|Publication number||US20100100095 A1|
|Application number||US 12/643,603|
|Publication date||Apr 22, 2010|
|Filing date||Dec 21, 2009|
|Priority date||Sep 22, 2000|
|Also published as||DE60138396D1, EP1318758A1, EP1318758B1, EP2011446A2, EP2011446A3, EP2011446B1, US6558385, US7645277, US7651494, US20030114850, US20060100619, WO2002024089A1|
|Publication number||12643603, 643603, US 2010/0100095 A1, US 2010/100095 A1, US 20100100095 A1, US 20100100095A1, US 2010100095 A1, US 2010100095A1, US-A1-20100100095, US-A1-2010100095, US2010/0100095A1, US2010/100095A1, US20100100095 A1, US20100100095A1, US2010100095 A1, US2010100095A1|
|Inventors||Michael E. McClurken, Robert Luzzi|
|Original Assignee||Salient Surgical Technologies, Inc.|
|Export Citation||BiBTeX, EndNote, RefMan|
|Referenced by (3), Classifications (21), Legal Events (2)|
|External Links: USPTO, USPTO Assignment, Espacenet|
This application is a continuation of U.S. application Ser. No. 11/316,798, filed Dec. 22, 2005, now pending, which is a continuation of U.S. application Ser. No. 10/354,643, filed Jan. 29, 2003, now pending, which is a continuation of U.S. application Ser. No. 09/668,403, filed Sep. 22, 2000, now U.S. Pat. No. 6,558,385. The entire disclosure of each of these patent applications is herein incorporated by reference to the extent it is consistent.
This invention relates generally to the field of devices for use in surgery upon tissues of the body. More particularly, the invention relates to an electrosurgical device and methods of treatment of body tissues.
Electrosurgical devices use electrical energy, most commonly radiofrequency (RF) energy, to cut tissue and/or cauterize blood vessels. During use, a voltage gradient is created at the tip of the device, thereby inducing current flow and related heat generation in the tissue. With sufficiently high levels of electrical energy, the heat generated is sufficient to cut the tissue and, advantageously, to cauterize severed blood vessels.
Current electrosurgical devices can cause the temperature of tissue being treated to rise significantly higher than 100° C., resulting in tissue desiccation, tissue sticking to the electrodes, tissue perforation, char formation and smoke generation. Peak tissue temperatures as a result of RF treatment of target tissue can be as high as 350° C., and such high temperatures may be transmitted to adjacent tissue via thermal diffusion. Undesirable results of such transmission to adjacent tissue include unintended thermal damage to the tissue.
One limitation of current electrosurgical devices arises from size constraints and dimensions. It is difficult to reach or gain access to some tissue and vessels due to anatomy and size constraints. Electrosurgical devices often have movable hinged scissors-like jaws at their tip that must open widely to be placed around the target tissue to be treated. Hinged jaws reduce visibility of the tip and often limit grasping capability of vessels due to force constraints. Further, devices currently used also often have long rigid shafts that cannot bend to maneuver around anatomical “tight” spots.
Laparoscopic or minimally-invasive surgery often involves multiple instrument passes through a trocar to achieve the desired tissue effect. Separate instruments are often required for coagulation and for cutting. Separate instruments may also be required to achieve surface hemostasis, such as when there is bleeding from the surface of an organ such as the liver. Multiple instrument passes are undesirable because they (1) waste valuable operating room time, (2) sometimes make it difficult to precisely relocate the target treatment site, (3) increase the risk of infection, and (4) increase the cost by increasing the number of different surgical instruments that are needed to complete the surgical procedure.
Accordingly, there is a need for a surgical device that reduces undesirable effects such as tissue desiccation and resulting tissue damage, char formation, smoke generation, and risk of infection, while at the same time providing improved accessibility to tissues and efficiency.
The invention provides an improved electrosurgical device for coagulating and cutting tissues of the body, utilizing the simultaneous infusion of a conductive solution and application of RF energy. This is accomplished with a device that includes a first electrode positioned on a first arm, and a second electrode positioned on a second arm, wherein at least one of the first arm or the second arm is translationally movable, and at least one of the first electrode or the second electrode is adapted to be coupled to a source of radiofrequency energy. The first arm and the second arm are coaxially arranged. In a preferred embodiment, the device comprises a housing having a proximal and a distal end; a tubular member having a proximal and a distal end, the tubular member extending from the distal end of the housing; a first, translationally movable arm extending from the distal end of the tubular member, the first arm including a first electrode; a second arm extending from the distal end of the tubular member, the second arm including a second electrode and being disposed coaxially with the first arm; at least one solution infusion opening on each electrode; and a solution delivery channel for delivery of a conductive solution to the solution infusion openings, wherein at least one of the first electrode or the second electrode is adapted to be coupled to a source of RF energy.
In a preferred embodiment, the first arm and second arm include at least one groove that surrounds the at least one solution infusion opening. Preferably, the groove(s) include spaced exit slots to allow conductive solution to exit the groove during use (e.g., when pressure is applied to tissues). The grooved arm serves to isolate the metal electrode from direct contact with bodily tissues being treated. Additionally, the grooved configuration provides constant spacing between the electrode and tissue to be treated. Further, the groove assists in preventing tissue pressure against the solution infusion openings during squeezing of the arms of the device, which could inhibit or reduce the flow of electrically conductive fluid locally.
Preferably, the device further comprises a translationally movable cutting mechanism to transect tissue after it has been coagulated. The device can also be used to achieve surface hemostasis with no special adjustments or removal of the instrument from the patient.
In a preferred embodiment, the device further includes a locking mechanism, to selectively lock one or both of the arms of the device in a desired position.
The invention also provides a corresponding method for treating tissues of the body, including, for example, blood vessels. The invention is useful for ligating and dividing a dorsal vein or other blood vessels that are located in deep cavities of the body, as well as for procedures involving polyp removal and laparoscopic tubal ligations.
The invention provides a combination of advantages. For example, the device provides conductive solution, such as saline, at the electrode-tissue interface to limit the peak tissue temperature, preferably to 100° C. or less. The provision of saline at the interface prevents tissue desiccation and the various effects of desiccation, such as tissue sticking to the electrodes, perforation of adjacent organs or tissue structures, char formation on electrodes and adjacent tissue, and smoke formation. The saline at the interface preferably maintains peak tissue temperature at or below 100° C. by (1) providing coupling of the electrode to the tissue with a wetted contact area that is much larger than that of a dry electrode, thus reducing current density and local RF heating near the electrode-tissue interface, (2) providing a convective cooling effect, such that the flowing liquid saline is heated by the warmer surface of RF-heated tissue, and (3) providing an evaporative cooling effect, such that excess RF power that cannot be conducted or convected away from the target tissue will be used to boil some fraction of the saline provided to the treatment surface.
The invention also provides an instrument that has a lower profile than standard coagulating forceps with hinged jaws. In a preferred embodiment, the device includes a tubular member that has an articulating or bending feature to enable the distal end effector region of the device, including first and second arms, to pass around anatomical features. According to the invention, the device is capable of being made with an outside diameter that is 25 mm or less.
Preferably, the device is capable of being made with an outside diameter that is 15 mm or less, more preferably 5 mm or less. As used herein, the outside diameter is the maximum size that the tubular member or first and second arms achieve as a result of device operation.
The invention further provides a multi-purpose instrument that can be used to provide both coagulation and cutting of tissue without having to be removed from the patient's body. In one embodiment, the instrument is fabricated so that it is capable of sealing and cutting a vessel, as well as causing surface hemostasis on tissue such as bleeding liver.
The invention provides a medical device that comprises a first electrode and a second electrode, wherein the electrodes are disposed coaxially to each other, and at least one of the electrodes is translationally movable. Preferably, the first electrode is provided on a first arm, and the second electrode is provided on a second arm of the device. According to the invention, the device comprises at least one translationally movable arm that can be selectively movable to a fixed position. Preferably, the device includes a locking mechanism, to allow the operator to move at least one arm of the device to a desired position and lock the arm in that position. Each electrode is provided with conductive solution. In a preferred embodiment, the electrodes include at least one groove to assist in delivery of the conductive solution to tissue.
In a preferred embodiment, the invention provides a medical device comprising a housing having a proximal and a distal end; a tubular member having a proximal and a distal end, the tubular member extending from the distal end of the housing; a first, translationally movable arm extending from the distal end of the tubular member, the first arm including a first electrode; a second arm extending from the distal end of the tubular member, the second arm including a second electrode and being disposed coaxially with the first arm; at least one solution infusion opening on each electrode; and a solution delivery channel for delivery of solution to the solution infusion openings. The device is configured such at least one of the first and second arms is adapted to be coupled to a source of radiofrequency energy. The invention can be used to treat tissues of the body, including blood vessels and surfaces of organs, such as the liver. Although the invention will be described herein in relation to these mentioned applications, it is understood that the device has other applications as well, and these are considered within the scope of the invention.
In the present description, elements in common between the embodiments of the figures are numbered identically, and such elements need not be separately discussed.
One preferred embodiment of the device is illustrated in
Attached to the distal portion of the housing is the tubular member 6. The tubular member 6 includes a lumen through which the actuation rods for the arms and cutting mechanism, the solution delivery channel, and the conductors pass. Although the dimensions of the tubular member 6 can be adapted for a desired purpose, the tubular member is preferably long (approximately 10 to approximately 50 cm, preferably approximately 20 cm to approximately 40 cm, more preferably approximately 25 cm to approximately 35 cm), with a diameter of about 2 mm to about 20 mm, preferably about 3 mm to about 10 mm. In one embodiment, the tubular member 6 is circular in outer shape and rigid, so as to pass easily through a trocar. Alternatively, the tubular member 6 is malleable. In yet another embodiment, the tubular member includes a deflectable tip that can be controlled by the surgeon during use, e.g., by using a wire connected to the tip that can be pulled to deflect the tip to one side.
At the most distal end of the tubular member 6 is located the end effector region E, comprising a collection of components that function together to cause the desired tissue effects to occur. This end effector region E of components consists of the cutting mechanism 7, the first arm with first electrode 8 and the second arm with second electrode 9, and is shown circled in
At the proximal portion of the housing is located the fluid supply tube 4, which contains saline or other electrically conductive solution such that the fluid flows into the solution supply channel in the housing from a source 10 such as an intravenous bag of solution hung from an intravenous (IV) pole, a pressurized elastomeric canister, a syringe pump, an intravenous volumetric infusion pump, or a peristaltic pump. Other configurations of supply sources can be provided, to achieve the purposes described herein. Also at the proximal portion of the housing are two wires 5, which are connected to a radiofrequency generator 11 such that electrical power is supplied to the device. It is contemplated that the device can include one cable that connects the radiofrequency generator to the electrodes of the device. The electrical connection can be made to be switched with a foot switch, a hand switch or both.
In one embodiment, the solution supply source 10 comprises a pressurized canister that can be adapted to be received within the housing 1, or it can be provided externally. When the solution supply source is received within the housing 1, the portion of the fluid supply tube that extends from the proximal portion of the housing can preferably be eliminated. In a further embodiment, the solution supply source can be attached to the exterior of the housing. The provision of the solution supply source as an internal component of the device, or as a component attachable to the exterior of the housing, thus preferably eliminates the “tethering” effect of a solution supply tube that runs from the proximal portion of the housing to an external supply source that is separate from the housing.
In yet another embodiment, the housing 1 may contain an electrical switch to turn the solution supply source on or off.
In still another embodiment, the housing 1 can contain a mechanical valve or flow control device, such that moving a linear or rotating piece from one position to another increases or decreases the flow resistance, and hence the flow rate of solution. Such a valve can be continuously adjustable or can be arranged to provide a series of pre-set levels of flow resistance such that the flow rate can be adjusted in fixed increments.
Additionally, the solution could be provided at a much higher “flush” rate that can be selected using an electrical switch located on the housing 1, or via a foot switch. Similarly, an additional tube can be provided to the distal region of the device to provide suction to rapidly remove accumulated blood, saline or other fluid in the operative site. In one embodiment, suction at the tip is activated by occluding a small circular opening located on the housing 1 (e.g., by virtue of the operator using a finger to cover the hole when suction is desired). With the suction always turned on, occluding the hole enables the suction “intake” to move from the hole in the housing to the tip of the device.
In the embodiment shown in
With continuing reference to
At its proximal end, gear rack 14 is operably connected to spring 16. Spring 16 is secured within housing 1 to anchor it in a desired location. Spring 16 serves to bias (e.g., push or force) cutting mechanism 7 proximally, thus returning the cutting mechanism 7 to a retracted position when trigger 3 is released, as shown in
Tubular member 6 extends from the distal end of the housing 1. Tubular member 6 is preferably made from a non-conductive polymer material such as polycarbonate, LCP (liquid crystal polymer) or other extrudable material that has moderate to high temperature resistance. Alternatively, tubular member 6 is fabricated from a metal, such as stainless steel or the like, and coated with a polymer material mentioned above. Tubular member 6 includes a lumen, though which the cutting actuation rod 15, arm actuation rod 12, solution delivery channel 4 and conductors 5 pass. The outside diameter of tubular member 6 is preferably of a size for passing through a cannula and the length is sufficient to reach an internal blood vessel to be cauterized or tissue to be treated when the tubular member is slidably inserted through the cannula and into the body of a patient, as discussed above.
Tubular member 6 may be integrally formed with the housing 1, or it may be secured to housing 1 in a suitable manner, such as with adhesives, or using such techniques as press-fit, heat-staking or ultrasonic welding.
The device includes end effector region, as shown labeled in the figures as E, which will now be described in more detail. The device of the invention provides a first, translationally movable arm and a second arm that is disposed coaxially with the first arm. As used herein, “coaxially” means the first arm and second arm are configured in a side-by-side arrangement, so that the arms extend in a parallel manner from the distal end of the tubular member 6. As discussed herein, the first arm of the device includes first electrode 8, and the second arm includes a second electrode 9. Thus, as the first arm moves in the distal direction, it approaches the second arm of the device. As each arm includes its respective electrode, movement of the first arm, with its first electrode, towards the second arm, with its second electrode, allows the user to grasp tissue to be treated with the arms and apply RF energy to treat the tissue as desired.
According to a preferred embodiment of the invention, each arm of the device is provided with its own solution delivery channel and conductor. As shown in
In addition to including a solution delivery channel, each arm of the device preferably includes a conductor for conducting RF energy from a source to the electrodes. As shown in
Solution infusion openings, in the form of a series of fine laser-drilled holes, each with a diameter of about 0.001 to about 0.010 inches, preferably about 0.005 to about 0.007 inches, allows the solution to exit the tubing. In an alternative embodiment, the solution infusion openings are formed by electrical discharge machining (EDM), chemical treatment, etching of the metal, or any suitable method for forming holes of the desired size in the tubing. Solution infusion openings are provided at sufficient intervals along the face of the electrode that will contact tissue to provide the desired effect. Preferably, the metal tubing is insulated everywhere except where it is desired that electrical energy be conducted to tissue. Preferably, at least one electrode is insulated.
The dimensions of the holes or openings and the spacing between holes, as well as the tubing inside diameter and tubing wall thickness are chosen so that the flow of saline is reasonably well distributed to all the openings. If the resistance to flow down the lumen of the tubing is small compared to the resistance to flow through an individual hole or opening, then all holes will provide sufficient flow for proper device operation. Generally, resistance to flow is inversely proportional to the fourth power of the diameter of the lumen or hole, so that doubling the size of the opening reduces resistance to flow to 1/16th of the initial value. Typically, the inside diameter of the tubing would range from 0.02 to 0.1 inches and wall thickness would range from 0.004 to 0.01 inches. However, it is understood that these measurements can be modified for a particular application as desired. In a preferred embodiment described in more detail below, solution infusion openings are included within a groove to achieve flow of conductive solution throughout the groove and across the surface of the electrode that is used to treat tissue as described herein.
In the embodiments shown in
A preferred embodiment of the device includes a large number of relatively small exit slots, approximately 0.005 inches to approximately 0.020 inches wide and from approximately 0.005 inches to approximately 0.020 inches deep.
Alternatively, the groove is fabricated from electrically non-conductive porous polymer or ceramic, preferably polymer or ceramic composed of a material that is easily wetted by the electrically conductive solution. In this embodiment, the solution exits through the sides of the groove by passing through the porous polymer or ceramic material. Wettability is usually expressed in terms of the contact angle formed between a drop of liquid lying on a solid surface, with small angles representing better wettability than large angles. Using a porous material that is more wettable reduces the amount of pressure required to initially force solution through the fine pores. Teflon™ (polytetrafluoroethylene), for instance, is not as well wetted by saline as most ceramics, and thus would be less desirable as a material from which to form the groove.
Using a porous material for the groove creates a very large number of very small exit slots, and is one method of providing solution exits that provide for uniform flow distribution while also being simple to manufacture.
It should be understood that there can be more than a single groove on an electrode. If the electrode is more rectangular or square-shaped, it may be desirable to have a system of criss-crossing or cross-hatched grooves evenly distributed over the surface of the electrode. It will be appreciated that the precise pattern of such a plurality of grooves can be modified to any desired pattern, while maintaining a gap of conductive solution between metal electrode and tissue that is not subject to compression by tissue even when the electrodes are pressed firmly together.
In a preferred embodiment shown in
Slightly prior to and during RF application, a flow rate of conductive fluid, such as physiologic saline (“normal” saline, or 0.9% NaCl solution) or lactated Ringer's™, is provided so that a total flow rate of about 0.1 to 10 cc/min is flowing from laser-drilled holes located on the proximal and distal electrodes. Preferably, a total flow rate of about 0.5 to 2 cc/min is flowing from the laser-drilled holes. Other suitable conductive solutions include hypertonic saline and Ringer's™ solution.
In use, the first, translationally movable arm containing first electrode 8 is moved in a distal direction toward the second, stationary arm containing second electrode 9.
Some of the current may flow between the two electrodes without passing through the blood vessel 24, by only passing through a film of conductive solution. This situation may occur at the edges of the blood vessel or tissue being treated. The majority of the current will preferably pass through conductive solution and then through the tissue being treated. Under some circumstances the tissue can become hot enough to have some of the conductive solution boil, as shown by the small vapor bubbles 37 in the conductive solution film. It will be understood that when the device is used as a monopolar device, the solution need not be delivered to the electrode not in use.
The solution infusion openings of the electrodes supply conductive solution to the treatment site. In an alternative embodiment, these solution infusion openings can be provided in the form of porous material such as metal. In this embodiment, the electrodes do not include discrete laser drilled solution infusion openings; rather, the electrode surface itself is porous to allow infusion of the conductive solution to the treatment site. Porous sintered metal is available in many materials (such as, for example, 316L stainless steel, titanium, Ni-Chrome, and the like) and shapes (such as cylinders, discs, plugs, and the like) from companies such as Porvair, located in Henderson, N.C.
Porous metal components can be formed by a sintered metal powder process or by injection molding a two-part combination of metal and a material that can be burned off later to form pores that connect (open cell) to each other. Such methods are known in the art. In this embodiment, conductive fluid will flow out of the electrode everywhere the pores are open. Preferably, the exterior (i.e., the portions of the components that do not comprise the portion of the device involved in tissue treatment) of such porous metal electrode components can be covered with a material that fills the pores and prevents both the flow of saline and the passing of electrical energy.
In yet another embodiment, a porous polymer is used in place of the porous metal. Although the polymer is non-conductive, the conductive solution provided will conduct the RF energy across the porous polymer wall and to the tissue to be treated. Suitable materials include high temperature open cell silicone foam and porous polycarbonates, among others. Porous ceramics would also fall into this category, since they could distribute flow, withstand high temperatures and be machinable or moldable for manufacturing purposes. Preferably, the material used transmits both fluid flow and electrical energy; thus, materials with properties midway between high-electrical conductivity metals and low electrical conductivity polymers are also contemplated, such as porous carbon-filled polymers.
Because the conductive solution, such as saline, is generally less electrically conductive than the previously described electrode metals (such as stainless steel), there are several steps that can optionally be taken to avoid dissipating an excess of electrical energy in the resistance of saline. Optionally, hypertonic saline is used instead of “normal” or physiologic saline. By adding more sodium chloride to the water it is possible to decrease the electrical resistivity of the solution by a factor of 3 to 5. Preferred hypertonic (i.e., saturated) saline includes 14.6% sodium chloride (NaCl) at 37° C. and has a resistivity of 5.9 ohm-cm. This is in contrast to “normal” saline, which is 0.90% NaCl, with resistivity of 50 ohm-cm at 37° C. (body temperature).
In yet another alternative embodiment, shown in
The frequency of the electrical energy is typically 500 kHz, and the power is typically in the range of about 10 to about 150, preferably in the range of about 30 to about 70 watts. A typical range of conductive solution flow rates is about 18-270 cc/hr. In a preferred embodiment, the total flow rate of conductive solution to both electrodes is approximately determined as 1.8 times the power in watts, with the result in cc/hr.
As discussed above, an RF source provides energy through the conductors, to the electrodes of the device. The RF source can be provided as a generator, as described. Alternatively, the source can be configured to be received within or attached to the housing of the device.
Optionally, the invention is provided with a cutting mechanism, indicated in the figures generally as 7. Preferably, the cutting mechanism 7 is independently movable from the first or second arm, or both. As described herein, the cutting mechanism serves to cut tissue preferably after application of RF energy, such that the tissue has been coagulated. Cutting tissue after coagulation reduces risk of bleeding from the tissues, especially with respect to highly vascularized tissue such as the liver, during treatment. However, it will be understood that the invention does not require tissue coagulation prior to cutting, for example in situations where bleeding is not a concern.
The cutting mechanism of the invention is preferably provided in the form of a sharp blade. However, it is apparent from the present description that the cutting mechanism need not be sharp, especially when the cutting mechanism is supplied with RF energy, as described below. In another embodiment, the cutting mechanism can be provided in the form of a wire. In yet another embodiment, the cutting mechanism is not itself sharp, but cuts tissue through the use of RF energy, as described herein.
Optionally, the device is configured to supply the cutting mechanism 7 with RF energy. Moreover, the device can be configured to allow the device to be switched between a bipolar mode in which RF energy is supplied to the first electrode, and a second bipolar mode in which RF energy is supplied to the cutting mechanism 7.
The cutting mechanism of the invention can be provided in a variety of suitable configurations to achieve cutting of the tissue.
As discussed herein, the cutting mechanism comprises an optional component of the device, to be used when the operator desires to cut a tissue or blood vessel during treatment. When the device is provided without a cutting mechanism, the first and second arms can be fabricated such that they do not include a slot to allow passage of the cutting mechanism through the arm and thereby through tissue. In this embodiment, the first and second arms are preferably provided in a “paddle-like” form, with varying amounts of roundness to the corners. This embodiment is depicted in
Preferably, the electrodes of this embodiment are hollow, to allow the flow of conductive solution, and with thin walls to allow the passage of the solution through to tissue. The passage of conductive solution is through either (1) small holes in solid metal or solid polymer (e.g., as shown in
The device of the invention can be used to coagulate and cut body tissues, such as a blood vessel, in a variety of applications. Exemplary applications are described herein, without intending to be limited thereto. Further, it is understood that the description herein can be used to treat a number of body tissues, and the invention is not limited to treatment of tissues provided as examples.
After cutting the blood vessel with the cutting mechanism 7, the result is shown in
In a preferred embodiment, the device includes a locking mechanism. Once the optimum separation distance is achieved between the first and second electrodes, further movement of the first electrode is prevented by engaging an electrode locking mechanism that locks the position of the electrode. In one embodiment, this locking mechanism is located on the housing near the actuation member 2 (shown in
The locking mechanism is provided to lock one, or both of the arms. When the device includes a first arm that is translationally movable, and a second, stationary arm, the locking mechanism is provided to selectively lock the first arm in a desired position. In turn, when the device includes a second arm that is translationally movable, the locking mechanism is provided to selectively lock the second arm in a desired position. Alternatively, when both arms are translationally movable, the locking mechanism can selectively lock or unlock one or both of the movable arms.
Generally, as the first and second electrodes are moved closer together, a larger fraction of the conductive solution flow may boil, leading to a “hotter” tissue surface temperature. Conversely, as the electrodes are positioned further away from each other, a smaller fraction of the conductive solution will boil, leading to a lower surface temperature effect.
In another embodiment, the device is capable of treating areas of the body that are difficult to reach anatomical sites. In this embodiment, the device is provided with the ability to articulate or flex, to allow the end effector region of the device to access areas of the body requiring treatment that may be difficult to reach using minimally invasive or noninvasive techniques. As used herein, “articulate” means the tubular member is capable of moving about a joint or a jointed area as described herein. In one preferred embodiment, the tubular member 6 is provided with the ability to articulate, to allow the operator to maneuver the device within the patient's body to reach the treatment site. Alternatively, the tubular member 6 can be angled or flexible, to facilitate engaging a tissue from a selected approach position.
In one embodiment, rotatable knob 58 is located on the housing to control movement of the articulation zone 53, and thereby control articulation of the device. As rotatable knob 53 is rotated by small incremental amount, the articulation zone 53 bends a correspondingly small incremental amount. This bending or articulating is shown in
The invention has been described as a bipolar surgical device, whereby RF energy is supplied to the first and second electrodes, or to one of the electrodes and the cutting mechanism. Alternatively, the device can be provided as a monopolar surgical instrument. In this embodiment, only one of the first or second electrode is provided with RF energy and a flow of conductive solution. In one preferred embodiment, the first, translationally movable arm containing the first electrode is provided with conductive solution and RF as previously described. According to this embodiment, the second arm is provided as a structural component only and is not provided with solution or electrical energy. In an alternative preferred embodiment, the second electrode is provided with conductive solution and RF energy, as previously described. According to this embodiment, the first arm is provided as a structural component only and is not provided with conductive solution or electrical energy. When the device is used as a monopolar device, the second electrode is provided as a pad placed under the patient, as a ground, or a dispersive electrode.
The invention contemplates alternative configurations for the first and second arms, and the first and second electrodes. In one embodiment, the first arm of the device is provided in the form of a spring-loaded ball tip. As shown in
In one embodiment, the second electrode is comprised of a plate 71 with a plurality of holes 72 in it, that convey a flow of conductive solution 74 down a lumen 73. The distal end portion 65 of the second arm comprises insulation covering the second electrode. Preferably, the plate 71 is metal.
The ball embodiment of the invention provides a combination of advantages. For example, if the ball becomes clogged with char it can easily be unclogged by pressing the ball distally against the second arm. As the ball is pushed against any solid object, the spring 70 compresses and the ball moves proximally to a position behind the rim 63, thus breaking off any adherent char. This unclogging feature is not intended to be routinely used, since the presence of saline normally prevents the creation of any char. However, there may be circumstances when the physician may inadvertently misuse the device by excessively turning up the power or turning down the flow rate, which might result in boiling off all the flow off saline, drying out the “wetness” of the device and causing char formation as the tissue temperature rises significantly above 100° C.
Preferably, when the first electrode of the device is provided in the form of a ball, the second arm is shaped with a concave surface facing the convex shape of the first electrode. This “matching” of electrode shapes provides improved electrode-tissue contact and hence faster and more uniform tissue coagulation. Alternatively, the second electrode of the device is provided in the form of a ball (
The invention provides a combination of advantages over electrosurgical devices in the art. The device provides tissue coagulation and cutting without tissue desiccation, sticking, perforation, smoke formation, char formation, or thermal spread of high temperatures. Further, the invention provides electrodes of a variety of shapes and orientations that are supplied with a flow of saline in order to maintain the electrode-tissue interface continuously wetted during the application of RF energy. This “wet” electrode design will limit the peak tissue temperature to 100° C. or less and prevent tissue sticking, tissue perforation, smoke formation, char formation, and high temperature thermal spread. These advantages lead to faster, easier and safer surgical procedures.
Further, the device of the invention provides the ability to treat tissue and vessels in hard-to-reach places. One preferred configuration of the device as a tubular, angled coagulator with a movable first electrode and an optional movable cutting mechanism leads to the advantage of a low profile both during insertion and during actuation, compared to scissors-type devices. The articulating end effector region of the device also confers a significant advantage of being able to reach difficult anatomical sites. This ultimately leads to faster surgical procedures, reduced cost and increased safety. Moreover, the ability to access hard-to-reach areas of the body for treatment using the device may allow surgeons to perform noninvasive or at least minimally invasive procedures. This in turn avoids risks associated with open surgical procedures, such as risk of infection, longer healing time, and the like.
The invention thus provides a multi-purpose instrument that can be used to provide both vessel or tissue coagulation and cutting, plus surface coagulation for stopping surface bleeding without having to remove the device from the trocar.
The design of the device enables bipolar coagulation and cutting without having to remove the device from its location at the target tissue. The device can also optionally be used in the bipolar mode to perform surface coagulation or coagulative “painting” with the space between the bipolar electrodes empty of tissue. The flow of saline is effective in achieving good coupling of RF energy to tissue even when used in this painting mode.
Additionally, the invention provides a device that can be used as a monopolar or bipolar device, and is switchable between the two modes.
The invention has been described with reference to various specific and preferred embodiments and techniques. However, it will be apparent to one of ordinary skill in the art that many variations and modifications may be made while remaining within the spirit and scope of the invention.
All publications and patent applications in this specification are herein incorporated by reference, to the extent it is consistent, and to the same extent as if each individual publication or patent application was specifically and individually incorporated by reference.
|Citing Patent||Filing date||Publication date||Applicant||Title|
|US8216233||Mar 21, 2008||Jul 10, 2012||Salient Surgical Technologies, Inc.||Surgical devices and methods of use thereof|
|US8348946||Jun 12, 2012||Jan 8, 2013||Medtronic Advanced Energy Llc||Surgical devices and methods of use thereof|
|US20050090816 *||Sep 6, 2002||Apr 28, 2005||Mcclurken Michael E.||Fluid-assisted medical devices, systems and methods|
|U.S. Classification||606/48, 606/50|
|International Classification||A61B18/12, A61B17/125, A61B18/00, A61B18/18, A61B18/14|
|Cooperative Classification||A61B2018/1455, A61B2018/1472, A61B17/32, A61B2018/00196, A61B18/1442, A61B2017/2945, A61B2018/00404, A61B2018/1412, A61B2018/00601, A61B2018/00029, A61B2018/145, A61B2018/1432, A61B2018/00589|
|Feb 10, 2011||AS||Assignment|
Effective date: 20080311
Free format text: CHANGE OF NAME;ASSIGNOR:TISSUELINK MEDICAL, INC.;REEL/FRAME:025787/0959
Owner name: SALIENT SURGICAL TECHNOLOGIES, INC., NEW HAMPSHIRE
|Feb 11, 2011||AS||Assignment|
Owner name: TISSUELINK MEDICAL, INC., NEW HAMPSHIRE
Free format text: ASSIGNMENT OF ASSIGNORS INTEREST;ASSIGNORS:MCCLURKEN, MICHEAL E.;LUZZI, ROBERT;SIGNING DATES FROM 20010125 TO 20010202;REEL/FRAME:025791/0714