Insulating boot for electrosurgical forceps
Either an endoscopic or open bipolar forceps includes a flexible, generally tubular insulating boot for insulating patient tissue, while not impeding motion of the jaw members. The jaw members are movable from an open to a closed position and the jaw members are connected to a source of electrosurgical energy such that the jaw members are capable of conducting energy through tissue held therebetween to effect a tissue seal. A knife assembly may be included that allows a user to selectively divide tissue upon actuation thereof. The insulating boot may be made from a viscoelastic, elastomeric or flexible material suitable for use with a sterilization process including ethylene oxide.
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This application claims the benefit of priority of U.S. Provisional Patent Application Ser. No. 60/722,213 by Scott DePierro et al., entitled “INSULATING BOOT FOR ELECTROSURGICAL FORCEPS” filed on Sep. 30, 2005, now U.S. patent application Ser. No. 11/529,798 published as U.S. Patent Application Publication No. US2007/0078458 A1, the entire contents of which is incorporated by reference herein. This application cross-references U.S. Provisional Patent Application Ser. No. 60/722,186 by Paul Guerra, entitled “METHOD FOR MANUFACTURING AN END EFFECTOR ASSEMBLY,” filed on Sep. 30, 2005, now U.S. patent application Ser. No. 11/529,414 published as U.S. Patent Application Publication No. US2007/0074807 A1 and U.S. Provisional Patent Application Ser. No. 60/722,359 by Kristin Johnson et al, entitled “FLEXIBLE ENDOSCOPIC CATHETER WITH LIGASURE,” [[both]] filed on Sep. 30, 2005, now U.S. patent application Ser. No. 11/540,779 published as U.S. Patent Application Publication No. US2007/0078559A1, the entire contents of both applications being incorporated by reference herein.
BACKGROUND1. Technical Field
The present disclosure relates to an insulated electrosurgical forceps and more particularly, the present disclosure relates to an insulating boot for use with either an endoscopic or open bipolar and/or monopolar electrosurgical forceps for sealing, cutting, and/or coagulating tissue.
2. Background of Related Art
Electrosurgical forceps utilize both mechanical clamping action and electrical energy to effect hemostasis by heating the tissue and blood vessels to coagulate, cauterize and/or seal tissue. As an alternative to open forceps for use with open surgical procedures, many modern surgeons use endoscopes and endoscopic instruments for remotely accessing organs through smaller, puncture-like incisions. As a direct result thereof, patients tend to benefit from less scarring and reduced healing time.
Endoscopic instruments are inserted into the patient through a cannula, or port, which has been made with a trocar. Typical sizes for cannulas range from three millimeters to twelve millimeters. Smaller cannulas are usually preferred, which, as can be appreciated, ultimately presents a design challenge to instrument manufacturers who must find ways to make endoscopic instruments that fit through the smaller cannulas.
Many endoscopic surgical procedures require cutting or ligating blood vessels or vascular tissue. Due to the inherent spatial considerations of the surgical cavity, surgeons often have difficulty suturing vessels or performing other traditional methods of controlling bleeding, e.g., clamping and/or tying-off transected blood vessels. By utilizing an endoscopic electrosurgical forceps, a surgeon can either cauterize, coagulate/desiccate and/or simply reduce or slow bleeding simply by controlling the intensity, frequency and duration of the electrosurgical energy applied through the jaw members to the tissue. Most small blood vessels, i.e., in the range below two millimeters in diameter, can often be closed using standard electrosurgical instruments and techniques. However, if a larger vessel is ligated, it may be necessary for the surgeon to convert the endoscopic procedure into an open-surgical procedure and thereby abandon the benefits of endoscopic surgery. Alternatively, the surgeon can seal the larger vessel or tissue.
It is thought that the process of coagulating vessels is fundamentally different than electrosurgical vessel sealing. For the purposes herein, “coagulation” is defined as a process of desiccating tissue wherein the tissue cells are ruptured and dried. “Vessel sealing” or “tissue sealing” is defined as the process of liquefying the collagen in the tissue so that it reforms into a fused mass. Coagulation of small vessels is sufficient to permanently close them, while larger vessels need to be sealed to assure permanent closure.
In order to effectively seal larger vessels (or tissue) two predominant mechanical parameters must be accurately controlled—the pressure applied to the vessel (tissue) and the gap distance between the electrodes—both of which are affected by the thickness of the sealed vessel. More particularly, accurate application of pressure is important to oppose the walls of the vessel; to reduce the tissue impedance to a low enough value that allows enough electrosurgical energy through the tissue; to overcome the forces of expansion during tissue heating; and to contribute to the end tissue thickness which is an indication of a good seal. It has been determined that a typical fused vessel wall is optimum between 0.001 and 0.006 inches (about 0.03 mm to about 0.15 mm). Below this range, the seal may shred or tear and above this range the lumens may not be properly or effectively sealed.
With respect to smaller vessels, the pressure applied to the tissue tends to become less relevant whereas the gap distance between the electrically conductive surfaces becomes more significant for effective sealing. In other words, the chances of the two electrically conductive surfaces touching during activation increases as vessels become smaller.
Many known instruments include blade members or shearing members which simply cut tissue in a mechanical and/or electromechanical manner and are relatively ineffective for vessel sealing purposes. Other instruments rely on clamping pressure alone to procure proper sealing thickness and are not designed to take into account gap tolerances and/or parallelism and flatness requirements which are parameters which, if properly controlled, can assure a consistent and effective tissue seal. For example, it is known that it is difficult to adequately control thickness of the resulting sealed tissue by controlling clamping pressure alone for either of two reasons: 1) if too much force is applied, there is a possibility that the two poles will touch and energy will not be transferred through the tissue resulting in an ineffective seal; or 2) if too low a force is applied the tissue may pre-maturely move prior to activation and sealing and/or a thicker, less reliable seal may be created.
As mentioned above, in order to properly and effectively seal larger vessels or tissue, a greater closure force between opposing jaw members is required. It is known that a large closure force between the jaws typically requires a large moment about the pivot for each jaw. This presents a design challenge because the jaw members are typically affixed with pins which are positioned to have small moment arms with respect to the pivot of each jaw member. A large force, coupled with a small moment arm, is undesirable because the large forces may shear the pins. As a result, designers must compensate for these large closure forces by either designing instruments with metal pins and/or by designing instruments which at least partially offload these closure forces to reduce the chances of mechanical failure. As can be appreciated, if metal pivot pins are employed, the metal pins must be insulated to avoid the pin acting as an alternate current path between the jaw members which may prove detrimental to effective sealing.
Increasing the closure forces between electrodes may have other undesirable effects, e.g., it may cause the opposing electrodes to come into close contact with one another which may result in a short circuit and a small closure force may cause pre-mature movement of the tissue during compression and prior to activation. As a result thereof, providing an instrument which consistently provides the appropriate closure force between opposing electrode within a preferred pressure range will enhance the chances of a successful seal. As can be appreciated, relying on a surgeon to manually provide the appropriate closure force within the appropriate range on a consistent basis would be difficult and the resultant effectiveness and quality of the seal may vary. Moreover, the overall success of creating an effective tissue seal is greatly reliant upon the user's expertise, vision, dexterity, and experience in judging the appropriate closure force to uniformly, consistently and effectively seal the vessel. In other words, the success of the seal would greatly depend upon the ultimate skill of the surgeon rather than the efficiency of the instrument.
It has been found that the pressure range for assuring a consistent and effective seal is between about 3 kg/cm2 to about 16 kg/cm2 and, preferably, within a working range of 7 kg/cm2 to 13 kg/cm2. Manufacturing an instrument which is capable of providing a closure pressure within this working range has been shown to be effective for sealing arteries, tissues and other vascular bundles.
Various force-actuating assemblies have been developed in the past for providing the appropriate closure forces to effect vessel sealing. For example, one such actuating assembly has been developed by Valleylab Inc., a division of Tyco Healthcare LP, for use with Valleylab's vessel sealing and dividing instrument commonly sold under the trademark LIGASURE ATLAS®. This assembly includes a four-bar mechanical linkage, a spring and a drive assembly which cooperate to consistently provide and maintain tissue pressures within the above working ranges. The LIGASURE ATLAS® is presently designed to fit through a 10 mm cannula and includes a bi-lateral jaw closure mechanism which is activated by a foot switch. A trigger assembly extends a knife distally to separate the tissue along the tissue seal. A rotating mechanism is associated with distal end of the handle to allow a surgeon to selectively rotate the jaw members to facilitate grasping tissue. U.S. Pat. Nos. 7,101,371 and 7,083,618 and PCT Application Ser. Nos. PCT/US01/01890 PCT/US02/01890, now WO 2002/080799, and PCT/US01/11340, now WO 2002/080795, describe in detail the operating features of the LIGASURE ATLAS® and various methods relating thereto. Copending U.S. application Ser. No. 10/970,307, now U.S. Pat. No. 7,232,440, relates to another version of an endoscopic forceps sold under the trademark LIGASURE V® by Valleylab, Inc., a division of Tyco Healthcare, LP. In addition, commonly owned, U.S. patent application Ser. No. 10/873,860, filed on Jun. 22, 2004 and entitled “Open Vessel Sealing Instrument with Cutting Mechanism and Distal Lockout”, now U.S. Pat. No. 7,252,667, and incorporated by reference in its entirety herein discloses an open forceps which is configured to seal and cut tissue which can be configured to include one or more of the presently disclosed embodiments described herein. The entire contents of all of these applications are hereby incorporated by reference herein.
For example, the commonly owned U.S. patent application Ser. No. 10/970,307 filed on Oct. 21, 2004 and entitled “Bipolar Forceps Having Monopolar Extension”, now U.S. Pat. No. 7,232,440, discloses an electrosurgical forceps for coagulating, sealing, and/or cutting tissue having a selectively energizable and/or extendable monopolar extension for enhanced electrosurgical effect. The instrument includes a monopolar element which may be selectively extended and selectively activated to treat tissue. Various different designs are envisioned which allow a user to selectively energize tissue in a bipolar or monopolar mode to seal or coagulate tissue depending upon a particular purpose. Some of the various designs include: (1) a selectively extendable and energizable knife design which acts as a monopolar element; (2) a bottom jaw which is electrically and selectively configured to act as a monopolar element; (3) tapered jaw members having distal ends which are selectively energized with a single electrical potential to treat tissue in a monopolar fashion; and (4) other configurations of the end effector assembly and/or bottom or second jaw member which are configured to suit a particular purpose or to achieve a desired surgical result.
However, a general issue with existing electrosurgical forceps is that the jaw members rotate about a common pivot at the distal end of a metal or otherwise conductive shaft such that there is potential for both the jaws, a portion of the shaft, and the related mechanism components to conduct electrosurgical energy (either monopolar or as part of a bipolar path) to the patient tissue. Existing electrosurgical instruments with jaws either cover the pivot elements with an inflexible shrink-tube or do not cover the pivot elements and connection areas and leave these portions exposed.
SUMMARYIt would be desirous to provide electrosurgical instruments with a flexible insulating boot that both permits pivoting and other associated movements of the jaw members and also reduces the potential for stray or miscellaneous currents affecting surrounding tissue.
The present disclosure relates to an electrosurgical forceps having a shaft with jaw members at a distal end thereof. The jaw members are movable about a pivot by actuation of a drive assembly that moves the jaw members from a first position wherein the jaw members are disposed in spaced relation relative to one another to a second position wherein the jaw members are closer to one another for grasping and treating tissue. The forceps also includes a movable handle that actuates the drive assembly to move the jaw members relative to one another.
At least one jaw member is adapted to connect to a source of electrical energy such that at least one of the jaw members is capable of conducting energy to tissue held therebetween to treat tissue. A flexible insulating boot is disposed on at least a portion of an exterior surface of at least one jaw member. The insulating boot is configured and made from a material that insulates tissue from various exposed areas of the shaft and the jaw members.
In one particularly useful embodiment, one end of the insulating boot is disposed on at least a portion of an exterior surface of the shaft and another end of the insulating boot is disposed on at least a portion of an exterior surface of at least one jaw member proximate the pivot such that movement of the jaw members is substantially unimpeded. In another embodiment according to the present disclosure, the insulating boot is made of at least one of a viscoelastic, elastomeric, and flexible material suitable for use with a sterilization process that does not substantially impair structural integrity of the boot. In particular, the sterilization process may include ethylene oxide.
The jaw members (or jaw member) may also include a series of stop members disposed thereon for regulating distance between the jaw members such that a gap is created between the jaw members during the sealing process.
The forceps may also include a knife that is selectively deployable to cut tissue disposed between the jaw members.
In one embodiment, the jaw members are configured to treat tissue in a monopolar fashion, while in another embodiment, the jaw members are configured to treat tissue in a bipolar fashion.
In one embodiment of the present disclosure, the present disclosure is directed to an electrosurgical forceps for sealing tissue having a pair of first and second shaft members each with a jaw member disposed at a distal end thereof. The jaw members are movable about a pivot from a first position in spaced relation relative to one another to at least one subsequent position wherein the jaw members cooperate to grasp tissue therebetween. At least one of the jaw members includes an electrically conductive sealing plate adapted to communicate electrosurgical energy to tissue held therebetween and a flexible insulating boot disposed on at least a portion of an exterior surface of at least one jaw member.
In yet another useful embodiment, the present disclosure relates to an electrosurgical forceps having a housing with a shaft affixed thereto. The shaft includes first and second jaw members attached to a distal end thereof. The forceps includes an actuator for moving jaw members relative to one another from a first position wherein the jaw members are disposed in spaced relation relative to one another to a second position wherein the jaw members cooperate to grasp tissue therebetween. Each jaw member is adapted to connect to a source of electrosurgical energy such that the jaw members are selectively capable of conducting energy to tissue held therebetween to treat tissue.
The forceps also includes a knife that is selectively moveable within a knife channel defined within at least one of the jaw members to cut tissue disposed therebetween. A monopolar element is housed within at least one jaw member and is selectively movable from a first proximal position within the jaw members to a second distal position within the jaw member(s). The monopolar element may be connected to the source of electrosurgical energy and may be selectively activatable independently of the jaw members. The forceps includes a flexible insulating boot disposed on at least a portion of at least one jaw member.
Various embodiments of the subject instrument are described herein with reference to the drawings wherein:
Referring initially to
Forceps 10 also includes an electrosurgical cable 310 that connects the forceps 10 to a source of electrosurgical energy, e.g., a generator (not shown). The generator includes various safety and performance features including isolated output, independent activation of accessories, and Instant Response™ technology (a proprietary technology of Valleylab, Inc., a division of Tyco Healthcare, LP) that provides an advanced feedback system to sense changes in tissue many times per second and adjust voltage and current to maintain appropriate power. Cable 310 is internally divided into cable lead 310a, 310b and 310c that each transmit electrosurgical energy through their respective feed paths through the forceps 10 to the end effector assembly 100. (See
Handle assembly 30 includes a fixed handle 50 and a movable handle 40. Fixed handle 50 is integrally associated with housing 20 and handle 40 is movable relative to fixed handle 50. Rotating assembly 80 is integrally associated with the housing 20 and is rotatable approximately 180 degrees in either direction about a longitudinal axis “A” (See
As best seen in
As mentioned above, end effector assembly 100 is attached at the distal end 14 of shaft 12 and includes a pair of opposing jaw members 110 and 120. Movable handle 40 of handle assembly 30 is ultimately connected to the drive assembly 150 that, together, mechanically cooperate to impart movement of the jaw members 110 and 120 from an open position wherein the jaw members 110 and 120 are disposed in spaced relation relative to one another, to a clamping or closed position wherein the jaw members 110 and 120 cooperate to grasp tissue therebetween. All of these components and features are best explained in detail in the above-identified commonly owned U.S. application Ser. No. 10/460,926, now U.S. Pat. No. 7,156,846.
Turning now to the more detailed features of the present disclosure as described with respect to
Each upper flange 45a and 45b also includes a force-actuating flange or drive flange 47a and 47b, respectively, each of which is aligned along longitudinal axis “A” and which abut the drive assembly 150 such that pivotal movement of the handle 40 forces actuating flange against the drive assembly 150 that, in turn, closes the jaw members 110 and 120.
Movable handle 40 is designed to provide a distinct mechanical advantage over conventional handle assemblies due to the unique position of the pivot pins 29a and 29b (i.e., pivot point) relative to the longitudinal axis “A” of the shaft 12 and the disposition of the driving flange 47 along longitudinal axis “A”. In other words, by positioning the pivot pins 29a and 29b above the driving flange 47, the user gains lever-like mechanical advantage to actuate the jaw members 110 and 120 enabling the user to close the jaw members 110 and 120 with lesser force while still generating the required forces necessary to effect a proper and effective tissue seal.
In addition, the unilateral closure design of the end effector assembly 100 will also increase mechanical advantage. More particularly, as best shown in
As best illustrated in
As best illustrated in
As best shown in
Jaw member 120 is designed to be fixed to the end of a rotating tube 160 that is part of the rotating assembly 80 such that rotation of the tube 160 around axis “B” of
Fixed jaw member 120 is connected to a second electrical potential through tube 160 that is connected at its proximal end to lead 310c. More particularly, as best shown in
A tubular insulating boot 500 is included that is configured to mount over the pivot 103 and at least a portion of the end effector assembly 100. The tubular insulating boot 500 is flexible to permit opening and closing of the jaw members 110 and 120 about pivot 103. The flexible insulating boot 500 is made typically of any type of visco-elastic, elastomeric or flexible material that is biocompatible. Such a visco-elastic, elastomeric or flexible material is preferably durable and is configured to minimally impede movement of the jaw members 110 and 120 from the open to the closed positions. The particularly selected material of the flexible insulating boot 500 has a dielectric strength sufficient to withstand the voltages encountered during electrosurgery, and is suitable for use with a sterilization process that does not substantially impair structural integrity of the boot, such as an ethylene oxide process that does not melt or otherwise impair the structural integrity of the insulating boot 500. The insulating boot 500 is dimensioned to further reduce stray electrical potentials so as to reduce the possibility of subjecting the patient tissue to unintentional electrosurgical RF energy.
As best shown in
Again, as previously mentioned, since one end of the tubular insulating boot 500 is disposed on at least a portion of the shaft 12 while the other end of the tubular insulating boot 500 is disposed on at least a portion of the exterior surfaces of fixed jaw member 120 and pivoting jaw member 110, operability of the pivoting jaw member 110 and the fixed jaw member 120, either with respect to reciprocation of the reciprocating sleeve 60 or rotation of the rotating tube 160, is not significantly limited by or impeded by the flexible insulating boot 500. The tubular insulating boot 500 does not interface with the shaft 12 but rather remains in a substantially stationary position axially with respect to reciprocating sleeve 60 and the jaw members 110 and 120.
As best shown in
The operating features and relative movements of the internal working components of the forceps 10 and the trigger assembly 70 are shown by phantom representation in the various figures and explained in more detail with respect to the aforementioned U.S. patent application Ser. No. 10/460,926, now U.S. Pat. No. 7,156,846, and also in U.S. patent application Ser. No. 10/970,307, now U.S. Pat. No. 7,232,440, the contents of both of which are incorporated herein in their entirety.
As can be appreciated, as illustrated in
As best shown in
As best shown in the exploded view of
The jaw members 110 and 120 are electrically isolated from one another such that electrosurgical energy can be effectively transferred through the tissue to form seal 450, as shown in
In addition, by virtue of the flexible insulating boot 500 of the present disclosure, desired motion of and force between the jaw members 110 and 120 is maintained and substantially unimpeded while at the same time insulating boot 500 further insulates the patient tissue from possible stray energy from the exterior surfaces of the jaw members 110 and 120 and the associated elements, e.g., pivot 103 (See
As mentioned above with respect to
As best shown in
Each shaft 1012a and 1012b includes a handle 1015 and 1017, respectively, disposed at the proximal end 1014a and 1014b thereof that each define a finger hole 1015a and 1017b, respectively, therethrough for receiving a finger of the user. Finger holes 1015a and 1017b facilitate movement of the shafts 1012a and 1012b relative to one another that, in turn, pivot the jaw members 1110 and 1120 from an open position wherein the jaw members 1110 and 1120 are disposed in spaced relation relative to one another to a clamping or closed position wherein the jaw members 1110 and 1120 cooperate to grasp tissue or vessels therebetween.
Shaft 1012a is secured about pivot 1065 and positioned within a cut-out or relief 1021 such that shaft 1012a is movable relative to shaft 1012b. More particularly, when the user moves the shaft 1012a relative to shaft 1012b to close or open the jaw members 1110 and 1120, the distal portion of shaft 1012a moves within cutout 1021. One of the shafts, e.g., 1012b, includes a proximal shaft connector 1077 that is designed to connect the forceps 1000 to a source of electrosurgical energy such as an electrosurgical generator (not shown).
The distal end of the cable 1070 connects to a handswitch 1050 to permit the user to selectively apply electrosurgical energy as needed to seal tissue or vessels grasped between jaw members 1110 and 1120 (See
As best shown in
In one embodiment, the length “L” of the insulating boot 1500 is such that the proximal end 1502 of the insulating boot 1500 is disposed on the outer edges 1210 and 1220 so that the pivot pin 1065 remains exposed. In an alternate embodiment shown in phantom in
In either embodiment, the insulating boot 1500 limits stray current dissipation to surrounding tissue upon activation and continued use of the forceps 1000. As mentioned above, the insulating boot 1500 is made from any type of visco-elastic, elastomeric or flexible material that is biocompatible and that is configured to minimally impede movement of the jaw members 1110 and 1120 from the open to closed positions. Moreover, in one embodiment, the material is selected to have a dielectric strength sufficient to withstand the voltages encountered during electrosurgery, and is suitable for use with a sterilization process that does not substantially impair structural integrity of the boot, such as an ethylene oxide process. More particularly, the insulating boot 1500 further reduces stray electrical potential so as to reduce the possibility of subjecting the patient tissue to unintentional electrosurgical RF energy.
As best shown in
Details relating to the jaw members 1110 and 1120 and various elements associated therewith are discussed in commonly-owned U.S. application Ser. No. 10/962,116, filed on Oct. 8, 2004, and entitled “Open Vessel Sealing Instrument with Hourglass Cutting Mechanism and Over-Ratchet Safety”, published as U.S. patent Application Publication No. US 2005/0154387 A1, now U.S. Pat. No. 7,811,283, the entire contents of which are hereby incorporated by reference herein.
As best illustrated in
As best seen in
In operation, the surgeon utilizes the two opposing handle members 1015 and 1017 to grasp tissue between jaw members 1110 and 1120. The surgeon then activates the hand-switch 1050 to provide electrosurgical energy to each jaw member 1110 and 1120 to communicate energy through the tissue held therebetween to effect a tissue seal. Once sealed, the surgeon activates the actuating mechanism to advance the cutting blade through the tissue to sever the tissue 400 along the tissue seal.
The jaw members 1110 and 1120 are electrically isolated from one another such that electrosurgical energy can be effectively transferred through the tissue to form a tissue seal. Each jaw member, e.g., 1110, includes a uniquely-designed electrosurgical cable path disposed therethrough that transmits electrosurgical energy to the electrically conductive sealing surface 1112. The two electrical potentials are isolated from one another by virtue of the insulative sheathing surrounding each cable lead 1071a, 1071b and 1071c. In addition, to further enhance safety, as noted previously, insulating boot 1500 may be positioned about at least a portion of the end effector assembly 1000, and optionally the pivot 1065, to limit stray current dissipation to surrounding tissue upon activation and continued use of the forceps 1010. As mentioned above, the insulating boot 1500 is made from any type of visco-elastic, elastomeric or flexible material that is biocompatible and that is configured to minimally impede movement of the jaw members 1110 and 1120 from the open to closed positions.
The presently disclosed insulating boot may also be utilized with a forceps 2010 designed for both bipolar electrosurgical treatment of tissue (either by vessel sealing as described above or coagulation or cauterization with other similar instruments) and monopolar treatment of tissue. For example,
More particularly,
The monopolar element 2154 may be connected to a reciprocating rod 2065 that extends through an elongated notch 2013 in the outer periphery of the shaft 2012 as best seen in
As best shown in
As best shown in
Details relating to this particular embodiment of a monopolar forceps is disclosed in aforementioned commonly-owned U.S. application Ser. No. 10/970,307, the entire contents of which are hereby incorporated by reference herein.
In a similar manner as discussed previously with respect to
Those skilled in the art recognize that the material properties of the insulating boot 2500 and operability considerations from disposition of the insulating boot 2500 are in all respects either similar to or in some cases identical to those described in the preceding discussion with respect to
As illustrated in
Upon release of a trigger such as trigger 2070 (See
Again, in a similar manner as discussed previously with respect to
Again, those skilled in the art recognize that the material properties of the insulating boot 2500 and operability considerations from disposition of the insulating boot 2500 are similar to those described in the preceding discussions.
As shown in
A control switch 2505 is preferably included that regulates the transition between bipolar mode and monopolar mode. Control switch 2505 is connected to generator 2300 via cables 2360 and 2370. A series of leads 2510, 2520 and 2530 are connected to the jaw members 2110″, 2120″ and the return electrode 2550, respectively. As best shown in the table depicted in
In a monopolar mode, jaw member 2110″ and 2120″ are both energized with the same electrical potential and the return pad 2550 is energized with a second electrical potential forcing the electrical current to travel from the jaw members 2110″ and 2120″, through the tissue and to the return electrode 2550. This enables the jaw members 2110″ and 2120″ to treat tissue in a monopolar fashion that, as mentioned above, advantageously treats a vascular tissue structures and/or allows quick dissection of narrow tissue planes. As can be appreciated, all of the leads 2510, 2520 and 2530 may be deactivated when the forceps 2010″ is turned off or idle.
Yet again, as discussed previously with respect to
An insulating layer 2540 is disposed between the skeleton 2532 and the tissue sealing surface 2522 to isolate the electrically conductive sealing surface 2522′ from hem 2535 during activation. The stamped tissue sealing surface 2522′ is formed of a double layer of sheet metal material separated by a slot or knife channel 2515 that allows selective reciprocation of a knife, such as knife 2185 disclosed in
It is envisioned that the tissue sealing surface 2522 may be curved or straight depending upon a particular surgical purpose. The jaw housing 2524 may be overmolded to encapsulate the hem 2535 of the skeleton 2532 and sealing plate 2522 that serves to insulate surrounding tissue from the conductive surfaces of the sealing plate 2522 as well as to give the jaw member 2520′ a desired shape at assembly.
In a similar manner as discussed previously with respect to
Details relating to the forceps 2010′, which is manufactured such that the distal end 2522a′ of the tissue sealing surface 2522 extends beyond the bottom jaw housing 2524, are disclosed in previously mentioned commonly owned U.S. patent application Ser. No. 10/970,307 that is incorporated by reference herein.
It is envisioned that the insulating material 2634 will isolate the monopolar portion 2632 during electrical activation of tissue surface 2622 and isolate the tissue surface 2622 during electrical activation of monopolar element 2632. As can be appreciated, the two different electrically conductive elements 2622 and 2632 are connected to electrical generator 2300 by different electrical connections and may be selectively activated by the user. Various switches or electrical control elements or the like (not shown) may be employed to accomplish this purpose.
Still yet again, to further enhance safety, as discussed previously with respect to
Bottom or second jaw member 2620 includes both an electrically conductive sealing surface 2622 for sealing purposes as well as an electrically conductive surface 2632 that is designed for monopolar activation are disclosed in previously mentioned commonly owned U.S. patent application Ser. No. 10/970,307 which is incorporated by reference herein.
As best shown in
As can be appreciated various switching algorithms may be employed to activate both the bipolar mode for vessel sealing and the monopolar mode for additional tissue treatments (e.g., dissection). Also, a safety or lockout may be employed either electrically, mechanically or electromechanically to “lock out” one electrical mode during activation of the other electrical mode. In addition, a toggle switch (or the like) may be employed to activate one mode at a time for safety reasons. The monopolar element 2754 may also include a safety (either mechanical, electrical or electro-mechanical—not shown) that only allows electrical activation of the monopolar element 2754 when the monopolar element 2754 is extended from the distal end of jaw member 2720. Insulating boot 2500 is included that is configured to mount over the pivot 2103 and at least a portion of the end effector assembly 2100.
Tissue sealing surface 2822 also includes a sealing surface extension 2822b that extends through a distal end 824a of the overmolded jaw housing 2824. As can be appreciated, sealing surface extension 2822b is designed for monopolar tissue dissection, enterotomies or other surgical functions and may be separately electrically energized by the user by a hand switch, footswitch or at the generator 2300 in a similar manner as described above (See
From the foregoing and with reference to the various figure drawings, those skilled in the art will appreciate that certain modifications can also be made to the present disclosure without departing from the scope of the same. For example and although the general operating components and intercooperating relationships among these components have been generally described with respect to a vessel sealing forceps, other instruments may also be utilized that can be configured to allow a surgeon to selectively treat tissue in both a bipolar and monopolar fashion. Such instruments include, for example, bipolar grasping and coagulating instruments, cauterizing instruments, bipolar scissors, etc.
Furthermore, those skilled in the art recognize that while the insulating boots 500, 1500, or 2500 are disclosed as having a generally tubular configuration, the cross-section of the generally tubular configuration can assume substantially any shape such as, but not limited to, an oval, a circle, a square, or a rectangle, and also include irregular shapes necessary to cover at least a portion of the jaw members and the associated elements such as the pivot pins and jaw protrusions, etc.
In addition, while several of the disclosed embodiments show endoscopic forceps that are designed to close in a unilateral fashion, forceps that close in a bilateral fashion may also be utilized with the insulating boot described herein. The presently disclosed insulating boot may be configured to fit atop or encapsulate pivot or hinge members of other known devices such as jawed monopolar devices, standard laparoscopic “Maryland” dissectors and/or bipolar scissors.
While several embodiments of the disclosure have been shown in the drawings, it is not intended that the disclosure be limited thereto, as it is intended that the disclosure be as broad in scope as the art will allow and that the specification be read likewise. Therefore, the above description should not be construed as limiting, but merely as exemplifications of preferred embodiments. Those skilled in the art will envision other modifications within the scope and spirit of the claims appended hereto.
Claims
1. An electrosurgical forceps, comprising:
- a shaft having a pair of jaw members at a distal end thereof, the jaw members being movable about a pivot from a first position wherein the jaw members are disposed in spaced relation relative to one another to a second position wherein the jaw members are closer to one another for grasping tissue, the shaft defining a longitudinal axis therethrough;
- a movable handle that actuates a drive assembly to move the jaw members relative to one another;
- at least one of the jaw members including a tissue-engaging surface adapted to connect to a source of electrical energy such that the at least one jaw member is capable of conducting energy to tissue held therebetween; and
- a flexible insulating boot mounted over the pivot, the flexible insulating boot having a proximal portion disposed on a portion of the shaft and a distal portion disposed on a portion of an exterior surface of the pair of jaw members proximal to the tissue-engaging surface of the at least one jaw member, the proximal portion and the distal portion of the flexible insulating boot disposed such that the flexible insulating boot remains in a substantially stationary position relative to the longitudinal axis and with respect to a reciprocating sleeve of the drive assembly and the jaw members when the drive assembly mechanically advances the reciprocating sleeve to apply a predetermined closure force between the jaw members.
2. An electrosurgical forceps according to claim 1, wherein at least one of the jaw members includes a series of stop members disposed thereon for regulating distance between the jaw members such that a gap is created between the jaw members during the sealing process.
3. An electrosurgical forceps according to claim 1, wherein the forceps includes a knife that is selectively deployable to cut tissue disposed between the jaw members.
4. An electrosurgical forceps according to claim 1, wherein the insulating boot is made of at least one of a viscoelastic, elastomeric, and flexible material suitable for use with a sterilization process that does not substantially impair structural integrity of the boot.
5. An electrosurgical forceps according to claim 4, wherein the sterilization process includes ethylene oxide.
6. An electrosurgical forceps according to claim 1, wherein the flexible insulating boot has a generally tubular configuration.
7. An electrosurgical forceps according to claim 1, wherein two jaw members are adapted to connect to the source of electrical energy such that the jaw members are capable of treating tissue in a bipolar manner upon selective activation of the forceps.
8. An electrosurgical forceps according to claim 1, wherein at least one jaw member is adapted to connect to the source of electrical energy such that the at least one jaw members is capable of treating tissue in a monopolar manner upon selective actuation of the forceps.
9. An electrosurgical forceps, comprising:
- a shaft having a pair of jaw members at a distal end thereof, the jaw members being movable about a pivot from a first position wherein the jaw members are disposed in spaced relation relative to one another to a second position wherein the jaw members are closer to one another for grasping tissue, the shaft defining a longitudinal axis therethrough;
- a drive assembly that includes a reciprocating sleeve and a movable handle that actuates the reciprocating sleeve and the drive assembly to move the jaw members relative to one another;
- at least one of the jaw members including a tissue-engaging surface adapted to connect to a source of electrical energy such that the at least one jaw member is capable of conducting energy to tissue held therebetween; and
- a flexible insulating boot defining an internal surface, the flexible insulating boot mounted over the pivot such that at least a portion of the internal surface is in direct contact with the pivot, the flexible insulating boot having a proximal portion disposed on a portion of the shaft and a distal portion disposed on a portion of an exterior surface of the pair of jaw members proximal to the tissue-engaging surface of the at least one jaw member such that at least a portion of the internal surface defined by the flexible insulating boot is in direct contact with the portion of the exterior surface of the pair of jaw members proximal to the tissue-engaging surface of the at least one jaw member, the proximal portion and the distal portion of the flexible insulating boot disposed such that the flexible insulating boot remains in a substantially stationary position relative to the longitudinal axis and with respect to the reciprocating sleeve and the jaw members when the drive assembly mechanically advances the reciprocating sleeve of the drive assembly to apply a predetermined closure force between the jaw members.
10. An electrosurgical forceps according to claim 9, wherein at least one of the jaw members includes a series of stop members disposed thereon for regulating distance between the jaw members such that a gap is created between the jaw members during the sealing process.
11. An electrosurgical forceps according to claim 9, wherein the forceps includes a knife that is selectively deployable to cut tissue disposed between the jaw members.
12. An electrosurgical forceps according to claim 9, wherein the insulating boot is made of at least one of a viscoelastic, elastomeric, and flexible material suitable for use with a sterilization process that does not substantially impair structural integrity of the boot.
13. An electrosurgical forceps according to claim 12, wherein the sterilization process includes ethylene oxide.
14. An electrosurgical forceps according to claim 9, wherein the flexible insulating boot has a generally tubular configuration.
15. An electrosurgical forceps according to claim 9, wherein two jaw members are adapted to connect to the source of electrical energy such that the jaw members are capable of treating tissue in a bipolar manner upon selective activation of the forceps.
16. An electrosurgical forceps according to claim 9, wherein at least one jaw member is adapted to connect to the source of electrical energy such that the at least one jaw members is capable of treating tissue in a monopolar manner upon selective actuation of the forceps.
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Type: Grant
Filed: Dec 7, 2012
Date of Patent: Apr 8, 2014
Assignee: Covidien AG
Inventors: Patrick L. Dumbauld (Lyons, CO), Paul Guerra (Los Gatos, CA), Roger F. Smith (Boulder, CO), Scott DePierro (Madison, CT)
Primary Examiner: Linda Dvorak
Assistant Examiner: Amanda Scott
Application Number: 13/708,335
International Classification: A61B 18/18 (20060101);