electrosurgical instrument

专利摘要:
ELECTROSURGICAL INSTRUMENT. An electrosurgical instrument for applying electromagnetic RF energy and / or EM frequency microwave energy to biological tissue, where the tip of the instrument has a protective casing with a smoothly contoured convex bottom surface facing outward from a body flat, and where the flat body has a tapered distal end, and where a lower part of the flat body extends beyond the protective casing at the tapered distal end. Also disclosed in this document is an interface joint for integrating a single set of cables (i) a fluid supply, (ii) a needle movement mechanism and (iii) a power supply (for example, a coaxial cable) , and a torque transfer device to allow controlled rotation of the cable assembly within the instrument channel of an endoscope. The interface link and the torque transfer device can be integrated as a single component.
公开号:BR112016015267B1
申请号:R112016015267-0
申请日:2014-12-31
公开日:2021-02-17
发明作者:Julian Mark Ebbutt；Christopher Paul Hancock；Steven Morris；Malcolm White；Brian Saunders
申请人:Creo Medical Limited；
IPC主号:

专利说明:

[0001] [0001] The invention relates to an electrosurgical apparatus and device for the distribution of radio frequency energy and / or microwave frequencies in biological tissues. In particular, the invention relates to an electrosurgical instrument capable of providing radio frequency (RF) energy to cut tissue and / or microwave frequency energy for hemostasis (i.e., the promotion of blood clotting). The invention may be particularly suitable in gastrointestinal (GI) procedures associated with the lower and upper GI tract, for example, to remove polyps in the intestine, that is, for endoscopic mucosa resection or endoscopic submucosal dissection. The invention can also lend itself to another procedure, for example, in general surgery or laparoscopic surgery. The present invention can find use in procedures in the ear, nose and throat and liver resection. The device can also be used to address procedures associated with the pancreas, for example, to resect or remove tumors or abnormalities in close proximity to the portal vein or pancreatic duct. BACKGROUND OF THE INVENTION
[0002] [0002] Surgical resection is a means of removing sections of organs from within the human or animal body. Such organs can be highly vascular. When the tissue is cut (divided or sectioned), small blood vessels called arterioles will be damaged or ruptured. The initial bleeding is followed by a clotting cascade in which the blood is transformed into a clot in an attempt to contain the bleeding point. During an operation, it is desirable for a patient to lose the least amount of blood possible, so several devices have been developed in an attempt to provide a blood-free cut. For endoscopic procedures, bleeding is also undesirable, and needs to be treated promptly, as the blood flow can obscure the operator's vision, which can prolong the surgery and potentially make the procedure necessary. shut down and another method used instead, for example, open surgery.
[0003] [0003] Electrosurgical generators are prevalent in hospital operating rooms, often for use in open and laparoscopic procedures and increasingly for use in endoscopy suites. In endoscopic procedures, the electrosurgical accessory is typically inserted through a lumen into an endoscope. In comparison to the equivalent access channel for laparoscopic surgery, this lumen is comparatively narrow in relation to the orifice and longer in length.
[0004] [0004] Instead of a sharp blade, it is known to use radio frequency (RF) energy to cut biological tissue. The cutting method using RF energy operates using the principle that as an electrical current passes through a tissue matrix (aided by the ionic content of cells and intercellular electrolytes), the impedance to the flow of electrons through the tissue generates heat. In practice, an instrument is arranged to apply an RF voltage across the tissue matrix that is sufficient to generate heat inside the cells to vaporize the water content of the tissue. However, as a result of this increased desiccation, particularly adjacent to the instrument's RF emission region (which has the highest current density of current flowing through the tissue), direct physical contact between the tissue and the instrument may be lost . The applied voltage, then, manifests itself as a voltage drop across this small void, which causes ionization in the void that leads to a plasma. Plasma has a very high volumetric resistivity compared to tissue. The energy supplied to the instrument maintains the plasma, that is, it completes the electrical circuit between the instrument and the tissue. The volatile material that enters the plasma slowly enough can be vaporized and the perception is, therefore, of a tissue dissecting plasma.
[0005] [0005] Document No. GB 2 472 972 describes an electrosurgical instrument in the form of a spatula comprising a flat transmission line formed from a sheet of a first dielectric material that has a first and second conductive layers on surfaces opposite, the flat transmission line being connected to a coaxial cable which is arranged to distribute either microwave or RF energy to the flat transmission line, the coaxial cable comprising an inner conductor, an outer coaxial conductor with the interior conductor and a second dielectric material that separates it from the exterior and interior conductors, the interior and exterior conductors extending beyond the second dielectric in a connection interface to overlap the opposite surfaces of the transmission line and to electrically contact the first conductive layer and second conductive layer, respectively. The first conductive layer is separated from the end of the transmission line that abuts the coaxial cable to electrically isolate the outer conductor from the first conductive layer and also the span distance is involved with matching the impedance of the energy supplied from that of the microwave source with the impedance of biological tissue, and the width of the first and second conductive layers is also selected to help create an impedance match between the transmission line and coaxial cable.
[0006] [0006] The spatula configuration set out in document No. GB 2 472 972 provides the desirable insertion loss between the coaxial feed line and the radiant end section, while providing desirable return loss properties to the edges of the spatula when in contact with air and biological tissue respectively. In more detail, the insertion loss along the structure can be less than 0.2 dB at the frequency of interest and the return loss less than (more negative than) -1 dB, preferably less than -10 dB. These properties can also indicate a well-adapted junction between the coaxial cable and the transmission line spatula structure, through which microwave energy is efficiently released into the spatula. Likewise, when the edges of the spatula are exposed to air or biological tissue that is not of interest, the return loss can be substantially zero (that is, very little power radiated to free space or undesirable tissue), whereas when in contact with the desirable biological tissue the return loss may be less than (more negative than) -3 dB, preferably less than -10 dB (that is, most of the energy in the spatula will be transferred to the tissue).
[0007] [0007] The instrument discussed in document No. GB 2 472 972 is intended to radiate microwave energy from the edges of the flat transmission line to cause tissue ablation or localized coagulation.
[0008] [0008] Document No. GB 2 472 972 also describes that the spatula discussed above may have an RF cutting portion integrated into it. The RF cutting portion can be formed using the first and second conductive layers mentioned above as active and return electrodes for RF energy. This arrangement can take advantage of the fact that the active and return electrodes are in close proximity to each other, thus establishing a preferred return path to allow the local tissue cutting action to take place without the need for a remote return block. or a highly conductive liquid, that is, saline solution, between the two electrodes.
[0009] [0009] In this example, the RF cut-off portion may comprise an RF voltage source coupled to the flat transmission line, a frequency diplexer / duplexer unit (or signal adder) comprising a low-pass filter to prevent that high frequency microwave energy goes back to the lower frequency RF energy source and a high pass filter to prevent lower frequency RF energy from going back to the higher frequency microwave energy source . In one example, the frequency diplexer / duplexer can be used to allow microwave and RF energy sources to be combined in the generator and distributed along a single channel, for example, coaxial cable, the guide assembly of waves or a twisted pair, for the spatula structure. The RF cutting energy can be distributed by itself in the fabric or it can be mixed or added to the microwave energy and distributed simultaneously to establish a mixed mode of operation. SUMMARY OF THE INVENTION
[0010] [0010] The present invention further develops the spatula concept discussed in document No. GB 2 472 972 and the way in which it interacts with a generator that provides RF and / or microwave energy for treatment.
[0011] [0011] In a first aspect, the invention provides an even more optimized configuration for the distal end of an electrosurgical instrument for controlled resection of biological tissue.
[0012] [0012] In a second aspect, the invention provides an interface joint to integrate in a single set of cables all among (i) a fluid supply, (ii) a needle movement mechanism and (iii) an energy supply ( for example, a RF cable and / or microwave energy supply). The cable assembly can be sized to fit through the instrument channel of a conventional endoscope.
[0013] [0013] In a third aspect, the invention provides a torque transfer device to allow the controlled rotation of the cable assembly within the instrument channel of the endoscope. The interface link and the torque transfer device can be integrated as a single component.
[0014] [0014] According to the first aspect of the invention, an electrosurgical instrument is provided for the application in biological tissue of radio frequency electromagnetic energy (EM) and / or microwave frequency EM energy, the instrument being is characterized by the fact that it comprises: an instrument tip comprising a planar body made of a first dielectric material that separates a first conductive element on the respective first surface from a second conductive element on a second respective surface, the second surface which it turns in the opposite direction to the first surface; a coaxial power cable comprising an inner conductor, an outer coaxial conductor with the inner conductor and a second dielectric material which separates the inner and outer conductors, the coaxial power cord being for transmitting an RF signal and / or an microwave; and a protective structure comprising a third piece of dielectric material assembled to cover the lower part of the planar body, in which the inner conductor is electrically connected to the first conductive element and the outer conductor is electrically connected to the second conductive element to allow the tip instrument receives the RF signal and / or the microwave signal, in which the protective structure has a contoured lower convex surface smoothly facing away from the planar body, where the planar body has a tapered distal end and where the the lower part of the planar body extends beyond the protective structure at the tapered distal end. This combination of characteristics represents an ideal configuration that balances the precision of treatment at the distal tip (which is accentuated due to the extension of the flat body over the protection structure) with the ease of safe handling of the instrument (due to the protective structure itself).
[0015] [0015] The portion of the lower side of the flat body that extends beyond the protective structure at the tapered distal end may be called the extension zone. The extension zone can be uniform around the perimeter of the tapered distal end. Alternatively, the extension zone itself can taper in width towards the distal tip of the flat body. The taper can be between a minimum value at the distal end and a maximum value at the proximal end of the distal tapered end. There may be zero extension at the distal tip, that is, the protective structure can be contiguous (that is, level with the flat body at that point). The extension zone can be dimensioned to provide a beneficial impact on the energy fields emitted by the device, but without adversely impacting the function of the protection structure.
[0016] [0016] The amplitude of the extension zone can be related, for example, in proportion to the geometry of the distal tip. The flat body can have any dimensions suitable for use in a specific process. For example, for endoscopic procedures, the instrument may have an overall outside diameter of 2.3 mm or less, preferably 1.2 mm or less. The width of the flat body can therefore be 2 mm or less. However, other procedures may be less restrictive, whereby the width of the flat body can be up to 9 mm. The width of the extension zone, that is, the distance by which the tapered distal end extends beyond the protection structure in a direction normal to the edge of the protection structure can be 0.2w or less, preferably 0, 1w or less, where w is the maximum width of the flat body (that is, the maximum dimension of the flat body in the direction of the diameter of the lumen or catheter through which it is inserted in use). Thus, due to a flat body having a width of 2 mm, the extension zone can have a maximum width of 0.2 mm.
[0017] [0017] In use, the first and second conductive elements may be arranged to provide a local return path to RF energy, that is, a low impedance route for RF energy to be transported between the first and second elements conductors. The first and second conducting elements can be layers of metallization formed on opposite surfaces of the first dielectric material. The first and second conducting elements can be arranged to establish a local electric field in a contact region in which the tip of the instrument makes contact with biological tissue. The local electric field can be extremely high, which can cause a microplasm (that is, a hot thermal plasma) to be formed in the distal lateral portions of the flat body, for example, in which contact with biological tissue is made. The microplasm may be desirable in terms of achieving an efficient cut.
[0018] [0018] However, for the microwave signal, the tip of the instrument can be modeled as a transmission line of parallel plates with the flat body representing dielectric material that separates two conductive plates. The microwave EM frequency energy radiation pattern, in this case, depends on the overall shape of the flat body and the microwave feed structure. In this particular case, the gap at the proximal end between the coaxial power line (central conductor) and the upper conductive layer plays an important role in ensuring that the microwave energy from the source is matched in terms of impedance to the load impedance. presented by the fabric. The total length of the flat transmission line arrangement is also important in terms of matching the impedance (or energy distribution) of (or from) the coaxial transmission line with (or in) the biological tissue, that is, the The structure can form a quarter-wave impedance transformer or a half-wavelength resonator. Using known simulation tools, this can be modeled to control from which edges the microwave frequency EM energy is radiated. For example, the tip of the instrument can be configured to inhibit microwave EM radiation from a distal end of the flat body.
[0019] [0019] The tapered distal end may have any suitable profile, for example, obtained through computer modeling of the device in specific use configurations. The tapered distal end may be curved or linear or a combination of the two. For example, the tapered distal end may comprise a linear tapering end at a curved distal tip, for example, a single radius curved distal tip. The tapered distal end may extend around the distal third of the flat body. In one embodiment, the curved distal end may have a curvature formed from a plurality of contiguous rounded sections, each rounded section having a radius of curvature less than its proximal neighbor. There can be three more sections of different radii. The plurality of contiguous rounded sections can be arranged so as to provide the curved distal end with an almost parabolic shape.
[0020] [0020] As mentioned above, the width of the flat body can be dictated by the intended use of the instrument. In endoscopic procedures, the width can be 2 mm or less, while for other less restrictive processes the width can be up to 3 mm, for example, any of 8 mm or less, 7 mm or less, 6 mm or less , 5 mm or less, 4 mm or less or 3 mm or less.
[0021] [0021] The length of the flat body (including the tapered distal end) can be related, for example, in proportion to its width, in order to distribute the RF and / or microwave frequency energy more efficiently. The length of the flat body can therefore be about 5w, for example, between 5w and 6w, preferably 5.3w where w is the maximum width of the flat body.
[0022] [0022] In one embodiment, the flat body has a maximum width of 2 mm and a maximum length of 10.6 mm. In this embodiment, the tapered distal edge may comprise a plurality of contiguous rounded sections consisting of a first rounded section having a length of 1.6 mm and a radius of curvature of 12.4 mm, a second rounded section having a length of 1 , 0 mm and a radius of curvature of 10.2 mm, a third rounded section having a length of 0.7 mm and a radius of curvature of 3.2 mm, a fourth rounded section having a length of 0.2 mm and a radius of curvature of 0.85 mm and a fifth round section having a length of 0.1 mm and a radius of curvature of 0.35 mm.
[0023] [0023] The first and second conducting elements can each comprise a metallization layer, the metallization layers being formed on opposite surfaces of the first dielectric material. The metallization layers can be adjusted back (for example, by 0.2 mm) from the lateral edges of the first dielectric material in a proximal region of the flat body, to reduce the intensity of the field in the region. The proximal region can comprise the proximal region of the flat body to the curved distal end. This can help to focus the energy distribution on the distal end. The inner conductor and the outer conductor can contact the first and second conducting elements in a coaxial manner, that is, the first and the second conducting elements can be shaped to be symmetrical about an axis that runs along the flat body of the coaxial power cable.
[0024] [0024] The bottom surface of the protective enclosure may slightly taper in its perimeter to correspond to the lower side of the flat body. The thickness of the protective casing may also decrease towards the distal end of the instrument tip. Thus, the outer portion of the protective housing may have a convex profile. The bottom surface may have a recessed channel that extends longitudinally formed thereon. The tapered edge profile and the recessed channel can cause the bottom surface of the protective enclosure to comprise a pair of protrusions. The shaped tapered flow shape of the structure can reduce the risk of the instrument penetrating the collateral tissue, assisting in its ability to slide. For example, this shape can reduce the risk of the instrument perforating the intestinal wall and cause perforation of the intestine, or it can protect the portal vein or pancreatic duct from being damaged. The particular dimensions of the hull (for example, length, width, thickness, etc.) can be adapted to suit the intended use and the intended area of the body to be operated.
[0025] [0025] The protective structure can be formed from a biocompatible non-conductive material, such as poly (ether-ether-ketone) (PEEK), ceramic (for example, alumina, zirconium dioxide or hardened dioxide alumina) zirconium (ΖΤΑ)) or biocompatible plastic that does not adhere to the intestinal wall (or other biological tissue) or similar. Alternatively, the hull can also be formed of a metallic material, for example, titanium, steel, or it can be a multilayered structure. It can be coupled (for example, glued) to any of the first and second conductive elements that are at the bottom of the first dielectric material. However, in one embodiment, the protective casing may be formed from the same material as the first dielectric material. The protective casing and the first dielectric material can be formed in one piece, as a unitary body. In this arrangement, one or more flat grooves can be formed (for example, cut) in the unitary body to allow a conductive material to be inserted to form the first and / or the second conductive material. The conductive material can be inserted by coating one or more internal surfaces of the compartment. Alternatively or additionally, the protective structure can be selectively metallized to form part of the first or second conductive elements.
[0026] [0026] The instrument may include a fluid supply conduit for distributing fluid (eg, saline) to the tip of the instrument. The fluid supply conduit may comprise a passage through the protective casing to distribute the fluid to the treatment site. The passageway may include an outlet located in the recessed channel of the protective enclosure. The coaxial power cable can form part of a multi-lumen conduit, the set for distributing RF and / or microwave frequency energy and fluid (liquid or gas) to the instrument. The fluid (protective structure) can be transported through a corresponding passage formed within the multi-lumen conduit assembly. The fluid supply conduit can also be used to deliver other materials to the treatment site, for example, a gas or a solid (for example, a powder). In one embodiment, fluid injection (saline or the like) is used to swell the biological tissue at the treatment site. This can be particularly useful where the instrument is used to treat the gut wall or esophageal wall, or to protect the portal vein or pancreatic duct when a tumor or other anomaly is located nearby, in order to protect these structures and create fluid cushioning. Swelling the tissue in this way can help reduce the risk of perforation of the intestine, damage to the esophageal wall or leakage of the pancreatic duct or damage to the portal vein, etc. This aspect of the invention can make it capable of treating other conditions in which the abnormality (tumor, growth, cysts, etc.) is close to a sensitive biological structure.
[0027] [0027] It is advantageous to be able to use the same instrument to distribute fluid while distributing microwave and / or RF energy, since deflation can occur (for example, due to fluid flow or loss of insufflation air) if a separate instrument is inserted in the region or during treatment. The ability to introduce fluid using the same treatment structure allows the level to be completed as soon as deflation occurs. In addition, the use of a single instrument to perform desiccation or dissection, as well as to introduce fluid, also reduces the time required to perform the general procedure, reduces the risk of causing damage to the patient and also reduces the risk of infection. More generally, fluid injection can be used to wash the treatment region, for example, to remove waste products or the tissue removed to provide better visibility during treatment. As mentioned above, this can be particularly useful in endoscopic procedures.
[0028] [0028] The lower surface of the protective structure may have a recessed channel that extends longitudinally formed therein and the fluid distribution mechanism may include an insulating needle guide tube mounted inside and extending proximally from the recessed channel and a retractable needle (e.g., hypodermic needle) slidably mounted on the needle guide tube. The needle may have an outer diameter of less than 0.6 mm, for example, 0.4 mm. The needle can be movable in the longitudinal direction between an extended position, in which it protrudes beyond the distal end of the instrument tip, and a retracted position, in which it is away from the distal end of the instrument tip, for example, below the flat body or is located close to the flat body.
[0029] [0029] Alternatively, the fluid supply conduit may comprise a tubular projection (for example, conical) formed integrally in the protective structure, for example, on a lower surface thereof. The projection tip can have an outlet for a fluid passage and therefore can act as a fixed needle-like tip for injecting fluid into the tissue. The tip of the cone can protrude slightly beyond the distal tip of the flat body.
[0030] [0030] According to the second aspect of the invention, an interface gasket is provided to interconnect an electrosurgical generator and an electrosurgical instrument (which can be an instrument according to the first aspect of the invention), in which the interface gasket comprises: a housing made of electrically insulating material, in which the housing has a first input to receive the radio frequency (RF) electromagnetic (EM) energy and / or the microwave frequency EM energy from the electrosurgical generator, a second input to receive the fluid and an outlet; a single cable assembly to connect the outlet to the electrosurgical instrument, the signal cable assembly comprising a flexible sleeve that defines a fluid flow path that is in fluid communication with the second inlet and that transmits a coaxial cable that is connected at the first entry.
[0031] [0031] The electrosurgical generator can be any device capable of distributing EM RF energy or EM microwave frequency energy for the treatment of biological tissues. For example, the generator can be used as described in document No. WO 2012/076844.
[0032] [0032] The electrosurgical instrument can be any device that in use is arranged to use EM RF energy or EM microwave frequency energy for the treatment of biological tissues. The electrosurgical instrument can use RF energy and / or microwave frequency EM energy for any or all of resection, coagulation and ablation. For example, the instrument may be a resection device as discussed here, but, alternatively, it may be any one of a pair of microwave forceps, a loop that radiates microwave energy and / or RF energy pairs. and an argon beam coagulator.
[0033] [0033] The housing may provide a double insulation barrier for the operator, that is, the housing may comprise an outer cover (first insulation level) that encapsulates a branched passageway (second insulation level) within which the various entrances are integrated into the single cable assembly. The branched passageway can provide an airtight volume that defines a fluid flow path between the second inlet and the outlet and which has a first port adjacent to the first inlet for the coaxial cable inlet.
[0034] [0034] In use, the interface set can be the location where the treatment fluid in the instrument is introduced. The interface joint operator can control the introduction of the fluid, for example, through a syringe or other fluid delivery mechanism attached to the second inlet. The interface gasket may also include a fluid delivery implantation mechanism that acts to instruct or control fluid delivery in the electrosurgical instrument. For example, the interface gasket may include a sliding trigger in the housing, the sliding trigger being attached to a connecting rod that extends out of the housing through the outlet. The push column can extend through the flexible rod to the electrosurgical instrument, in which it is possible to control the fluid distribution structure. For example, the electrosurgical instrument may include a retractable needle that is switchable in and out of fluid communication with the fluid flow path in the flexible rod by sliding the push column back and forth.
[0035] [0035] In this arrangement, the branched passage may include a second door adjacent to the sliding trigger for the admission of the push column.
[0036] [0036] Both the first door and the second door can comprise a sealing plug that defines an airtight passage for the coaxial cable and the push column, respectively. The sealing plug can be formed from an elastically deformable material, for example, silicone rubber, in which the coaxial cable and push column are encapsulated in the material as they pass through it. Sealing the first and second ports in this way means that the only route for the flow of the interface gasket is through the outlet along the fluid flow path in the flexible sleeve.
[0037] [0037] The branched passage can have any suitable configuration. In one embodiment, which is formed from a pair of Y-shaped conduits, which are connected to each other to define a first length in line with the outlet, a second length that extends on one side of the first length at an angle oblique to the first length and a third length extending on one side of the second length. The first length can have the push column that extends through it and can end is at the proximal end in a sealing plug. The second length can have the coaxial cable that passes through it and can end at its proximal end in a sealing plug. The third length can end at the second port to receive the fluid. In this arrangement, the housing may have a pistol-like shape. However, in another embodiment, the branched passageway can have a more compact configuration, in which the different lengths of the passageway travel substantially in parallel with respect to each other. In this arrangement, the housing may be an elongated capsule sized to fit an operator's hand.
[0038] [0038] The interface joint may be particularly suitable for assembling a plurality of inputs into a single cable assembly (i.e., the multi-lumen cable assembly mentioned above) before being inserted through the instrument channel of a endoscope. To achieve this goal, the cable assembly can have an outside diameter of 9 mm or less, for example, 2.8 mm or less for a flexible video colonoscope.
[0039] [0039] In order to facilitate the manipulation of the instrument at the distal end of the instrument channel of the endoscope, the flexible sleeve can be provided with longitudinal braids in it to assist in the transfer of torque, that is, to transfer a twisting movement at the end proximal of the cable assembly to the distal end of the cable assembly, where it can cause birrotational rotation of the instrument due to the fact that the instrument is connected to the cable assembly. The flexible sleeve may comprise an inner tube and an outer tube which are connected or otherwise not connected together with a metallized braiding tube in the middle. The inclination of the braid can be variable along the length of the cable assembly. For example, it may be useful to have a wider slope in a region, for example, a distal portion of the cable, where flexibility is important, in order to prevent the metallic braid from interfering with the RF field or micro-field. waves on the instrument, a distal portion of the flexible sleeve can be provided where the braid is absent. The distal part can be manufactured separately and fixed (for example, glued or welded) to the braided portion.
[0040] [0040] The housing may also comprise a strain relief element mounted on the outlet and around the flexible sleeve. The function of the strain relief element is to limit the movement of the sleeve in that location to avoid over-flexing that can damage the internal components.
[0041] [0041] The flexible sleeve may comprise a multi-lumen tube. Lumens can be formed by inserting an extruded separating element into a single lumen tube. The extruded separator element can include a plurality of transverse channels (for example, two, three or more). One of the transverse channels can carry the pressure column (if present). The other channels can be left empty, which can ensure that there is always a fluid flow path open between the instrument and the interface gasket to guide the coaxial cable and one or more transverse holes to transport the fluid supply and control conduit of wire (s). The fluid flow path can flood the internal cavity formed by the flexible sleeve and the coaxial cable can be immersed in the liquid.
[0042] [0042] A distal end of the push column can be connected to a proximal end of a needle bolt that has a needle attached to its distal end. The bolt can be hollow with one or more openings in its external wall that make its interior in fluid communication with the fluid flow path through the flexible sleeve. The distal end of the bolt can be opened so that the needle mounted on the distal end is in fluid communication with the fluid flow path. The proximal end of the bolt can be sealed by the pressure column.
[0043] [0043] According to the third aspect of the invention, a torque transfer unit is provided for the rotation of the electrosurgical instrument at the distal end of an endoscope by transferring the user's rotation force in a flexible sleeve connected to the electrosurgical instrument, characterized in that the torque transfer unit comprises an elongated clamp arranged to provide a clamping force along the length of the flexible sleeve that is outside the endoscope, the elongated clamp comprising: an upper elongated housing member , a lower elongated housing element hingedly connected to the upper elongated housing and member defining a passage for the flexible sleeve, wherein the upper elongated housing member and the lower elongated housing member are pivotable between a release position where the torque transfer unit is capable of sliding up and down the ma flexible sleeve and a clamping position, wherein the flexible sleeve is clamped between the upper elongated housing member and the lower elongated housing member.
[0044] [0044] The torque transfer unit can thus be designed to slide freely along the length of the flexible sleeve to a position that is convenient for use. Once in position, the torque transfer unit can hold the sleeve by turning the upper elongated housing member and the lower elongated housing member together. The torque transmission unit may include a release clamp that allows the upper elongated housing member and the lower elongated housing member to be secured in place at any point. The clamp can be a resilient locking element in one of the upper elongated housing element and the lower elongated housing member, which a correspondent clings to the other.
[0045] [0045] The upper elongated housing member and the inner elongated housing member can each carry a U-shaped clamping member, the U-shaped clamping members being arranged to oppose one the other to provide substantially uniform clamping pressure on the flexible sleeve when the upper elongated housing member and the lower elongated housing member are in the clamping position. In a preferred embodiment, a deformable intermediate handle tube is the position around the flexible sleeve between the flexible sleeve and the U-shaped fasteners. The intermediate handle tube can be made of silicone or any other suitable compatible material. In use, the intermediate handle tube grips the compression flexible sleeve and fixes the position of the torque transfer unit. The intermediate handle tube acts to distribute the load on the flexible sleeve that can prevent local damage to the sleeve wall.
[0046] [0046] In use, when the distal tip of the electrosurgical instrument is correctly positioned in relation to the distal end of the flexible endoscope within the field of view on the video monitor of the endoscope, it is intended that the endoscopist will lock and block the exchange transfer unit at the exit point of the flexible rod of the endoscope working channel and immediately adjacent to the XY endoscope controls. When held in place, the torque transfer unit provides longitudinal and rotary finger and thumb position control of the distal tip of the instrument. The variable positioning and tightening of the torque transfer unit allows the instrument to use endoscopes of different lengths (for example, flexible endoscopes with working channels between 60 and 170 cm in length).
[0047] [0047] Here, radio frequency (RF) can mean a stable fixed frequency in the range of 10 kHz to 300 MHz, and microwave frequency can mean a stable fixed frequency in the range of 300 MHz to 100 GHz. RF energy it must be high enough to prevent the energy from causing nerve stimulation and low enough to prevent the energy from causing tissue whitening or unnecessary thermal margin or damage to the tissue structure. Preferred unique frequencies for RF energy include any or more of the following: 100 kHz, 250 kHz, 400 kHz, 500 kHz, 1 MHz, 5 MHz. Preferred local frequencies for microwave energy include 915 MHz, 2, 45 GHz, 5.8 GHz, 14.5 GHz, 24 GHz. BRIEF DESCRIPTION OF THE DRAWINGS
[0048] [0048] The examples that embody the invention, as discussed in detail below with reference to the accompanying drawings, in which:
[0049] [0049] Fig. 1 is a schematic view of a complete electrosurgery system in which the present invention is applied;
[0050] [0050] Fig. 2 is a cross-sectional view of an interface joint which is an embodiment of the present invention;
[0051] [0051] Fig. 3 is a perspective sectional view of the hinge interface shown in Fig. 2;
[0052] [0052] Fig. 4A is an exploded view of a torque transfer unit which is an embodiment of the invention;
[0053] [0053] Fig. 4B is a perspective view of the torque transmission unit of Fig. 4A in an assembled state;
[0054] [0054] Fig. 5 is a schematic perspective view of another interface gasket which is an embodiment of the invention;
[0055] [0055] Fig. 6 is a schematic perspective view of an integrated interface gasket and torque transfer unit which is an embodiment of the invention;
[0056] [0056] Fig. 7 is a schematic perspective view of another integrated interface gasket and torque transfer unit which is an embodiment of the invention;
[0057] [0057] Fig. 8 is an exploded view of a distal end assembly for an electrosurgery device which is a modality of the invention;
[0058] [0058] Fig. 9A is a top perspective view of the distal end assembly of Fig. 8 in an assembled state;
[0059] [0059] Fig. 9B is a bottom perspective view of the distal end assembly of Fig. 8 in an assembled state;
[0060] [0060] Fig. 10 is a cross-sectional view of an interface cable suitable for use with the present invention;
[0061] [0061] Fig. 11A is a top view of a bipolar structure used in the distal end assembly of Fig. 8;
[0062] [0062] Fig. 11B is a side view of a bipolar structure used in the distal end assembly of Fig. 8;
[0063] [0063] Fig. 11C is a bottom view of a bipolar structure used in the distal end assembly of Fig. 8;
[0064] [0064] Fig. 12A is a view of a needle assembly suitable for use with the distal end assembly of Fig. 8;
[0065] [0065] Fig. 12B is an enlarged cross-sectional view through the needle assembly shown in Fig. 12A;
[0066] [0066] Fig. 13 is a schematic drawing illustrating a fluid flow path through an interface cable that is suitable for use with the present invention;
[0067] [0067] Fig. 14A is a top view of a protective structure used in the distal end assembly of Fig. 8;
[0068] [0068] Fig. 14B is a cross-sectional view through the protection structure used in the set of the distal end of Fig. 8;
[0069] [0069] Fig. 15A is a perspective view of a plug used in the interface joint shown in Fig. 2;
[0070] [0070] Fig. 15B is a cross-sectional view through the plug shown in Fig. 15A;
[0071] [0071] Fig. 16A is a perspective view of a Y-shaped connector used on the interface joint shown in Fig. 2;
[0072] [0072] Fig. 16B is a cross-sectional view through the Y-shaped connector shown in Fig. 16A
[0073] [0073] Fig. 17A is an isometric view of several phases in the manufacture of a distal end assembly for an electrosurgical device which is a modality of the invention; and
[0074] [0074] Fig. 17B is an end view of the complete distal end assembly shown in Fig. 17A. DETAILED DESCRIPTION; MORE OPTIONS AND PREFERENCES
[0075] [0075] Various aspects of the present invention are presented below in the context of an electrosurgery system that provides an invasive electrosurgical instrument for use in endoscopic procedures for the removal of polyps and malignant tumors through the controlled administration of both microwave energy and RF. However, it is to be understood that the aspects of the invention presented here do not have to be limited to that specific application. They can also be applicable in modalities where only RF energy is needed or when only RF energy and fluid distribution are needed.
[0076] [0076] Fig. 1 is a schematic diagram of a complete electrosurgery system 100 that is capable of selectively supplying the distal end of an invasive electrosurgical instrument with any or all of the RF energy, microwave energy and fluid , for example, saline or hyaluronic acid. System 100 comprises a generator 102 for the supply of controllable electromagnetic energy (EM) and / or microwave frequency EM energy. A generator suitable for this purpose is described in WO 2012/076844, which is incorporated herein by reference.
[0077] [0077] Generator 102 is connected to a common interface 106 by an interface cable 104. Interface gasket 106 is also connected to receive a fluid supply 107 from a fluid delivery device 108, such as a syringe . The interface gasket 106 houses a needle movement mechanism that is operable by sliding a trigger 110. The function of the interface gasket 106 is to combine the inputs of the generator 102, fluid distribution device 103 and needle movement mechanism in a single flexible rod 112 extending from the distal end of the interface gasket 106. The interior configuration of the interface gasket 106 is discussed in more detail below.
[0078] [0078] The flexible rod 112 is insertable through the entire length of an instrument (working) channel of an endoscope 114. A torque transfer unit 116 is mounted at a proximal length of the rod 112 between the interface gasket 106 and endoscope 114. The torque transfer unit 116 engages the rod to allow it to be rotated within the instrument channel of the endoscope 114.
[0079] [0079] The flexible rod 112 has a distal assembly 118 that is shaped to pass through the instrument channel of the endoscope 114 and projection (e.g., inside the patient) at the distal end of the endoscope tube. The distal end assembly includes an active tip to distribute the RF EM energy and / or the microwave EM energy in biological tissue and a retractable hypodermic needle to supply fluid. These combined technologies provide a unique solution for cutting and destroying unwanted tissue and the ability to seal blood vessels around the target area. Through the use of the retractable hypodermic needle, the surgeon is able to inject saline and / or hyaluronic acid with a marker dye added between the tissue layers in order to stretch and mark the position of a lesion to be treated. Injecting fluid in this way elevates and separates the tissue layers making it easier to dry around the lesion and flatten through the submucosal layer, reducing the risk of perforation of the intestinal wall and unnecessary thermal damage to the muscle layer.
[0080] [0080] As discussed in more detail below, the distal assembly 118 also includes a protective polymer structure positioned under the active tip to assist in a resection action of the type of tissue flattening, again helping to protect against inadvertent perforation and ensuring viability of the remaining tissue, which in turn facilitates faster healing and post-operation recovery.
[0081] [0081] The structure of the distal assembly discussed below can be specially designed for use with a conventional directional flexible endoscope that has a working channel with an internal diameter of at least 2.8 mm and a channel length of between 60 cm and 170 cm cm. As such, most of the comparatively small diameter instrument (less than 3 mm) is housed within the lumen of a much larger polymer isolation device and Predominantly, that is, the flexible endoscope channel, which typically has an outer diameter from 11 mm to 13 mm. In practice, only 15 mm to 25 mm of the distal assembly protrudes from the distal end of the channel endoscope, in order not to block the field of view or adversely affect the camera's focus. The protruding part of the distal assembly is the only part of the instrument that never comes into direct contact with the patient.
[0082] [0082] At the proximal end of the working channel of the endoscope, which is typically kept at 50 cm to 30 cm from the patient, the flexible rod 112 emerges from the working channel door and extends for more than 30 cm to 100 cm for the interface gasket 106. In use, interface gasket 106 is typically maintained by a gloved assistant throughout the procedure. The interface gasket 106 is designed and manufactured from polymeric materials in order to provide primary and secondary electrical insulation with extended clearance and clearance distances. The interface cable 104 is connected to the generator 102 through a coaxial interface of the QMA type, which is intended to allow continuous clockwise or counterclockwise rotation. This allows the interface gasket 106 to rotate with the torque transfer unit 116 under the control of the endoscopist. The assistant supports the interface joint 106 throughout the procedure, in order to assist the endoscopist with the rotation of a sympathetic instrument, needle control and fluid injection. COMMON INTERFACE AND TORQUE TRANSFER UNIT
[0083] [0083] Figs. 2 and 3 show the structure of an interface joint 120 which is an embodiment of the invention. The interface gasket comprises a rigid plastic reservoir 122, which encloses several internal components. In Figs. 2 and 3 a half of the housing 122 is removed to show the interior of the joint. The housing 122 is in the form of a pistol, that is, it has an upper cylinder portion 121 and an adjacent lower portion 123 that extends outwardly from a proximal end of the upper cylinder portion at an oblique angle. The upper cylinder portion 121 contains the needle movement mechanism, while the adjacent lower portion 123 contains the connections for the fluid and energy feeds.
[0084] [0084] The interface joint core 120 is a pair of Y-shaped conduits 124, 126 that are coupled together to define a branched passageway. The Y-shaped conduits can be made from polycarbonate or other suitable hard plastic and are shown in more detail in Figs 16A and 16B, a first length 128 of the branched passageway is mounted and is located along the upper cylinder portion 121 of housing 122. The first length 128 receives at its proximal end a push rod 130 to control the implantation of the retractable needle. The push rod 130 has a curved proximal end 132, which is mounted, for example, hot mounted, on a needle slider 134. The needle slider 134 is slidably mounted on the upper cylinder portion 131. The needle slider 134 includes a thumb trigger designed 136 to move the slider to or from, which causes the needle to slide in and out of the distal assembly. The proximal end of the first length 128 is sealed by a silicone plug 138, which is shown in more detail in Figs. 15A and 15B.
[0085] [0085] A second length 140 of the branched passage is mounted at and is located along the lower adjacent portion 123, that is, at an angle oblique to the first length of 128. The second length 140 transmits a coaxial cable 142 from a QMA type connector proximal 144 to the proximal end of the first length 128, where it meets the pressure shaft 130 and exits interface joint 120 through distal outlet 146. The connector type QMA 144 is connected to the interface cable a from the generator. The coaxial cable 142 can be a Sucoform 047 coaxial cable coated with a 30 μm layer of Parylene C. The coaxial cable 142 can pass through a silicone sealing plug 148 at the proximal end of the second length 140.
[0086] [0086] A third length 150 of the branched passage leads out of the second length 140 to provide an outward facing fluid receiving port 152. Fluid receiving port 152 may be a Luer Lock thread for a sealing engagement with a suitable syringe or similar. The sealing plug 148 and the cap 138 cause the branched passage to be hermetically sealed, whereby the fluid has introduced a fluid receiving port 152 can only exit the interface gasket 120 through the distal outlet 146.
[0087] [0087] The distal outlet 146 of the interface joint receives through it a proximal portion of the flexible axis 154 which is introduced into the instrument channel of the endoscope. The flexible rod carries the fluid, the push column 130 and the coaxial cable 142 as discussed below. A proximal end of the flexible rod 154 is connected directly inside the branched passage, so that there is a certain overlap along the upper cylinder portion 121. This connected joint is masked by a cover 156 (for example, silicone rubber) that fits like a stretched glove and plugs into place. The cover 156 acts as a strain relief element and also functions as an end of the flexible rod bend restrictor.
[0088] [0088] The main user of interface board 120 may be the assistant of the endoscopist. In use, the operator typically offers the instrument's distal tip to the endoscopist for insertion of the flexible endoscope's working channel, makes the electrical connection between the common interface 120 and the interface cable (which is connected to the generator) and, then, it supports the interface joint 120 itself throughout the procedure. During the procedure, the operator can inject distension / marker fluids as needed through syringes of 5 to 20 ml attached to the fluid receiving port 152 and operate the needle slider 134, as indicated by the endoscopist.
[0089] [0089] The flexible rod 154 comprises an outer cannula tube containing coaxial cable 142, pushing column 130 and fluid. The specific internal structure of the flexible rod is discussed below with reference to Fig. 10. The distal assembly is attached to the outer cannula tube in a way that means that any rotation applied to the tube is passed to the distal assembly. Therefore, to allow the manipulation of the distal rotating assembly, a torque transmission unit is mounted on the flexible shaft, in order to facilitate its rotation.
[0090] [0090] Figs. 4A and 4B show a torque transfer unit 158 which is an embodiment of the invention. Essentially, the torque transfer unit 158 is an elongated clamp that transmits a grip force along a length of the flexible rod. By taking a stem length, the torque transfer unit can apply a lower maximum pressure and therefore prevent damage to the flexible stem and its contents.
[0091] [0091] As shown in Fig. 4A, the torque transfer unit 158 comprises an upper elongated elongation member 160 and a lower elongated housing member 162, which are pivoted together around a pivot column 164 at its distal end . The upper elongated housing member 160 and the lower elongated housing member 162 each carry the U-shaped fixing member 166. The fixing members 166 are opposed to each other, where the articulation of the elongated housing member upper 160 and the lower elongated housing member 162 in relation to the other changes the distance between the fastening elements 166. A deformable tube 168 is mounted between the fixing members 166. Deformable tube 168 is threaded on the flexible rod, which passes through the holes 170 on the proximal and distal faces of the torque transfer unit 158. In use, the upper elongated housing member 160 and the lower elongated housing member 162 are pivotable between a release position in which the torque transmission unit can be slid up and down from the flexible rod and into a clamping position, where the deformable tube 168 is flattened between the clamping components to transmit a clamping force on the shaft the flexible. The upper elongated housing member 160 and the lower elongated housing member 162 can be retained in the clamping position by a release clamp 172. The distal end of the torque transfer unit 158 has a series of circumferential recesses designed to be gripped by the thumb and operator's index finger for easy rotation.
[0092] [0092] Fig. 5 is a perspective view of an interface joint 180 in conjunction with a torque transmission unit 158 which is another embodiment of the invention. The torque transfer unit 158 is the same as that discussed above with reference to Figs. 4A and 4B and will not be discussed again.
[0093] [0093] The articulation interface 180 in this modality comprises a body similar to compact barrel 182, which facilitates rotation by the endoscopist's assistant. In particular, interface cable 104 is connected in axial alignment with the body 182, for example, via a rotary quick-connect coaxial connector. Body 182 includes a nested cylinder 184 for receiving a syringe 188 for supplying fluid. Nested barrel 184 may include a viewing window 186 to show how much fluid is left.
[0094] [0094] In this modality, a needle slider 190 is mounted towards the nose of the body 180 for the thumb control while the body 182 is supported in the palm of the hand. The sliding controller 190 can have free reciprocal movement as in the embodiment shown in Figs. 2 and 3. A locking mechanism (not shown) can be provided to lock and set the cursor in a fully retracted needle position. Alternatively, the slider can have a spring loaded action that presses the mechanism in the retracted state. With the spring loaded option, the user (assistant) would be required to hold the slider forward against the spring while injecting the liquid.
[0095] [0095] Fig. 6 is a perspective view of a combined interface gasket and torque transfer unit 192 which is another embodiment of the invention. All the functions of the torque transfer unit and interface gaskets discussed above are provided here within a single molded assembly. However, the combined unit is able to slide along the flexible axis in use, which means that the length of the instrument must be carefully combined with the length of the endoscope working channel. However, an advantage of this arrangement is that there is more microwave energy available at the active tip in the distal assembly due to the fact that a shorter instrument length means less energy is lost.
[0096] [0096] The combined unit 192 comprises a worn drum 194 with a faceted distal end 196 to facilitate rotary control of the finger and thumb. A needle slider 198 is mounted towards the rear of barrel 194 due to the support position and natural waiting for the endoscopist during these procedures.
[0097] [0097] As an alternative to the 198 needle slide, an articulated rocker-type control lever could be used for ease of finger control. With this design, the needle slide (or tipper) lock forwards and backwards would be necessary, or a backwards lock and a control designed forwards to allow a handled operation and an injection of fluid by the endoscopist, that is, to give the endoscopist the freedom to use his other hand to hold or handle the endoscope.
[0098] [0098] Fig. 7 is a perspective view of a combined interface gasket and torque transfer unit 200 which is another embodiment of the invention. The combined unit 200 is similar to the device shown in Fig. 6 with the exception of a remote syringe fluid injection coupling 201. The combined unit 200 comprises a thin, barrel-like body 202 with a faceted distal end 204 and a needle slide 206 that works as discussed above. The 202 body has a slim and compact design as it does not need to house a syringe. Instead, the body 202 is connected to a fluid receiving port 208 through a fluid supply line 210. This arrangement can allow the device to be used with larger syringes with an unrestricted barrel diameter. The body in this arrangement can also be lighter than the one shown in Fig. 6. In this embodiment, the distal end 204 of the body 202 includes a flat face in recess 212, which allows a location against the endoscope inlet cover for greater stability. As with the device shown in Fig. 6, this solution (as shown) requires that the length of the instrument is closely aligned with the length of the working channel of a third party's endoscope and thus offers the potential for greater availability of microwave energy at the tip of the instrument.
[0099] [0099] It may be possible to raise the short axial adjustment up to 100 mm inside the combined drum-shaped units shown in Figs. 6 and 7. This can allow the endoscopist to adjust the length of the instrument to the flexible endoscopy of his choice. This additional functionality can also minimize the number of product variants needed to cover today's third-party endoscopes.
[0100] [0100] Figs. 15A, 15B, 16A and 16B also show details of some internal components of the interface gasket.
[0101] [0101] Figs. 15A and 15B are, respectively, seen in perspective and in cross-section of the stopper 138 which seals the proximal end of the first length of the branched passage. The stopper comprises a luer lock fitting 246 and an integral sealing diaphragm 248, for example, made of a resilient deformation rubber.
[0102] [0102] Figs. 16A and 16B show the Y-shaped conduits 250 from which the passageway is formed. Each Y-shaped conduit has a main linear channel between the first input 252 and an output 254 and a second channel at an angle oblique to the main linear channel, the second channel having a second input 256 and joining the main linear channel approximately half its length. The first entry 252 and the second entry 256 have a luer lock slot 258. DISTAL ASSEMBLY CONFIGURATION
[0103] [0103] Figs. 8, 9A and 9B show details of a distal assembly 214 comprising an active tip which is an embodiment of the invention. Fig. 8 shows an exploded view of the components that form the distal assembly 214. The distal assembly 214 is mounted on the distal end of the tube, outer cannula 216 of the flexible shaft 154 which is discussed above. In order to offer a torque function, most of the outer cannula tube 216 is formed of a braided tube, for example: comprising a braided wire (for example, stainless steel) assembled wound between the radially inner polymer layer and a radially outer polymer layer. However, to prevent the braided material from interfering with the distribution of microwave and / or RF frequency EM energy for the distal assembly, the distal portion 218 of the outer cannula tube 216 is made exclusively of polymer layers, that is: without an internal braid.
[0104] - montar a montagem distal no eixo flexível, - proporcionar uma superfície inferior protetora da ponta ativa, - proporcionar um compartimento protetor para a agulha e - localizar a ponta ativa em relação ao cabo coaxial. As partes da estrutura do casco 222 que executam essas funções são discutidas em mais detalhe abaixo, com referência às Figs. 14A e 14B. [0104] The distal portion 218 of the outer layer of the cannula 216 fits into a corresponding proximal part 220 of the protective shell 222. The protective shell is formed of poly (ether-ether-ketone) (PEEK) or any other suitable engineering plastic and has a form that allows you to perform a series of functions, namely: - mount the distal assembly on the flexible shaft, - provide a protective bottom surface for the active tip, - provide a protective needle compartment and - locate the active tip in relation to the coaxial cable. The parts of hull structure 222 that perform these functions are discussed in more detail below, with reference to Figs. 14A and 14B.
[0105] [0105] The distal assembly 214 includes an active tip 224, which is a flat piece of dielectric material (eg alumina) with conductive layers (eg gold) on its upper and lower surfaces. The distal end of the active tip 224 is curved. The conductive layers are electrically connected to the inner and outer conductors of the coaxial cable 142 which are conducted by the flexible shaft 216. At the distal end of the coaxial cable 142, its outer sheath is removed to expose a length of the outer conductor 226. The inner conductor 228 of the coaxial cable extends beyond the distal end of the external conductors 226. The coaxial cable 142 and the active tip 224 are mounted relative to each other, so that the protruding part of the inner conductor 228 is in a first layer conductive of the active tip, while the outer conductor 226 is placed in electrical connection with a second conductive layer by means of a conductive plate element 230. The first conductive layer is isolated from the outer conductor 226 and the second conductive layer is isolated from the conductor internal 228. Further details of the configuration of the active tip are discussed below, with reference to Figs. 11A to 11C.
[0106] [0106] When assembled, as shown in Figs. 9A and 9B, the active tip 224 and the coaxial cable 142 are connected to each other and to the hull 222 by applying epoxy adhesive over the portion of the inner conductor 228 projecting from the outer conductor. This epoxy adhesive also serves to form an end plug for the outer cannula tube, that is, a fluid-tight seal, which means that the only outlet for the fluid inserted in the interface gasket is through the needle.
[0107] [0107] Hull 222 includes a recess for retaining a needle guide tube 232, for example made of polyamide. In use, the distal assembly 214 has close contact with the patient. The needle 234 can be extended beyond the distal end of the active tip 224 and retracted back to the inside of the guide tube 232 by controlling the interface joint sliding mechanism. In its extended position, the needle is used by the endoscopist to inject fluid in order to distend and mark the tissue locally. The conductive layers at the active tip 224 form bipolar electrodes for the distribution of microwave and / or RF frequency energy.
[0108] [0108] The needle orientation 232 extends back in and close to the distal assembly to provide an extended leak release to ensure that microwave / RF activation only occurs through the distal tip region of the active tip 224.
[0109] [0109] Likewise, it can be seen that the conductive layer 236 is recessed back behind the distal tip region of the active tip 224. This is done on the upper and lower faces to increase the follow-up / release distance at the proximal end of the active tip, also ensuring that the microwave / RS energy is concentrated at the distal end and the intentional active element of the tip.
[0110] [0110] Fig. 10 shows a typical cross section of flexible shaft 154. The flexible shaft can be run for 2.3 m (or 2.0 m), that is, the entire length of the instrument that connects the interface joint. distal assembly. During use, most of the length of the shaft is located inside the working channel of the flexible endoscope. The flexible shaft 154 comprises the outer cannula tube 216 (that is, the braided tube discussed above), which forms a fluid-tight cannula 237 and an electrical barrier between the patient and the user and the coaxial Sucoform 142 case, which in itself it is only additionally isolated. The external cannula tube 216 also houses an extruded 3-lumen PTFE 238 tube that provides a low-friction passage towards the pressure axis 130 and stability / support to the construction, while ensuring that the fluid passage is maintained along the entire length of the cannula at all times.
[0111] [0111] Along the length of the flexible shaft 154, the coaxial cable 142 (for example: the Sucoform bag 047) forms a lumen of a composite construction with a double insulated external cannula tube and a braided tube 216, forming the rod of the flexible protection instrument. To deal with the potential thermal risk represented by the use of activation, controls can be imposed on the use of microwave energy by the generator. For example, in the first case, the activation can be limited to 20 s (continuous output) and, henceforth, the incidence of medium power proximal end of the distal assembly can be limited to 4W. This control can be enforced independently of the endoscopist, for example, using generator software. With this control in place, a temperature of 40 ° C was observed after 20s of continuous activation on the polymer surface of the instrument stem immediately distal from the interface joint. After 20 s the temperature fails, as the endoscopist's activation of additional continuous microwave is automatically interrupted by the generator software. The full 20s activation capability can be avoided until 240s (12 χ 20 s) have passed.
[0112] [0112] In practice, this may not be necessary to activate the clotting function for more than 10 s due to concerns about perfusion at the tip, resulting in potential damage to the complete wall thickness.
[0113] [0113] Figs. 11A, 11B and 11C illustrate the dimensions of an example of an active tip 224 that can be used in embodiments of the invention. The total length of the active tip is 10.6 mm, with a maximum width of 2 mm and a height of 0.5 mm. The metallization layer on the active tip has a thickness of 0.03 mm. The curved distal end is manufactured in the form of a plurality of rounded sections of decreasing length and radius towards the distal tip. In this modality, there are five different radial sections, but more can be used. The length of each section and its corresponding radius of curvature are shown in Table 1:
[0114] [0114] As mentioned above, the conductive layers on both surfaces are separated from the edges of the dielectric substrate by a distance of 0.2 mm over 6 mm close to the tip. And, to ensure that the upper conductive layer is isolated from the outer conductor of the coaxial cable, the upper conductive layer is spaced from the proximal edge of the dielectric substrate at a distance of 0.6 mm.
[0115] [0115] Figs. 12A and 12B illustrate the transition from pressure shaft 130 to needle 234. A needle tip 240 is attached to pressure shaft 130 at a proximal end of its own and is connected to needle 234 at a distal end thereof. A set of holes on the outer surface of needle tip 240 allows fluid to flow from the flexible stem for dispensing out of needle 234. As shown in Figure 12B, pressure shaft 130 acts as a stop at the proximal end of tip 240, preventing the fluid from escaping in the wrong direction.
[0116] [0116] Fig. 13 schematically illustrates the flow path for the fluid. Immediately close to the distal assembly, the injected fluid that has passed through the flexible axis 154 of the syringe is forced through four small radial holes 242 central to the needle tip 240 and from there into the hypodermic needle 234 for injection into the patient.
[0117] [0117] Figs. 14A and 14B show the shape of the protective hull 222. As shown more clearly in Figure 9B, the distal end of the hull has a shape that allows the active tip to overlap it by about 0.2 mm around the distal end , except at the distal tip. The surface that comes into contact with the lower part of the active tip thus has a maximum width of 2 mm, which is restricted to 1.6 mm in an intermediate portion 223 before gradually reducing to its distal tip in a distal portion 225. The distal tip can be a single radial curve, for example, with a radius of 0.2mm.
[0118] [0118] Meanwhile, the proximal end of the hull defines an oblong recess to receive the proximal end of the active tip. The oblong recess is bounded by a pair of wings 244 on each side, which act to retain and align the active tip, as well as to define a volume to receive the adhesive covering the exposed internal conductor of the coaxial cable.
[0119] [0119] Fig. 17A shows several stages in the assembly of a distal end portion 300 for an electrosurgical instrument which is another embodiment of the invention. The leftmost view in Fig. 17A shows an inner tube 302 made of a conductive material. This inner tube 302 represents the inner conductor of the coaxial power discussed above. The second point of view from the left in Fig, 17A shows an outer tube 304, first over the inner tube 302. The outer tube 304 can be formed as a tube of dielectric insulating material with a conductive coating on its outer surface. The conductive coating acts as the external conductor of the coaxial supply.
[0120] [0120] At the distal end of the outer tube, a portion of the conductive coating is marked to expose a 306 portion of dielectric material. An island 308 of the conductive coating is left on the upper surface of the outer tube at its distal end. The island 308 is separated (that is, electrically isolated) from the rest of the conductive coating 304 by the conductive coating of the exposed portion formed on the lower surface of the outer tube at its distal end with a shape and size similar to that of the island 308. However, the tongue remains in electrical contact with the rest of the conductive coating, that is, it is an extension of the external conductor.
[0121] [0121] A hole 310 (for example, with a diameter of 1 ram) is formed on the island 308 through the conductive coating and insulating material, exposing the inner tube 302. The hole is then filled with a conductive material (for example , epoxy silver) to electrically connect the inner tube 302 to the island 308. As a result, the distal end of the outer tube has two opposite electrical contacts on its outer surface. A first contact (the island 308) is in electrical connection with the inner tube 302 (that is, the inner conductor) and a second contact (the tongue) is in electrical connection with the conductive lining of the outer tube 304 (ie, the external conductor).
[0122] [0122] The third point of view from the left in Fig. 17A shows the next stage in the assembly, where a tip of the instrument 312 is inserted at the distal end of the outer tube 304. The tip of the instrument 312 comprises a flat part 314 of the rigid dielectric , for example: a ceramic, like alumina. The outer tube 304 has two opposite tabs 316, which can receive and retain the flat part 314, for example, in the form of an interference fit or using an appropriate adhesive.
[0123] [0123] The lateral edges of the flat piece 314 are tapered in a semi-parabolic manner towards its distal end. The upper and lower flat surfaces have conductive layers, for example: gold or silver metallization, formed on them. The top layer 318 is visible in Fig. 17A.
[0124] [0124] The rightmost point of view in Fig. 17A shows the final stage of the assembly, in which the first and second contacts are electrically connected to the upper and lower conductive layers, respectively, at the tip of the instrument 312 using a part from conductive blade 318.
[0125] [0125] Fig. 17B shows an end view of the distal end portion 300, after assembly, here it can be seen that the lower part of the conductive sheet 320 has a hole 322 formed therein through which the retractable needle discussed above you can pass.

权利要求:
Claims (15)
[0001]
Electrosurgical instrument for the application in biological tissue of radio frequency electromagnetic energy (EM) and / or microwave frequency EM energy, the instrument characterized by the fact that it comprises: a tip of the instrument comprising a flat body made of a first dielectric material that separates a first conductive element on a first surface of the same from a second conductive element on a second surface thereof, the second surface being turned away from the first surface ; a coaxial power cable (142) comprising an inner conductor (228), an outer conductor (226) coax with the inner conductor and a second dielectric material that separates the inner and outer conductors, the coaxial power cord being for transmitting a RF signal and / or a microwave signal; and a protective housing (222) comprising a third piece of dielectric material assembled to cover the lower part of the flat body, where the inner conductor (228) is electrically connected to the first conductor element and the outer conductor (226) is electrically connected to the second conductor element to allow the tip of the instrument to receive the RF signal and / or the microwave signal , wherein the protective housing (222) has a smoothly contoured bottom convex surface facing outward from the flat body, where the flat body has a tapered distal end, and wherein the lower part of the flat body extends beyond the protective casing (222) at the tapered distal end.
[0002]
Electrosurgical instrument, according to claim 1, characterized by the fact that the lower part of the flat body extends beyond the protective casing (222) at the tapered distal end of 0.2w or less, where w is the maximum width of the flat body.
[0003]
Electrosurgical instrument, according to claim 1 or 2, characterized by the fact that the tapered distal end extends around a distal third of the flat body.
[0004]
Electrosurgical instrument according to any one of claims 1 to 3, characterized by the fact that the tapered distal end comprises any one of: a rounded distal tip; a continuous curve; and a continuous curve having a curvature formed from a plurality of contiguous rounded sections, each rounded section having a radius of curvature less than its proximal neighbor.
[0005]
Electrosurgical instrument according to any one of claims 1 to 4, characterized by the fact that the flat body has a length between 5w and 6w, where w is the maximum width of the flat body.
[0006]
Electrosurgical instrument according to any one of claims 1 to 5, characterized by the fact that the maximum width of the flat body is 9 mm or less.
[0007]
Electrosurgical instrument according to any one of claims 1 to 6, characterized by the fact that the first and second conducting elements each comprise layers of metallization, the metallization layers being formed on the opposite surfaces of the first dielectric material.
[0008]
Electrosurgical instrument, according to claim 7, characterized by the fact that the metallization layers are separated from the lateral edges of the first dielectric material in a proximal region of the flat body.
[0009]
Electrosurgical instrument according to any one of claims 1 to 8, characterized by the fact that the protective casing (222) is made of poly (ether-ether-ketone) (PEEK) or ceramic.
[0010]
Electrosurgical instrument according to any one of claims 1 to 9, characterized by the fact that the protective casing (222) and the first dielectric material are formed in a single piece.
[0011]
Electrosurgical instrument according to any one of claims 1 to 10, characterized in that the protective housing (222) is selectively metallized to form part of the first conductive element or the second conductive element.
[0012]
Electrosurgical instrument according to any one of claims 1 to 11, characterized in that it includes a fluid supply conduit for transporting fluid to the tip of the instrument for distribution outside the instrument, wherein the fluid supply conduit comprises a sleeve (216) that defines a lumen for transporting fluid to the tip of the instrument, the sleeve (216) having the flat body and the protective shell fixed at a distal end thereof and being arranged to carry the coaxial cable (142) in the lumen.
[0013]
Electrosurgical instrument according to claim 12, characterized in that it includes a fluid delivery mechanism mounted at the distal end of the sleeve lumen, the fluid delivery mechanism being operable to distribute the fluid from the lumen through the protective housing ( 222).
[0014]
Electrosurgical instrument according to claim 13, characterized by the fact that the lower surface of the protective casing (222) has a recess channel that extends longitudinally, formed therein, and in which the fluid distribution mechanism includes a insulating needle guide tube (232) mounted there and extending proximally from the recess channel and a retractable needle (234) slidably mounted on the needle guide tube.
[0015]
Electrosurgical instrument according to claim 13, characterized in that the lower surface of the protective housing (222) has a tubular protrusion integrally formed therein, the tip of the protrusion having an outlet to eject a fluid.

类似技术:

---

公开号 | 公开日 | 专利标题

---

BR112016015267B1|2021-02-17|electrosurgical instrument

---

JP2020531055A|2020-11-05|Electrosurgical device for delivering RF and / or microwave energy into living tissue

---

KR20210093246A|2021-07-27|Interface joint for connecting electrosurgical generator and electrosurgical instruments

---

KR20200045463A|2020-05-04|Interface joint for electrosurgical devices

---

BR112020004123A2|2020-09-01|electrosurgical apparatus

同族专利:

---

公开号 | 公开日

---

AU2014375127B2|2019-01-17|

---

EP3187139B1|2018-11-21|

---

JP6524101B2|2019-06-05|

---

DK3187139T3|2019-02-18|

---

GB201423386D0|2015-02-11|

---

CA3035423A1|2015-07-09|

---

JP2017500958A|2017-01-12|

---

JP6803902B2|2020-12-23|

---

BR112016015267A2|2017-08-08|

---

KR20160104640A|2016-09-05|

---

AU2018282275A1|2019-01-17|

---

EP3089689A2|2016-11-09|

---

WO2015101787A3|2015-08-27|

---

ES2678943T3|2018-08-21|

---

EP3089689B1|2018-05-16|

---

PT3089689T|2018-07-24|

---

EP3187139A1|2017-07-05|

---

DK3089689T3|2018-07-23|

---

GB201323171D0|2014-02-12|

---

US20160324576A1|2016-11-10|

---

CN105934214A|2016-09-07|

---

GB201522417D0|2016-02-03|

---

GB2530449B|2016-05-04|

---

CN105934214B|2020-09-15|

---

GB2523246A|2015-08-19|

---

GB2523246B|2016-02-17|

---

PT3187139T|2019-02-18|

---

CA2934981A1|2015-07-09|

---

AU2014375127A1|2016-07-21|

---

CA2934981C|2021-04-27|

---

US20200030031A1|2020-01-30|

---

CN109276309A|2019-01-29|

---

SG10201610081VA|2017-01-27|

---

CA3035423C|2021-06-01|

---

JP2019069198A|2019-05-09|

---

GB2530449A|2016-03-23|

---

AU2018282275B2|2019-10-17|

---

WO2015101787A2|2015-07-09|

---

SG11201605131SA|2016-07-28|

---

CN109276309B|2021-08-03|

---

ES2711174T3|2019-04-30|

---

US10729495B2|2020-08-04|

---

BR112016015267A8|2020-06-09|

引用文献:

---

公开号 | 申请日 | 公开日 | 申请人 | 专利标题

---

---

US5275597A|1992-05-18|1994-01-04|Baxter International Inc.|Percutaneous transluminal catheter and transmitter therefor|

---

JPH0663057A|1992-08-18|1994-03-08|Olympus Optical Co Ltd|High-frequency treatment means|

---

DE69432361T2|1993-05-14|2004-04-22|Boston Scientific Corp., Natick|CATHETER FOR VARIOUS IN-SITU TISSUE THERAPIES|

---

US5336222A|1993-03-29|1994-08-09|Boston Scientific Corporation|Integrated catheter for diverse in situ tissue therapy|

---

US5366476A|1993-04-02|1994-11-22|Laparomed Corporation|Handle for laparoscopic instrument|

---

US5733319A|1996-04-25|1998-03-31|Urologix, Inc.|Liquid coolant supply system|

---

US6223085B1|1997-05-06|2001-04-24|Urologix, Inc.|Device and method for preventing restenosis|

---

US6287305B1|1997-12-23|2001-09-11|Team Medical, L.L.C.|Electrosurgical instrument|

---

US6221039B1|1998-10-26|2001-04-24|Scimed Life Systems, Inc.|Multi-function surgical instrument|

---

JP4347443B2|1998-11-10|2009-10-21|オリンパス株式会社|High frequency treatment tool|

---

US6558385B1|2000-09-22|2003-05-06|Tissuelink Medical, Inc.|Fluid-assisted medical device|

---

US6942662B2|2001-12-27|2005-09-13|Gyrus Group Plc|Surgical Instrument|

---

JP4313205B2|2001-12-27|2009-08-12|ジラスメディカルリミティド|Surgical instruments|

---

JP2005312807A|2004-04-30|2005-11-10|Olympus Corp|Energy therapy device|

---

GB0425842D0|2004-11-24|2004-12-29|Gyrus Group Plc|An electrosurgical instrument|

---

US8068921B2|2006-09-29|2011-11-29|Vivant Medical, Inc.|Microwave antenna assembly and method of using the same|

---

US20090082762A1|2007-09-20|2009-03-26|Ormsby Theodore C|Radio frequency energy transmission device for the ablation of biological tissues|

---

US7642451B2|2008-01-23|2010-01-05|Vivant Medical, Inc.|Thermally tuned coaxial cable for microwave antennas|

---

US8945111B2|2008-01-23|2015-02-03|Covidien Lp|Choked dielectric loaded tip dipole microwave antenna|

---

WO2010053700A1|2008-11-10|2010-05-14|Microcube, Llc|Methods and devices for applying energy to bodily tissues|

---

US20100185197A1|2009-01-21|2010-07-22|Satomi Sakao|Medical treatment apparatus, treatment instrument and treatment method for living tissue using energy|

---

US20100249769A1|2009-03-24|2010-09-30|Tyco Healthcare Group Lp|Apparatus for Tissue Sealing|

---

GB2472972A|2009-07-20|2011-03-02|Microoncology Ltd|A microwave antenna|

---

GB201021032D0|2010-12-10|2011-01-26|Creo Medical Ltd|Electrosurgical apparatus|

---

US9011421B2|2011-01-05|2015-04-21|Covidien Lp|Energy-delivery devices with flexible fluid-cooled shaft, inflow/outflow junctions suitable for use with same, and systems including same|

---

GB2487199A|2011-01-11|2012-07-18|Creo Medical Ltd|Electrosurgical device with fluid conduit|

---

EP2693969B1|2011-04-08|2016-02-03|Covidien LP|Microwave device for treating tissue|

---

KR101248959B1|2011-05-12|2013-04-01|신경민|Electrode device having flexible tube for high frequency thermotherapy|

---

GB2503673A|2012-07-03|2014-01-08|Creo Medical Ltd|Electrosurgical device with convex under surface|

---

GB2513872A|2013-05-08|2014-11-12|Creo Medical Ltd|Electrosurgical apparatus|CN108135649A|2015-08-06|2018-06-08|阿帕玛医疗公司|Multipurpose electrode|

---

GB2543509B|2015-10-19|2020-10-14|Creo Medical Ltd|Electrosurgical instrument|

---

GB2545179B|2015-12-07|2020-09-09|Creo Medical Ltd|Electrosurgical instrument|

---

EP3520727A4|2016-09-29|2020-09-16|National University Corporation Shiga University OF Medical Science|Tissue joiner|

---

US20190380763A1|2016-10-31|2019-12-19|U.S. Patent Innovations, LLC|Attachment for electrosurgical system|

---

US20180168717A1|2016-12-15|2018-06-21|Medtronic Advanced Energy Llc|Electrosurgical blade with minimally exposed edge, alternative to coated blade|

---

GB2559595B|2017-02-10|2021-09-01|Creo Medical Ltd|Electrosurgical apparatus and electrosurgical instrument|

---

GB2564124B|2017-07-04|2021-08-25|Creo Medical Ltd|Control device for an electrosurgical instrument|

---

GB2565573A|2017-08-17|2019-02-20|Creo Medical Ltd|Interface joint for an electrosurgical apparatus|

---

GB2565575A|2017-08-17|2019-02-20|Creo Medical Ltd|Electrosurgical apparatus for delivering RF and/or microwave energy into biological tissue|

---

GB2579084A|2018-11-20|2020-06-10|Creo Medical Ltd|An interface joint for interconnecting an electrosurgical generator and an electrosurgical instrument|

---

WO2021009648A1|2019-07-16|2021-01-21|Cathrx Ltd|Pulse field ablation catheter|

法律状态:
2020-08-04| B06U| Preliminary requirement: requests with searches performed by other patent offices: procedure suspended [chapter 6.21 patent gazette]|

---

2020-12-08| B09A| Decision: intention to grant [chapter 9.1 patent gazette]|

---

2021-02-17| B16A| Patent or certificate of addition of invention granted|Free format text: PRAZO DE VALIDADE: 20 (VINTE) ANOS CONTADOS A PARTIR DE 31/12/2014, OBSERVADAS AS CONDICOES LEGAIS. |

优先权:

---

申请号 | 申请日 | 专利标题

---

GBGB1323171.7A|GB201323171D0|2013-12-31|2013-12-31|Electrosurgical apparatus and device|

---

GB1323171.7|2013-12-31|

---

PCT/GB2014/053857|WO2015101787A2|2013-12-31|2014-12-31|Electrosurgical apparatus for delivering rf and/or microwave energy into biological tissue|

---