Abstract:
A method for powering an electrosurgical instrument includes the steps of inserting a removable battery assembly into an electrosurgical instrument and activating the power control circuit to power the electrosurgical instrument. The removable battery assembly includes a power control circuit powered by at least one energy storage cell, a radio-frequency-signal-generation assembly communicatively coupled to the power control circuit and operable to selectively produce a radio-frequency signal, and a battery assembly/instrument interface operably coupled to the radio-frequency-signal-generation assembly. The battery assembly/instrument interface includes a first plurality of connectors removably connectable with at least one corresponding connector coupled to the electrosurgical instrument, at least one of the first plurality of connectors being operable to supply the radio-frequency signal to the electrosurgical instrument.

Description:
CROSS-REFERENCE TO RELATED APPLICATIONS 
     This application claims the priority, under 35 U.S.C. §119, of U.S. Provisional Patent Application Ser. Nos. 61/037,788 filed Mar. 19, 2008, and 61/101,005 filed Sep. 29, 2008, and is a continuation-in-part of U.S. patent application Ser. No. 12/270,111, filed Nov. 13, 2008, and is a divisional application of U.S. patent application Ser. No. 12/324,873, filed Nov. 27, 2008 (which CIP and divisional applications claim the priority, under 35 U.S.C. §119, of U.S. Provisional Patent Application Ser. Nos. 60/990,784 filed Nov. 28, 2007, 61/030,748 filed Feb. 22, 2008), the entire disclosures of which are all hereby incorporated herein by reference in their entireties. 
    
    
     STATEMENT REGARDING FEDERALLY SPONSORED RESEARCH OR DEVELOPMENT 
     n/a 
     FIELD OF THE INVENTION 
     The present invention lies in the field of medical cauterization and cutting devices. The present disclosure relates to a method for powering a surgical instrument, in particular, a cordless electrosurgical forceps for sealing and/or cutting tissue. 
     BACKGROUND OF THE INVENTION 
     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, laparoscopes, and endoscopic/laparoscopic installments for remotely accessing organs through body orifices or smaller, puncture-like incisions. As a direct result thereof patients tend to benefit from less scarring and reduced healing time. 
     Laparoscopic 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 installment manufacturers who must find ways to make laparoscopic instruments that fit through the smaller cannulas. 
     Many 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 electrosurgical forceps, a surgeon can 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 from 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 close them permanently, while larger vessels need to be sealed to assure permanent closure. 
     To seal larger vessels (or tissue) effectively 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 (which term also refers to tissue when used hereinafter and vice versa). 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. Below this range, the seal may shred or tear and, above this range, the lumens may not be sealed properly or effectively. 
     With respect to effective sealing of 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. In other words, the chances of the two electrically conductive surfaces touching during activation increases as vessels become smaller. 
     Many known installments include blade members or shearing members that 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 that, 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 prematurely move prior to activation and sealing and/or a thicker, less reliable seal may be created. 
     As mentioned above, to seal larger vessels or tissue properly and effectively, 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 that 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 that 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 premature movement of the tissue during compression and prior to activation. As a result thereof, providing an instrument that 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&#39;s expertise, vision, dexterity, and experience in judging the appropriate closure force to seal the vessel uniformly, consistently, and effectively. 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. 
     The number of operations needed to uniformly, consistently, and effectively seal the vessel or tissue with such a device influences the procedure, for example, by increasingly relying on the skill of the surgeon. Typical actuation assemblies require the surgeon to perform at least four steps. With the device jaws in the normally open position, the surgeon closes the jaws by actuating a main lever. This lever can have a “ball-point pen” actuation, in that it is a push-to-lock and push-again-to-unlock (or pull-to-lock and pull-again-to-unlock) or it can just be a pull and release lever. With the main lever motion, the jaws close and impart the sealing force to the tissue or vessel. The surgeon, in a second step, presses a button to actuate the electrocautery (signal) and seal the tissue. With appropriate electronic measurements or indicators, the device informs the surgeon when sealing is complete. In a third step, the surgeon pulls a cutting trigger, which physically moves a blade distally to cut the sealed tissue. If the trigger is open-biased (for example, with a spring), it can retract the blade automatically from the tissue when released. If the blade does not stick in the tissue and does retract, the surgeon is required, in a fourth step, to unlock the main lever by pulling it, again, and letting it spring back to its original, open position through the force of a larger bias, such as an another spring, or merely lets it return to the original un-actuated position. If the blade sticks in the extended position, which would prevent the jaws from opening thereafter, a safety device can exist to retract the blade and insure that the jaws can be opened after the surgical procedure is carried out. 
     It has been found that the pressure range for assuring a consistent and effective seal is between about 3 kg/cm 2  to about 16 kg/cm 2  and, preferably, within a working range of 7 kg/cm 2  to 13 kg/cm 2 . Manufacturing an instrument that 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 beer developed by Valleylab Inc., a division of Tyco Healthcare LP, for use with Valleylab&#39;s vessel sealing and dividing installment commonly sold under the registered trademark LIGASURE ATLAS®. This assembly includes a four-bar mechanical linkage, a spring, and a drive assembly that cooperate to consistently provide and maintain tissue pressures within the above working ranges. The LIGASURE ATLAS® is designed to fit through a 10 mm cannula and includes a bi-lateral jaw closure mechanism that 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 rotate the jaw members selectively to facilitate grasping tissue. Descriptions of such systems and various methods relating thereto can be found in U.S. Pat. Nos. 7,083,618, 7,101,371, and 7,150,749. The contents of all of these applications are hereby incorporated by reference herein. 
     All of the prior art RF vessel sealing devices require a table-top power-and-signal supply box connected to the electrodes of the jaws through a cumbersome power-and-signal supply line. The supply box takes up precious room within an operating suite. In addition, the supply box is expensive to produce, requiring the surgeon/hospital to expend significant amounts of capital to keep the unit on hand. Additionally, the supply line adds cost to produce and maintain. Importantly, the supply line commonly interferes with the surgeon&#39;s full freedom of movement during use. 
     It would be desirable to eliminate the need for large tabletop power supplies and controllers. In particular, it would be desirable to develop a vessel-sealing instrument that is entirely independent of the tabletop power-and-signal supply box and the supply line. It would be also desirable to miniaturize the power supply and controllers for the sealing instrument. 
     SUMMARY OF THE INVENTION 
     The device according to an exemplary embodiment of the invention is a surgical bipolar cauterization and cutting device (possibly power-assisted) that can be used, in particular, to seal and cut tissue when desired. In an embodiment of the device, measures for carrying out both the cauterization and cutting functions can be entirely contained within the device. The invention overcomes the above-noted and other deficiencies of the prior art by providing a smaller, simpler vessel-sealing installment where power is supplied by one or more batteries. The invention entirely eliminates the need for large tabletop power supplies and controllers by miniaturizing the power supply and controllers for the sealing installment. This miniaturization occurs in various embodiments and includes, in particular, a hand-held sealing instrument having no power or control cords; it is self-powered and all control circuitry and power supplies reside in the handle of instrument. The inventive instrument provides various configurations for locating the control and power-supply circuitry, some of which allow the circuitry to be entirely removed from the device and modularly exchanged with other circuitry. Significantly, the instrument of the invention improves upon the sealing end effector by incorporating a passively articulating end effector. Accordingly, sealing is easier to affect and becomes more reliable due to the customized placement now made possible. 
     The power-assisted actuation assembly of the present invention reduces the number of steps to effect the surgical procedure and, while doing so, provides additional benefits. With the jaws of the inventive device in the normally open position, the surgeon closes the jaws by actuating a main lever. Like the prior art, this lever can have the pull-to-lock and pull-again-to-unlock actuation assembly. With this first pulling motion, the jaws close and impart a first intermediate sealing force to the tissue or vessel. This force is not the final compressive force but is merely an intermediate stage that securely holds the tissue therebetween. Thereafter, in a second step, the surgeon merely presses a single button on the device and the entire procedure is carried out automatically—the procedure including, for example, a determination of Optimal Tissue Compression (OTC), an electrocautery process to cause sealing of the tissue, a cutting movement through the sealed tissue, and a release of the jaws back to the intermediate stage. The process is finalized in the third step by a second pulling motion on the main lever to open the jaws fully. It is noted that, in another exemplary embodiment of the invention, the electronic control assembly can be configured to automatically actuate the main lever and, thereby, open the jaws for release of the sealed/cut tissue, making it ready for the next sealing/cutting procedure. With the invention, therefore, the surgeon can effect a sealing and cutting procedure with only two or three steps, these steps not requiring the surgeon to provide any significant external force (such as physically moving a trigger) other than initiating the first closure of the main lever. 
     As set forth in the preceding paragraph, the device of the instant invention is able to automatically compress the tissue at a pre-defined force that allows beneficial healing without irretrievably harming the compressed tissue. It is known that, when tissue is being compressed (whether a single layer or multiple layers) and before cutting the tissue, it is desirable for the tissue to be at a certain compressive state (OTC) so that a desirous medical change can occur; at the same time, the tissue should not be compressed too far to cause tissue necrosis. Because there is no way to precisely control the exact kind of tissue that is being placed within the compressing jaws, it is not possible to ensure that the tissue is compressed within an Optimal Tissue Compression range, referred to as an OTC range. Therefore, ruling out of tissue necrosis is difficult or not possible for prior art electrocautery devices. 
     The OTC range of tissue is a compression range in which liquid is removed from the tissue (i.e., desiccates the tissue) without damaging or necrosing the tissue. As the liquid from the tissue exits the tissue however (due to compression exerted upon the tissue by the jaws), the compressive force that is being imposed upon the tissue naturally reduces—because the jaws are “locked” in position and less mass is present between the opposing jaws due to the desiccation. In some instances, this reduction can allow the imparted tissue compression to exit the OTC range. The device of the invention includes an OTC detection device that provides feedback actively to the motorized jaws compressing the tissue. This self-adjusting compression device keeps compression force on the interposed tissue within the OTC compression range even after being desiccated. More specifically, after the main lever is compressed and the automatic control switch is actuated, the device of the invention begins monitoring characteristics of either the jaws or the tissue or both to determine whether or not the tissue is compressed within the OTC range. When in that range, the device automatically starts the sealing and cutting procedure. 
     In one exemplary embodiment, as the jaw control lever is actuated, a force switch axially present in the jaw actuation mechanism determines if the force supplied to the tissue between the jaws is sufficient for desirable sealing and cutting. If not, then electronics of the switch prevent energy from being supplied to the end effector. Alternatively, the force switch can be used to determine if the force supplied to the tissue between the jaws is insufficient for desirable sealing and cutting. If so, then electronics of the switch prevent energy from being supplied to the end effector. Such an exemplary force switch can be found in U.S. Patent Publication No. US20070267281 and is incorporated herein by reference In its entirety. This force switch can be applied to any of the end effector embodiments described herein. 
     In an exemplary embodiment the device/force switch can be configured to indicate to the surgeon (audibly, visually, or tactily) that the tissue that is about to be sealed and cut is within a desirable OTC range. A delay can be pre-programmed in the indicator device to give the surgeon time to abort, if desired, before the surgeon applies energy for sealing and cutting. If the surgeon does not abort the procedure, electrocautery begins and the tissue is sealed. Without any further activation or movement by the surgeon, the device shifts the motorized blade distally to cut the already sealed tissue. When the blade arrives at a distal end of the cutting stroke, the device causes the blade to retract automatically from the tissue without any further actuation by the surgeon. In an exemplary embodiment, appropriately positioned limit switches can be used to activate the retraction. Powered retraction ensures that the blade does not stick in the tissue and that it retracts every time. At this point, the procedure is completed and, if appropriate motorized assemblies are included, the device can then automatically unlock the main lever, allowing it to spring back to its original open position (for example, through the force of a bias device, such a spring). Thus, there is no need to include the redundant prior art safety device between the main lever and the trigger to retract the blade and insure that the jaws can be opened after the surgical procedure is carried out. 
     Consequently, the invention overcomes the above-noted and other deficiencies of the prior art by reducing the number of steps that the surgeon needs to undertake to effect tissue sealing and cutting. Simultaneously, the invention substantially decreases the amount of physical force needed heretofore needed to carry out such an operation. By relieving the surgeon of having to force the jaws closed and/or to extend and retract the blade, the surgeon has more physical energy to complete the overall surgical procedure, which can be many hours in length or which must be repeated for many different patients over the course of a day. 
     The invention overcomes the above-noted and other deficiencies of the prior art by entirely eliminating the need for large tabletop power supplies and controllers and does this by miniaturizing the power supply and controllers for the sealing instrument. This miniaturization occurs in various embodiments and includes, in particular, an entirely hand-held sealing instrument having no power or control cords. Thus, all control circuitry and power supplies reside inside the handle of instrument. In another embodiment, the power supply is self-contained but located at a distance from the instrument. In yet another embodiment, the power supply and the control electronics are located at a distance from the instrument. 
     Generally, endoscopic surgical control handles include a long shaft between an end effector and a handle portion manipulated by the surgeon. This long shaft enables insertion to a desired depth and rotation about the longitudinal axis of the shaft, thereby positioning the end effector to a degree. With judicious placement of the trocar and use of graspers, for instance, through another trocar, often this amount of positioning is sufficient. It is understood, however, that positioning of the end effector is constrained by the trocar. Thus, depending upon the nature of the operation to be carried out, it may be desirable to have adjustment in the positioning of the end effector in addition to the limited functional movements of insertion and rotation. In particular, it would be desirable to orient the end effector at an axis transverse to the longitudinal axis of the shaft of the instrument. While prior art non-articulating sealing instruments have great utility and may be successfully in many surgical procedures, they are limited to insertion and rotation movements. The present invention enhances such operation with the ability to move the end effector obliquely. In particular, the invention overcomes the above-noted and other deficiencies of the prior art by providing a passively articulating end effector to the sealing instrument. 
     As used in the art and as used herein, transverse movement of a medical end effector relative to an instrument shaft is referred to conventionally as “articulation.” Articulated positioning permits the surgeon to more easily engage tissue in some instances. In prior art medical devices including control of articulation, the articulation movement is directed actively from the device handle. This active control can be mechanical and/or electrical. For example, some prior art devices have levers at the top of the control handle and, when pivoted left, the end effector articulates left and, when pivoted right, the end effector articulates right. Some operate with opposite movement. To effect such active articulation, it is very difficult for the operator to use only one hand. Thus, often, the operator must hold the handle with one hand and pivot the articulation lever with the other hand. As is known, the trend for laparoscopic and other similar medical devices is to make them operable with a single hand—this is because surgeons using two devices, one in each hand, often lose control of the second hand when it is necessary to remove their hand from that second device to operate an articulation lever of the first device. Loss of device control is undesirable and extends the surgical procedure if a device falls outside the view of the operating surgeon. One prior art device uses electrical measures to actively control articulation In U.S. Pat. No. 7,213,736 to Wales et al., the disclosure argues that electrical power is supplied to an electrically actuated polymer to articulate the end effector actively in the desired direction. The device in U.S. Pat. No. 7,328,828 to Ortiz et al., requires the surgeon to control articulation by hand (see reference numeral 18). Such exemplary prior art devices can be characterized by referring to them as “active articulation” devices, in which an articulation control device is present on the handle and extends through the articulation joint to force the articulation in either articulation direction. In other words, the forces required to perform articulation are generated internally in the device. 
     The invention, in contrast, includes a passive articulation joint that permits the surgeon to orient the end effector along an axis transverse to the longitudinal axis of the shaft of the instrument without active articulation. 
     The articulation assembly of the present invention has no mechanical control device in the handle to effect direct control of articulating movement of the end effector. There is also no articulation control device present at the handle that extends through the articulation joint to force the end effector to articulate in a direction. Instead, articulation of the end effector is dependent upon pressure between a surface of the environment in which the end effector exists and an exterior surface of the end effector, for example, at a location distal of the articulation joint. A torque to pivot the Inventive end effector about the articulation axis arises from forces external to the device. One force is present by the user holding the handle. The other force acts distal of the articulation joint and is imparted by the environment in which the end effector is present and against which the end effector is being held. In other words, the forces required to perform articulation are external to the device. This motion can be and is referred to herein as “passive articulation” and the “articulation joint” of the present invention operates with passive articulation—it requires a torque external to the device to articulate the end effector about the axis of the passive articulation joint. 
     Articulating surgical instruments generally use one or more firing bars that move longitudinally within the installment shaft and through the articulation joint to carry out a function of the end effector. One common problem with these surgical Instruments is control of the firing bar through the articulation joint. At the articulation joint, the end effector is longitudinally spaced away from the shaft so that the edges of the shaft and end effector do not collide during articulation. This gap must be filled with support material or structure to prevent the firing bar from buckling out of the joint when the single or multiple firing bars is subjected to longitudinal firing loads. What is needed is a support structure that guides and supports the single or multiple firing bars through the articulation joint and bends or curves as the end effector is articulated. 
     U.S. Pat. No. 5,673,840 to Schulze et al. describes a flexible articulation joint that is formed from an elastomeric or plastic material that bends at the flexible joint or “flex neck”. The tiring bars are supported and guided through a hollow tube within the flex neck. The flex neck is a portion of the jaw closure mechanism and moves longitudinally relative to the end effector, shaft, and firing bars when the jaws are closed on tissue. The firing bars then move longitudinally within the flex neck as the staples are fired and tissue is cut. 
     U.S. Pat. No. 5,797,537 to Oberlin et al. (owned by Richard-Allan Medical industries, Inc.) describes an articulation joint that pivots around a pin, rather than bends around a flex joint. In this instrument, firing bars are supported between a pair of spaced support plates connected at one end to the shaft and at another end to the end effector. At least one of those connections is a slidable connection. The support plates extend through the articulation joint adjacent to the flexible drive member in the plane of articulation such that the support plates bend through the gap in the plane of articulation and the flexible firing bar bends against the support when the tip is articulated in one direction from its aligned position. U.S. Pat. No. 6,330,965 to Milliman et al. from U.S. Surgical teaches the use of support plates that are fixedly attached to the shaft and slidably attached to the end effector. 
     Although these known support plates guide a firing bar through an articulation joint, it is believed that performance may be enhanced. For instance, it is often desirable for the firing bar to be accelerated rapidly during firing to ensure sufficient momentum for severing tissue effectively. Rigidly attached support plates may tend to dislodge in response, allowing the firing bar to blow out from the articulation joint. As a further example, it is desirable for the instrument to operate in the same manner whether articulated or not. Increased friction when articulated would be inconvenient and distracting to the clinician if required to exert, a varying amount of firing force. Consequently, the present, invention provides an improved articulation mechanism for the surgical installment that enhances support to the firing bar through the articulation joint. 
     In one aspect of the invention, the surgical instrument has a handle portion that releases a lock to allow articulation of the end effector and to permit cutting while articulated. The articulating-release and cutting mechanisms are transferred through a shaft to the articulation mechanism. The articulation mechanism responds to forces that the user imparts to the end effector and allows articulation of the end effector out of line with the longitudinal axis of the shaft. The cutting mechanism responds to the cutting motion and is coupled for movement through the articulation mechanism and the end effector. A cutter support device allows the cutting mechanism to be supported and keep it in place as articulation occurs. 
     The movable distal end effector can be center-biased In an advantageous embodiment. This means that, after the distal end is passively moved into a new articulation position (by engaging the end effector with a feature of the environment, such as surrounding tissue), the next actuation of the articulation lock release will permit the end effector to return to a center position under the urging of a center-biasing device (if the end effector is free from contact with the environment). In one embodiment, the biasing device is at least one biasing spring and can be, for example, two biasing springs imparting a biasing force in opposing and, therefore, centering directions. Alternatively, the center-biasing device can be a set of spring-loaded plungers disposed on either side of the end effector at the clevis to urge the end effector independently towards the center position. These embodiments are explained in detail in U.S. Pat. Nos. 7,404,508 and 7,491,080 to Smith et al., which are hereby incorporated by reference herein in their entireties. 
     In one exemplary embodiment, the trigger that permits/inhibits passive movement is in a normally locked position. This lock is released by pulling in the trigger. Once the distal end effector is in a desired position, the user releases the trigger, thereby locking the distal end effector in Its new position. 
     The device according to an exemplary embodiment of the invention is a surgical bipolar cauterization and cutting device that can be used, in particular, to seal and cut tissue when desired. In one embodiment of the device, measures for carrying out both the cauterization and cutting functions can be entirely contained within the device. 
     Actuation of the device is accomplished using at least one servo in an exemplary embodiment. 
     The device may also be actuated by multiple electric motors, by hydraulics or pneumatics, or by the transmission of energy through a flexible drive shaft in any way such that the actuation assembly can be contained primarily or entirely in the distal portion of the device. 
     The work accomplished by any of these measures can be converted into desirable motions through any single or combination of screw drive, gear drive, wedge, toggle, cam, belt, pulley, cable, bearing, or the like push rod. In particular, a screw drive is used to transmit the work of the electric motor into linear motion. In one embodiment, the motor for the screw drive resides in the handle. A flexible rotating cable is connected from the motor to a threaded shaft. Thus, when the motor turns in either direction, the rotation of the flexible cable is transmitted to the threaded drive shaft and, because the stapling actuator and cutting slide is disposed on the drive shaft, both functions are carried out by distal movement: of the slide. In a second embodiment, the motor resides entirely in the end effector and has a shaft connected to the slide drive shaft, either directly or through transmission gears. In such a case, all that is needed in the handle is the on/off and drive shaft direction actuators, the former for turning the motor on and off and the latter determining which direction the motor will spin. 
     In one aspect of the invention, the instrument actuates an end effector with a longitudinally translating firing mechanism that is supported advantageously through an articulation mechanism by either flanking support plates or a rigid support channel, in the former embodiment, to better respond to firing loads on the firing mechanism, one or more ends of each support plate are resiliently or springedly engaged to one side of the articulation mechanism, and thus are better able to avoid buckling of the firing mechanism. For example, the pair of support plates flanks the firing mechanism across the articulation mechanism, each support plate including an end springedly engaged to a frame recess formed in the articulation mechanism to assist in preventing buckling of the firing mechanism within or out of the articulation mechanism. In the channel embodiment, the channel floats in the articulation mechanism and has surfaces that support either side of the firing mechanism as articulation occurs in either direction and, thus, avoid buckling of the firing mechanism. The channel has a floor and two sides. The support channel rests freely in a cavity inside the articulation mechanism. Ends of the channel are curved to match curves of the cavity. The support channel has various internal surfaces to contact and support the firing mechanism as it is bent within the articulation mechanism and, thereby, assists in preventing buckling of the firing mechanism within or out of the articulation mechanism. 
     The invention overcomes the above-noted and other deficiencies of the prior art by improving wear resistance and lubricity of the working end of the sealing instrument by utilizing hard-coat anodizing at selected locations on the working area of the installment. 
     In still a further aspect of the invention, a surgical instrument has a handle portion that includes a jaw closing device, a blade-firing device, and an articulation unlocking device, each operable through a shaft at the end of which is the end effector. The end effector includes, in one exemplary embodiment, a jaw fixedly coupled to the shaft and an anvil pivotally coupled to the shaft and controlled by the jaw closing device. Of course, both jaws can be pivotable, whether co dependently or independently. The blade-firing device is connected from the handle to the end effector through, the shaft and through the articulation mechanism or joint (when such joint is present). The blade-firing device carries out the cutting when actuated. The articulation mechanism allows movement of the end effector with respect to the shaft. The articulation mechanism is distally coupled to the shaft and permits passive articulation (also referred to as natural articulation) of the end effector after the articulation unlocking device is actuated (i.e., unlocked). With such actuation, the end effector is free to articulate in response to a force(s) that acts upon the end effector. In other words, when the articulation lock is unlocked, pressure of the environment against the end effector will cause articulation of the end effector with respect to the shaft. 
     With the foregoing and other objects in view, there is provided, in accordance with the Invention, a method for powering an electrosurgical instrument, the method including the steps of Inserting a removable battery assembly into an electrosurgical instrument and activating the power control circuit to power the electrosurgical instrument. The removable battery assembly includes a power control circuit powered by at least one energy storage cell, a radio-frequency-signal-generation assembly communicatively coupled to the power control circuit and operable to selectively produce a radio-frequency signal, and a battery assembly/Instrument Interface operably coupled to the radio-frequency-signal-generation assembly. The battery assembly/instrument interface includes a first plurality of connectors removably connectable with at least one corresponding connector coupled to the electrosurgical installment. At least one of the first plurality of connectors is operable to supply the radio-frequency signal to the electrosurgical instrument. 
     With the objects of the invention in view, there is also provided a method for powering a surgical Instrument, the method including the steps of inserting a removable battery assembly Into a cautery and cutting electrosurgical instrument, detecting, with the battery assembly, a connection between the battery assembly/instrument interface and the cautery and cutting electrosurgical instrument, and selectively providing at the battery assembly/instrument interface the output radio-frequency signal in response to detecting the connection. The battery assembly includes at least one energy storage cell, a power control circuit powered by the at least one energy storage cell, a radio-frequency-signal-generation assembly communicatively coupled to the power control circuit and operable to produce an output radio-frequency signal, and a battery assembly/instrument interface coupled to the radio-frequency-signal-generation assembly and having a plurality of connectors removably connectable with a plurality of corresponding connectors within the cautery and cutting electrosurgical instrument, at least one of the plurality of connectors being operable to supply the output radio-frequency signal to the cautery and cutting electrosurgical instrument. 
     In accordance with another mode of the invention, the battery assembly is removed from the electrosurgical instrument and a different removable battery assembly is inserted into the electrosurgical instrument. 
     In accordance with an added mode of the invention, a connection between the battery assembly/instrument interface and the electrosurgical instrument is detected and the radio-frequency signal is provided in response to detecting the connection. 
     In accordance with an additional mode of the invention, the battery assembly detects a connection between the battery assembly/instrument interface and the electrosurgical instrument and the radio-frequency signal is selectively provided at the battery assembly/instrument interface in response to detecting the connection. 
     In accordance with yet another mode of the invention, the output radio-frequency signal is a radio-frequency driving wave. 
     In accordance with yet a further mode of the invention, the electrosurgical instrument includes a surgical handle configured to support a bipolar end effector having jaws with bipolar contacts and a cutting blade disposed between the jaws, the surgical handle defining an aseptically sealable battery-holding compartment configured to hold the removable battery assembly, and the surgical handle includes a plurality of connectors electrically connecting the radio-frequency-signal-generation assembly to the bipolar contacts for supplying the radio-frequency signal to the bipolar contacts upon activation of the electrosurgical instrument. 
     In accordance with yet an added mode of the invention, the handle has a device selectively exposing the aseptically sealable battery-holding compartment to the environment. 
     In accordance with yet an additional mode of the invention, the battery assembly is removed from the electrosurgical instrument, the battery assembly is inserted into a battery-assembly charging unit, and the battery assembly is reinserted into the electrosurgical instrument or a different electrosurgical instrument. 
     In accordance with again another mode of the invention, the radio-frequency-signal-generation assembly is removably connected to the battery assembly as a signal processing sub-assembly. 
     In accordance with again an added mode of the invention, the signal processing sub-assembly is separated from the battery assembly and a different signal processing sub-assembly is attached to the battery assembly. 
     In accordance with again an additional mode of the invention, the battery assembly is removed from the electrosurgical installment, the signal processing sub-assembly is removed from the battery assembly, and a different signal processing sub-assembly is attached to the battery assembly. 
     In accordance with still another mode of the invention, the battery assembly includes the signal processing sub-assembly and a battery subassembly The battery subassembly has the energy storage cell and the battery assembly/instrument interface. 
     In accordance with still a further mode of the invention, the energy storage cell comprises a plurality of lithium polymer cells. 
     In accordance with still an added mode of the invention, the energy storage cell is driven to a current capacity discharge greater than a rated storage capacity of the energy storage cell. In particular, the energy storage cell is driven to a current, capacity discharge between about 10 to about 15 times greater than a rated storage capacity of the at least one energy storage cell. 
     In accordance with still an additional mode of the invention, the power control circuit Includes a buck power supply. 
     In accordance with another mode of the invention, the battery assembly is removed from the electrosurgical Instrument, the battery assembly is autoclaved, and the battery assembly is reinserted into the electrosurgical instrument or a different electrosurgical instrument. 
     In accordance with an added mode of the invention, the battery assembly is hermetically sealed. 
     In accordance with an additional mode of the invention, the electrosurgical installment is a cautery and cutting instrument with an end effector having jaws and a cutting blade disposed between the jaws. 
     In accordance with a concomitant mode of the invention, the radio-frequency signal is produced with the radio-frequency signal generation assembly dependent upon the power control circuit. 
     Endoscopic and laparoscopic surgery requires the physician to be able to use both hands independently. Prior art devices, with their active articulation controls, require both hands for using the single device. The prior art devices, therefore, make such surgeries extremely difficult or not possible A significant advantage of the present invention is that the articulation of the end effector is passive and lockable without a need for a second hand. In other words, the end effector can be unlocked, subsequently moved into a desired articulated position, and, then, caused be retained in the new position—all of this being done with a one-handed operation. 
     A further advantage of the present invention is that the axial movement of the end effector is dynamically rotatable about the longitudinal axis of the device at any time by the user. A rotation device axially fixedly but rotationally freely connects the handle to the distal components including the shaft, the articulation mechanism, and the end effector. Rotation of the distal components occurs by applying a rotational force to the rotation device about the longitudinal axis of the shaft in the desired direction. In an embodiment where passive articulation is present, pulling the rotation device in a direction away from the end effector unlocks the end effector to permit passive articulation (in an exemplary embodiment, the rotation device is bell-shaped). This rotating movement, in combination with the off-axis articulation movement of the end effector creates a compound angle at the distal end of the device to aid in accurate positioning of the end effector. 
     To support the blade-firing mechanism, a pair of support plates can flank the firing mechanism across the articulation mechanism, each support plate including an end springedly engaged to a frame recess formed in the articulation mechanism, or a rigid channel can surround the firing mechanism across the articulation mechanism. Alternatively, a U-shaped or H-shaped rigid channel can be provided for such support (and for electrically isolating the cutting and jaw-moving controls from one another). Thereby, an improved sealing and cutting instrument may incorporate a blade-firing device that withstands high firing loads yet does not introduce significantly increased firing forces when articulated. 
     The device may be manufactured in different lengths and/or be manufactured in diameters appropriate for either laparoscopic or endoscopic use, or both. A replaceable staple cartridge can be used. In addition, the actuation device can be constructed to attach to a distal end of a flexible endoscope. 
     The Optimal Tissue Compression (OTC) range of tissue is a compression range in which liquid is removed from the tissue (i.e., desiccates the tissue) without damaging or necrosing the tissue. In one exemplary embodiment, as the jaw control lever is actuated, a force switch axially present in the jaw actuation mechanism determines if the force supplied to the tissue between the jaws is sufficient for desirable sealing and cutting. If not, then electronics of the switch prevent energy from being supplied to the end effector. Alternatively, the force switch can be used to determine if the force supplied to the tissue between the jaws is insufficient for desirable sealing and cutting. If so, then electronics of the switch prevent energy from being supplied to the end effector. Such a force switch can be found in U.S. Patent Publication No. US20070267281 and is Incorporated herein by reference in its entirety. In an exemplary embodiment, the force switch can be configured to indicate to the surgeon (audibly, visually, or tactily) that the tissue is within a desirable OTC range. A delay can be pre-programmed in the indicator device to give the surgeon time to abort, if desired, before the surgeon applies energy for sealing and cutting. This force switch can be applied to any of the end effector embodiments described herein, 
     Other features that are considered as characteristic for the invention are set forth in the appended claims. 
     Although the invention is illustrated and described herein as embodied in method for powering a surgical instrument, it is, nevertheless, not intended to be limited to the details shown because various modifications and structural changes may be made therein without departing from the spirit of the invention and within the scope and range of equivalents of the claims. 
     The construction and method of operation of the Invention, however, together with additional objects and advantages thereof will be best understood from the following description of specific embodiments when read in connection with the accompanying drawings. 
     Other features that are considered as characteristic for the invention are set forth in the appended claims. As required, detailed embodiments of the present invention are disclosed herein; however, it is to be understood that the disclosed embodiments are merely exemplary of the invention, which can be embodied in various forms. Therefore, specific structural and functional details disclosed herein are not to be interpreted as limiting, but merely as a basis for the claims and as a representative basis for teaching one of ordinary skill in the art to variously employ the present invention in virtually any appropriately detailed structure. Further, the terms and phrases used herein are not intended to be limiting; but rather, to provide an understandable description of the invention. While the specification concludes with claims defining the features of the invention that are regarded as novel, it is believed that the invention will be better understood from a consideration of the following description in conjunction with the drawing figures, in which like reference numerals are carried forward. The figures of the drawings are not drawn to scale. 
     Before the present invention is disclosed and described, it is to be understood that the terminology used herein is for the purpose of describing particular embodiments only and is not intended to be limiting. The terms “a” or “an”, as used herein, are defined as one or more than one. The term “plurality,” as used herein, is defined as two or more than two. The term “another,” as used herein, is defined as at least a second or more. The terms “including” and/or “having,” as used herein, are defined as comprising (i.e., open language). The term “coupled,” as used herein, is defined as connected, although not necessarily directly, and not necessarily mechanically, 
     As used herein, the term “about” or “approximately” applies to all numeric values, whether or not explicitly indicated. These terms generally refer to a range of numbers that one of skill in the art would consider equivalent to the recited values (i.e., having the same function or result). In many instances these terms may include numbers that are rounded to the nearest significant FIG. In this document, the term “longitudinal” should be understood to mean in a direction corresponding to an elongated direction of the device between the end effector and the control handle. The terms “program,” “software application.” and the like as used herein, are defined as a sequence of instructions designed for execution on a computer system. A “program,” “computer program,” or “software application” may include a subroutine, a function, a procedure, an object method, an object implementation, an executable application, an applet, a servlet, a source code, an object code, a shared library/dynamic load library and/or other sequence of instructions designed for execution on a computer system. 
    
    
     
       BRIEF DESCRIPTION OF THE DRAWINGS 
       Advantages of embodiments of the present invention will be apparent from the following detailed description of the preferred embodiments thereof, which description should be considered in conjunction with the accompanying drawings in which: 
         FIG. 1  is a fragmentary, perspective and partially cut away view of the end effector of the present invention with the shaft removed and with the jaws in a closed orientation; 
         FIG. 2  is a fragmentary, perspective view of the end effector of  FIG. 1  with one jaw in an open orientation past a max-open position and with the lower jaw removed; 
         FIG. 3  is a fragmentary, side elevational view of the end effector of  FIG. 1  with the lower jaw removed and with the upper jaw is an open orientation past the max-open position; 
         FIG. 4  is a fragmentary, longitudinally cross-sectional view of the end effector of  FIG. 1  in a first longitudinally cross-sectional plane parallel to a plane of the blade; 
         FIG. 5  is a fragmentary, longitudinally cross-sectional view of the end effector of  FIG. 1  in a third longitudinally cross-sectional plane coplanar with the blade plane; 
         FIG. 6  is a colored, fragmentary, partially transparent, side elevational view of the end effector of  FIG. 1  with the upper jaw removed and the lower jaw in a closed orientation; 
         FIG. 7  is a colored, fragmentary, partially transparent, side elevational view of the end effector of  FIG. 1  with the upper jaw removed, the lower jaw in a partially open orientation, and the blade in a retracted position; 
         FIG. 8  is a colored, fragmentary, partially transparent, side elevational view of the end effector of  FIG. 7  with the blade in an extended position; 
         FIG. 9  is a colored, fragmentary, partially transparent, side elevational view of the end effector of  FIG. 7  with the lower jaw in an extended open position to restrict movement of the blade body and the blade control device; 
         FIG. 10  is a fragmentary, transverse cross-sectional view of the end effector of  FIG. 1  in a second transverse cross-sectional plane transverse to the linear extent of the blade and through the blade body and the pivot bosses of the jaws; 
         FIG. 11  is a fragmentary, longitudinally cross-sectional view of the end effector of  FIG. 1  in a third longitudinally cross-sectional plane transverse to the blade plane and through a blade control device; 
         FIG. 12  is a process flow diagram illustrating the steps for operating a prior art electrocautery sealing and cutting surgical device; 
         FIG. 13  is a fragmentary perspective view of an exemplary embodiment of a passive articulating electrocautery sealing and cutting surgical device according to the invention with the jaws in an open orientation past a max-open position, a blade in a partially extended position, and an articulation joint in an aligned articulation position; 
         FIG. 14  is a fragmentary perspective and partially transparent view of the passive articulating electrocautery sealing and cutting surgical device of  FIG. 13  with a distal joint portion removed, an upper proximal joint portion removed, a transparent lower proximal joint portion, and a transparent outer shaft portion; 
         FIG. 15  is a fragmentary perspective and partially transparent view of the passive articulating electrocautery sealing and cutting surgical device of  FIG. 14  with the jaws in a closed orientation and the lower proximal joint portion removed; 
         FIG. 16  is a fragmentary enlarged perspective and partially transparent view from above the passive articulating electrocautery sealing and cutting surgical device of  FIG. 13  with a transparent articulation joint and a transparent outer shaft portion; 
         FIG. 17  is a fragmentary elevational and partially transparent view of a joint of the passive articulating electrocautery sealing and cutting surgical device of  FIG. 13 ; 
         FIG. 18  is a fragmentary elevational and partially transparent side view of a passive articulating electrocautery sealing and cutting surgical device of with a right side cover of the handle removed and a battery assembly Inserted within the handle; 
         FIG. 19  is a perspective view of the underside of the passive articulating electrocautery sealing and cutting surgical device of  FIG. 18  showing a switch disposed on an underside of the first trigger; 
         FIG. 20  is a fragmentary elevational side view of the passive articulating electrocautery sealing and cutting surgical device of  FIG. 18  with the battery assembly partially inserted within the handle; 
         FIG. 21  is an enlarged fragmentary elevational side view of the battery compartment of the handle of  FIG. 18  with the right side cover of the handle removed and a door in an intermediate position partially ejecting the battery assembly from the battery compartment; 
         FIG. 22  is a fragmentary perspective and partially transparent view of the passive articulating electrocautery sealing and cutting surgical device of  FIG. 18 : 
         FIG. 23  is a fragmentary perspective and partially transparent view of the passive articulating electrocautery sealing and cutting surgical device of  FIG. 18  with both halves of the handle removed and the first trigger partially depressed; 
         FIG. 24  is a fragmentary perspective and partially transparent view of the passive articulating electrocautery sealing and cutting surgical device of  FIG. 23  with the first trigger fully depressed; 
         FIG. 25  is a fragmentary elevational and partially transparent view of the passive articulating electrocautery sealing and cutting surgical device of  FIG. 24  with the first and second triggers depressed; 
         FIG. 26  is a fragmentary elevational and partially transparent view of the passive articulating electrocautery sealing and cutting surgical device of  FIG. 25  with the first and second triggers partially released from the depressed position of  FIG. 25 ; 
         FIG. 27  is a fragmentary elevational and partially transparent view of the passive articulating electrocautery sealing and cutting surgical device of  FIG. 26  with the first trigger partially released from the depressed position of  FIG. 26 , and the second trigger fully released; 
         FIG. 28  is an enlarged fragmentary perspective and partially transparent view of the upper portion of the second articulation trigger of the passive articulating electrocautery sealing and cutting surgical device of  FIG. 18  with the left and right side covers of the handle removed; 
         FIG. 29  is a fragmentary enlarged perspective and partially transparent view of the passive articulating electrocautery sealing and cutting surgical device of  FIG. 13 to 17  with the jaws open; 
         FIG. 30  is an elevational side view of an electrocautery sealing and cutting surgical device according to the present invention; 
         FIG. 31  is a fragmentary elevational side view of the electrocautery sealing and cutting surgical device of  FIG. 30  with a left side cover of the handle removed and a battery assembly inserted within the handle; 
         FIG. 32  is a fragmentary elevational side view of the electrocautery sealing and cutting surgical device of  FIG. 30  with a left side cover of the handle removed and a first trigger depressed; 
         FIG. 33  is a fragmentary elevational side view of the electrocautery sealing and cutting surgical device of  FIG. 30  with a left side cover of the handle removed and the battery door opened and automatically ejecting the battery assembly from the battery chamber; 
         FIG. 34  is a fragmentary elevational side view of the electrocautery sealing and cutting surgical device of  FIG. 30  with a left side cover of the handle removed and the battery assembly separated from the handle; 
         FIG. 35  is a perspective and partially transparent view of the battery assembly of  FIG. 30 ; 
         FIG. 36  is a perspective and partially cut-away view of an alternative embodiment of the inventive battery assembly according to the present invention; 
         FIG. 37  is an exploded perspective view of the battery assembly of  FIG. 36 ; 
         FIG. 38  is a fragmentary elevational side view of an alternative embodiment of the passive articulating electrocautery sealing and cutting surgical device according to the present invention with a left side cover of the handle removed and a battery inserted within the handle; 
         FIG. 39  is a fragmentary elevational side view of the passive articulating electrocautery sealing and cutting surgical device of  FIG. 38  with first and second triggers depressed to a first position; 
         FIG. 40  is a fragmentary elevational side view of the passive articulating electrocautery sealing and cutting surgical device of  FIG. 38  with the first trigger depressed to the first position and the second trigger depressed to a second position; 
         FIG. 41  is a fragmentary elevational side view of the passive articulating electrocautery sealing and cutting surgical device of  FIG. 40  with the first trigger depressed to the first position and the second trigger depressed to a third position; 
         FIG. 42  is an elevational side view of the passive articulating electrocautery sealing and cutting surgical device of  FIG. 38 ; 
         FIG. 43  is a fragmentary and partially exploded elevational side view of the passive articulating electrocautery sealing and cutting surgical device of  FIG. 38  with the left side cover of the handle removed, a battery door opened, and the battery outside a battery chamber; 
         FIG. 44  is a fragmentary side perspective view of another exemplary embodiment of a passive articulating electrocautery sealing; and cutting surgical device according to the present invention with a left side cover of the handle removed, a battery assembly inserted within the handle, and a removable, sealed proximal signal generation circuitry assembly; 
         FIG. 45  is a fragmentary elevational side view and partially cross-sectional view of the passive articulating electrocautery sealing and cutting surgical device of  FIG. 44 ; 
         FIG. 46  is a fragmentary side perspective and exploded view of the passive articulating electrocautery sealing and cutting surgical device of  FIG. 44  with the left side cover present and with the proximal signal generation circuitry assembly in a removed position; 
         FIG. 47  is a fragmentary enlarged perspective and partially transparent view of another exemplary embodiment of an electrocautery sealing and cutting surgical end effector according to the present invention with serrated jaws in a max-open position; 
         FIG. 48  is a fragmentary perspective view of the electrocautery sealing and cutting surgical end effector of  FIG. 47  with the jaws open past the max-open position; 
         FIG. 49  is a fragmentary enlarged perspective view from a distal end of the electrocautery sealing and cutting surgical end effector of  FIG. 48  with an outer portion of the upper jaw removed; 
         FIG. 50  is a fragmentary enlarged perspective view from a proximal side of the electrocautery sealing and cutting surgical end effector of  FIG. 47 ; 
         FIG. 51  is a fragmentary enlarged perspective view from a distal side of a passive articulating electrocautery sealing and cutting surgical end effector according to the present invention with the jaws past, a max-open position and with the blade removed; 
         FIG. 52  is a fragmentary enlarged perspective and partially transparent view from a distal side of the passive articulating electrocautery sealing and cutting surgical end effector of  FIG. 51 ; 
         FIG. 53  is a fragmentary enlarged perspective and partially transparent view from a distal side of the passive articulating electrocautery sealing and cutting surgical end effector of  FIG. 52  with an upper part of a two-part proximal articulation joint portion removed; 
         FIG. 54  is a fragmentary, side elevational view of an exemplary embodiment of a powered-blade electrocautery and cutting device according to the present invention with a right side cover and end effector removed; 
         FIG. 55  is a perspective view from above a side of a jaw control slide of the device of  FIG. 54 ; 
         FIG. 56  is a perspective view from above a side of a blade control slide of the device of  FIG. 54 ; 
         FIG. 57  is a perspective view from above a side of the jaw and blade control slides of  FIGS. 55 and 56 ; 
         FIG. 58  is a fragmentary, perspective view of the device of  FIG. 54  in a jaw-open and blade-retracted state with a control trigger removed; 
         FIG. 59  is a fragmentary, perspective view of the device of  FIG. 58  in a jaw-closed and blade-retracted state; 
         FIG. 60  is a fragmentary, perspective view of the device of  FIG. 59  in a jaw-closed and blade-extended state; 
         FIG. 61  is a fragmentary, side elevational view of another exemplary embodiment of a powered-blade electrocautery and cutting device according to the present invention 
         FIG. 62  is a fragmentary, perspective view of the device of  FIG. 61  in a jaw-open and blade-retracted state with a control trigger removed; 
         FIG. 63  is a fragmentary, perspective view of the device of  FIG. 62  in a jaw-closed and blade-retracted state; 
         FIG. 64  is a fragmentary, perspective view of the device of  FIG. 63  in a jaw-closed and blade-extended state; 
         FIG. 65  is a process flow diagram illustrating the steps for operating a prior art electrocautery sealing and cutting surgical device; 
         FIG. 66  is a process flow diagram illustrating the steps for operating one exemplary embodiment of an electrocautery sealing and cutting surgical device according to the present invention, and 
         FIG. 67  is a process flow diagram illustrating the steps for operating another exemplary embodiment of an electrocautery sealing and cutting surgical device according to the present invention. 
     
    
    
     DETAILED DESCRIPTION OF THE INVENTION 
     Aspects of the invention are disclosed in the following description and related drawings directed to specific embodiments of the invention. Alternate embodiments may be devised without departing from the spirit or the scope of the invention. Additionally, well-known elements of exemplary embodiments of the invention will not be described in detail or will be omitted so as not to obscure the relevant details of the invention. 
     Before the present invention is disclosed and described, It is to be understood that the terminology used herein is for the purpose of describing particular embodiments only and is not Intended to be limiting. It must be noted that, as used In the specification and the appended claims, the singular forms “a,” “an” and “the” include plural references unless the context clearly dictates otherwise. 
     While the specification concludes with claims defining the features of the invention that are regarded as novel, it is believed that the invention will be better understood from a consideration of the following description in conjunction with the drawing figures, in which like reference numerals are carried forward. The figures of the drawings are not drawn to scale. 
     Referring now to the figures of the drawings in detail and first, particularly to  FIG. 1  thereof, there is shown an exemplary embodiment of a bipolar cautery and cutting end effector  100  of the present invention. In many of the figures of the drawings, the proximal portion of the device (e.g., the handle) is not shown or is illustrated only diagrammatically, for example, the exemplary embodiment shown in  FIGS. 1 to 11 . In the figures, a cutting actuation wire  10  extends a distance proximally to a non-illustrated cutting actuation assembly that is capable of moving the cutting actuation wire  10  in the longitudinal direction (L). Similarly, a pair of jaw actuation wires  20 ,  30  extends proximally towards the non-illustrated jaw actuation assembly, which is capable of moving the jaw actuation wires  20 ,  30  in the longitudinal direction (L). The wires  20 ,  30  can extend all of the way back to the actuation assembly and can be individually actuatable or separately actuatable. Alternatively, the wires  20 ,  30  can meet at an intermediate point and, thereafter, a single actuator can extend proximally back to the actuation assembly. 
     The bipolar cautery and cutting end effector  100  of this embodiment of the present invention is shown only to its proximal end in these figures. Between this proximal end and the non-illustrated actuation assembly is an outer sheath  40  (illustrated only diagrammatically by dashed lines) having an outer shape that is substantially similar or identical to an outer shape of the clevis  110  or that transitions from a first shape smoothly to the outer shape of the clevis  110 . For example, in a flexible embodiment of the outer sheath  40 , the outer sheath  40  can be comprised of a flexible inner coil (e.g., of stainless steel) with an outer coating of a polymer that is, for example, heat-shrunken upon the coil. In a non-flexible exemplary embodiment of the outer sheath  40 , the sheath  40  can be a one-piece tube-shaped cannula of stainless steel. Other similar embodiments for flexible and non-flexible end effector extensions are also envisioned 
     The end effector  100  has a pair of opposing jaws  120 ,  130 , each pivotally connected to the clevis  110 .  FIG. 1  shows the jaws in the clevis-aligned, closed position and  FIG. 2  shows one jaw in a clevis-aligned, extended open position. As will be describe below in more detail, this particular open position is referred to as “extended” because it is exaggerated from a desired fully-open position of the jaws  120 ,  130 . 
     The cutting actuation wire  10  is connected at its distal end to a cutting assembly  140 , which is best seen in  FIG. 5  and includes a blade body  150 , a blade lock bias device  160 , and a blade control device  170 . More specifically, the distal end of the cutting actuation wire  10  is connected to the proximal end of the blade body  150 . An intermediate portion of the blade body  150  defines a control slot  152 , which will be described in further detail below. The blade body  150  has a distal end at which is a cutting blade  154 . Here, the blade  154  is perpendicular to the longitudinal axis of the blade body  150  but, in other exemplary embodiments, can be at an angle thereto. Extending from the blade body  150  is at least one blade boss  156 . See, e.g.,  FIG. 2 . In one exemplary embodiment, there are two opposing and identical blade bosses  156 , one on either side of the blade body  150 . 
     The blade  154  is positioned within the jaws  120 ,  130  to cut tissue therebetween and, in particular, before, during, and/or after the cautery jaws  120 ,  130  have sealed the tissue on either side of the cut. To insure that the blade  154  does not extend distally until the user desires such extension, a non-illustrated bias device in the actuation handle imparts a proximally directed bias at all times. When the user desires to extend the blade  154  distally, the user actuates the blade extension control and overcomes the proximally directed bias of this actuation handle bias device. The proximally directed bias is a force sufficient to keep the blade body  150  in the proximal-most position within the end effector  100  but not enough to cause damage to the blade assembly or to the end effector  100 . 
     The cutting assembly  140  includes its own bias device  160  for locking the blade body  150  dependent upon a current position of the jaws  120 ,  130 , and which is explained along with the blade control device  170 . As shown in  FIG. 3 , the blade control device  170  resides within the control slot  152  of the blade body  150 . The blade control device  170  has a proximal surface  172  oriented orthogonal to the longitudinal axis of the blade body  150 , and, in this exemplary embodiment, also orthogonal to the longitudinal axis of the end effector  300 . This orientation of the proximal surface  172  provides a bearing surface for the distal end  162  of the blade lock bias device  160 , which, in this exemplary embodiment, is a compression spring. The blade control device  170  also has a distal end with a distal bearing surface  174  having a shape corresponding with the interior shape of the distal end of the control slot  152 . Here, the two shapes are curved, in particular, semi-circular. These shapes can take any form, even angular or pointed, and can even be different. All that is needed in this cooperative engagement is for the distal end of the control slot  152  to be able to impart a force on the distal bearing surface  174  when the blade body  150  is moved proximally to, thereby, correspondingly move the blade control device  170  along with the blade body  150 . The blade lock bias device  160  is positioned and pre-tensioned to force the blade control device  170  towards and/or into the distal end of the control slot  152 . 
     Because the size of the end effector  100  is about 3.2 mm in diameter or less, the end effector parts are very small. A blade  154  having few millimeters in length and less for its height can be easily forced from between the jaws  120 ,  130  and/or bent if it is not properly protected. To prevent undesirable orientations and/or conditions from occurring, each of the jaws  120 ,  130  is provided with an internal blade control trough  132 , shown in  FIG. 2 , for example. This trough  132  provides a guiding surface along which the blade body  150  can move and between which, the blade  154  travels. It is desirable for the blade body  150  and blade  154  to travel in the respective troughs of the jaws  120 ,  130  substantially without friction. It is not necessary for a part of the blade body  150  to touch the control trough  132  so long as the trough  132  provides a position-limiting area for the blade body  150  in the longitudinal and transverse directions. If the blade body  150  and/or blade  154  is permitted to move distally while the jaws  120 ,  130  are open to such an extent that the blade  154  is no longer within the troughs, then forces from the environment, for example, imparted from tissue present between the jaws  120 ,  130 , can cause undesirable lateral movement of the blade  154  or blade body  150 . With such small dimensions, even a small amount of lateral movement could damage the blade body  150  and/or the blade  154  and, if plastically bent in the lateral direction, could prevent the jaws  120 ,  130  from closing—which would prevent the end effector  100  from being removed, for example, from a channel in which the control shaft is present, such as when in a lumen of a trocar or a multi-channel endoscope. The bosses  156  and the blade control device  170  are present for this desired control. 
       FIG. 2  shows the end effector  100  with the lower jaw  120  removed. In this figure, it is possible to see the distal shape of the clevis  110 , especially near the bosses  156  at the distal end of the blade body  150  near the blade  154 . It can be seen that a boss stop cavity  112  is present and has an interior shape corresponding to the exterior shape of the boss  156 . If a boss  156  is present on both sides of the blade  154 , then a corresponding boss stop cavity  112  is present in a manner corresponding to the configuration illustrated in  FIG. 5 , for example, but on the other side of the blade  154 . The boss stop cavities  112  provide a secure position for the blade  154  and blade body  150  when the blade body  150  is biased in the proximal direction. As can be seen, the cavities  112  prevent, the blade from moving up or down in the plane of the blade  154  and the cavity in which the blade  154  is present in the clevis  110  prevents rotation of the blade  154  or blade body  150  therein. 
     As stated above, it is desirable for the blade  154  to be disposed within the troughs of the jaws  120 ,  130  at all times when it is extended from the retracted position shown in  FIG. 2 , for example. In order to provide this control, reference is made to  FIGS. 6 to 9 . As can be seen in  FIG. 6 , a blade-extension control boss  134  on the interior side of each jaw  120 ,  130  provides a blocking surface  136  that is absent from the travel line of the blade boss  156  as the blade  154  is extended because the jaws  120 ,  130  are substantially closed and in-line with the outer surface of the clevis  110 . In this closed orientation, if it is desired to extend the blade body  150  between the jaws, the bosses  134  would not prevent such movement. As shown in  FIG. 6 , the blade-extension control boss  134  has a jaw-max-open control surface  138  at a distance from the bottom of the boss cavity  112 . As such, the jaw  130  can be moved from the closed position of  FIG. 6  to the max-open position of  FIG. 7  and still permit distal movement of the blade  154 . As used herein, the “max-open position” of the jaws is a position where the jaws are open and the blade  154  is still protected within the troughs of the jaws  120 ,  130 . So, if the jaw(s) is(are) open at the max-open position of  FIGS. 7 and 8 , then the blade  154  can be extended to its fully distal position shown in  FIG. 8 . As is clearly shown, the blade  154  still resides within the control trough  132 . In this distal-most position, it becomes apparent that the jaw  130  has a second proximal control device  139  (see  FIG. 8 ) extending proximally from the proximal end of the jaw  130 . In any extended position of the blade  154 , the second proximal control device  139  is in a position where it does not block distal movement of the blade control device  170 . In other words, from the closed position of the jaws  120 ,  130  to the max-open position of the jaws  120 ,  130 , the second proximal control device  139  remains below (as viewed in  FIG. 8 ) the blade control device  170 . 
     In contrast to the above, when the jaws  120 ,  130  are open past the max-open position, the blade  154  should not be allowed to extend out from the clevis  110 . The feature of the end effector  100  that prevents such extension from occurring is, for example, the blade-extension control boss  134 . As the jaws  120 ,  130  open past the max-open position, the blade-extension control boss  134  necessarily moves directly distal (in front of) the blade boss  156  as shown in  FIG. 9 . In this orientation, the blade  154  is prevented from distal movement by the blade-extension control boss  134 . 
     As the blade body  150  moves distally, the blade control device  170 , forced distally by the blade lock bias device  160 , moves distally along with the position of the distal end of the control slot  152 . As best shown in  FIGS. 4 and 11 , the blade control device  170  has at least one transverse portion  172  extending orthogonal to the longitudinal axis of the end effector  100 , for example, in the same direction as the blade boss  156 . As such, the blade control device  170  can move distally forward along with the blade body  150 , but only for a limited distance. Each of the jaws  120 ,  130  has the second proximal control device  139  as shown in  FIG. 9 . Therefore, with the second proximal control device  139  directly distal of the transverse portion  172 , the blade control device  170  is not permitted to move distal of the position shown in  FIG. 9 . When both of the jaws  120 ,  130  are within their respective max-open positions, the blade body  150  can move distally. See  FIG. 8 , for example. More specifically, when the blade control device  170  moves forward from the disengaged position, for example, shown in  FIG. 7 , to the engaged position, for example, shown in  FIG. 8 , each jaw  120 ,  130  is prevented from opening any further than the max-open position. The advantageous feature allowing the blade body  150  to extend distally when the jaws  120 ,  130  are open less than the max-open position is presented by balancing the relative positions of the blade bosses  156  and the radial location of the second proximal control devices  139  on each of the jaws  120 ,  130 . 
     Another advantageous feature of the end effector  100  is that the jaws  120 ,  130  can pivot, in the plane of the blade  154 , while the blade  154  is extended. As apparent in  FIG. 8 , the jaw  130  can “rock” upwards from the down-most position until it is prevented from further upward movement by the interior surface  137  of the tang of jaw  130 . This permitted rocking movement is especially advantageous for tracking within a channel of an endoscope, for example. The second proximal control device  139  also acts to limit the opening extent of each jaw when the blade body  150  is extended in any amount. 
     The end effector  100  described herein can be used as a medical cauterization device, in addition to a cutting device. This means that, to cauterize tissue between the jaws  120 ,  130 , it is desired to pass current between the two opposing tissue-contacting inner jaw faces  135 . If the parts touching the jaws  120 ,  130  were not appropriately insulated, then current would pass between the jaws  120 ,  130  in a short circuit. To prevent such short-circuiting from occurring, in this exemplary embodiment, various end effector parts are insulated. First, with respect to the embodiment illustrated in  FIGS. 1 to 11 , it is noted that each of the two jaw actuation wires  20 ,  30  is used to pass current to the respective connecting jaw  120 ,  130 . To prevent electrical short circuiting of these wires  20 ,  30  from the non-illustrated proximal control handle to the end effector  100 , the wires  20 , are provided with an electrical insulator over their entire extent except for the non-illustrated connections at the control handle and the electrical connection portions  32  adjacent the tangs of the jaws  120 ,  130 . The insulator can be of any appropriate electrically insulating material, for example, a coating or a deposition. The clevis  110  is also provided with an electrical Insulator on all or part of its exterior surface. If the entire clevis  110  is so coated, there is no chance of short-circuiting the electrical current passing through the wires  20 ,  30 . Similarly, at least the blade body  150  is provided with the electrical insulation. With such insulation, the possibility of passing current through the cutting actuation wire  10  is prevented, or substantially eliminated. If desired, the bias device  160  can be electrically insulated as well. At this point, electrical current can be presented to the entirety of the jaws  120 ,  130 . By selective placement of an electrical insulator, the electrical current can be made to pass only through the inner faces  135  of the jaws  120 ,  130 . More specifically, if the entirety of the jaws  120 ,  130  except for the inner jaw faces  135  is provided with an electrical insulator, then any electrical current passing between the wires  20 ,  30  will only pass between the two opposing faces  135 . To insure that current does not pass from either jaw  120 ,  130  to the clevis  110  at the jaw pivot bosses  114 , especially where the jaws  120 ,  130  have frictional contact with the pivot bosses  114 , a jaw pivot bushing  180  made of an electrical insulating material or covered with such a material is provided between the respective jaw  120 ,  130  and pivot boss  114 . See, e.g.,  FIG. 10 . 
     One exemplary embodiment for insulating the wires  20 ,  30  includes a polyamide coating. An exemplary embodiment for providing insulated jaws  120 ,  130 , includes an anodized hardcoat of polytetrafluoroethylene (PTFE) with the inner jaw faces  135  having the coating removed or with the jaws  120 ,  130  coated everywhere except the faces  135 . Another exemplary embodiment for such a coating is a hard-coat anodization, which will provide wear resistance and lubricity where present. 
     The actuation assemblies of the present invention reduce the number of steps to effect the sealing and cutting surgical procedure. This improvement is illustrated and explained with respect to  FIG. 12 , in which four steps are illustrated to perform an electrocautery sealing and cutting procedure with the invention. With the device jaws in the normally open position, in Step  1 , the surgeon closes the jaws by actuating a main lever. With the first pulling motion, the jaws close and impart the sealing force to the tissue or vessel. In Step  2 , the surgeon actuates electrocautery and seals the tissue. In Step  3 , the surgeon pulls a trigger to move the cutting blade distally and the sealed tissue is cut. Typically, the blade is retracted upon release of the trigger. The surgeon, in Step  4 , if desired, repeats the process (dashed line). 
     It is beneficial if electrocautery is effected when tissue is at an optimal state for a desirable medical change to occur after the sealing and cutting procedure. Therefore, within the steps of compressing the tissue and carrying out electrocautery for sealing (but before cutting), the device can be configured to carry out an OTC-determination step. This determination can be carried out in various ways. In one exemplary embodiment according to the invention, electrodes on either side of the tissue sense an impedance of the tissue disposed between the jaws (e.g. at the jaw mouth surfaces). OTC can be determined by comparing the measured impedance to a known range of Impedances value corresponding to an OTC state of the tissue. As the tissue desiccates, the impedance of the tissue changes. Therefore, the active feedback circuitry can be provided to continuously monitor the impedance and to indicate to the surgeon to open or close the jaws accordingly (with appropriate indicators at the control handle, e.g., ↑=open or ↓=close) so that the OTC state is maintained up to and including the time that sealing and cutting is performed. 
     The OTC feedback device performs particularly well when coupled to a mechanism for closing and opening the jaws. Passing an upper OTC value in a positive direction means that too much pressure is being imparted on the tissue and the motorized jaws are opened to an extent that brings the measured value back within the OTC range. In contrast, passing the lower OTC value in a negative direction means that too little pressure is being imparted on the tissue and the motorized jaws are closed to an extent that brings the measured value back within the OTC range. This self-adjusting compression device keeps compression force on the interposed tissue within the OTC compression range during and after desiccation. When in the OTC range after desiccation, the device notifies the surgeon of this fact, referred to as a “procedure-ready state” With this information, a delay can be pre-programmed in the device so that the sealing does not occur until after a time period expires, for example, any amount of time up to 5 seconds. In one exemplary embodiment, if the actuation device is pressed again, then the procedure is aborted and the surgeon can reposition the jaws or entirely abort the operation, if the surgeon does nothing during the delay period, then the device automatically starts the sealing procedure. Indicating information for the procedure-ready state can be conveyed to the surgeon audibly (e.g., with a speaker), visually (e.g., with an LED), or tactily (e.g., with a vibration device). 
     In another exemplary embodiment of the device, the end effector is passively articulated with respect to the shaft/handle of the device as described in U.S. Pat. Nos. 7,404,508 and 7,491,080, previously incorporated by reference.  FIGS. 13 to 16  illustrate a first exemplary embodiment of a distal end of a passive articulating electrocautery sealing and cutting surgical end effector  1300  of the present invention. The end effector  1300  has an articulation joint  1302  in an aligned or centered articulation position (as compared to  FIG. 17 , which shows the articulation joint of the invention in a left-articulated position). 
     In this exemplary embodiment of the articulation device, a distal articulation joint portion  1310  also acts as a jaw clevis  1312  and a proximal articulation joint portion  1320  is formed from upper and lower proximal articulation parts  1322 ,  1324 . These parts  1322  and  1324  are fixed to the distal end of an outer shaft or sleeve  1330 , which connects a non-illustrated control handle to the end effector  1300 . Electrocautery jaws  1340 ,  1342  are attached rotatably to the jaw clevis  1312 . A cutting blade  1350  is disposed between the jaws  1340 ,  1342  and rides within blade control troughs  1341 ,  1343  similar to trough  132  of the embodiment of  FIGS. 1 to 11  to prevent the blade  1350  from, being displaced laterally to an impermissible extent. Control of each of the jaws  1340 ,  1342  is effected, first fin a proximal direction) by a respective link  1360 ,  1562  rotatably connected to each of the jaws  1340 ,  1342 . The link connection point is located offset from the pivot point  1314  or, in the embodiment show, the pivot boss. The boss  1314  extends from the clevis  1312  and through or Inside a pivot hole of the respective jaw  1340 ,  1342 . With appropriate fastening, the jaw  1340 ,  1342  remains pivotally connected about the pivot point  1314 . A similar jaw boss extends, parallel to the axis of the pivot hole, from the jaw  1340 ,  1342 . A distal end of the link  1360 ,  1562  is mounted pivotally about this jaw boss. In such a configuration, force exerted upon the proximal end of the link  1360 ,  1562  will pivot a respective jaw about its own pivot point  1314 . 
     The proximal end of the link  1360 ,  1562  is pivotally connected to a jaw drive block  1370  disposed slidably within the distal articulation joint portion  1310 . Like the jaws  1340 ,  1342 , the block  1370  has a drive boss extending therefrom through a proximal boss hole of the link  1360 ,  1562 . With the link  1360 ,  1562  secured in this manner, any longitudinal movement of the block  1370  within the distal articulation joint portion  1310  will cause a pivoting motion of each the jaws  1340 ,  1342 , thereby causing jaw opening and closing movements. The exemplary boss-and-hole connections mentioned above are only included as example connections and any similar kind of connection, including reversal of the connection is envisioned for the invention. 
     With the distal articulation joint portion  1310  removed, it is apparent in  FIG. 14  that the jaw drive block  1370  is connected at its proximal end to a jaw actuator  1390  that, in this illustration is a rectangular-cross-sectioned drive band. This band  1390  is flexible, at least in the distal portion including the articulation joint, so that articulation of the end effector  1300  can occur. Also apparent In  FIG. 14  is the control portion  1352  of the blade  1350 , which, like the jaw actuator  1390 , is flexible, at least in the distal portion including the articulation joint, and extends proximally back to the respective actuator at the device&#39;s control handle. 
     To support both the band  1390  and the control portion  1352  of the blade  1350  within the proximal articulation joint portion  1320  (partially removed and partially transparent in  FIG. 14 ), a support block  1426  is provided. This support block  1426  can have one groove in which to support the controls  1352 ,  1390  (in which it would have a cross-sectional Π-shape), two grooves in which to support, the controls  1352 ,  1390  (in which it would have a cross-sectional H-shape), two holes in which to support the controls  1352 ,  1390  (in which it would have a bisected vertically disposed rectangular cross-sectional shape), or any other similarly functioning configuration. In the illustration shown, the support block  1426  is the first exemplary shape. 
     To support both the band  1390  and the control portion  1352  of the blade  1350  within the articulating portion of the joint  1302 , an articulation support  1480  is provided. The articulation support  1480 , in a preferred embodiment, is similar to the dogbone  1080  present in the articulation joint of the devices shown in U.S. Pat. Nos. 7,404,508 and 7,491,080 (see, e.g.,  FIGS. 62 and 66  therein), in that it has a groove to support rods/bands passing therethrough but is different, at least, in that the articulation support  1480  is H-shaped to define separate upper and lower supporting chambers for each of the two controls  1352 ,  1390  to electrically insulate the bands from one another. Functioning of the articulation support  1480  is best shown with respect, to  FIGS. 16 and 17 . 
     When the articulation joint  1302  is aligned or straight, the controls  1352 ,  1390  are also straight within the articulation joint  1302 , as shown in  FIGS. 14 to 16 . In this orientation, the portions of the controls within the articulation joint  1302  do not touch any of the inner bearing surfaces of the articulation support  1480 . These bearing surfaces include left and right proximal surfaces  1620 ,  1621 , left and right intermediate surfaces  1622 ,  1623 , and left and right distal surfaces  1624 ,  1625 . When the articulation joint  1302  is articulated as shown in  FIG. 17 , for example, each of the controls  1352 ,  1390  touches at least one of these surfaces  1620 - 1625 . One of the controls  1352 ,  1390  is shown diagrammatically with dashed lines in  FIG. 17 . When articulated, the outer surface of the control  1352 ,  1390  touches approximately up to the entire outer intermediate surface  1622 ,  1623 , which, in this illustration is the right intermediate surface  1623 . The left intermediate surface  1622  is free from the touch of the control  1352 ,  1390 . In contrast, the control  1352 ,  1390  does not touch either of the outer proximal and distal surfaces  1621 ,  1625  (right in this case) but touches both of the inner proximal and distal surfaces  1620 ,  1624 . The position shown in  FIG. 17  is the far left articulated position of articulation joint  1302 . 
     The proximal articulation joint portion  1320  and the distal articulation joint portion  1310  define a chamber in which the support block  1426  is contained. This chamber is best shown in  FIGS. 16 and 17  and will be explained with regard to  FIG. 17 . The distal articulation joint portion  1310  define two opposing interior surfaces  1712 ,  1714  each at a similar acute angle with respect to the centerline of the distal articulation joint portion  1310  and opening in the proximal direction, likewise, together, the two portions  1322 ,  1324  of the proximal articulation joint portion  1320  define two similar opposing interior surfaces  1722 ,  1724  each at a similar acute angle with respect to the centerline of the proximal articulation joint portion  1320  but opening in the distal direction. 
     In the configuration of  FIGS. 13 to 17 , electrical conduction through the two jaws  1340 ,  1342  is accomplished by connecting one electrical pole to the proximal end of the jaw control band  1390  at the non-illustrated control handle. In one exemplary embodiment, the control band  1390  is insulated over its entire exterior surface with the exception of the proximal connection described and a portion at the jaw drive block  1370  where the control band  1390  is connected. In an alternative exemplary embodiment, the control band  1390  is bare and all other surfaces are insulated. Electrical conduction through the link  1360  is accomplished by electrically insulating the jaw drive block  1370  all over its exterior surface except for the band  1390  connection and the surface of the jaw drive block  1370  touching the proximal pivot, of the link  1360 . In one exemplary configuration, the outer surface of the jaw drive block  1370  boss and the proximal borehole inner surface of the link  1360  are both be tree from insulation. In the exemplar configuration of the drawings, on the other hand, the jaw drive block  1370  and the proximal borehole inner surface of the link  1360  are both insulated. In a similar manner, electrical conduction to the jaw  1340  from the link  1360  can occur by, for example, by having an insulative coating all over the lower jaw  1340  except for the inner surface of the jaw pivot hole and by not having insulative coating on the exterior of the jaw boss  1314 . With an insulating sleeve  1442  electrically separating the jaw  1340  from the clevis  1312 , electricity can be conducted to the jaw  1340 . To insure that electricity from the jaw  1340  does not conduct to anywhere other than the mouth surface  1444  of the jaw  1340 , insulation is not present at least on a portion of the mouth surface  1444 . 
     In one exemplary embodiment of the second pole electrical conduction path, the second electrical pole is connected electrically to the proximal end of a wire  1450  (illustrated diagrammatically by a dotted line in  FIG. 14 ). The wire  1450  extends through the sleeve  1330  and through the articulation joint  1302  by any appropriate lumen present in either part of the proximal articulation joint portion  1320  and in the distal articulation joint portion  1310 . By exiting at the clevis  1312  near the pivot point of the jaw  1342 , a small contact area can be left free from insulation and the wire  1450  connected there. Like jaw  1340 , to insure that electricity from the jaw  1342  does not conduct to anywhere other than the mouth surface  1446  of the jaw  1342 , insulation is not present at least on a portion of the mouth surface  1446 . 
     In another exemplary embodiment of the second pole electrical conduction path, the second electrical pole is connected electrically to the proximal end of the sleeve  1330 , which is insulated from the jaw control band  1390 . The sleeve  1330  is electrically conductively connected to at least one part  1322 ,  1324  of the proximal articulation joint portion  1320 . Next, the at least one part  1322 ,  1324  has a non-insulated surface electrically conductively connected to a non-insulated surface of the distal articulation joint portion  1310 . For example, the lower surface of the upper part  1322  that slides on the upper surface of the distal articulation joint portion  1310  can both be free from insulation and remain in electrical contact as the joint articulates. If the jaw  1340  is insulated from the distal articulation joint portion  1310 , then the surface facing the proximal tang of the jaw  1342  and the proximal tang can both be free from an insulating surface layer and, due to the direct sliding connection therebetween, the jaw  1342  becomes electrically conductively connected to the second pole. By insulating the remainder of the exterior surface of the jaw  1342  except for the mouth surface, the mouth surface becomes the only place that electricity can conduct from jaw  1342  to jaw  1340 . One exemplary embodiment of the insulatlve coating for the above configuration is a TEFLON® hardcoat anodization. 
       FIGS. 18 to 28  show a first exemplary embodiment of a control handle  1800  of the bipolar cautery and cutting device of the present invention. Within the first control handle housing  1802 , is a jaw control trigger  1810 , a blade control trigger  1820 , a blade-firing spool  1822 , and a passive articulation lock control trigger  1830 . A number of lumens/devices extend from the control handle  1800  to the end effector of the invention. The outermost hollow lumen is the sleeve  1330 . Coaxially disposed within the sleeve  1330  is a hollow passive articulation lock lumen  1840 . Coaxially disposed within the passive articulation lock lumen  1840  is a hollow jaw control lumen  1850  and coaxially disposed within the jaw control lumen  1850  is the distal end of the control portion  1352  of the blade  1350 . Each of these devices can be in any alternative form (e.g., rod, band, hollow lumen) as desired. 
     The jaw control trigger  1810  is pivotally connected inside the handle  1800 . The jaw control trigger  1810  has a cam surface  1812  against which a jaw cam follower  1860  moves. The jaw cam follower  1860  is fixedly connected to the jaw control lumen  1850  in the longitudinal direction of the sleeve  1330  to cause the close/open movement of the jaws as the jaw control trigger  1810  is squeezed/released. An overforce protection device  1870  is provided in the handle  1800  and limits the amount of force that is imparted upon the jaw control lumen  1850  when closing the jaws. The overforce protection device  1870 , in the exemplary embodiment shown, is disposed within the jaw cam follower  1860 . Not illustrated in  FIG. 18  is an overforce compression spring disposed between the jaw cam follower  1860  and an overforce adjustment knob  1872 . The jaw control trigger  1810  can be a simple squeeze trigger or a click-on/click-off device.  FIG. 19  is an illustration of an exemplary embodiment of the latter configuration. 
       FIG. 18  also illustrates a battery assembly  1880  contained within the grip portion  1804  of the control handle  1800 .  FIGS. 20 and 21  illustrate one exemplary configuration of how the battery is placed within and removed from the grip portion  1804 . A trapdoor  2010  is mounted pivotally at the bottom of the grip portion  1804  of the handle  1800 . By pressing a trapdoor release button  2020 , the trapdoor  2010  springs open, for example, with the assistance of a non-illustrated torsion spring. At a side of the battery assembly  1880  (for example, the upper side) is a first part  2080  of a connector assembly for removably securing the battery assembly  1880  within the grip portion  1804  of the handle  1800 . Within the handle  1800  is a second part  2082  of the connector assembly that, together with the first part  2080 , removably secures the battery assembly  1880  within the grip portion  1804  and electrical connects circuitry within the battery assembly  1880  to the jaws of the end effector for supplying the radio-frequency signal thereto. 
     As shown in  FIGS. 20 and 21 , the battery assembly  1880  has a trapdoor flange  2090  that operatively Interacts with a battery eject flange  2012  at the pivoting end of the trapdoor  2010 . In this configuration, when the trapdoor  2010  is released from its closed and locked position, the torsion spring, depending on the magnitude of its spring constant, will automatically eject the battery assembly  1880  from the handle grip  1804  to a small or large distance. In the former configuration, it is desirable for the battery to be ejected only partially so that the operating room staff can easily grab the ejected battery from the handle  1800  without touching the handle  1800  itself. In the latter configuration, the surgeon can place the handle grip  1804  over a battery disposal container and, by pressing the trapdoor release button  2020 , the battery assembly  1880  will be ejected from the handle  1800  completely and will fall into the disposal container. As such, the operating room staff can easily and quickly install a replacement battery assembly  1880 . 
     It is noted here that the handle  1800  and its internal components are entirely free from electronic circuitry. This is a unique and significant aspect of the invention. By placing all of the power generation, regulation, and control circuitry of the cautery device of the invention within the battery assembly  1880 , the handle  1800  and end effector  100 ,  1300  can be made with entirely low-cost and disposable components. With such a configuration, all of the expensive circuitry can be reused repeatedly, at least until the circuitry or battery fails. Under expected normal conditions, the life of the battery assembly  1880  will extend to hundreds of uses. 
       FIGS. 22 to 28  illustrate operation of the handle  1800 . In  FIG. 22 , the handle  1800  is in its rest state with no triggers actuated.  FIGS. 23 and 24  show the jaw-closing trigger  1810  in intermediate and fully closed positions, respectively. As can be seen from  FIG. 22 , the jaw cam follower  1860  moves back with the jaw control lumen  1850 . The jaws are fully closed when the jaw cam follower  1860  is at the position shown in  FIG. 23 . The remaining distance traveled by the jaw-closing trigger  1810  does not pull the jaw control lumen  1850  further proximally. Instead, the overforce protection device  1870  begins to actuate by compressing the non-illustrated compression spring disposed between the jaw cam follower  1860  and the overforce adjustment knob  1872 . This configuration insures that sufficient force is employed against tissue disposed between the jaws of the end effector. 
     The view of  FIG. 25  shows the jaw-closing trigger  1810  in the almost fully depressed position (locked by the device of  FIG. 19 , for example) and the blade control trigger  1820  also in the fully depressed position. When the blade control trigger  1820  is depressed, the uppermost end of the trigger  1820 , resting inside a blade control spool  1822 , moves distally to carry the spool  1822  distally along the jaw control lumen  1850 . The spool  1822  is fixedly connected to the control portion  1352  of the blade  1350  through, for example, a pin  1824  that passes through the spool  1822  orthogonal to the spool axis and through the control portion  1352 . In this way, any movement of the spool  1822  is translated into a corresponding movement of the blade  1350 . A clearance for the pin  1824  is cut out of the bottom of the jaw control lumen  1850  as shown in  FIGS. 18 ,  25  and  26 , for example. An exemplary embodiment of the jaw control lumen  1850  has the lumen in the shape of a rod from the proximal end (shown in  FIGS. 25 and 26 ) all the way to the articulation joint, at which point it can be shaped as shown in  FIGS. 14 to 17 , for example. A vertical slot can be formed all the way along the bottom of the jaw control lumen  1850  to allow for slidable translation of the control portion  1352  of the blade  1350  with respect to the jaw control lumen  1850  and to the sleeve  1330 . The vertical slot also adds lateral support to the band-shaped control portion  1352  all along the extent of the jaw control lumen  1850 . 
     As can be seen in  FIG. 25 , the blade control trigger  1820  has a proximal cam surface  2532  that fits into a cam recess  2512  when both triggers  1810 ,  1820  are in their rest state as shown in  FIGS. 18 and 27 . However, when the jaw-closing trigger  1810  is depressed, as shown in  FIG. 25 , the cam surface  2532  cannot reside within the cam recess  2512 . This configuration is advantageous to assist with retraction of the blade  1350 . If for example, the blade  1350  were to stick inside tissue between the jaws after cutting, a proximally directed force on the control portion  1352  would be needed to remove the blade  1350 . To eliminate the need for a separate blade return bias device, the invention takes advantage of the relatively strong return bias device (non-illustrated) present for the jaw-closing trigger  1810 . This designed “mis-alignment” of the cam surface  2532  and the cam recess  2512  permits the jaw closing return bias device to retract the blade  1350  automatically when the jaw-closing trigger  1810  is allowed to return to its rest position. As shown in the progression of  FIGS. 25 to 26 , return of the depressed jaw-closing trigger  1810  presses the trigger  1810  against the cam surface  2532  up until the cam surface  2532  returns, once again, into the cam recess  2512 , as shown in  FIG. 27 . 
     At any time during the steps of tissue clamping, tissue cutting, and trigger returning with the cautery/cutting device of the invention, the surgeon is able to articulate the end effector  100 ,  1300  as desired.  FIG. 28  illustrates an exemplary configuration for unlocking the articulation joint to, thereafter, permit passive articulation of the end effector  100 ,  1300 . The passive articulation lock control trigger  1830  is operatively connected to a hollow articulation spool  2832 , which articulation spool  2832  is longitudinally fixedly connected to the passive articulation lock lumen  1840  and coaxial disposed and longitudinally slidable with respect to the jaw control lumen  1850 . When the passive articulation Sock control trigger  1830  is depressed, the articulation spool  2832  translates proximally and moves the passive articulation lock lumen  1840  correspondingly to remove an obstruction to passive articulation. An exemplary embodiment of such obstruction is depicted in  FIG. 29 . There, the passive articulation lock lumen  1840  is shown within the sleeve  1330 . The distal end of the passive articulation lock lumen  1840  defines an articulation lock cutout  2942  shaped to correspond to a proximal end of an articulation locking key  2944 . The locking key  2944  can be press-fitted in the cutout  2942  or attached therein in any similar manner. With the locking key  2944  attached to the end of the passive articulation lock lumen  1840 , any translation of the passive articulation lock lumen  1840  will move the locking key  2944  correspondingly, in the exemplary embodiment, shown, the distal end of the locking key  2944  is formed with a protrusion  2946  shaped to interlock with at least one keyhole located on the proximal end of the distal articulation joint portion  1310 . In this embodiment, there are three keyholes  2912 ,  2913 ,  2914  to allow the end effector  100 ,  1300  to be locked in one of three orientations. Of course, this number is not limiting and neither is the placement of the keyholes  2912 ,  2913 ,  2914 . Further, the key-keyhole configuration can be reversed as desired. 
       FIGS. 30 to 37  illustrate other exemplary configurations of a cordless, entirely self-contained cautery and cutting device of the Invention. The second control handle  3000 , like the first control handle  1800 , has a jaw control trigger  3010  and a blade control trigger  3020 . This exemplary embodiment of the control handle  3000  has a shaft rotation knob  3030 , which allows the surgeon to rotate the shaft, and, thereby, the entire end effector assembly at the distal end of the device. Further, this exemplary embodiment is shown without a passive articulation end effector but can include one as described herein. In such an embodiment, the knob  3030  can be pulled proximally sufficiently far to disengage the passive articulation lock, such as the locking key  2944  described above (The mechanism is described in detail in U.S. Pat. No. 7,491,080 to Smith et al., already incorporated herein by reference, and, therefore, it is not necessary to set forth, again, this disclosure.) Simply put, a small proximal movement of the knob  3030 , retracts the locking key  2944  to permit passive articulation of the articulation joint  1302  and release of the knob  3030  will allow the knob  3030  to spring distally (under the force of a return bias device, e.g., a compression spring) and re-engage the locking key  2944  with the distal articulation joint portion  1310  to prevent further passive articulation 
     Also present on this handle  3000  is a cautery firing trigger  3040 . With the cautery firing trigger  3040  immediately above the blade control trigger  3020 , operation of the device is significantly simplified and ergonomic. When operating this handle  3000 , the surgeon depresses the jaw control trigger  3010 , as shown in  FIG. 32 , to compress the tissue between the jaws. The jaw control trigger  3010  has a blade cam flange  3112  and a proximal lever  3114 . As shown in the progression from  FIG. 31 to 32 , depression of the jaw control trigger  3010  causes the blade cam flange  3112  to pivot counter-clockwise away from a blade shuttle post  3142  of the blade shuttle  3144 . Depression also causes the proximal lever  3114  to pivot counter-clockwise and, via a link  3146 , cause a trigger sled  3118  to move proximally. Without the blade cam flange  3112  being moved from the rest position shown in  FIG. 31 , the cam surface  3113  is in a position preventing the blade shuttle  3144  from moving distally, thereby preventing any movement of the end effector blade until the jaw control trigger  3010  is depressed. 
     With the jaw control trigger  3010  depressed, however, the blade shuttle  3144  is free to move distally, such depression and movement being shown in  FIG. 34 . In this position, the blade shuttle post  3142  rests within a slot formed by the cam surface  3113  and is prevented from moving any further distally. The distal end of the blade shuttle  3144  also has a pin within a groove that limits distal movement of the blade shuttle  3144  past the position shown in  FIG. 34 . A non-illustrated compression spring is disposed to move the blade control trigger  3020  distally when pressure is removed therefrom. If the blade is stuck in any way, proximal movement of the blade and blade shuttle  3144  may be halted before returning to the rest position shown in  FIG. 32 , for example. The cam surface  3113 , however, is shaped to force the blade shuttle post  3142  proximally any time the jaw control trigger  3010  returns to the rest position shown, for example, in  FIG. 30 . This means that the jaw control trigger  3010  acts as a return assist for the blade and its movement assembly. 
     With the jaws compressing the tissue therebetween, cautery occurs by presenting the index finger (for example) at the cautery-firing trigger  3040  and depressing the cautery-firing trigger  3040 . Without further movement of any part of the surgeon&#39;s single hand, the index finger can be slid downward along the cautery-firing trigger  3040  and immediately contact the surface of the blade control trigger  3020 . This sliding movement of the finger can be quickly translated into a depression movement of the blade control trigger  3020  to cut the now-cauterized tissue between the jaws, which is shown in  FIG. 34 . At this point, the surgeon&#39;s fingers are relatively aligned with one another and are grasping the blade-firing trigger  3020 , the jaw control trigger  3010 , and the grip portion  3004 . To restart the process again, all that the surgeon needs to do is to release the fingers holding the blade-firing trigger  3020  and the jaw control trigger  3010  and to reposition the jaws about the new tissue to be cauterized and cut. The process is, then, repeated as desired. 
     The battery assembly of the present invention is not simply a bipolar cauterization power supply. In prior art bipolar cautery devices, all of the power generation and regulation circuitry exists in expensive counter-top boxes, each of which is required to be plugged into an electric mains to function. A power distribution cord connects the prior art cautery device to the counter-top box, which cord limits the range of movement of the surgeon and adds cost to those devices. The invention, in contrast, entirely eliminates the need for the cord and the counter-top box by providing a self-contained power supply and regulation device  1880 ,  3500 , also referred to herein as the battery assembly, which is explained with regard to  FIGS. 34 and 35 . 
       FIG. 34  shows a battery connection assembly with non-illustrated conductive traces connecting regulated power lines from a distribution panel  3410  to the two electrical poles for each of end effector jaws. The distribution panel  3410  has a set of conductors  3420  to be connected electrically to individual supply ports  3512  of a supply array  3510 . At least one power cell  3520  (e.g., a set of 2 to 6 lithium polymer cells having a high discharge current capacity on the order of 10-15 times the rated storage capacity (known as 10-15C) is electrically connected to voltage control circuitry  3530 , which can be, for example, a buck power supply controlling the output signal voltage. Radio-frequency signal generating circuitry  3540  receives the output signal and converts it Into a high-frequency alternating-current signal, which AC signal is supplied to the end effector jaws through the conductive supply ports  3512  and the distribution panel  3410 . 
     With such a configuration, the control handle  3000  becomes entirely free from any power supply or power circuitry. This means that the relatively expensive supply and circuitry can be reused in the inventive interchangeable battery assembly  3500  and the relatively cheap handle parts of the mechanical control handle  3000  with its shaft and end effector can be thrown away after the single operative use. If desired, the relatively expensive parts can be even further subdivided as shown In  FIGS. 36 and 37 . The battery assembly  3600  of these figures is similar in function and shape to the battery assembly  3500 . However, the radio-frequency signal generating circuitry  3540  is contained within a separable signal processing sub-assembly  3640  having a set of non-illustrated circuit connection leads on a signal connection surface(s)  3642 , which leads are connected to and from the radio-frequency signal, generating circuitry  3540 . If the two sub-assemblies  3620 ,  3640  of the battery assembly  3600  are each provided with an appropriate part of a connection device, such as the tongue-and-groove configuration shown in  FIG. 37 , then the user has the ability to replace either the battery/boost sub-assembly  3620  or the signal processing sub-assembly  3640  as desired. 
     Even though it might be beneficial if the battery assembly  3500  is hermetically sealed for medical use (because the control handle defines an internal battery chamber  3406  that can be shut off from the aseptic operating environment), the battery assembly  3500  need not be autoclavable. An “aseptic seal” or “aseptically sealed,” as used herein, means a seal that sufficiently isolates a compartment (e.g., inside a handle) and components disposed therein from a sterile field of an operating environment into which the handle has been introduced so that no microbiological organisms from one side of the seal are able to transfer to the other side of the seal. Further, “hermetic” or “hermetically sealed” means a seal, or container that is substantially air tight and prevents microorganisms from passing across the seal or into or out of the container. 
     With the control handle  3000  in the operating suite, operating staff can request circulating staff outside the aseptic field to insert the battery assembly  3500  into the chamber  3406 . The aseptic control handle  3000  with the inserted battery assembly can be made entirely aseptic for use in the operating room after operating staff closes the battery door  3430 , which door has a hermetic seal. Of course, the battery assembly  3500  can be made to autoclave and, therefore, the battery assembly can be brought into the sterile file as desired. 
     Like the first control handle  1800 , the second control handle  3400  also can be provided with a battery assembly ejection device. As shown in  FIGS. 33 and 34 , the battery door  3430  is mounted pivotally to a lower part of the grip portion  3004  of the control handle  3400 . By pressing a trapdoor release button  3320 , the battery door  3430  springs open, for example, with the assistance of a non-illustrated torsion spring. As shown in  FIGS. 33 and 34 , the battery assembly  3500  has a door cam surface  3390  that operatively interacts with a battery eject flange  3312  at the pivoting end of the battery door  3430 . In this configuration, when the battery door  3430  is released from its closed and locked position, the torsion spring, depending on the magnitude of its spring constant, will automatically eject the battery assembly  3500  from the handle grip  3004  to a small or large distance. As above, the battery assembly  3500  can be ejected only partially so that the circulating staff can easily grab the ejected battery from the handle  1800  without touching the handle  1800  itself. Alternatively, any of the operating staff can place the handle grip  3004  over a battery disposal container and, by pressing the trapdoor release button  3320 , eject the battery assembly  3500  from the handle  3000  completely, permitting it to fall into the disposal container. As such, the operating/circulating room staff can easily and quickly install a replacement battery assembly  3500 . 
     The functional components of the embodiment of the third control handle  3800  in  FIGS. 38 to 43  are similar to the second control handle  3000 . In this embodiment, however, the trigger mechanisms operate in a different way and the radio-frequency signal generating circuitry  3840  is located in the disposable control handle  3800  and not within the battery assembly  3880 . 
     The third control handle  3800 , like the first control handle  1800 , has a jaw control trigger  3810 , a blade control trigger  3820 , and a grip portion  3804 . Here, a blade return spring  3826  provides a distally directed bias to keep a blade control spool  4022  in a proximal position (shown in  FIG. 40 , for example) and, thereby, the blade in a retracted position. 
     Instead of an articulation lock trigger  1830 , this embodiment has a rotatable knob  3830 . The shaft rotation knob  3830  allows the surgeon to rotate the shaft and, thereby, the entire end effector assembly at the distal end of the device. This exemplary embodiment is shown without a passive articulation end effector but can include one as described herein. 
     Also present on this handle  3800  is a cautery-firing trigger  4240 . In this embodiment, the cautery-firing trigger  4240  is immediately above a thumb rest  4204  on the side of the grip portion  3804  of the control handle  3800 . The cautery-firing trigger  4240  and the thumb rest  4204  can be mirror symmetrical on both sides of the grip portion  3804 . 
     The progression from  FIGS. 38 to 41  reveals a novel multi-safety-trigger assembly that prevents the blade from firing unless and until the jaws are closed. This safety-trigger assembly includes the jaw control trigger  3810 , the blade control trigger  3820 , a jaw trigger link  3812 , a jaw trigger slide  3814 , a jaw spool  3816 , a blade control pivot  3822 , a blade control pin  3824 , a blade control spool  4022 , and a jaw overforce protection device  3850 . This exemplary embodiment is shown without a passive articulation end effector but can include one as described herein. 
     The jaw control trigger  3810  has an upper flange  3811  and a pivot  3912  about which the jaw control trigger  3810  can be rotated. The proximal end of the upper flange  3811  is connected pivotally to a proximal end of the jaw trigger link  3812 . The distal end of the jaw trigger link  3812  is pivotally connected to a proximal portion of the jaw trigger slide  3814 . The jaw trigger slide  3814  has a guide track  3914  in which the pivot  3912  is disposed. The proximal end of the jaw trigger slide  3814  has an upwardly projecting spool control flange  3918  engaged with the jaw spool  3816  to translate the jaw spool  3816  longitudinally as the jaw trigger slide  3814  translates longitudinally. To carry out the jaw movement motion (open/close), the surgeon exerts pressure upon the jaw control trigger  3810  towards the grip  3804  to pivot the jaw control trigger  3810  about the pivot  3912  to the position shown in  FIG. 39 . At the same time, the jaw link  3812  pivots and exerts a proximally directed force to the jaw trigger slide  3814  to move the jaw trigger slide  3814  to the proximal position, also shown in  FIG. 39 . At the end of the jaw link  3812  movement, the distal end of the jaw link  3812  is higher than the proximal end of the jaw link  3812 . This movement of the jaw trigger slide  3814  causes the jaw spool  3816  to translate proximately a corresponding amount. Closing movement of the jaws is effected because the jaw spool  3816  is longitudinally connected to a jaw movement lumen  3990 . With respect to the configuration shown in  FIGS. 1 to 11 , the jaw movement lumen  3990  is the jaw actuation wires  20 ,  30 , and, with respect to the configuration shown in  FIGS. 13 to 17 , the jaw movement lumen  3900  is the jaw actuator  1390 . 
     The blade control trigger  3820  moves, initially, with the  FIGS. 38 to 39  movement of the jaw control trigger  3810  but does not cause any blade movement. A guide groove  3921  is present to prevent firing of the knife while the jaws remain open and the blade control trigger  3820  needs to be moved out of the distal vertical portion of the guide groove  3921 . As can be seen best in  FIG. 41 , the guide groove  3921  does not allow the blade control trigger  3820  to move proximally until it enters a lower horizontal portion of the guide groove  3921 , and entry cannot, occur until the jaw control trigger  3810  is also in the horizontal position shown in  FIGS. 39 to 41 ; thus, the invention ensures that the jaws are closed when the blade is required to move. Actuation of the blade control trigger  3820  from the position shown in  FIG. 39  to the position shown in  FIG. 40  removes the safety that prevents firing of the blade. When in the position of  FIG. 40 , the blade control trigger  3820  can now be translated longitudinally proximally (i.e., not in a circular motion about its pivot) from the position shown in  FIG. 40  to the position shown in  FIG. 41 . 
     Present on the jaw control trigger  3810  is a blade actuation boss  3813  (which is shown within a boss groove  4024  hidden behind a lower portion of the blade control pivot  3822  in  FIG. 40 ). As the blade control trigger  3820  (along with jaw control trigger  3810 ) is moved proximally, the blade actuation boss  3813  carries/transports/moves the lower end of the blade control pivot  3822  about its pivot point in a counter-clockwise direction. Correspondingly, the upper portion of the blade control pivot  3822 , with its pin groove  4026  carrying the blade control pin  3824 , is moved counter-clockwise about the pivot point of the blade control pivot  3822 . The blade control pivot  3822  is forked at the upper portion to accommodate the blade control spool  4022  therein and to capture the blade control spool  4022  so that the blade control spool  4022  moves distally when the blade control pin  3824  is moved. The blade control spool  4022  is connected longitudinally to the blade movement lumen  4052  that causes the distal/proximal movement of the blade. With respect to the configuration shown in  FIGS. 1 to 11 , the blade movement lumen  4052  is the cutting actuation wire  10  and, with respect to the configuration shown in  FIGS. 13 to 17 , the blade movement lumen  4052  is the control portion  1352  of the blade  1350 . 
     Operation of the device is significantly simplified and ergonomic. When operating this handle  3800 , the surgeon depresses the jaw control trigger  3810  as shown in  FIG. 39 . The blade control trigger  3820  follows the movement of the jaw control trigger  3810  without actuating the blade. With the jaws compressing the tissue therebetween, cautery occurs by presenting the thumb (for example) at the cautery-firing trigger  4240  and depressing the cautery-firing trigger  4240 . Next, as shown from the transition from  FIG. 39  to  FIG. 40 , the blade control trigger  3820  is depressed. This action does not move the blade, however. Instead, it merely acts to unlock an ability to move the blade; in essence, it is a safety release. With the blade control trigger  3820  in the depressed position, the combined sub-assembly of the jaw control trigger  3810  and the blade control trigger  3820  can be moved proximally, as shown by the transition from  FIG. 40  to  FIG. 41 . Such movement is not circular (as are the other embodiments described above). Rather, the movement is linear. With such linear movement, a corresponding movement of the blade and cutting of the now-cauterized tissue between the jaws is carried out. At this point, the surgeon&#39;s fingers are relatively aligned with one another and are grasping the blade-firing trigger  3020 , the jaw control trigger  3010 , and the grip portion  3004 . To restart the process again, all that the surgeon needs to do is to release the fingers holding the blade firing and jaw control triggers  3020 ,  3010  (or push the fingers holding the triggers  3020 ,  3010  distally) and reposition the jaws about the new tissue to be cauterized and cut. The process is, then, repeated as desired. 
     Like the configuration of  FIGS. 30 to 34 , the battery assembly  3880  is removable from a compartment  4305  within the grip portion  3804  of the control handle  3800  and is interchangeable with other similar battery assemblies  3880 . Ejection of the battery assembly  3880  can be carried out, for example, with a battery ejection assembly similar to the battery ejection assembly  2010 ,  2012 ,  2090  shown in  FIGS. 20 and 21 , but other similarly functioning assemblies can be employed as well. Unlike the configuration of  FIGS. 30 to 34 , the radio-frequency signal generating circuitry  3840  is not contained within the batten assembly  3880 . Instead, it is located in a proximal location within the upper portion of the control handle  3800 . (Of course, the circuitry  3840  can be located anywhere in the control handle  3800  in this embodiment.) In such a configuration, the radio-frequency signal generating circuitry  3840  can be disposed when the control handle  3800  is discarded. 
     In an advantageous alternative exemplary embodiment of the radio-frequency signal generating circuitry  3840  and disposable control handle  3800 , the control handle  4400  has a removable and interchangeable circuit casing  4406 , which is hermetically sealed and autoclavable. The circuit casing  4406  houses the radio-frequency signal generating circuitry  3840  and, therefore, enables the reuse of this circuitry  3840 . Electrical connection of the radio-frequency signal generating circuitry  3840  can be effected with leads  4608 , for example, made of gold-plated copper. Removable connection of the circuit casing  4406  can be made by many mechanical configurations. For example, a T-slide connection, a tongue-and-groove connection, a press-fit connection, and even a magnetic connection. 
       FIGS. 47 to 50  illustrate another exemplary embodiment of a distal end of an electrocautery sealing and cutting surgical end effector  4700  of the present invention. This end effector  4700  is not shown with an articulation joint although the articulation joint of the invention can be employed here equally. This embodiment acknowledges characteristics of forming the jaws  4710 ,  4720  from a solid piece of material and, based thereupon, forms each of the jaws  4710 ,  4720  from two pieces of different materials—the outer piece  4712 ,  4722  being of a material having good heat insulating properties and the inner piece  4714 ,  4724  being of a material having good strength properties. Each of the inner pieces  4714 ,  4724  has a mouth surface  4716 ,  4726  coated with an electrically conductive material to provide the radio-frequency signal to tissue disposed between the jaws  4710 ,  4720 . For example, the conductor material can be plates of stainless steel or gold-coated copper. Electricity is presented to the mouth surfaces  4716 ,  4726  through portions of the end effector  4700  as in the previously described embodiments or, in the exemplary embodiment shown, through two insulated wires  4730 ,  4740  shown, respectively with differently dashed lines. Each of the wires  4730 ,  4740  terminates at a jaw connection  4718 ,  5028  and the wire is electrically connected to the conductive coating of the mouth surfaces  4716 ,  4726 . 
       FIGS. 51 to 53  illustrate another exemplary embodiment of a distal end of a passively articulating electrocautery sealing and cutting surgical end effector  5100  of the present invention. This end effector  5100  is shown with an articulation joint but the articulation joint can be removed if desired. Like the embodiment of  FIGS. 47 to 50 , this embodiment acknowledges the characteristics of forming the jaws  5110 ,  5120  from a solid piece of material and, instead, forms each of the jaws  5110 ,  5120  from two pieces of different materials with the outer piece  5112 ,  5122  being of a material having good heat insulating properties and the inner piece  5114 ,  5124  being of a material having good strength properties. Each of the inner pieces  5114 ,  5124  has a conductive mouth surface providing the radio-frequency signal to tissue disposed between the jaws  5110 ,  5120 . For example, the conductor material can be plates of stainless steel and the outer piece  5112 ,  5122  can be stainless steel with an insulating covering. Electricity is presented to the mouth surfaces through portions of the end effector  5100  as in the previously described embodiments or, in the exemplary embodiment shown, through two insulated wires  5140  illustrated, respectively, with differently dashed lines. Each of the wires  5140  terminates at a jaw connection  5118 ,  5128  and is electrically connected to the conductive coating of the mouth surfaces of the inner pieces  5114 ,  5124 . 
     In contrast to the previous end effector embodiments where the jaws have independent pivoting devices, the end effector  5100  includes a single jaw pivoting assembly. In this embodiment, each side of the clevis  5130  has a jaw pivot slot  5132  in which slides a jaw pivot rod  5134 . As best shown in  FIG. 53 , the proximal portion of each of the jaws  5110 ,  5120  defines a control slot  5326 ,  5328  in which the jaw pivot rod  5134  slides. A jaw control rod  5330  is connected longitudinally to the jaw pivot rod  5134  and longitudinal movement of the jaw control rod  5330  causes the jaw pivot rod  5134  to slide along the jaw pivot slot  5132  and move correspondingly within the control slots  5326 ,  5328  of the jaws  5110 ,  5120 . As shown in  FIGS. 51 to 53 , distal movement of the jaw control rod  5330  opens the jaws  5110 ,  5120  and proximal movement of the jaw control rod  5330  closes the jaws  5110 ,  5120 . 
     Articulation of the end effector  5100  is carried out at a control handle. When a passive articulation lock control trigger is actuated, a passive articulation lock lumen  5340  is moved proximally to remove an obstruction to passive articulation. An exemplary embodiment of such obstruction is depicted in  FIGS. 52 and 53 . There, the passive articulation lock lumen  5340  is shown within the sleeve  1330 . The distal end of the passive articulation lock lumen  5340  defines an articulation lock cutout  5342  shaped to correspond to a proximal end of an articulation Socking key  5344 . The locking key  5344  can be press-fitted in the cutout  5342  or attached therein in any similar manner. With the locking key  5344  attached to the end of the passive articulation lock lumen  5340 , any translation of the passive articulation lock lumen  5340  will move the locking key  5344  correspondingly. In the exemplary embodiment shown, the distal end of the locking key  5344  is formed with a protrusion  5346  shaped to interlock, with at least one keyhole located on the proximal end of the clevis  5130 . In this embodiment, there are three keyholes  5332 ,  5333 ,  5334  to allow the end effector  5100  to be locked in one of three orientations. Of course, this number is not limiting and neither is the placement of the keyholes  5332 ,  5333 ,  5334 . Further, the key-keyhole configuration can be reversed as desired. 
     The embodiments discussed above each include manual actuation of the grasping and cutting sub-assemblies.  FIGS. 54 to 60  illustrate an embodiment where the jaw movement mechanism is manual and the blade movement mechanism is electrically powered and controlled.  FIGS. 61 to 64  illustrate an embodiment where the jaw and blade movement mechanisms are both electrically powered and controlled. Thus, any strenuous hand activity by the surgeon required during the cauterization/cutting procedure for prior art devices is substantially reduced or entirely eliminated. In all of these figures, the end effector is removed for clarity.  FIGS. 65 to 67  illustrate how the electronically controlled grasping and cutting device of the present invention reduces the number of steps required to carry out a single cauterization/cutting procedure. 
     In the exemplary embodiment of the blade-powered device  5400  of  FIGS. 54 to 57 , a non-illustrated removable battery is inserted into a battery compartment  5405  within a handle portion  5404  of the device  5400 . A jaw control trigger  5410  is pivotally connected to the device  5400  and has a flange  5412  pivotally connected to an end of a jaw control rod  5490 . Thus, pivoting movement of the jaw control trigger  5410  causes a longitudinal translation movement of the jaw control rod  5490 . The jaw control rod  5490  is longitudinally connected to a manual jaw slide  5492 , which is shown by itself in  FIG. 55 . Behind the mount  5494  is a connection that causes a corresponding translation of the jaw actuator  1390  with any movement of the manual jaw slide  5492 . 
     The manual jaw slide  5492  is slidably disposed upon a blade control slide  5422 , shown by Itself in  FIG. 56 . Both the manual jaw slide  5492  and the blade control slide  5422  are shown separate from the device  5400  in  FIG. 57 . As shown in  FIG. 57 , the blade control slide  5422  has a protruding boss  5426  that allows interaction of the blade control slide  5422  with the manual jaw slide  5492 . In particular, closing of the jaws by a distal movement of the manual jaw slide  5492  results in a partial distal movement of the blade control slide  5422 . 
     Movement of these parts and control of the both the blade and jaw mechanisms are illustrated in  FIGS. 58 to 60 . In  FIG. 58 , the jaw control trigger  5410  is removed. In the proximally disposed orientation of both the manual jaw slide  5492  and the blade control slide  5422  in  FIG. 58 , the jaws are open and the blade is retracted. With a depression of the jaw control trigger  5410 , the jaw control rod  5490  moves distally, causing the jaw actuator  1390  to move distally and close the jaws. The jaw control trigger  5410  has a sensor  5414  that detects a fully depressed position thereof. When this sensor  5414  (e.g., a microswitch) is actuated or detects the fully depressed position, a jaws-closed state is recognized, thereby indicating that the blade can be moved safely within the jaws of the end effector. As such, electronics  5440  connected to the sensor  5414  powers the cautery device to deliver energy to the tissue disposed between the jaws. When the cauterization process is complete, tissue cutting can commence. The electronics  5440  detects this state and actuates a blade control servo  5420 . In the exemplary embodiment shown, actuation of the blade control servo  5420  causes a counter-clockwise rotation of the blade movement crank  5424 , which, due to the steady positioning of the manual jaw slide  5492 , allows the blade control slide  5422  (along with the blade control servo  5420 ) to move distally from the blade-retracted position shown in  FIG. 59  to the blade-extended position shown in  FIG. 60 . Other non-illustrated microswitches and/or circuitry can detect a completed blade extension and, thereafter, cause the blade control servo  5420  to reverse (clockwise movement) and, thereby, withdraw the blade from the cauterized tissue disposed between the jaws to complete the tissue cutting process. As shown, the blade movement crank  5424  remains substantially still as the jaws are closed. 
     A return spring  5496  can be disposed to bias the jaw control rod  5490  distally to, thereby, cause jaw separation when the surgeon is not depressing the jaw control trigger  5410 . Similarly, the blade control slide  5422  can be biased (e.g., spring-loaded) in a proximal direction to keep the blade in the retracted position when at a steady state and to assist in removal from cauterized tissue between the jaws when stuck thereto. 
     In the exemplary embodiment of the jaw-and-blade-powered device  6100  of  FIGS. 61 to 64 , a non-illustrated removable battery is inserted into a battery compartment  6105  within a handle portion  6104  of the device  6100 . A jaw control trigger  6110  is pivotally connected to the device  6100  but, in this embodiment, has no mechanical connection to control of the jaws. Instead, all control of the jaws occurs through a sensor  6114  that detects one or more depressed positions of the jaw control trigger  6110 . When this sensor  6114  (e.g., a single or multi-position micros witch) is actuated or detects a partially depressed position, it sends a signal corresponding to the state of compression to jaw control circuitry  6142 , which, in turn, controls movement of a jaw-movement servo  6144 . 
     If jaw control is dependent only upon a fully closed jaw control trigger position, then the servo  6144  moves the jaws from the open to closed position when the jaw control trigger  6110  is fully depressed. On the other hand, if jaw control is dependent upon a relative jaw control trigger position, then the servo  6144  moves the jaws between the jaw-open to jaw-closed position corresponding to a degree of depression of the jaw control trigger  6110 . Either way, the circuitry  6142  causes the jaw control servo  6144  to rotate the jaw movement crank  6146  (e.g., counter-clockwise) and move the automatic jaw slide  6192  distally to effect distal movement of the jaw actuator  1390 , which, in turn, closes the jaws. Thus, pivoting movement of the jaw control trigger  6110  causes a corresponding electronically controlled and regulated translation of the jaw actuator  1390 . With appropriately positioned non-illustrated force sensors, control of the jaw-movement servo  6144  can be regulated to prevent compression force upon tissue disposed between the jaws from exceeding a certain pre-set maximum value (and, conversely, can be regulated to insure compression force upon tissue disposed between the jaws exceeds a certain pre-set minimum value). 
     The automatic jaw slide  6192  is slidably disposed upon a blade control slide  5422  in the device  6100 . As in the blade-powered assembly of  FIGS. 54 to 60 , closing of the jaws by distal movement of the automatic jaw slide  6192  results in a partial distal movement of the blade control slide  5422 . 
     Movement of these parts and control of the both the blade and jaw mechanisms are illustrated in  FIGS. 62 to 64 , in which, the jaw control trigger  6110  is removed for clarity. In the proximally disposed orientation of both the automatic jaw slide  6192  and the blade control slide  5422  in  FIG. 62 , the jaws are open and the blade is retracted. With a depression of the jaw control trigger  6110 , the jaw control circuitry  6142  causes the jaw control servo  6144  to move the automatic jaw slide  6192  distally, causing the jaw actuator  1390  to move distally and close the jaws, as shown from the progression from  FIG. 62  to  FIG. 63 . 
     With the jaws in a closed position (which can be detected by the circuitry  6142 ), cautery electronics  6140 , also connected to the sensor  6114  and/or the jaw movement circuitry  6142 , power the cautery portions of the jaws to deliver energy to the tissue disposed therebetween. When the cauterization process is complete, tissue cutting can commence. The cautery electronics  6140  detects this end state and actuates a blade control servo  5420 . In the exemplary embodiment shown, actuation of the blade control servo  5420  causes a counter-clockwise rotation of the blade movement crank  5424 , which, due to the steady positioning of the automatic jaw slide  6192 , allows the blade control slide  5422  (along with the blade control servo  5420 ) to move distally from the blade-retracted position shown in  FIG. 63  to the blade-extended position shown in  FIG. 64 . Other non-illustrated microswitches and/or circuitry can detect a completed blade extension and, thereafter, cause the blade control servo  5420  to reverse (clockwise movement) and, thereby, withdraw the blade from the cauterized tissue disposed between the jaws to complete the tissue cutting process. As shown, the blade movement crank  5424  remains substantially still as the jaws are closed. 
     A return spring can be disposed to bias the jaw and blade servos  5402 ,  6144  proximally to, thereby, cause jaw separation and retraction of the blade when the surgeon is not depressing the jaw control trigger  6110  and/or to assist in removal of the blade from cauterized tissue between the jaws when stuck, thereto. 
     The exemplary embodiments with servo-controlled blade and/or jaw assemblies are shown herein only with the power generation circuitry In the handle. Nonetheless, these embodiments should not be considered limiting. All of the alternative and/or additional embodiments mentioned herein are applicable in any combination to each of these embodiments, for example, some circuitry can be placed in the battery itself or in a removable cartridge. 
     The actuation assemblies of the present invention reduce the number of steps to effect the sealing and cutting surgical procedure. This improvement is illustrated and explained with respect to  FIGS. 65 to 67 . To begin,  FIG. 67  illustrates four steps that are needed to perform a prior art electrocautery sealing and cutting procedure. With the device jaws in a normally open position, in Step  1 , the surgeon closes the jaws by actuating a main lever. With the first pulling motion, the jaws close and impart, the sealing force to the tissue or vessel. In Step  2 , the surgeon actuates electrocautery and seals the tissue. In Step  3 , the surgeon pulls a trigger to move the cutting blade distally and the sealed tissue is cut. Typically, the blade is retracted upon release of the trigger. The surgeon, in Step  4 , unlocks the main lever and, if desired, can repeat the process (dashed line). Each of Steps  1 ,  3  and  4 , requires the surgeon to expend a significant amount of energy with his/her hand. For surgical procedures taking a long time and requiring a number of such sealings/cuttings, the surgeon can become tired. 
     The device of the invention, in contrast, dramatically reduces the forces required to effect the surgical procedure and, at the same time, reduces the total number of steps for completing the procedure—the combination of which conserves energy needed to carry out procedures over extended periods of time. This reduction is illustrated and explained with respect to  FIGS. 66 and 67 . To begin the inventive procedure, the surgeon closes the jaws in Step  1  by actuating a main lever  5410 ,  6110  of the device. With this first pulling motion, the jaws close and impart, a first intermediate sealing force to the tissue or vessel. Thereafter, in Step  2 , the surgeon makes a single actuation (e.g., presses a button, moves a toggle, rolls a wheel) on the device and the entire surgical procedure is carried out automatically. With respect to a configuration where the unlocking of the main lever is manual, only the sealing and cutting is performed automatically in Step  2 . The main lever is unlocked by the surgeon in Step  3 . In contrast, when the main lever is also electrically operated, both Steps  2  and  3  of  FIG. 66  are performed with no other action than pressing the procedure-actuation switch, which is not illustrated but can be positioned on the side of the handle body similar to the button  4240  in  FIG. 42 . 
     It is beneficial if electrocautery is effected when tissue is at an optimal state for a desirable medical change to occur after the sealing and cutting procedure. Therefore, within the steps of compressing the tissue and carrying out electrocautery for sealing (but before cutting), these exemplary devices can be configured to carry out an OTC-determination step. This determination can be carried out in various ways. In one exemplary embodiment according to the invention, electrodes on either side of the tissue sense an impedance of the tissue disposed between the jaws (e.g., at the jaw mouth surfaces). OTC can be determined by comparing the measured impedance to a known range of impedances value corresponding to an OTC state of the tissue. As the tissue desiccates, the impedance of the tissue changes. Therefore, the active feedback circuitry can be provided to continuously monitor the impedance and to indicate to the surgeon to open or close the jaws accordingly (with appropriate indicators at the control handle, e.g., ↑=open or ↓=close) so that the OTC state is maintained up to and including the time that sealing and cutting is performed. But, with the servo-controlled jaw movement assembly shown in  FIGS. 61 to 64 , the jaw movement circuitry  6142  can be programmed to open or close the jaws with speed, precision, and accuracy. 
     The OTC feedback device performs particularly well when coupled to a mechanism for closing and opening the jaws. Passing an upper OTC value in a positive direction means that too much pressure is being imparted on the tissue and the motorized jaws are opened to an extent that brings the measured value back within the OTC range. In contrast, passing the lower OTC value in a negative direction means that too little pressure is being imparted on the tissue and the motorized jaws are closed to an extent that brings the measured value back within the OTC range. This self-adjusting compression device keeps compression force on the interposed tissue within the OTC compression range during and after desiccation. When in the OTC range after desiccation, the device notifies the surgeon of this fact, referred to as a “procedure-ready state.” With this information, a delay can be pre-programmed in the device so that the sealing does not occur until after a time period expires, for example, any amount of time up to 5 seconds. In one exemplary embodiment, if the actuation device is pressed again, then the procedure is aborted and the surgeon can reposition the jaws or entirely abort the operation. If the surgeon does nothing during the delay period, then the device automatically starts the sealing procedure. Indicating information for the procedure-ready state can be conveyed to the surgeon audibly (e.g., with a speaker), visually (e.g., with an LED), or tactily (e.g., with a vibration device). 
     Immediately after the tissue is sealed, embodiments of the device automatically start the cutting procedure by powering the blade from its retracted position to its extended position. Without any further activation or movement by the surgeon, the blade is, then, returned to its retracted position to complete the sealing/cutting procedure. In an exemplary embodiment, the retraction can be activated by appropriately positioned limit switches that are disposed In the blade-movement area to be contacted at the appropriate time. Alternatively, the stroke of the powered extension/retraction device can be limited to go no further than desired limits. Endpoint switches can be coupled with a mechanical gearbox but use of the servo provides advantages because the servo can pulse modulate the speed and the distance of travel. Powered retraction Insures both that the blade does not remain in the cut tissue and that the blade is fully retracted. If desired, a motorized assembly can be included to unlock the main lever after blade retraction, allowing the main lever to spring back to its original open position (for example, through the force of a bias device, such a spring). 
     Closing of the jaws and movement of the blade is, in an exemplary embodiment, carried out utilizing one or more servos. One embodiment described above included a partial servo assembly where the jaws are controlled by hand and the knife is controlled by servo. However, another exemplary partial servo embodiment can provide an assembly where the jaws are controlled by the servo and the knife is controlled manually. Both movements are executed by moving an object, such as a rod or a beam, along the longitudinal axis of the device. By appropriate placement of one or more servos, these objects are connected directly to distal end of the servo arm (or via an intermediate linkage system). Thus, actuation of the respective servo moves the control rod longitudinally along the axis of the device. The range of the jaw-servo can be between the fully closed and fully opened orientation of the jaws. The jaw-servo can control the jaws whether the device is a single-moving jaw assembly or a dual-moving jaw assembly. If desired, two jaw-servos can independently operate the dual-moving jaw assembly. Either way, by controlling the jaw(s) with a servo, exact control of the jaws is made possible and, with a connection to an OTC feedback device, can permit exact and rapid jaw position control dependent upon measured values, e.g., voltage, current, tissue compression, tissue impedance, to name a few. Another beneficial advantage of servo-controlled jaw movement is that the servo can vary the jaw compressing force throughout the cutting procedure to further insure that the OTC range is maintained. 
     An advantageous feature that is provided by regulating the cutting blade with a servo is that the designer or even the surgeon can exactly regulate the speed of the cut. So, for example, if the surgeon knows that it would be beneficial for the speed of the cut to increase for a particularly tough compressed tissue, then the surgeon could turn a non-illustrated dial (for instance) that would effect a blade speed change. 
     The power-assisted actuation assembly of the present invention reduces the number of steps to carry out the surgical cautery/cutting procedure. With the jaws of the inventive device in the normally open position, the surgeon closes the jaws by actuating the jaw-closing trigger  5410 ,  6110 . Like the prior art, this lever  5410 ,  6110  can have the pull-to-lock and pull-again-to-unlock actuation assembly. With this first pulling motion, the jaws close and impart a first intermediate sealing force to the tissue or vessel. This force need not be the final compressive force but merely can be an intermediate stage that securely holds the tissue therebetween. Thereafter, in a second step, the surgeon merely presses a single button on the device and the entire procedure is carried out automatically—the procedure including, for example, a determination of Optimal Tissue Compression (OTC), an electrocautery process to cause sealing of the tissue, a cutting movement through the sealed tissue, and a release of the jaws back to the intermediate stage. The process is finalized in the third step by a second pulling motion on the main lever to open the jaws fully, it is noted that, in another exemplary embodiment of the invention, the electronic control assembly can be configured to automatically actuate the main lever and, thereby, open the jaws for release of the sealed/cut tissue, making it ready for the next, sealing/cutting procedure. With the invention, therefore, the surgeon can effect a sealing and cutting procedure with only two or three steps, these steps not requiring the surgeon to provide any significant external force (such as physically moving a trigger) other than initiating the first closure of the main lever. 
     As set forth in the preceding paragraph, the device of the instant invention is able to automatically compress the tissue at a pre-defined force that allows beneficial healing without irretrievably harming the compressed tissue. It is known that, when tissue is being compressed (whether a single layer or multiple layers) and before cutting the tissue, it is desirable for the tissue to be at a certain compressive state (OTC) so that a desirous medical change can occur; at the same time, the tissue should not be compressed too far to cause tissue necrosis. Because there is no way to precisely control the exact kind of tissue that is being placed within the compressing jaws, it is not possible to ensure manually that the tissue is compressed within an Optimal Tissue Compression range, referred to as an OTC range. Therefore, ruling out of tissue necrosis is difficult or not possible for prior art electrocautery devices. 
     The foregoing description and accompanying drawings illustrate the principles, preferred embodiments and modes of operation of the invention. More specifically, the encrypted identification systems and methods according to the present invention have been described with respect to an inventory system and process. However, the invention should not be construed as being limited to the particular embodiments discussed above. Additional variations of the embodiments discussed above will be appreciated by those skilled in the art as well as for applications, unrelated to inventory, that require encrypted identification of parts. 
     The above-described embodiments should be regarded as illustrative rather than restrictive. Accordingly, it should be appreciated that variations to those embodiments can be made by those skilled in the art without departing from the scope of the invention as defined by the following claims.