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WO2024217998A1 - Instrument hf doté d'une partie mâchoire - Google Patents

Instrument hf doté d'une partie mâchoire Download PDF

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Publication number
WO2024217998A1
WO2024217998A1 PCT/EP2024/059961 EP2024059961W WO2024217998A1 WO 2024217998 A1 WO2024217998 A1 WO 2024217998A1 EP 2024059961 W EP2024059961 W EP 2024059961W WO 2024217998 A1 WO2024217998 A1 WO 2024217998A1
Authority
WO
WIPO (PCT)
Prior art keywords
instrument
metal electrode
contact surface
support structure
porous support
Prior art date
Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
Pending
Application number
PCT/EP2024/059961
Other languages
German (de)
English (en)
Inventor
Tom Schweitzer
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
Aesculap AG
Original Assignee
Aesculap AG
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Application filed by Aesculap AG filed Critical Aesculap AG
Priority to CN202480025827.XA priority Critical patent/CN120957681A/zh
Publication of WO2024217998A1 publication Critical patent/WO2024217998A1/fr
Anticipated expiration legal-status Critical
Pending legal-status Critical Current

Links

Classifications

    • 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
    • A61B18/1442—Probes having pivoting end effectors, e.g. forceps
    • A61B18/1445—Probes having pivoting end effectors, e.g. forceps at the distal end of a shaft, e.g. forceps or scissors at the end of a rigid rod
    • 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
    • A61B2018/00065—Material properties porous
    • 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
    • A61B2018/00315—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body for treatment of particular body parts
    • A61B2018/00345—Vascular system
    • 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
    • A61B2018/00607—Coagulation and cutting with the same instrument
    • 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
    • A61B2018/0063—Sealing
    • 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
    • A61B18/1442—Probes having pivoting end effectors, e.g. forceps
    • A61B2018/1452—Probes having pivoting end effectors, e.g. forceps including means for cutting
    • A61B2018/1455—Probes having pivoting end effectors, e.g. forceps including means for cutting having a moving blade for cutting tissue grasped by the jaws

Definitions

  • HF instrument with a jaw part
  • a medical high-frequency surgery instrument in particular a bipolar vessel sealing instrument, with at least one metal electrode in a jaw part.
  • HF surgery high-frequency surgery
  • a high-frequency alternating current is passed through the human body or a body part in order to specifically cauterize (coagulation) or cut (electrotomy) tissue through the heating caused thereby.
  • the tissue damaged in this way is later reabsorbed by the surrounding healthy tissue.
  • a significant advantage over conventional cutting techniques with a scalpel is that bleeding can be stopped simultaneously with the cut by closing the affected vessels, in the sense of coagulation.
  • the monopolar HF technique is most frequently used in HF surgery.
  • One pole of the HF voltage source is connected to the patient via a counter electrode with the largest possible surface area, for example through contacts on the operating table on which the patient lies, through contact bracelets or contact foot bands or through adhesive electrodes.
  • This counter electrode is often called the neutral electrode.
  • the other pole is connected to the surgical instrument and this forms the so-called active electrode.
  • the current flows via the path of least resistance from the active electrode to the neutral electrode. In the immediate vicinity of the active electrode, the Current density is highest, this is where the thermal effect is strongest. The current density decreases with the square of the distance.
  • the neutral electrode should have as large an area as possible and be well connected to the body so that the current density in the body is kept low and no burns occur. The skin on the neutral electrode is not noticeably heated by the large area.
  • the jaw parts consist of or have the thin metal electrode, which acts as a contact surface to the tissue, a plastic spacer, which provides electrical and thermal insulation, and a carrier component, which is intended and designed to ensure force introduction and contains a closing mechanism.
  • the carrier component gives the jaw part the necessary stability and rigidity.
  • a jaw part of this type designed in a sandwich construction, is complex and costly to manufacture.
  • the various components that have to be connected to one another lead to an accumulation of manufacturing tolerances, which reduces the accuracy of fit and thus the quality of the jaw part or the HF instrument.
  • One approach to remedying these disadvantages is to design/form the metal electrode or a branch of the jaw part as a solid component, i.e.
  • the metal electrode is made entirely from a (non-porous) solid material according to this prior art.
  • Such an overall solid metal electrode is particularly rigid against thermal and/or mechanical deformation, but has a high thermal mass, which, particularly in the case of larger jaw parts, means that a large part of the energy supplied to the metal electrode by an HF generator does not flow into the tissue sealing, but into the heating of the solid metal electrode.
  • the object of the present disclosure is to remedy or at least reduce the disadvantages of the prior art.
  • the object of the present disclosure is to provide an HF instrument with a jaw part that is easy to manufacture, has low tolerances and a low thermal mass. This object is achieved by an HF instrument according to the independent claim 1 and by the HF instrument according to a subordinate claim.
  • an HF instrument in particular a bipolar vessel sealing instrument, with at least one metal electrode, which includes a solid, i.e. non-porous or closed contact surface for contacting tissue.
  • the metal electrode also includes a support section facing away from the contact surface, which has or is a porous or open support structure.
  • One aspect of the present disclosure therefore consists in designing/providing (preferably exclusively) the electrode side that is to be brought into (physical) contact with a patient's tissue as a closed, non-porous contact surface, completely or in sections, for example by (thin) closed metal plate, a closed metal layer, a closed metal coating, etc.
  • the remaining metal electrode is to be designed/provided at least partially or completely as a support structure or with an open (porous or grid-like, etc.) support structure, which is intended and designed to support the contact surface (at least in some areas) and to give it stability against load-related (mechanical and/or thermal) deformation.
  • Solid is to be understood as meaning that the contact surface is uninterrupted and smooth.
  • the HF instrument which is designed, for example, as a preferably bipolar HF instrument in a scissors or forceps design or a laparoscopic design.
  • the HF instrument contains at least one, preferably two, metal electrode(s), which are formed in a jaw part of the HF instrument, each in a branch.
  • the preferably two branches are movable relative to one another via a joint or hinge.
  • the metal electrode includes at least one flat section which forms the contact surface and faces an intermediate space/interior of the jaw part, i.e. forms a front side of the metal electrode.
  • the contact surface is provided and designed to contact the tissue.
  • the metal electrode also includes the support section which is designed/oriented away from the intermediate space of the jaw part, i.e. forms a rear side of the metal electrode.
  • the support section includes or is the porous support structure.
  • the HF instrument has in particular a distal instrument to which the metal electrode is attached.
  • the distal instrument has a jaw part with two branches, at least one of which can be pivoted towards the other branch, wherein the metal electrode is attached to at least one of the branches on a side facing the other branch.
  • the HF instrument also preferably has a proximal handle and a shaft which connects the handle to the distal instrument.
  • the porous support structure is preferably made of metal. Porosity means that the support structure has a cavity portion, preferably evenly distributed over its volume. In other words, the support structure is formed with a large number of three-dimensionally arranged cavities. Such a porous support structure can stiffen the metal electrode without increasing the thermally relevant mass of the metal electrode to a significant extent.
  • the porous support structure can be an additively manufactured structure. Additive manufacturing involves manufacturing processes that are formed by applying material, preferably in layer-building processes, and thus differs from abrasive manufacturing processes in which material is removed.
  • the porous support structure can be a 3D-printed structure, which can be formed, for example, by means of selective laser melting, selective electron beam melting, laser cladding, wire arc/plasma arc energy deposition or wire feed electron deposition.
  • the metal electrode can be formed monolithically with the support section. Monolithic is understood to mean consisting of a uniform, non-separable unit.
  • the metal electrode can be formed as a single piece. This means that at least the contact surface and the support section can be formed monolithically/as a single piece with the porous support structure.
  • the monolithic design of the metal electrode can achieve a high component rigidity.
  • the metal electrode can be manufactured be simplified because a joining process between the support section and the contact surface can be dispensed with.
  • the reduction in the number of components can prevent an accumulation of manufacturing tolerances, which increases manufacturing accuracy and thus the quality of the jaw part of the HF instrument.
  • the metal electrode can include a blade guide channel that is open towards the contact surface and extends in a longitudinal direction of the metal electrode for guiding a blade.
  • the blade guide channel can be arranged centrally or at least essentially centrally.
  • the blade guide channel can be designed as a groove-shaped geometry in the contact surface.
  • the blade guide channel can extend on the back of the contact surface in a kind of step shape, oriented normal to the contact surface, and the blade guide channel can delimit at least one, in particular two, volumes/spaces positioned next to the blade guide channel with the contact surface.
  • the porous support structure can be formed in this space/in these spaces.
  • the porous support structure can be connected/formed to the contact surface and the blade guide channel, preferably in one piece.
  • the blade guide channel can have a closed geometry.
  • the support section can contain solid (in the sense of closed/non-porous) stiffening ribs.
  • the support section can contain the solid stiffening ribs in addition to the porous support structure, which preferably segment the support section and the porous support structure is arranged/formed in the segments thus formed.
  • the porous support structure can be formed more easily and is less susceptible to defects, in particular to manufacturing errors such as local layer connection errors/defects in the additively manufactured porous support structure.
  • the contact surface of the metal electrode can be tongue-shaped, wherein the reinforcing ribs are aligned normal to the blade guide channel and can preferably be arranged/formed so as to be distributed substantially evenly or in sections so as to be evenly distributed over a longitudinal extension of the metal electrode.
  • the contact surface can be a long, narrow surface with a round tip on one of the narrow edges of the contact surface.
  • the tip can be formed on a distal section of the contact surface.
  • the blade guide channel can extend centrally, in an extension of the tip, in the metal electrode.
  • the reinforcing ribs can be arranged in a majority number transversely to the longitudinal extension of the metal electrode. A distance between the reinforcing ribs can be substantially constant. In a region of the round tip, a single one of the reinforcing ribs can be aligned substantially in the extension direction of the blade guide channel.
  • the stiffening ribs between the blade guide channel and the contact surface can be designed as essentially triangular angle pieces.
  • an edge of the stiffening ribs can be arranged at approximately a 45° angle to the contact surface.
  • the support section can be surrounded by a plastic casing.
  • the branch can be formed on the side facing away from the gap of the component, i.e. towards the outside, with the plastic sheath which covers the metal electrode. The plastic sheath acts as an electrical and/or thermal insulator and protects the porous support structure from point-based force attacks, since the plastic sheath distributes the attacking force into the support structure.
  • the plastic sheath can be formed with a predetermined elasticity, which additionally protects the support structure and thus the branch and the jaw part.
  • the plastic sheath can be formed from an overmolding material which, at least in sections, engages in the porous support structure.
  • the plastic sheath can engage/penetrate the pores of the porous support structure and a claw/positive fit between the plastic sheath and the porous support structure can be achieved.
  • the plastic sheath can penetrate the porous support structure completely or superficially.
  • the plastic material can fill at least a portion of the porous volume of the support structure.
  • the plastic jacket By designing the plastic jacket in this way, an accumulation of mass during the overmolding and the resulting distortion of the component can be avoided/prevented. Furthermore, by clawing the plastic jacket into the porous support structure, a good, practically inseparable connection can be made between the plastic jacket and the metal electrode. In addition, an additional joining step between the metal electrode and the plastic jacket can be dispensed with during the overmolding. Furthermore, any (near-surface) defects in the porous support structure can be compensated for by the plastic of the plastic jacket.
  • the porous support structure can be designed as a lattice/grid. In other words, the porous support structure can be constructed from three-dimensionally periodically arranged lattice and cell structures.
  • Common lattice cells are body-centered cubic cells, face-centered cubic cells, simple cubic cells, or space frameworks.
  • Other possible lattice types/lattice lattice structures are the part graph lattice, the volume graph lattice, the 3D conformal structure lattice, the unit graph lattice, the quad graph lattice, or the Gnd graph lattice.
  • Such lattice structures can be produced in different porosities using additive manufacturing processes.
  • a lattice can absorb forces in different spatial directions and thus contribute to stiffening the jaw part or the metal electrode without significantly increasing the mass.
  • the type of lattice can be adapted/selected depending on the type and size of the jaw part.
  • the porous support structure can be designed as a sponge structure or a bionic structure.
  • a bionic structure is understood to be a structure that is based on geometries from nature or biology.
  • the porous support structure can be designed as a honeycomb structure or as a load-oriented geometry, for example.
  • the porosity of the porous support structure can be designed differently/load-oriented at different locations on the metal electrode. It is also conceivable to change the dimensions of rod structures or to design them differently depending on the load situation/location on the metal electrode.
  • a load-appropriate lattice structure can be formed from the rod structures.
  • the contact surface of the metal electrode or the metal electrode can have high-load and low-load areas and the high-load areas can be reinforced compared to the low-load areas.
  • hinge elements of the jaw part can be formed as a single piece with the metal electrode.
  • force transmission elements of the HF instrument can be formed as a single piece with the metal electrode.
  • energy transmission elements of the HF instrument can be formed as a single piece with the metal electrode.
  • a comparatively thin, closed (non-porous/non-lattice-like) contact surface for example made of a metal layer or a metal plate, which has a property that is unstable (easily deformable) against thermal and/or mechanical stress and to support (stiffen) this by means of an open (porous/lattice-like) support structure (on the back/side facing away from the patient's tissue) which has a property that is stable (difficult to deform) against thermal and/or mechanical stress, or in other words, is stiff/stiffer than the contact surface (or the layer/plate forming the contact surface).
  • the object is achieved by the HF instrument, in particular a bipolar vessel sealing instrument, with at least one metal electrode, which includes a contact surface for contacting tissue, wherein the metal electrode is produced by a generative manufacturing process/an additive manufacturing process/3D printing.
  • Fig. 1 shows an HF instrument according to the disclosure
  • Fig. 2 shows a jaw part of the HF instrument according to the disclosure with two branches
  • Fig. 3 shows a metal electrode of the branch of the jaw part without a porous support structure
  • Fig. 4 shows the metal electrode of the branch of the jaw part with the porous support structure
  • Fig. 5 shows a cross section of only the branch of the jaw part.
  • Fig. 1 shows an HF instrument according to the disclosure in the form of a bipolar vessel sealing instrument 1.
  • the vessel sealing instrument 1 includes an actuating or gripping section 3 at a proximal end.
  • the actuating or gripping section 3 is intended and designed to be gripped by an operator/surgeon and forms a substantially pistol-shaped gripping section.
  • a cable 5 is also formed on the actuating or handle section 3, which connects the vessel sealing instrument 1 to a high-frequency generator (not shown).
  • the actuating or handle section 3 also contains a button 7, via which a power supply can be requested from the high-frequency generator by actuating it.
  • a shaft 9 is connected distally to the actuating or handle section 3.
  • the shaft 9 has a substantially rod- or tube-shaped geometry.
  • the jaw part 11 is formed at a distal end of the shaft 9 and thus at a distal end of the vessel sealing instrument 1.
  • the jaw part 11 is intended and designed to function as a cutting and sealing section with which the operator can make cuts in tissue parts and on vessels and then close or seal cut areas and/or vessels.
  • Fig. 2 shows an enlarged view of the jaw part 11 in an open state.
  • the jaw part 11 includes a first branch 13 and a second branch 15, which are connected to one another in an articulated manner by a hinge 17. Both the first branch 13 and the second branch 15 contain an outward-facing plastic casing 19.
  • the gap 21 of the jaw part 11 is formed between the two branches 13, 15 when the jaw part 11 is in the open state.
  • Both the first branch 13 and the second branch 15 also contain a metal electrode 23.
  • the metal electrode 23 contains a contact surface 25.
  • the contact surface 25 of the first branch 13 and the contact surface 25 of the second branch 15 essentially delimit the gap 21 as a flat surface.
  • the contact surfaces 25 are provided and designed to contact the tissue.
  • the first branch 13 and the second branch can be moved relative to one another about the joint 17 using a handle (see 27 in Fig. 1).
  • a blade guide channel 27 open towards the gap 21 is formed in the contact surface 25 of the first branch 13 and in the contact surface 25 of the second branch 15.
  • the blade guide channel 27 is provided and designed to guide a blade (not shown) in the axial direction, starting from the shaft 9 or starting from a blade element formed on the shaft 9.
  • the axial direction is to be understood as a longitudinal extension direction of the shaft 9.
  • Fig.3 shows the metal electrode 23 from a rear side or from a side facing away from the contact surface 25. In the embodiment shown in Fig.3, a porous support structure is not shown for better illustration.
  • the metal electrode 23 has a substantially tongue-shaped geometry with a tip 29, which is formed at a distal end of the metal electrode 23.
  • a force transmission element 31 is formed at a proximal end of the metal electrode 23.
  • the blade guide channel 27 extends between the tip 29 and the force transmission element 31.
  • the blade guide channel 27 has a groove-shaped geometry that is open towards the contact surface 25 and extends in a width direction of the metal electrode 23 centrally away from the contact surface 25 to the rear side.
  • the metal electrode 23 also includes stiffening ribs 33 that protrude perpendicularly from the blade guide channel 27.
  • the stiffening ribs 33 are designed as essentially triangular angle pieces between the blade guide channel 27 and the contact surface 25.
  • the stiffening ribs 33 are arranged evenly distributed over the longitudinal extension of the metal electrode 23.
  • a stiffening rib 33 is also formed on the tip 29, which extends essentially in the longitudinal extension direction of the blade guide channel 27.
  • the metal electrode 23 also includes a hinge pin 35, which extends in the width direction of the metal electrode 23.
  • the hinge pin 35 has an essentially round cross-sectional area and is part of the hinge 17.
  • the metal electrode 23 is formed as a single piece.
  • the contact surface 25, the blade guide channel 27, the force transmission element 31, the stiffening ribs 33 and the hinge pin 35 are formed as a single piece.
  • Fig.4 shows the metal electrode 23 from Fig.3 with a porous support structure in the form of a grid 37.
  • the grid 37 is formed between the contact surface 25, the blade guide channel 27 and the stiffening ribs 33.
  • the grid 37 is formed as a single piece with the metal electrode 23.
  • the grid 37 is a three-dimensional grid structure.
  • the grid 37 forms with the stiffening ribs 33 has a support section 39.
  • This support section 39 essentially forms the back of the metal electrode 23 and increases the rigidity of the metal electrode 23 or the associated branch 13, 15.
  • the grid 37 is essentially formed in spaces or spatial sections delimited by the stiffening ribs 33, the blade guide channel 27 and the contact surface 25.
  • the grid 37 can extend, starting from the contact surface 25, on the back of the metal electrode 23 essentially as far as the blade guide channel 27.
  • the support section 39 can be formed only from the grid 37.
  • the metal electrode 23 can be formed without the stiffening ribs 33.
  • the grid 37 is an additively manufactured support structure. In other words, the grid 37 is formed from metal using generative manufacturing processes/additive manufacturing processes/3D printing. Preferably, the entire metal electrode 23 is manufactured additively.
  • the grid 37 is or will be molded additively onto a base body of the metal electrode 23.
  • the grid 37 is shown here as a cuboid-shaped grid.
  • Fig. 5 shows a cross section through one of the branches 13, 15 of the jaw part 11.
  • the contact surface 25 forms a T-shape with the U-shaped blade guide channel 27.
  • the grid 37 is formed between the blade guide channel 27 and the contact surface 25.
  • the plastic jacket 19 is formed as an overmolding material. This means that the plastic jacket 19 engages in pores of the grid 37 and is thus positively connected to the metal electrode 23.
  • the metal electrode 23 forms an integral branch 13, 15 with the plastic sheath 19.
  • the plastic sheath 19 can only penetrate superficially into the grid 37 or penetrate the grid 37 almost completely.
  • List of reference symbols 1 Vessel sealing instrument 3. Actuating or handle section 5 Cable 7 Button 9 Shaft 11 Jaw 13 First branch 15 Second branch 17 Hinge 19 Plastic sheath 21 Intermediate space 23 Metal electrode 25 Contact surface 27 Blade guide channel 29 Tip 31 Force transmission element 33 Stiffening ribs 35 Hinge pin 37 Grid 39 Support section

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

Abstract

La présente invention concerne un instrument HF (1), en particulier un instrument bipolaire pour sceller des vaisseaux, comprenant au moins une électrode métallique (23) qui comprend une surface de contact (25) pour entrer en contact avec un tissu, l'électrode métallique (23) comprenant une partie support (39) qui est tournée à l'opposé de la surface de contact (25) et qui a ou est une structure de support poreuse (37). L'invention concerne également l'électrode métallique (23) qui est produite à l'aide d'un procédé de fabrication génératif.
PCT/EP2024/059961 2023-04-19 2024-04-12 Instrument hf doté d'une partie mâchoire Pending WO2024217998A1 (fr)

Priority Applications (1)

Application Number Priority Date Filing Date Title
CN202480025827.XA CN120957681A (zh) 2023-04-19 2024-04-12 具有钳口部分的hf器械

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
DE102023109870.5 2023-04-19
DE102023109870.5A DE102023109870A1 (de) 2023-04-19 2023-04-19 HF-Instrument mit einem Maulteil

Publications (1)

Publication Number Publication Date
WO2024217998A1 true WO2024217998A1 (fr) 2024-10-24

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ID=90735365

Family Applications (1)

Application Number Title Priority Date Filing Date
PCT/EP2024/059961 Pending WO2024217998A1 (fr) 2023-04-19 2024-04-12 Instrument hf doté d'une partie mâchoire

Country Status (3)

Country Link
CN (1) CN120957681A (fr)
DE (1) DE102023109870A1 (fr)
WO (1) WO2024217998A1 (fr)

Citations (3)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US6770072B1 (en) * 2001-10-22 2004-08-03 Surgrx, Inc. Electrosurgical jaw structure for controlled energy delivery
US20210369333A1 (en) * 2020-05-29 2021-12-02 Gyrus Acmi, Inc. D/B/A Olympus Surgical Technologies America Monolithic ceramic surgical device and method
US20220160419A1 (en) * 2019-01-28 2022-05-26 Apyx Medical Corporation Electrosurgical devices and systems having one or more porous electrodes

Family Cites Families (6)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US5609151A (en) * 1994-09-08 1997-03-11 Medtronic, Inc. Method for R-F ablation
DE69829921T2 (de) * 1997-08-04 2006-05-04 Ethicon, Inc. Vorrichtung zur Behandlung von Körpergewebe
US6558385B1 (en) * 2000-09-22 2003-05-06 Tissuelink Medical, Inc. Fluid-assisted medical device
AU2001239987A1 (en) * 2000-03-06 2001-09-17 Tissuelink Medical, Inc. Fluid delivery system and controller for electrosurgical devices
WO2009064808A1 (fr) * 2007-11-13 2009-05-22 Boston Scientific Scimed, Inc. Appareil, système et procédé de coagulation et ablation de tissus
US20210196358A1 (en) * 2019-12-30 2021-07-01 Ethicon Llc Electrosurgical instrument with electrodes biasing support

Patent Citations (3)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US6770072B1 (en) * 2001-10-22 2004-08-03 Surgrx, Inc. Electrosurgical jaw structure for controlled energy delivery
US20220160419A1 (en) * 2019-01-28 2022-05-26 Apyx Medical Corporation Electrosurgical devices and systems having one or more porous electrodes
US20210369333A1 (en) * 2020-05-29 2021-12-02 Gyrus Acmi, Inc. D/B/A Olympus Surgical Technologies America Monolithic ceramic surgical device and method

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Publication number Publication date
DE102023109870A1 (de) 2024-10-24
CN120957681A (zh) 2025-11-14

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