves with an instrument interstitially inserted into the body, e.g. needles

Definitions

  • the present disclosure relates to the field of microwave ablation treatment equipment, and in particular to a microwave ablation needle and a microwave ablation needle.
  • microwave ablation therapy has become one of the important treatments for soft tissues such as liver cancer, kidney cancer and thyroid.
  • Microwave ablation uses an antenna to radiate microwaves.
  • the microwaves cause the ions and polar water molecules in the tissue to rotate and vibrate and rub each other to produce a thermal effect.
  • the treatment area can quickly reach a high temperature, the tissue is solidified, dehydrated and necrotic, so as to achieve the purpose of treatment.
  • the outer conductor of the coaxial cable forms an induced current, which causes the ablation area to be uncontrollable and forms an ellipsoid.
  • the purpose of the present disclosure includes, for example, providing a microwave ablation needle and a microwave ablation needle, which can effectively suppress the induced current and eliminate the influence of the induced current on the ablation morphology, so that the heating area is concentrated in the radiation area, and a more ideal spherical ablation is obtained. Shape to meet clinical needs.
  • the embodiments of the present disclosure can be implemented as follows:
  • an embodiment provides a microwave ablation needle, which includes an outer tube, a cooling tube, a coaxial cable, and an electrode;
  • the outer tube includes a first branch and a second branch arranged in sequence from the distal end to the proximal end of the outer tube.
  • the end of the first branch away from the second branch forms the distal end of the outer tube; wherein the material of the first branch is Ceramic materials or polymer materials;
  • the cooling tube is arranged in the outer tube, the cooling tube and the outer tube are spaced apart and a first cooling channel is formed between the cooling tube and the outer tube; wherein the material of the cooling tube is a polymer material; the distal end of the cooling tube is located in the first branch Inside the distal end to form an installation space in the distal area of the cooling pipe;
  • the coaxial cable is arranged in the cooling pipe, the coaxial cable and the cooling pipe are spaced apart and a second cooling channel is formed between the cooling pipe and the coaxial cable; the distal end of the coaxial cable is located in the distal end of the cooling pipe;
  • At least part of the electrode is located in the installation space and is electrically connected to the distal end of the coaxial cable.
  • the first branch pipe and the second branch pipe are inserted and matched.
  • the outer peripheral wall of the first branch pipe is provided with a first annular groove, and the distal end of the second branch pipe is inserted into the first annular groove.
  • the first branch and the second branch are welded.
  • the first branch and the second branch are detachably connected.
  • the electrode is a cylindrical electrode, and the distal end of the first branch tube is closed and provided with spikes, so as to be configured as a closed installation space;
  • Part of the cylindrical electrode is located in the distal end of the cooling tube and is electrically connected to the coaxial cable; the remaining part of the cylindrical electrode protrudes from the distal end of the cooling tube and is located in the first branch, and the distal end of the cylindrical electrode is connected to the first branch.
  • the distal end face of a branch tube is spaced apart.
  • the electrode is a needle electrode, and the distal end of the first branch tube is open;
  • the needle electrode includes a spike head and a connector connected to the proximal end surface of the spike head;
  • the spike head is connected to the distal end of the first branch pipe and closes the opening at the distal end of the first branch pipe.
  • the spike head is spaced from the distal end of the cooling pipe; the part of the connector is located in the cooling pipe and is configured to be far from the coaxial cable. Terminals are electrically connected.
  • the outer peripheral wall of the spike head is provided with a second annular groove recessed in a direction close to the inside of the spike head, and the distal end of the first branch pipe is inserted and fitted with the second annular groove.
  • the spike head is welded to the first branch.
  • the spike head is detachably connected to the first branch pipe.
  • the coaxial cable includes a first segment and a second segment that are sequentially connected in a direction from a distal end to a proximal end thereof, and an end of the first segment away from the second segment forms the distal end of the coaxial cable,
  • the first segment is configured to be connected to the electrode;
  • the first section is a section of the coaxial cable with a bare inner conductor
  • the second section is a section of the coaxial cable with a bare insulation layer.
  • the maximum distance between the shielding layer peeling opening at the end of the second segment away from the first segment and the end of the second branch pipe is 1/4 of the length of the microwave wavelength.
  • the microwave ablation needle further includes a sensing element, which is arranged on the outer peripheral wall of the first branch tube and configured to sense part of the radiation current of the coaxial cable to enhance the radiation capability.
  • the sensing element is arranged around the outer peripheral wall of the first branch pipe.
  • the sensing element is sprayed on the outer peripheral wall of the first branch pipe.
  • the sensing element is a pipe section, and the sensing element is sleeved on the outer peripheral wall of the first branch pipe.
  • the outer peripheral wall of the first branch pipe is provided with a third annular groove, and the sensing element is located in the third annular groove and does not protrude from the notch of the third annular groove.
  • the length of the sensing element in the extension direction of the first branch is L1
  • the distance between the connection position of the first branch and the second branch to the proximal end of the electrode is L2
  • L1 is less than L2.
  • the sensing element is made of one of copper, iron, aluminum, gold, silver, palladium, platinum, tin, nickel, zinc, and alloys thereof.
  • an embodiment provides a microwave ablation needle, which includes a handle and the above-mentioned microwave ablation needle;
  • the handle is connected to the proximal end of the second branch pipe.
  • the handle includes a first chamber and a second chamber.
  • the first chamber and the second chamber are respectively communicated with the first cooling channel and the second cooling channel to form cooling. Liquid circulation loop.
  • the beneficial effects of the embodiments of the present disclosure include, for example:
  • the microwave ablation needle includes an outer tube, a cooling tube, a coaxial cable and an electrode. It can form a sleeve structure and a cooling channel for the cooling liquid to flow through the mutual sheathing of the outer tube, the coaxial cable and the cooling tube.
  • the induced current generated after the electrode is energized can be consumed, and at the same time, the heat generated by the sleeve structure's consumption of the induced current can be taken away by the flow of the cooling liquid in the cooling channel. Therefore, the microwave ablation needle can effectively suppress the induced current and eliminate the influence of the induced current on the ablation morphology, so that the heating area is concentrated in the radiation area, and a relatively ideal spherical ablation morphology is obtained to meet clinical needs.
  • Fig. 1 is a schematic structural diagram of a microwave ablation needle adopting a cylindrical electrode in the present disclosure
  • FIG. 2 is a schematic diagram of a partial structure of a microwave ablation needle adopting a cylindrical electrode in the present disclosure
  • Fig. 3 is a schematic structural diagram of a microwave ablation needle adopting a cylindrical electrode in the present disclosure
  • FIG. 4 is a schematic diagram of the structure of a microwave ablation needle adopting a needle electrode in the present disclosure
  • FIG. 5 is a schematic diagram of a partial structure of a microwave ablation needle adopting a needle electrode in the present disclosure
  • Fig. 6 is a schematic structural diagram of a microwave ablation needle adopting a needle electrode in the present disclosure
  • FIG. 7 is a schematic diagram of a partial structure of a microwave ablation needle with a cylindrical electrode provided with a sensing element in the present disclosure
  • FIG. 8 is a schematic diagram of a partial structure of a microwave ablation needle adopting a needle-shaped electrode provided with a sensing element in the present disclosure.
  • Icon 200-microwave ablation needle; 210-electrode; 211-cylindrical electrode; 212-needle electrode; 2121-pointed tip; 2122-connector; 2123-second annular groove; 220-outer tube; 221-th One branch; 2211-first annular groove; 2212-third annular groove; 222-second branch; 230-coaxial cable; 231-first section; 232-second section; 240-cooling pipe; 241- The first cooling channel; 242-the second cooling channel; 250-installation space; 260-induction component; 300-microwave ablation needle; 310-handle; 311-first chamber; 312-second chamber;
  • FIG. 1 and FIG. 2 show the structure of a microwave ablation needle using a cylindrical electrode in an embodiment of the present disclosure.
  • the present disclosure provides a microwave ablation needle 200, which includes an outer tube 220, a cooling tube 240, a coaxial cable 230, and an electrode 210.
  • the outer tube 220 includes a first branch 221 and a second branch 222 arranged in sequence from the distal end to the proximal end of the outer tube 220, and the end of the first branch 221 away from the second branch 222 forms the distal end of the outer tube 220 , The end of the second branch pipe 222 away from the first branch pipe 221 forms the proximal end of the outer pipe 220; wherein, the material of the first branch pipe 221 is a ceramic material or a polymer material.
  • the cooling tube 240 is arranged in the outer tube 220, and the cooling tube 240 and the outer tube 220 are spaced apart, and a first cooling channel 241 is formed between the cooling tube 240 and the outer tube 220; optionally, the outer circumference of the cooling tube 240 The wall and the inner peripheral wall of the outer tube are spaced apart, so that the first cooling channel 241 has an annular structure surrounding the cooling tube 240; wherein the material of the cooling tube 240 is a polymer material; the distal end of the cooling tube 240 is located in the first branch 221 There is a distance between the distal end of the cooling pipe 240 and the inner wall of the distal end of the first branch pipe 221 to form an installation space 250 near the distal end of the cooling pipe 240.
  • the coaxial cable 230 is arranged in the cooling pipe 240, the coaxial cable 230 and the cooling pipe 240 are spaced apart, and a second cooling channel 242 is formed between the cooling pipe 240 and the coaxial cable 230; optionally, the same
  • the outer peripheral wall of the shaft cable 230 is spaced from the inner peripheral wall of the cooling pipe 240, so that the second cooling channel 242 has a ring structure surrounding the coaxial cable 230; the distal end of the coaxial cable 230 is located inside the cooling pipe 240, and the same
  • the distal end of the shaft cable 230 is spaced from the inner wall of the distal end of the first branch pipe 221.
  • At least part of the electrode 210 is located in the installation space 250 and is electrically connected to the distal end of the coaxial cable 230.
  • the working principle of the microwave ablation needle 200 is:
  • the microwave ablation needle 200 includes an outer tube 220, a cooling tube 240, a coaxial cable 230, and an electrode 210.
  • the cooling tube 240 is sheathed outside the coaxial cable 230
  • the outer tube 220 is sheathed outside the cooling tube 240.
  • a sleeve structure and a flow channel for the cooling liquid to flow are formed.
  • the role of the sleeve structure is to consume induced current to suppress the induced current; when the sleeve structure suppresses the induced current, the heat generated can pass through the cooling flowing in the first cooling channel 241 and the second cooling channel 242 Take away the liquid.
  • the microwave ablation needle 200 can inhibit the induced current during the working process, and eliminate the influence of the induced current on the ablation form, and obtain a more ideal spherical ablation form.
  • the second branch pipe 222 can be made of a metal material or a polymer material filled with a continuous wire braid.
  • a branch tube 221 is made of ceramic material or polymer material, and the cooling tube 240 is made of polymer material. Therefore, when the microwave ablation needle 200 is assembled on the microwave ablation needle 300 in cooperation with other structures, it can ensure the microwave ablation needle 300 The use of strength and durability.
  • the microwave ablation needle 200 is installed on the microwave ablation needle 300, during use, since the microwave ablation needle 300 needs to be punctured into the human body, the first branch 221 and the second branch are set 222, it needs to be made of materials that meet the requirements of medical biocompatibility.
  • the second branch pipe 222 can be made of 304 stainless steel, 316 stainless steel, cobalt-chromium alloy, nickel-titanium alloy, or titanium alloy, or a polymer tube filled with a continuous wire braid, such as 304 stainless steel braid reinforced PI (PolyimideFilm) tube, etc.;
  • the first branch 221 may be made of ceramic materials such as alumina ceramics or zirconia ceramics, or polymer materials;
  • the cooling tube 240 may be a polymer material tube such as PEEK (polyetheretherketone), PI (PolyimideFilm), or PTFE (Polytetrafluoroethylene) polytetrafluoroethylene.
  • PEEK polyetheretherketone
  • PI PolyimideFilm
  • PTFE Polytetrafluoroethylene
  • the function of the microwave ablation needle 200 is to suppress induced current, and during use, in order to improve the microwave energy suppression effect, the connection area between the electrode 210 and the coaxial cable 230 needs to be relatively located there.
  • the microwave ablation needle 200 is in the induction current suppression area. Therefore, when the cooling pipe 240 is installed, the distal end of the cooling pipe 240 is located inside the distal end of the first branch pipe 221 to form an installation space 250 in the distal area of the cooling pipe 240 ; When the electrode 210 is installed, the electrode 210 needs to be electrically connected to the coaxial cable 230.
  • the coaxial cable 230 needs to be arranged in the cooling pipe 240, and the distal end of the coaxial cable 230 is located in the distal end of the cooling pipe 240. Therefore, after the electrode 210 is installed in the installation space 250, the electrode 210 can be The distal end of the coaxial cable 230 is electrically connected, and the part where the electrode 210 and the coaxial cable 230 are electrically connected can be relatively located in the installation space 250 defined by the cooling tube 240 and the outer tube 220, so as to ensure the electrode of the microwave ablation needle 200
  • the induced current emitted by 210 is located in the induced current suppression area to ensure the suppression effect of the microwave ablation needle 200 on the induced current.
  • the electrode 210 when the electrode 210 is installed, the electrode 210 may be a cylindrical electrode 211, and the distal end of the first branch pipe 221 is closed and provided with spikes to be configured to close the installation space 250.
  • the electrode 210 is a cylindrical electrode 211
  • part of the electrode 210 is located in the cooling tube 240, and the remaining part extends from the distal end of the cooling tube 240 and is located in the first branch 221, At this time, the cylindrical electrode 211 does not have a blocking effect on the first branch 221.
  • the remote of the first branch 221 can be removed.
  • the end is set as a closed end, and the distal end of the first branch pipe 221 is provided with spikes extending from the first branch pipe 221 in a direction away from the second branch pipe 222, and the spikes are configured to penetrate the human body.
  • the installation space 250 can be closed, so that the first cooling flow passage 241 and the second cooling flow passage 242 are connected to each other at the installation space 250, so that the The cooling liquid can flow into the second cooling flow channel 242 or the cooling liquid in the second cooling flow channel 242 can flow into the first cooling flow channel 241.
  • the cooling liquid can flow in the microwave ablation needle 200.
  • the microwave ablation needle 200 has the function of suppressing the induced current, the flow of the cooling liquid will take away and suppress the induced current. The heat.
  • the cylindrical electrode 211 can be made of copper, iron, aluminum, gold, silver, palladium, platinum, tin, nickel, zinc, and alloys thereof.
  • the pillar electrode 211 is provided with copper.
  • the cylindrical electrode 211 when the cylindrical electrode 211 is configured, since the installation space 250 is enclosed by the first branch pipe 221, the cylindrical electrode 211 is located in the installation space 250, and the cylindrical electrode 211 located in the inner part of the distal end of the cooling tube 240 is the same as the same.
  • the shaft cable 230 is electrically connected; the remaining part of the cylindrical electrode 211 is located in the distal end of the first branch 221, and is not in contact with the inner end surface of the distal end of the first branch 221, so that the distal end of the cylindrical electrode 211 and the first branch 221 remote interval setting.
  • the proximal end of the first branch 221 when connecting the first branch 221 and the second branch 222, the proximal end of the first branch 221 is provided with a first annular groove 2211, the first annular groove 2211 is located on the outer peripheral wall of the first branch 221, The distal end of the annular groove 2211 is spaced from the distal end of the first branch pipe 221, and the proximal end of the first annular groove 2211 extends to the proximal end surface of the first branch pipe 221, in other words, on the outer peripheral wall of the first branch pipe 221 A first annular groove 2211 radially inward is provided, and the distal end of the second branch pipe 222 is snap-fitted with the first annular groove 2211. That is, the distal end of the second branch pipe 222 is sleeved outside the proximal end of the first branch pipe 221, and a part of the second branch pipe 222 is snap-fitted with the first annular groove 2211.
  • the wall thickness of the first branch pipe 221 at the first annular groove 2211 can be reduced, so that after the second branch pipe 222 is clamped with the first annular groove 2211, the second The outer wall of the branch pipe 222 will not protrude outward from the outer wall of the first branch pipe 221, and the two will not form a stepped structure at the connecting joint, which is convenient for operation.
  • the outer diameters of the first branch pipe 221 and the second branch pipe 222 may be set equal, so that the outer wall of the first branch pipe 221 and the outer wall of the second branch pipe 222 are located in the same annular surface.
  • first branch pipe 221 and the second branch pipe 222 may be fixedly connected by welding or the like, or the first branch pipe 221 and the second branch pipe 222 may be detachably connected.
  • first branch pipe 221 and the second branch pipe 222 can be connected by bonding.
  • first annular groove 2211 can hold the glue. Therefore, the stability of the adhesion can be improved, and at the same time, after the adhesion is completed, the first annular groove 2211 and the glue contained in the first annular groove 2211 can also play a role of sealing.
  • the coaxial cable 230 includes a first section 231 and a second section 232 that are arranged in sequence from the distal end to the proximal end thereof.
  • the end of the first section 231 away from the second section 232 forms the same
  • the distal end of the shaft cable 230, the end of the second section 232 away from the first section 231 forms the proximal end of the coaxial cable 230;
  • the first section 231 is a section of the coaxial cable 230 with bare inner conductors, and the second section 232 It is a section of the coaxial cable 230 with bare insulation;
  • the coaxial cable 230 connected to the electrode 210 is relatively located in the induced current suppression area of the microwave ablation needle 200, so the first section 231 is configured to be connected to the electrode 210, and the first section 231 and the second section
  • the segments 232 all extend into the first branch pipe 221.
  • the length of the connection between the electrode 210 and the first segment 231 is less than or equal to the length of the second segment 232.
  • the maximum distance between the shielding layer stripping opening at the end of the second segment 232 away from the first segment 231 and the end of the adjacent second branch pipe 222 is 1/4 the length of the microwave wavelength .
  • the wavelength of the microwave is
  • C is the speed of light
  • f is the frequency of microwaves
  • ⁇ is the composite dielectric constant composed of the material of the first branch 221, the cooling liquid, the insulating medium of the coaxial cable 230, and the cooling tube 240.
  • FIG. 3 shows the structure of a microwave ablation needle using cylindrical electrodes in the present disclosure.
  • the present disclosure also provides a microwave ablation needle 300.
  • the microwave ablation needle 300 includes a handle 310 and the above-mentioned microwave ablation needle 200.
  • the handle 310 is connected to the proximal end of the second branch pipe 222, and the handle 310 includes a first chamber 311 and a second chamber 312 that are independent of each other.
  • the first chamber 311 and the second chamber 312 are independently arranged and
  • the first chamber 311 and the second chamber 312 are connected to the first cooling channel 241 and the second cooling channel 242 respectively and are not connected to each other, and jointly form a cooling liquid circulation circuit.
  • the microwave ablation needle 300 adopts the above-mentioned microwave ablation needle 200, which can consume the induced current through the sleeve structure formed by the microwave ablation needle 200 and the filler filled in the sleeve, and thus can be used in the working process. In, it plays the role of restraining the induced current, and eliminates the influence of the induced current on the ablation morphology, and obtains a more ideal spherical ablation morphology.
  • this embodiment also provides a medical device, which includes a microwave generating device (not shown in the figure), a liquid supply device (not shown in the figure), and the above-mentioned microwave ablation needle 300;
  • the microwave generating device is connected with the coaxial cable 230 to provide microwave energy to the coaxial cable 230;
  • the liquid supply device is connected with the first chamber 311 and the second chamber 312 at the same time, so as to connect to the first cooling channel 241 and the second chamber 312.
  • the second cooling channel 242, the first chamber 311, and the second chamber 312 supplement the circulating cooling liquid, and promote the circulating flow of the cooling liquid, so that the cooling liquid can take away the heat generated when the sleeve structure suppresses the induced current.
  • this medical device because it uses the above-mentioned microwave ablation needle 300, it can play a role through the sleeve structure formed by the microwave ablation needle 200 and the filler filled in the sleeve.
  • the effect of consuming the induced current and the medical device can suppress the induced current during the microwave ablation treatment, and eliminate the influence of the induced current on the ablation morphology, so that the heating area is concentrated in the radiation area to obtain a more ideal
  • the spherical ablation shape meets clinical needs.
  • FIG. 4 and FIG. 5 show the structure of a microwave ablation needle using needle electrodes in the disclosure. It should be noted that, in the present disclosure, when the electrode 210 is configured, the electrode 210 may also be a needle-shaped electrode 212.
  • the electrode 210 is a needle electrode 212
  • its positional relationship and connection with the outer tube 220, the cooling tube 240, and the coaxial cable 230 are the same as the cylindrical electrode 211, the outer tube 220, the cooling tube 240 and the same in the above content.
  • the arrangement of the shaft cable 230 is the same, and the microwave ablation needle 200 using the needle electrode 212 also uses the cooling tube 240 to be sheathed outside the coaxial cable 230, and then the outer tube 220 is sheathed outside the cooling tube 240 to form
  • the microwave ablation needle 200 using the needle electrode 212 can also effectively suppress the induced current and eliminate the influence of the induced current on the ablation morphology, so that the heating area is concentrated in the radiation area, and a relatively ideal spherical ablation morphology is obtained to meet clinical needs.
  • the needle electrode 212 when the needle electrode 212 is used, the difference from the above-mentioned microwave ablation needle 200 using the cylindrical electrode 211 is that the distal end of the first branch 221 of the microwave ablation needle 200 is opened, and the needle electrode 212 is installed in the opening and closes the opening.
  • the needle electrode 212 includes a spike head 2121 and a connector 2122 connected to the proximal end surface of the spike head 2121.
  • the proximal end surface of the spiked head 2121 is spaced from the distal end of the cooling tube 240, so that the first cooling channel 241 and the second cooling channel 242 are connected through the gap between them; the part of the connector 2122 is located in the cooling tube Inside the distal end of 240 and configured to be electrically connected to the distal end of the coaxial cable 230.
  • the spike head 2121 When the spike head 2121 is connected to the distal end of the first branch pipe 221, it can close the opening at the distal end of the first branch pipe 221, so that the installation space 250 is closed, so that the first cooling channel 241 and the second cooling channel 242 can pass through
  • the installation spaces 250 are connected to each other, and the cooling liquid in the first cooling flow passage 241 can flow into the second cooling flow passage 242 or the cooling liquid in the second cooling flow passage 242 can flow into the first cooling flow passage 241.
  • the cooling liquid can flow in the microwave ablation needle 200.
  • the microwave ablation needle 200 has the function of suppressing the induced current, the flow of the cooling liquid will take away and suppress the induced current. The heat.
  • the portion of the outer peripheral wall of the spike head 2121 is close to the spike head
  • the inner direction of 2121 is recessed to form a second annular groove 2123, the distal end of the second annular groove 2123 is spaced from the distal end of the spike head 2121, and the proximal end of the second annular groove 2123 extends to the proximal end of the spike head 2121
  • the distal end of the first branch pipe 221 is inserted and fitted with the second annular groove 2123.
  • the wall thickness at the position where the spike head 2121 has the second annular groove 2123 is small, so that the first branch pipe 221 can be sleeved on the spike head.
  • the outer wall of the first branch 221 does not protrude from the outer wall of the spike head 2121.
  • the first branch 221 and the spike The spike 2121 does not form a step at the connection position.
  • proximal end of the spike head 2121 and the distal end of the first branch pipe 221 may be fixedly connected by welding or the like, or the proximal end of the spike head 2121 and the distal end of the first branch pipe 221 can be detachably connected.
  • the proximal end of the spike head 2121 and the distal end of the first branch tube 221 may be connected by bonding.
  • the second annular groove 2123 at the proximal end of the spike head 2121 can play the role of accommodating glue. This arrangement can improve the stability of the adhesion, and at the same time, after the adhesion is completed, the second annular groove is passed through the second annular groove. 2123 and the glue contained in the second annular groove 2123 can also function as a seal.
  • the microwave ablation needle 200 further includes a sensing element 260, the sensing element 260 is sleeved outside the first branch 221, and the sensing element 260 is wrapped in the radiation area of the coaxial cable 230 The part of the radiation current on the coaxial cable 230 is induced to the sensing element 260, which indirectly increases the radiation ability of the electrode 210 to act on the lesion tissue, thereby improving the ablation effect.
  • the sensing element 260 can be sprayed on the outside of the first branch pipe 221 by plasma spraying, which is sprayed around the circumference of the first branch pipe 221 to form a ring structure; or, the sensing element 260 is set as a pipe section and is directly sleeved on the first branch pipe. In charge of 221 outside.
  • the length of the sensing element 260 in the extending direction of the first branch 221 is L1, the joint position of the first branch 221 and the second branch 222 to the connection position of the first section 231 and the second section 232 The distance between is L2, and L1 is less than L2.
  • the proximal end of the electrode 210 is flush with the connection position of the first section 231 and the second section 232, that is, the first branch 221
  • the distance from the joint position with the second branch pipe 222 to the proximal end of the electrode 210 is L2.
  • the sensing element 260 may be made of one of copper, iron, aluminum, gold, silver, palladium, platinum, tin, nickel, zinc, and alloys thereof.
  • the sensing element 260 in the present disclosure is made of 304 stainless steel .
  • the outer circumferential wall of the first branch pipe 221 is provided with a third annular groove 2212, the third annular groove 2212 is recessed inward along the radial direction of the first branch pipe 221, the sensing element 260 is located in the third annular groove 2212, the sensing element 260
  • the connection with the first branch pipe 221 is firm and reliable, and it is not easy to fall off; and the wall thickness of the first branch pipe 221 at the third annular groove 2212 is small, which is convenient for the sensing element 260 to sense the radiation current on the coaxial cable 230.
  • an induction element 260 may be provided on the outer peripheral wall of the first branch pipe 221 to enhance the radiation ability and enhance the ablation effect.
  • FIG. 6 shows the structure of a microwave ablation needle using a needle electrode in the present disclosure.
  • the present disclosure also provides a microwave ablation needle 300.
  • the microwave ablation needle 300 includes a handle 310 and the above-mentioned microwave ablation needle 200.
  • the handle 310 is connected to the proximal end of the second branch pipe 222.
  • the handle 310 includes a first chamber 311 and a second chamber 312.
  • the first chamber 311 and the second chamber 312 are connected to the first cooling channel 241 and the first cooling channel 241 and the second chamber 312, respectively.
  • the two cooling channels 242 are connected and form a cooling liquid circulation loop together.
  • the microwave ablation needle 300 adopts the microwave ablation needle 200 using the needle electrode 212, which can consume the induced current through the sleeve structure formed by the microwave ablation needle 200 and the filler filled in the sleeve. Furthermore, in the working process, it can suppress the induced current and eliminate the influence of the induced current on the ablation morphology, so as to obtain a more ideal spherical ablation morphology.
  • the present disclosure also provides a medical device.
  • the medical equipment includes a microwave generating device, a liquid supply device, and the above-mentioned microwave ablation needle 300; wherein the microwave generating device and the coaxial cable 230 Connected to provide microwave energy to the coaxial cable 230; the liquid supply device communicates with the first chamber 311 and the second chamber 312 at the same time to connect to the first cooling channel 241, the second cooling channel 242, and the first chamber
  • the circulating cooling liquid is supplemented in the 311 and the second chamber 312, and the cooling liquid is promoted to circulate, so that the cooling liquid can take away the heat generated by inhibiting the induced current.
  • the medical device can play a role through the sleeve structure formed by the microwave ablation needle 200 and the filler filled in the sleeve.
  • the effect of consuming induced current can be suppressed during the microwave ablation treatment, and eliminate the influence of the induced current on the ablation morphology, so that the heating area is concentrated in the radiation area, and an ideal spherical ablation morphology is obtained to meet clinical needs. .
  • the present disclosure provides a microwave ablation needle and a microwave ablation needle, which can effectively suppress the induced current and obtain an ideal spherical ablation form.

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Abstract

本公开涉及微波消融治疗设备领域，具体而言，涉及一种微波消融针头及微波消融针。一种微波消融针头，其包括外管、冷却管、同轴电缆以及电极。外管包括沿外管的远端到近端的方向上依次设置的第一分管以及第二分管，第一分管远离第二分管的一端形成外管的远端；其中，第一分管的材质为陶瓷材料或高分子材料。冷却管设置在外管内，冷却管与外管间隔设置且在冷却管与外管之间形成第一冷却流道；其中，冷却管的材质为高分子材料；冷却管的远端位于第一分管的远端内部，以在冷却管的远端区域形成安装空间。该微波消融针头能有效抑制感应电流，消除感应电流对消融形态的影响。

Description

一种微波消融针头及微波消融针
相关申请的交叉引用
本公开要求于2020年01月07日提交中国专利局的申请号为202010013350.7、名称为“一种微波消融针头及微波消融针”的中国专利申请的优先权。
技术领域
本公开涉及微波消融治疗设备领域，具体而言，涉及一种微波消融针头及微波消融针。
背景技术
近年来，微波消融治疗已成为治疗肝癌、肾癌和甲状腺等软组织的重要治疗手段之一。微波消融是利用天线辐射微波，微波使组织中的离子和极性水分子旋转振动，相互摩擦而产生热效应，使治疗区域快速达到很高的温度，组织凝固，脱水而坏死，从而达到治疗目的。
现有的微波消融针的天线辐射过程中，同轴电缆的外导体形成感应电流，导致消融区域不可控制，形成椭球形。
发明内容
本公开的目的包括，例如，提供了一种微波消融针头及微波消融针，其能够有效抑制感应电流，消除感应电流对消融形态的影响，使得加热区域集中在辐射区域，获得比较理想的球形消融形态，满足临床需求。本公开的实施例可以这样实现：
第一方面，实施例提供一种微波消融针头，其包括外管、冷却管、同轴电缆以及电极；
外管包括沿外管的远端到近端的方向上依次设置的第一分管以及第二分管，第一分管远离第二分管的一端形成外管的远端；其中，第一分管的材质为陶瓷材料或高分子材料；
冷却管设置在外管内，冷却管与外管间隔设置且在冷却管与外管之间形成第一冷却流道；其中，冷却管的材质为高分子材料；冷却管的远端位于第一分管的远端内部，以在冷却管的远端区域形成安装空间；
同轴电缆设置在冷却管内，同轴电缆与冷却管间隔设置且在冷却管与同轴电缆之间形成第二冷却流道；同轴电缆的远端位于冷却管的远端内；
至少部分电极位于安装空间内，并与同轴电缆的远端电连接。
可选的，第一分管与第二分管插接配合。
可选的，第一分管的外周壁设有第一环形槽，第二分管的远端插接于第一环形槽内。
可选的，第一分管与第二分管焊接。
可选的，第一分管与第二分管可拆卸地连接。
可选的，电极为柱型电极，第一分管的远端封闭并具备尖刺，以配置成封闭安装空间；
部分柱型电极位于冷却管的远端内，并与同轴电缆电连接；其余部分的柱型电极凸出于冷却管的远端并位于第一分管内，且柱型电极的远端与第一分管的远端端面具有间距。
可选的，电极为针型电极，第一分管的远端开口；
针型电极包括尖刺头以及连接于尖刺头近端端面上的连接头；
尖刺头与第一分管的远端连接，并封闭第一分管远端的开口，尖刺头与冷却管的远端间隔设置；连接头的部分位于冷却管内且配置成与同轴电缆的远端 电连接。
可选的，尖刺头的外周壁设有在靠近尖刺头内部的方向上凹陷的第二环形槽，第一分管的远端与第二环形槽插接配合。
可选的，尖刺头与第一分管焊接连接。
可选的，尖刺头与第一分管可拆卸地连接。
可选的，同轴电缆包括沿其远端到近端的方向上依次连接的第一分段及第二分段，第一分段远离第二分段的一端形成同轴电缆的远端，第一分段配置成与电极连接；
第一分段为同轴电缆裸露内导体分段，第二分段为同轴电缆裸露绝缘层的分段。
可选的，第二分段远离第一分段的一端的屏蔽层剥离口与第二分管的端部间的最大间隔为微波波长的1/4长度。
可选的，微波消融针头还包括感应件，感应件设于第一分管的外周壁上，配置成感应同轴电缆的部分辐射电流，以增强辐射能力。
可选的，感应件环绕第一分管的外周壁设置。
可选的，感应件喷涂于第一分管的外周壁上。
可选的，感应件为管段，感应件套设于第一分管的外周壁上。
可选的，第一分管的外周壁设有第三环形槽，感应件位于第三环形槽内且不凸出第三环形槽的槽口。
可选的，感应件在第一分管的延伸方向上的长度为L1，第一分管与第二分管的连接位置处到电极的近端之间的距离为L2，L1小于L2。
可选的，感应件采用铜、铁、铝、金、银、钯、铂、锡、镍、锌及其合金中一种制成。
第二方面，实施例提供一种微波消融针，其包括手柄以及上述的微波消融针头；
手柄与第二分管的近端连接，手柄包括第一腔室及第二腔室，第一腔室及第二腔室分别与第一冷却流道及第二冷却流道导通并共同形成冷却液循环回路。
与现有技术相比，本公开实施例的有益效果包括，例如：
该微波消融针头包括外管、冷却管、同轴电缆及电极。其通过外管、同轴电缆及冷却管间的相互套设，能够形成套筒结构以及供冷却液流动的冷却流道。
通过这样的套筒结构能够消耗电极通电后所产生的感应电流，同时通过冷却液在冷却流道中的流动能够将套筒结构消耗感应电流所产生的热量带走。由此，该微波消融针头能够有效抑制感应电流，消除感应电流对消融形态的影响，使得加热区域集中在辐射区域，获得比较理想的球形消融形态，满足临床需求。
附图说明
为了更清楚地说明本公开实施例的技术方案，下面将对实施例中所需要使用的附图作简单地介绍，应当理解，以下附图仅示出了本公开的某些实施例，因此不应被看作是对范围的限定，对于本领域普通技术人员来讲，在不付出创造性劳动的前提下，还可以根据这些附图获得其他相关的附图。
图1为本公开采用柱型电极的微波消融针头的结构示意图；
图2为本公开采用柱型电极的微波消融针头的局部结构示意图；
图3为本公开采用柱型电极的微波消融针的结构示意图；
图4为本公开采用针型电极的微波消融针头的结构示意图；
图5为本公开采用针型电极的微波消融针头的局部结构示意图；
图6为本公开采用针型电极的微波消融针的结构示意图；
图7为本公开采用柱型电极的微波消融针头上设有感应件的局部结构示意图；
图8为本公开采用针型电极的微波消融针头上设有感应件的局部结构示意图。
图标：200-微波消融针头；210-电极；211-柱型电极；212-针型电极；2121-尖刺头；2122-连接头；2123-第二环形槽；220-外管；221-第一分管；2211-第一环形槽；2212-第三环形槽；222-第二分管；230-同轴电缆；231-第一分段；232-第二分段；240-冷却管；241-第一冷却流道；242-第二冷却流道；250-安装空间；260-感应件；300-微波消融针；310-手柄；311-第一腔室；312-第二腔室；。
具体实施方式
为使本公开实施例的目的、技术方案和优点更加清楚，下面将结合本公开实施例中的附图，对本公开实施例中的技术方案进行清楚、完整地描述，显然，所描述的实施例是本公开一部分实施例，而不是全部的实施例。通常在此处附图中描述和示出的本公开实施例的组件可以以各种不同的配置来布置和设计。
因此，以下对在附图中提供的本公开的实施例的详细描述并非旨在限制要求保护的本公开的范围，而是仅仅表示本公开的选定实施例。基于本公开中的实施例，本领域普通技术人员在没有作出创造性劳动前提下所获得的所有其他实施例，都属于本公开保护的范围。
应注意到：相似的标号和字母在下面的附图中表示类似项，因此，一旦某一项在一个附图中被定义，则在随后的附图中不需要对其进行进一步定义和解释。
在本公开的描述中，需要说明的是，若出现术语“上”、“下”、“内”、“外”等指示的方位或位置关系为基于附图所示的方位或位置关系，或者是该发明产品使用时惯常摆放的方位或位置关系，仅是为了便于描述本公开和简化描述，而不是指示或暗示所指的装置或元件必须具有特定的方位、以特定的方位构造和操作，因此不能理解为对本公开的限制。
此外，若出现术语“第一”、“第二”等仅用于区分描述，而不能理解为指示或暗示相对重要性。
需要说明的是，在不冲突的情况下，本公开的实施例中的特征可以相互结合。
请参考图1和图2，图1及图2示出了本公开实施例中采用柱型电极的微波消融针头的结构。本公开提供了一种微波消融针头200，其包括外管220、冷却管240、同轴电缆230以及电极210。
其中，外管220包括沿外管220的远端到近端的方向上依次设置的第一分管221以及第二分管222，第一分管221远离第二分管222的一端形成外管220的远端，第二分管222远离第一分管221的一端形成外管220的近端；其中，第一分管221的材质为陶瓷材料或高分子材料。
可选的，冷却管240设置在外管220内，冷却管240与外管220间隔设置且在冷却管240与外管220之间形成第一冷却流道241；可选的，冷却管240的外周壁与外管的内周壁具有间距，从而使第一冷却流道241呈围绕冷却管240的环形结构；其中，冷却管240的材质为高分子材料；冷却管240的远端位于第一分管221的内部，且冷却管240的远端与第一分管221的远端内壁具有间距，以在靠近冷却管240的远端区域形成安装空间250。
可选的，同轴电缆230设置在冷却管240内，同轴电缆230与冷却管240 间隔设置且在冷却管240与同轴电缆230之间形成第二冷却流道242；可选的，同轴电缆230的外周壁与冷却管240的内周壁具有间距，从而使第二冷却流道242呈围绕同轴电缆230的环形结构；同轴电缆230的远端位于冷却管240的内，且同轴电缆230的远端与第一分管221的远端内壁具有间距。
本公开中，可选的，至少部分电极210位于安装空间250内，并与同轴电缆230的远端电连接。
该微波消融针头200的工作原理是：
该微波消融针头200包括外管220、冷却管240、同轴电缆230以及电极210，其通过将冷却管240套设在同轴电缆230外，再将外管220套设在冷却管240外，从而形成套筒结构以及供冷却液流动的流道。其中，套筒结构的作用是消耗感应电流，以抑制感应电流；在套筒结构抑制感应电流时，其产生的热量能够通过在第一冷却流道241和第二冷却流道242中流动的冷却液的带走。
由此，当电极210与同轴电缆230电连接，且处于电导通的状态时，其产生的感应电流便会受到套筒结构的抑制作用，同时抑制感应电流产生的热量会随着冷却液的流动散失，由此，该微波消融针头200在工作的过程中，其能够起到抑制感应电流的作用，并消除感应电流对消融形态的影响，获得比较理想的球形消融形态。
可选的，在配置第一分管221、第二分管222及冷却管240时，第二分管222可以采用金属材料或连续的金属丝编织物填充的高分子材料制成，与此同时，由于第一分管221采用陶瓷材料或高分子材料制成，冷却管240采用高分子材料制成，故该微波消融针头200在与其他结构配合装配在微波消融针300上时，其能够保证微波消融针300的使用强度以及耐用性。其外，需要说明的 是，该微波消融针头200在安装至微波消融针300上后，在使用的过程中，由于微波消融针300需要穿刺进入人体，故在设置第一分管221及第二分管222时，需要采用符合医用生物相容性要求的材料制作。
例如，在配置第二分管222时，第二分管222可以采用304不锈钢、316不锈钢、钴铬合金、镍钛合金或钛合金等金属材料，或连续的金属丝编织物填充的高分子管，如带304不锈钢编织层增强PI(PolyimideFilm聚酰亚胺薄膜)管等制成；
在配置第一分管221时，第一分管221可以采用氧化铝陶瓷或者氧化锆陶瓷等陶瓷材料，或高分子材料制成；
在配置冷却管240时，冷却管240可以采用PEEK(poly ether ether ketone聚醚醚酮)、PI(PolyimideFilm聚酰亚胺薄膜)或者PTFE(Poly tetra fluoroethylene)聚四氟乙烯等高分子材料管材。
可选的，由上述内容可知，该微波消融针头200的作用是抑制感应电流，而在使用的过程中，为提高微波能量抑制效果，需要使电极210与同轴电缆230的连接区域相对位于该微波消融针头200的感应电流抑制区域内，由此，在安装冷却管240时，冷却管240的远端位于第一分管221的远端内部，以在冷却管240的远端区域形成安装空间250；而在安装电极210时，电极210需要与同轴电缆230电连接。故需要将同轴电缆230配置在冷却管240内，并且同轴电缆230的远端位于冷却管240的远端内，由此，在将电极210安装至安装空间250内后，电极210能够与同轴电缆230的远端电连接，同时电极210与同轴电缆230电连接的部分能够相对位于冷却管240与外管220共同限定的安装空间250内，从而能够保证该微波消融针头200的电极210发出的感应电流位于感应电流抑制区域内，以保证该微波消融针头200对感应电流的抑制作 用。
请参阅图2，可选的，在本公开中，在安装电极210时，电极210可以为柱型电极211，第一分管221的远端封闭并具备尖刺，以配置成封闭安装空间250。
当电极210为柱型电极211时，柱型电极211在安装至安装空间250之后，部分电极210位于冷却管240内，其余部分从冷却管240的远端伸出并位于第一分管221内，此时柱型电极211对第一分管221不具备封堵作用，此时为使得安装空间250能够封闭，且能够刺入人体，故在配置第一分管221时，可以将第一分管221的远端设置为封闭端，同时第一分管221的远端具备从第一分管221向远离第二分管222的方向延伸的尖刺，尖刺配置成刺入人体。由此，通过这样的设置方式，能够使得安装空间250封闭，以使得第一冷却流道241与第二冷却流道242在安装空间250处相互导通，从而使得第一冷却流道241中的冷却液能够向第二冷却流道242中流动，或第二冷却流道242中的冷却液能够向第一冷却流道241中流动。并在微波消融针头200使用的过程中，使得冷却液能够在微波消融针头200中流动，当微波消融针头200起到抑制感应电流的作用时，通过冷却液的流动，带走抑制感应电流所产生的热量。
需要说明的是，当电极210为柱型电极211时，柱型电极211可以采用铜、铁、铝、金、银、钯、铂、锡、镍、锌及其合金制成，本公开中，柱型电极211设置为铜。
具体的，在配置柱型电极211时，由于安装空间250被第一分管221所封闭，故柱型电极211位于安装空间250内，并且位于冷却管240远端内部分的柱型电极211与同轴电缆230电连接；其余部分的柱型电极211位于第一分管221的远端内，且未与第一分管221的远端内端面接触，以使得柱型电极211 的远端与第一分管221的远端间隔设置。
在本公开中，在连接第一分管221及第二分管222时，第一分管221的近端设有第一环形槽2211，第一环形槽2211位于第一分管221的外周壁上，第一环形槽2211的远端与第一分管221的远端具有间距，第一环形槽2211的近端延伸至第一分管221的近端端面上，换句话说，在第一分管221的外周壁上设有沿其径向向内的第一环形槽2211，第二分管222的远端与第一环形槽2211卡接配合。也即，第二分管222的远端套接在第一分管221的近端外，且第二分管222的部分与第一环形槽2211卡接配合。
需要说明的是，通过设置第一环形槽2211，能够减小第一分管221在第一环形槽2211处的壁厚，从而在第二分管222与第一环形槽2211卡接后，使第二分管222的外壁不会向外凸出第一分管221的外壁，二者在连接接缝处不会形成台阶结构，便于操作。例如，第一分管221和第二分管222的外径可以设置为相等，从而使第一分管221的外壁和第二分管222的外壁位于同一环形面内。
可选的，第一分管221与第二分管222可以采用焊接等方式固定连接，或第一分管221与第二分管222可拆卸地连接。
可选的，第一分管221与第二分管222可以采用粘接的方式连接，此外，由于第一分管221近端设有第一环形槽2211，第一环形槽2211能够起到容纳粘胶的作用，从而能够提高粘接的稳定性，同时在粘接完成后，通过第一环形槽2211及容纳在第一环形槽2211内的粘胶还能够起到密封的作用。
在本公开中，同轴电缆230包括沿其远端到近端的方向上依次设置的第一分段231及第二分段232，第一分段231远离第二分段232的一端形成同轴电缆230的远端，第二分段232远离第一分段231的一端形成同轴电缆230的近 端；第一分段231为同轴电缆230裸露内导体分段，第二分段232为同轴电缆230裸露绝缘层的分段；
同样的为使得与电极210连接的同轴电缆230相对位于该微波消融针头200的感应电流抑制区域内，故第一分段231配置成与电极210连接，并且第一分段231及第二分段232均伸入第一分管221内。并且，电极210与第一分段231连接的长度小于或等于第二分段232的长度。在设置第二分段232时，第二分段232远离第一分段231的一端的屏蔽层剥离口与相邻的第二分管222的端部间的最大间隔为微波波长的1/4长度。其中，微波的波长为
Figure PCTCN2020083723-appb-000001
其中C为光速，f为微波的频率，ε为第一分管221的材料、冷却液、同轴电缆230绝缘介质和冷却管240组成的复合介电常数。
请参照图3，图3示出了本公开中采用柱型电极的微波消融针的结构。基于上述的微波消融针头200，本公开还提供一种微波消融针300，该微波消融针300包括手柄310以及上述的微波消融针头200。
其中，手柄310与第二分管222的近端连接，手柄310包括相互独立的第一腔室311及第二腔室312，换句话说，第一腔室311和第二腔室312独立设置且互不导通，第一腔室311及第二腔室312分别与第一冷却流道241及第二冷却流道242导通并共同形成冷却液循环回路。
该微波消融针300通过采用上述的微波消融针头200，其能够通过微波消融针头200所形成的套筒结构以及填充在套筒中的填充物起到消耗感应电流的作用，进而能够在工作的过程中，起到抑制感应电流的作用，并消除感应电流对消融形态的影响，获得比较理想的球形消融形态。
基于上述微波消融针300，本实施例还提供一种医疗设备，医疗设备包括 微波发生装置(图未示)、供液装置(图未示)以及上述的微波消融针300；
其中，微波发生装置与同轴电缆230连接，以向同轴电缆230提供微波能量；供液装置同时与第一腔室311及第二腔室312连通，以向第一冷却流道241、第二冷却流道242、第一腔室311及第二腔室312中补充循环的冷却液，并促使冷却液循环流动，以使得冷却液能够带走套筒结构抑制感应电流时产生的热量。
综上，该医疗设备在进行微波消融治疗的过程中，由于其采用了上述的微波消融针300，其能够通过微波消融针头200所形成的套筒结构以及填充在套筒中的填充物起到消耗感应电流的作用，进而该医疗设备在进行微波消融治疗的过程中，能够起到抑制感应电流的作用，并消除感应电流对消融形态的影响，使得加热区域集中在辐射区域，获得比较理想的球形消融形态，满足临床需求。
请参照图4及图5，图4和图5为公开中采用针型电极的微波消融针头的结构。需要说明的是，在本公开中，在配置电极210时，电极210还可以为针型电极212。
当电极210为针型电极212时，其与外管220、冷却管240以及同轴电缆230的位置关系和连接方式均与上述内容中的柱型电极211与外管220、冷却管240以及同轴电缆230的设置方式相同，且采用了针型电极212的微波消融针头200同样采用将冷却管240套设在同轴电缆230外，再将外管220套设在冷却管240外，从而形成套筒结构以及供冷却液流动的冷却流道，并通过这样的套筒结构消耗电极210通电后所产生的感应电流，同时通过冷却液在冷却流道中的流动能够将套筒结构消耗感应电流所产生的热量带走。
由此，采用了针型电极212的微波消融针头200同样能够有效抑制感应电流，消除感应电流对消融形态的影响，使得加热区域集中在辐射区域，获得比 较理想的球形消融形态，满足临床需求。
需要说明的是，当采用针型电极212时，与上述的采用柱型电极211的微波消融针头200的不同之处在于，该微波消融针头200的第一分管221的远端开口，针型电极212安装于开口，并封闭开口。同时，针型电极212包括尖刺头2121以及连接于尖刺头2121近端端面上的连接头2122。尖刺头2121的近端端面与冷却管240的远端间隔设置，从而使第一冷却流道241与第二冷却流道242通过二者之间的间隙连通；连接头2122的部分位于冷却管240的远端内且配置成与同轴电缆230的远端电连接。
当尖刺头2121与第一分管221的远端连接时，其能够封闭第一分管221远端的开口，使得安装空间250封闭，从而使得第一冷却流道241与第二冷却流道242通过安装空间250相互导通，第一冷却流道241中的冷却液能够向第二冷却流道242中流动，或第二冷却流道242中的冷却液能够向第一冷却流道241中流动。且在微波消融针头200使用的过程中，使得冷却液能够在微波消融针头200中流动，当微波消融针头200起到抑制感应电流的作用时，通过冷却液的流动，带走抑制感应电流所产生的热量。
其外，在连接针型电极212与第一分管221时，为便于针型电极212与第一分管221的定位及配合，可选的，尖刺头2121的外周壁的部分在靠近尖刺头2121内部的方向上凹陷以形成第二环形槽2123，第二环形槽2123的远端与尖刺头2121的远端具有间距，第二环形槽2123的近端延伸至尖刺头2121的近端端面上，第一分管221的远端与第二环形槽2123插接配合。
应当理解，通过在尖刺头2121的外周壁设置第二环形槽2123，尖刺头2121具有第二环形槽2123的位置处的壁厚小，从而能够使第一分管221套设在尖刺头2121外后，也即第一分管221插接在第二环形槽2123内后，使第一分管 221的外壁不凸出尖刺头2121的外壁，例如，本公开中，第一分管221和尖刺头2121在连接位置处没有形成台阶。
可选的，尖刺头2121的近端与第一分管221的远端可以采用焊接等方式固定连接，或尖刺头2121的近端与第一分管221的远端可拆卸地连接。
可选的，尖刺头2121的近端与第一分管221的远端可以采用粘接的方式连接。并且，在尖刺头2121的近端的第二环形槽2123能够起到容纳粘胶的作用，这样的设置方式，能够提高粘接的稳定性，同时在粘接完成后，通过第二环形槽2123及容纳在第二环形槽2123内的粘胶还能够起到密封的作用。
请参阅图7和图8，本公开中，可选的，微波消融针头200还包括感应件260，感应件260套设在第一分管221外，感应件260包裹在同轴电缆230的辐射区域，同轴电缆230上部分的辐射电流感应到感应件260上，间接提高电极210的辐射能力以作用到病灶组织中，提高消融效果。
可选的，感应件260可以采用等离子喷涂的方式喷涂在第一分管221外，其围绕第一分管221的四周喷涂以形成环形结构；或者，感应件260设为管段，直接套设在第一分管221外。需要说明的是，感应件260在第一分管221的延伸方向上的长度为L1,第一分管221与第二分管222的接缝位置至第一分段231与第二分段232的连接位置之间的距离为L2，L1小于L2。需要说明的是，在电极210套设在第一分段231外时，电极210的近端与第一分段231和第二分段232的连接位置处齐平，也即，第一分管221与第二分管222的接缝位置到电极210的近端的距离为L2。
可选的，感应件260可以采用铜、铁、铝、金、银、钯、铂、锡、镍、锌及其合金中一种制成，例如，本公开中感应件260采用304不锈钢制成。
可选的，第一分管221的外周壁设有第三环形槽2212，第三环形槽2212 沿第一分管221的径向向内凹陷，感应件260位于第三环形槽2212内，感应件260与第一分管221的连接牢固可靠，不易脱落；且第一分管221在第三环形槽2212处的壁厚小，便于感应件260感应同轴电缆230上的辐射电流。
应当理解，电极210为柱型电极211或者针型电极212时，均可以在第一分管221的外周壁设置感应件260，以增强辐射能力，增强消融效果。
请参照图6，图6示出了本公开中采用针型电极的微波消融针的结构。基于上述的采用针型电极212的微波消融针头200，本公开还提供一种微波消融针300，该微波消融针300包括手柄310以及上述的微波消融针头200。其中，手柄310与第二分管222的近端连接，手柄310包括第一腔室311及第二腔室312，第一腔室311及第二腔室312分别与第一冷却流道241及第二冷却流道242导通并共同形成冷却液循环回路。
该微波消融针300通过采用针型电极212的微波消融针头200，其能够通过微波消融针头200所形成的套筒结构以及填充在套筒中的填充物起到消耗感应电流的作用。进而能够在工作的过程中，起到抑制感应电流作用，并消除感应电流对消融形态的影响，获得比较理想的球形消融形态。
基于上述采用针型电极212的微波消融针300，本公开还提供一种医疗设备，医疗设备包括微波发生装置、供液装置以及上述的微波消融针300；其中，微波发生装置与同轴电缆230连接，以向同轴电缆230提供微波能量；供液装置同时与第一腔室311及第二腔室312连通，以向第一冷却流道241、第二冷却流道242、第一腔室311及第二腔室312中补充循环的冷却液，并促使冷却液循环流动，以使得冷却液能够带走抑制感应电流所产生的热量。
综上，该医疗设备在进行微波消融治疗的过程中，由于其采用了上述的微波消融针300，其能够通过微波消融针头200所形成的套筒结构以及填充在套 筒中的填充物起到消耗感应电流的作用。进而该医疗设备在进行微波消融治疗的过程中，能够起到抑制感应电流作用，并消除感应电流对消融形态的影响，使得加热区域集中在辐射区域，获得比较理想的球形消融形态，满足临床需求。
以上所述，仅为本公开的具体实施方式，但本公开的保护范围并不局限于此，任何熟悉本技术领域的技术人员在本公开揭露的技术范围内，可轻易想到的变化或替换，都应涵盖在本公开的保护范围之内。因此，本公开的保护范围应以所述权利要求的保护范围为准。
工业实用性：
综上所述，本公开提供了一种微波消融针头及微波消融针，其能够有效抑制感应电流，获得比较理想的球形消融形态。

Claims (20)

  1. 一种微波消融针头，其特征在于，包括：
    外管，所述外管包括沿所述外管的远端到近端的方向上依次设置的第一分管以及第二分管，所述第一分管远离所述第二分管的一端形成所述外管的远端；其中，所述第一分管的材质为陶瓷材料或高分子材料；
    冷却管，所述冷却管设置在所述外管内，所述冷却管与所述外管间隔设置且在所述冷却管与所述外管之间形成第一冷却流道；其中，所述冷却管的材质为高分子材料；所述冷却管的远端位于所述第一分管的远端内部，以在所述冷却管的远端区域形成安装空间；
    同轴电缆，所述同轴电缆设置在所述冷却管内，所述同轴电缆与所述冷却管间隔设置且在所述冷却管与所述同轴电缆之间形成第二冷却流道；所述同轴电缆的远端位于所述冷却管的远端内；以及
    电极，至少部分所述电极位于所述安装空间内，并与所述同轴电缆的远端电连接。
  2. 根据权利要求1所述的微波消融针头，其特征在于：
    所述第一分管与所述第二分管插接配合。
  3. 根据权利要求2所述的微波消融针头，其特征在于：
    所述第一分管的外周壁设有第一环形槽，所述第二分管的远端插接于所述第一环形槽内。
  4. 根据权利要求1-3中任一项所述的微波消融针头，其特征在于：
    所述第一分管与所述第二分管焊接。
  5. 根据权利要求1-3中任一项所述的微波消融针头，其特征在于：
    所述第一分管与所述第二分管可拆卸地连接。
  6. 根据权利要求1-5中任一项所述的微波消融针头，其特征在于：
    所述电极为柱型电极，所述第一分管的远端封闭并具备尖刺，以配置成封闭所述安装空间；
    部分所述柱型电极位于所述冷却管的远端内，并与所述同轴电缆电连接；其余部分的所述柱型电极凸出于所述冷却管的远端并位于所述第一分管内，且所述柱型电极的远端与所述第一分管的远端端面具有间距。
  7. 根据权利要求1-5中任一项所述的微波消融针头，其特征在于：
    所述电极为针型电极，所述第一分管的远端开口；
    所述针型电极包括尖刺头以及连接于所述尖刺头近端端面上的连接头；
    所述尖刺头与所述第一分管的远端连接，并封闭所述第一分管远端的开口，所述尖刺头与所述冷却管的远端间隔设置；所述连接头的部分位于所述冷却管内且配置成与所述同轴电缆的远端电连接。
  8. 根据权利要求7所述的微波消融针头，其特征在于：
    所述尖刺头的外周壁设有在靠近所述尖刺头内部的方向上凹陷的第二环形槽，所述第一分管的远端与所述第二环形槽插接配合。
  9. 根据权利要求7或者8所述的微波消融针头，其特征在于：
    所述尖刺头与所述第一分管焊接连接。
  10. 根据权利要求7或者8所述的微波消融针头，其特征在于：
    所述尖刺头与所述第一分管可拆卸地连接。
  11. 根据权利要求1-10中任意一项所述的微波消融针头，其特征在于：
    所述同轴电缆包括沿其远端到近端的方向上依次连接的第一分段及第二分段，所述第一分段远离所述第二分段的一端形成所述同轴电缆的远端，所述第一分段配置成与所述电极连接；
    所述第一分段为所述同轴电缆裸露内导体分段，所述第二分段为所述同轴电缆裸露绝缘层的分段。
  12. 根据权利要求11所述的微波消融针头，其特征在于：
    所述第二分段远离所述第一分段的一端的屏蔽层剥离口与所述第二分管的端部间的最大间隔为微波波长的1/4长度。
  13. 根据权利要求1-12中任一项所述的微波消融针头，其特征在于：
    所述微波消融针头还包括感应件，所述感应件设于所述第一分管的外周壁上，配置成感应所述同轴电缆的部分辐射电流，以增强辐射能力。
  14. 根据权利要求13所述的微波消融针头，其特征在于：
    所述感应件环绕所述第一分管的外周壁设置。
  15. 根据权利要求13或者14所述的微波消融针头，其特征在于：
    所述感应件喷涂于所述第一分管的外周壁上。
  16. 根据权利要求13或者14所述的微波消融针头，其特征在于：
    所述感应件为管段，所述感应件套设于所述第一分管的外周壁上。
  17. 根据权利要求13-16中任一项所述的微波消融针头，其特征在于：
    所述第一分管的外周壁设有第三环形槽，所述感应件位于所述第三环形槽内且不凸出所述第三环形槽的槽口。
  18. 根据权利要求13-17中任一项所述的微波消融针头，其特征在于：
    所述感应件在所述第一分管的延伸方向上的长度为L1，所述第一分管与所述第二分管的连接位置处到所述电极的近端之间的距离为L2，所述L1小于所述L2。
  19. 根据权利要求13-18中任一项所述的微波消融针头，其特征在于：
    所述感应件采用铜、铁、铝、金、银、钯、铂、锡、镍、锌及其合金中一 种制成。
  20. 一种微波消融针，其特征在于：
    所述微波消融针包括手柄以及如权利要求1-19中任意一项所述的微波消融针头；
    所述手柄与所述第二分管的近端连接，所述手柄包括第一腔室及第二腔室，所述第一腔室及所述第二腔室分别与所述第一冷却流道及所述第二冷却流道导通并共同形成冷却液循环回路。
PCT/CN2020/083723 2020-01-07 2020-04-08 一种微波消融针头及微波消融针 WO2021139017A1 (zh)

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