Patent Publication Number: US-10314642-B2

Title: Electrocautery method and apparatus

Description:
CROSS-REFERENCE TO RELATED APPLICATIONS 
     This application is a divisional of U.S. patent application Ser. No. 12/062,516, filed Apr. 4, 2008, now abandoned, which is a divisional of U.S. patent application Ser. No. 11/671,891, filed Feb. 6, 2007, which issued as U.S. Pat. No. 8,696,662, which is a continuation-in-part of U.S. application Ser. No. 11/382,635, filed May 10, 2006, which issued as U.S. Pat. No. 7,862,565, and Ser. No. 11/371,988, filed Mar. 8, 2006, which issued as U.S. Pat. No. 7,803,156. U.S. application Ser. No. 11/382,635 claims the benefit of provisional application nos. 60/725,720 filed on Oct. 11, 2005 and 60/680,937 filed on May 12, 2005. The entireties of the foregoing applications are incorporated herein by this reference thereto. 
    
    
     BACKGROUND OF THE INVENTION 
     1. Field of the Invention 
     The invention relates to tissue cauterization. More particularly, the invention concerns an electrocautery system with various electrodes and a mechanism for automated or user-selected operation or compensation of the electrodes. 
     2. Description of the Related Art 
     Various physiological conditions call for tissue and organ removal. A major concern in all tissue removal procedures is hemostasis, that is, cessation of bleeding. All blood vessels supplying an organ or a tissue segment to be removed have to be sealed, either by suturing or cauterization, to inhibit bleeding when the tissue is removed. For example, when the uterus is removed in a hysterectomy, bleeding must be inhibited in the cervical neck, which must be resected along the certain vessels that supply blood to the uterus. Similarly, blood vessels within the liver must be individually sealed when a portion of the liver is resected in connection with removal of a tumor or for other purposes. Achieving hemostasis is necessary in open surgical procedures as well as minimally invasive surgical procedures. In minimally invasive surgical procedures, sealing of blood vessels can be especially time consuming and problematic because there is limited access via a cannula and other small passages. 
     Achieving hemostasis is particularly important in limited access procedures, where the organ or other tissue must be morcellated prior to removal. Most organs are too large to be removed intact through a cannula or other limited access passage, thus requiring that the tissue be morcellated, e.g. cut, ground, or otherwise broken into smaller pieces, prior to removal. 
     In addition to the foregoing examples, there exist a variety of other electrosurgical instruments to seal and divide living tissue sheets, such as arteries, veins, lymphatics, nerves, adipose, ligaments, and other soft tissue structures. A number of known systems apply radio frequency (RF) energy to necrose bodily tissue. Indeed, some of these provide significant advances and enjoy widespread use today. Nevertheless, the inventors have sought to identify and correct shortcomings of previous approaches, and to research possible improvements, even when the known approaches are adequate. 
     In this respect, one problem recognized by the inventors concerns the small size of today&#39;s electrode structures. In particular, many electrosurgical instrument manufacturers limit the total length and surface area of electrodes to improve the likelihood of completely covering the electrodes with tissue. This small electrodes strategy results in the surgeon having to seal and divide multiple times to seal and divide long tissue sheets adequately. Such time consuming processes are also detrimental to patients, increasing anesthetic time and potentially increasing the risk of injury to surrounding structures, as the delivery of energy and division of tissue is repeated again and again. 
     The consequences of partial electrode coverage can be significant. This condition can cause electrical arcing, tissue charring, and inadequate tissue sealing. Mechanical, e.g. blade, or electrosurgical division of tissue is performed immediately following tissue sealing, and the division of inadequately sealed tissue can pose a risk to the patient because unsealed vessels may hemorrhage. Arcing presents its own set of problems. If electrocautery electrodes generate an arc between them, instead of passing RF energy through targeted tissue, the tissue fails to undergo the intended electrocautery. Furthermore, depending upon the path of the arc, this might damage non-targeted tissue. Another problem is that adjacent electrodes in a multiple electrode system may generate electrical cross-talk or generate excessive thermal effect in the transition zone between two adjacent electrodes that fire sequentially. Previous designs prevented this by imposing a mechanical standoff for the jaws that the electrodes were fastened onto. However, this standoff prevented very thin tissue from making contact with the opposing electrodes, preventing an optimal electrical seal in these regions. These standoffs, if too shallow, can also result in arcing between electrodes. 
     At typical radiofrequency energy (RF) frequencies in the 300 kHz to 10 MHz range, tissue impedance is largely resistive. Prior to tissue desiccation, initial impedances can vary greatly depending on the tissue type and location, vascularity, etc. Thus, to ascertain the adequacy of tissue electrode coverage based solely on local impedance is imprecise and impractical. A feasible and dependable methodology for determining electrode coverage by tissue would allow for the development of electrodes of greater length and surface area for use in the safe and rapid sealing and division of tissue sheets during surgical procedures. It would therefore be advantageous to provide a methodology for determining the area of tissue coverage of one or more electrodes. 
     SUMMARY 
     An electrode structure and a mechanism for automated or user-selected operation or compensation of the electrodes, for example to determine tissue coverage and/or prevent arcing between bottom electrodes during electrocautery is disclosed. 
    
    
     
       BRIEF DESCRIPTION OF THE DRAWINGS 
         FIG. 1  is a block diagram of the components and interconnections of an electrocautery system according to the invention; 
         FIG. 2  is a combination block and schematic diagram illustrating an electrocautery device with a first embodiment of compensating circuitry according to the invention; 
         FIG. 3  is a combination block and schematic diagram illustrating an electrocautery device with a second embodiment of compensating circuitry according to this invention; 
         FIG. 4  is a combination block and schematic diagram illustrating an electrocautery device with a third embodiment of compensating circuitry according to the invention; 
         FIG. 5  is a combination block and schematic diagram illustrating an electrocautery device with circuitry for selectively firing electrodes according to the invention; and 
         FIG. 6  is a block diagram showing an electrode having a dielectric coating according to the invention. 
     
    
    
     DETAILED DESCRIPTION 
     In view of the problems of conventional technology that the inventors have recognized (as discussed above), the inventors have sought to improve the ability of a user to control electrocautery electrodes after said electrode have been inserted into the body. Further areas of their focus include improving the efficiency of transferring power to electrode structures, and improving the accuracy of measurements taken from the electrode structure in situ. One benefit of implementing these improvements is the ability to use larger electrode surfaces, with the advantageous consequences discussed above. 
       FIG. 1  illustrates one embodiment of electrocautery system  100 . The system  100  includes an electrode structure  102  that is electrically driven by a power, electrode selector, and compensator module  108 . The module  108  is operated in accordance with user input conveyed via one or more user interfaces  110 . 
     As explained below in greater detail, certain components of the system  100  may be implemented with digital data processing features. These may be implemented in various forms. 
     Some examples include a general purpose processor, digital signal processor (DSP), application specific integrated circuit (ASIC), field programmable gate array (FPGA) or other programmable logic device, discrete gate or transistor logic, discrete hardware components, or any combination thereof designed to perform the functions described herein. A general purpose processor may be a microprocessor, but in the alternative, the processor may be any conventional processor, controller, microcontroller, or state machine. A processor may also be implemented as a combination of computing devices, e.g. a combination of a DSP and a microprocessor, a plurality of microprocessors, one or more microprocessors in conjunction with a DSP core, or any other such configuration. 
     As a more specific example, a digital data processing includes a processor, such as a microprocessor, personal computer, workstation, controller, microcontroller, state machine, or other processing machine, coupled to digital data storage. In the present example, the storage includes a fast-access storage, as well as nonvolatile storage. The fast-access storage may be used, for example, to store the programming instructions executed by the processor. Storage may be implemented by various devices. Many alternatives are possible. For instance, one of the components may be eliminated. Furthermore, the storage may be provided on-board the processor, or even provided externally to the apparatus. 
     The apparatus also includes an input/output, such as a connector, line, bus, cable, buffer, electromagnetic link, antenna, IR port, transducer, network, modem, or other means for the processor to exchange data with other hardware external to the apparatus. 
     As mentioned above, various instances of digital data storage may be used, for example, to provide storage used by the system  100  ( FIG. 1 ), to embody the storage, etc. Depending upon its application, this digital data storage may be used for various functions, such as storing data, or to store machine-readable instructions. These instructions may themselves aid in carrying out various processing functions, or they may serve to install a software program upon a computer, where such software program is then executable to perform other functions related to this disclosure. 
     An exemplary storage medium is coupled to a processor so the processor can read information from, and write information to, the storage medium. In the alternative, the storage medium may be integral to the processor. In another example, the processor and the storage medium may reside in an ASIC or other integrated circuit. 
     In contrast to storage media that contain machine-executable instructions (as described above), a different embodiment uses logic circuitry to implement processing data processing features of the system. 
     Depending upon the particular requirements of the application in the areas of speed, expense, tooling costs, and the like, this logic may be implemented by constructing an application-specific integrated circuit (ASIC) having thousands of tiny integrated transistors. Such an ASIC may be implemented with CMOS, TTL, VLSI, or another suitable construction. Other alternatives include a digital signal processing chip (DSP), discrete circuitry (such as resistors, capacitors, diodes, inductors, and transistors), field programmable gate array (FPGA), programmable logic array (PLA), programmable logic device (PLD), and the like. 
     Electrode Structure  102   
     Referring to  FIG. 1 , the electrode structure  102  includes first and second electrode surfaces  103 - 104 . The electrode surface  104  is formed by a group of electrodes, such as individual electrodes  104   a ,  104   b , etc. In one instance, the electrodes may be substantially contiguous. The electrode surface  103 , in one instance, includes a single electrode, as illustrated. In another instance, the surface  103  includes multiple electrodes, of the same or different number than the electrodes  104 . 
     In one embodiment the electrode surfaces  103 - 104  are arranged to provide electrical power to a targeted tissue area using opposed, bipolar electrodes. The use of opposed, bipolar electrodes is advantageous because it concentrates energy flux between the electrodes and limits the effect on adjacent tissue that is not confined within the opposed electrodes. 
     In one case, the electrode structures  103 - 104  may have generally similar geometries to contact tissue in a symmetric fashion. Alternatively, the electrode structures  103 - 104  may have dissimilar geometries. For example, one electrode structure may comprise a probe for insertion into a natural body orifice with the other electrode structure being structured to engage an exterior tissue surface apart from the body orifice. In some instances, more than two electrode structures may be employed, but at least two electrode structures, or separate regions of a single structure, are energized with opposite polarity to apply RF energy to the targeted tissue. In some instances, the electrode structures may be different regions formed as part of a single support structure, e.g. a single elastic tube or shell which may be placed over an organ or other tissue mass and which has two or more electrode surfaces formed thereon. 
     The different electrode surfaces are isolated from each other when high frequency energy of the same or opposite polarity is applied to them. In still other instances, a single electrode structure may have a plurality of electrically conductive or active regions, where the electrically conductive regions may be energized with the same or an opposite polarity. 
     In some instances, it may be desirable to provide additional structure or components on the electrode structures to enhance or increase the effective electrical contact area between the electrode structure and the tissue. In particular, the electrode structures may include tissue-penetrating elements to enhance electrical contact i.e. reduce electrical impedance between the electrode and the tissue and increase the total surface contact area between the electrode and the tissue. Exemplary tissue-penetrating elements include needles, pins, protrusions, channels, or the like. A particular example includes pins having sharpened distal tips so that they can penetrate through the tissue surface and into the underlying tissue mass. The pins may have depths in the range from 1 mm to 5 cm, or from 3 mm to 1 cm. The diameters of the pins range from 0.1 mm to 5 mm, or from 0.5 mm to 3 mm. In one instance, the pins are evenly distributed over the tissue-contact area of an electrode structure, with a pin density in the range from 0.1 pin/cm 2  to 10 pin/cm 2 , or from 0.5 pin/cm 2  to 5 pin/cm 2 . When tissue-penetrating elements are used, they may be dispersed in a general uniform matter over the electrically active area of the electrode structure. The pins or other tissue-penetrating elements may be provided in addition to an electrically conductive conformable or rigid electrode surface, but in some instances the pins may provide the total electrically conductive or active area of an electrode structure. 
     In one example, the electrodes comprise a plurality of different electrically conductive regions, where the regions may be electrically isolated from each other or may be electrically coupled to each other. Single electrode structures may include three, four, five, and as many as ten or more discrete electrically conductive regions thereon. Such electrically conductive regions may be defined by electrically insulating regions or structure between them. 
     One example of a multiple-electrode surface  104  is a plurality of electrically conductive strips that are separated by a gap which may be an air gap, a plastic member or other insulator. The gap is preferably less than 0.5 mm. In addition, multiple tissue-penetrating pins may be disposed along the length of each electrically conductive strips. The electrically conductive strips may be energized in an alternating polarity configuration. Most simply, opposing strips are connected to opposite polls on a single power supply. Electrical connections may be rearranged, however, to power the strips in virtually any pattern. Moreover, it is also possible to isolate different regions of each strip electrically to permit powering those regions at different polarities; or to set the electrodes to the same polarity but with various sequences of firing pattern that can include firing every electrode, firing specific electrode, or firing multiple electrodes simultaneously. 
     Although shown as flat plates, the electrode structure  102  may be implemented in a variety of different shapes without departing from the scope of the invention. For instance, the electrode structures  103 - 104  may be generally curved to facilitate placement over a tubular body structure or tissue mass. In one case, electrode configurations are specifically configured to have a geometry intended to engage a particular organ or tissue geometry. In other cases, the electrode configurations are conformable so that they can be engaged against and conform to widely differing tissue surfaces. In this regard, electrode strips may be constructed from such material as, for example, conformable meshes, permitting the electrode structures to be flattened out or to assume a wide variety of other configurations. Additionally, the insulating structures may also be formed from a flexible or conformable material, permitting further reconfiguration of the electrode structures. The structure  102  may be implemented according in any one, or a combination, of known shapes configurations, which are familiar to the ordinarily skilled artisan. Some exemplary shapes include opposing jaws, cylinder, probe, flat pads, etc. In this regard, the electrodes may be configured in any manner suitable for engaging a tissue surface. 
     Thus, the electrodes can be rigid, flexible, elastic, inelastic (non-distensible), planar, non-planar, or the like, and may optionally employ tissue-penetrating elements to enhance electrical contact between the electrode structure and the tissue, as well as to increase the electrode area. Electrode configurations may be conformable so that they can be engaged against and conform to widely differing tissue surfaces, or they are specifically configured to have a geometry intended to engage a particular organ or tissue geometry. In both instances, the electrode structures may further be provided with tissue-penetrating elements. 
     Optionally, electrode structures may include both a conductive surface and a non-conductive surface. In some embodiments this is accomplished by leaving one surface as an exposed metallic face, while the other surface of the electrode is covered or insulated with, for example, a dielectric material. In the case of rigid electrodes, the insulation can be laminated, coated, or otherwise applied directly to the opposed surface. In the case of flexible and elastic electrodes, the insulating layer is flexible so that it can be expanded and contracted together with the electrode without loss or removal. In some cases, a separate, expandable sheet of material covers the face for which insulation is desired. In some embodiments, all electrode surfaces may be coated with a dielectric material. 
     In one embodiment, the electrically active regions of the electrode structures have an area ranging from one to fifty cm 2  or larger. Further details and examples of electrode structures are explained in the U.S. patent applications as identified incorporated herein by reference above. 
     Power Supply  106   
     The power supply  106  includes one or multiple power supplies. Basically, the power supply  106  generates high frequency, such as RF, power for application to targeted tissue through one or more electrically active regions of the electrode structure  102 . As described below, the duration and magnitude of power cauterizes or necroses tissue between the electrode surfaces  103 - 104 . 
     Exemplary frequency bands include 100 kHz to 10 MHz or 200 kHz to 750 kHz. Power levels depend on the surface area and volume of tissue being treated, with some examples including a range from 10 W to 500 W, or 25 W to 250 W, or 50 W to 200 W. Power may be applied at a level of from 1 W/cm 2  to 500 W/cm 2 , or 10 W/cm 2  to 100 W/cm 2 , for example. 
     The power supply  106  may be implemented using various conventional general purpose electrosurgical power supplies. The power supply  106  may employ sinusoidal or non-sinusoidal wave forms and may operate with fixed or controlled power levels. Suitable power supplies are available from commercial suppliers. 
     In one embodiment, the power supply provides a constant output power, with variable voltage and current, where power output varies based upon load. Thus, if the system sees a very high impedance load, the voltage is maintained at a reasonable level to avoid arcing. With tissue electrocautery, impedance ranges from two ohms to 1000 ohms, for example. By applying constant power, the power supply  106  can provide significant current at low impedance to achieve initial desiccation when the tissue is first being cauterized and, as cauterization proceeds, to apply higher voltage to complete the tissue sealing process. Thus, the power supply  106  can provide larger current and smaller voltage at the beginning of the cauterization process and a higher voltage and lower current at the sealing phase of the process. Control of such power generator is based, at least in part, on the system  100  monitoring power. 
     In one embodiment, the power supply  106  includes a mechanism for setting the desired power. This setting may occur by real-time control, pre-set selection by a user, default settings, selection of predetermined profile, etc. In one embodiment, pulse width modulation is used in connection with a flyback transformer. The system charges a primary of the flyback transformer and produces a regulated output. The secondary may be regulated, for example, to 15 volts at a desired number of amperes to produce the desired power output. Based upon the period, as determined by the width of the pulse which charges the primary, the power curve is determined. Thus, the invention establishes a certain level of power in the primary of the flyback transformer and the same level of power is provided by the secondary without regard to impedance of the load, i.e. the tissue. 
     The power supply  106  may include digital data processing equipment, such as mentioned above. This optional equipment, if implemented, is used to establish and control features and operation of the power supply  106 . 
     As illustrated, the power supply  106  is a source of power for multiple electrodes of the structure  102 . Accordingly, the power supply  106 , or the module  108 , provides multiple output channels, each of which is independently adjustable. In this embodiment, the system  100  includes a conductive supply path of multiple conductors  108   c  to provide power to the electrodes, and a return path  108   b  for providing a ground path and/or feedback to the power supply or vice versa, depending on the direction of current flow. 
     In a more particular embodiment, the module  108  has multiple outputs  108   c  routed to the individual electrodes by a digital data processor of the module  108 . These multiple outputs are independently operated by the processor and readily modulated and assignable. Thus, the processor may assign an output to any one or more of the electrode elements at a certain point in operation of a cauterization cycle, and dynamically reassign them other points of time. For example, if the power source were a four channel power source and the electro-surgical device had sixteen electrodes, then each channel may support four electrodes in electro-surgical device. However, this arrangement may be varied so that some channels support more electrodes than others. 
     User Interface  110   
     The user interface  110  comprises one or more devices for a human to exchange information with the module  108 , including the power supply  106 . There may be a common user interface, or separate user interfaces for each component  106 ,  108 . The user interface may be implemented in various ways, with the following serving as some examples. As for human-to-machine flow, some examples of the interface  110  include buttons, dials, switches, keyboards, remote control console, or other mechanical devices. Other examples include pointing devices such as a mouse, trackball, etc. Still other examples include digitizing pads, touch screens, voice input, or any other example suitable for the purposes described herein. As for the machine-to-human exchange, the interface  110  may employ a video monitor, display screen, LEDs, mechanical indicators, audio system, or other example suitable for the purposes described herein. 
     User input is conveyed from the interface to the module  108  via the link  108   a.    
     Sensors 
     The system  100  may also include various sensors attached to various components of the system  100 . The sensors, which are not shown in  FIG. 1  to avoid cluttering the diagram, may be attached to components such as the electrodes  103 - 104 , subparts of the module  108 , equipment of the power supply  106 , and the like. Examples of these sensors include devices for sensing voltage, current, impedance, phase angle between applied voltage and current, temperature, energy, frequency, etc. More particular, some of these devices include voltmeters, analog-to-digital converters, thermistors, transducers, ammeters, etc. 
     Module  108   
     As shown above, the module  108  includes one or more power supplies  106 . Aside from this function, module  108  may be implemented to perform some or all of automated or user-selected operation or compensation of the electrodes in the manner shown below. According to one aspect, the module  108  may be used to target a specific region of tissue, or the control firing order of electrodes, by selectively limiting power application to electrodes whose selection is predetermined, machine-selected, or user-selected. According to another aspect, the module  108  may introduce impedance into the electrode circuitry to provide a predetermined, machine-selected, or user-selected impedance matching or compensation. 
     According to one optional aspect of the module  108 , the module  108  may target a specific region of tissue by selectively limiting power application to electrodes whose selection is predetermined, machine-selected, or user-selected. In this regard, the module  108  has a variety of outputs  108   b - 108   c  individually coupled to each of the electrodes  103 - 104 . As one example, the outputs  108   b - 108   c  may comprise wires, cables, busses, or other electrical conductors. In the illustrated example, there are multiple conductors  108   c  leading to the multiple electrodes  104   a ,  104   b , etc. 
     The module  108  applies voltage from the power supply  106  across the first and second electrode surfaces  103 - 104 , such that the voltage is applied exclusively to selected ones of the electrodes. These electrodes may be selected according to user input from the interface  110 , selected by a machine-implemented analysis, and/or selected by a default state. In this regard, the module  108  may include a switching network of electrical and/or mechanical switches, relays, or other mechanism to provide power to selected ones of the electrodes. As shown, the power supply  106  is integrated into the module  108 , and computer control selectively activates selected output conductors. 
     Whether by independent switching network or computer regulated activation of output conductors, the module  108  activates electrodes according to input from user interface  110 , or input from a machine such as a digital data processing device as discussed above. Depending upon the nature of the application, such controlled application of power to electrodes may be performed in accordance with a machine-selected criteria or analysis, default state, or user input. 
       FIG. 5  illustrates a typical application of one example of a processor-controlled switching network, shown in context of two power supplies, electrode structures, and a targeted tissue region. In this example, the electrode surfaces are configured as follows. The electrode surfaces are substantially parallel during performance of electrocautery, each electrode of one surface is aligned with its counterpart in the other electrode surface. In this example, there are two electrodes from the upper surface corresponding to each electrode of the lower surface. 
     Significantly, the module  108  selectively limits power application to certain electrodes, to target a specific region of tissue. Electrodes may be selected for a different end, as well. Namely, the module  108  may monitor or control the selection of electrodes to prevent firing of adjacent electrodes of the same electrode surface concurrently or sequentially. Ensuring that electrode firing occurs in this spaced-apart fashion prevents unintentional arcing between electrodes and improves the effectiveness of electrocautery. In one embodiment, the controlled firing order is implemented by computer control, and particularly, by a digital data processing component of the module  108 . As an alternative to computer control, mechanical means may be used, such as an electromechanical distributor or other device. 
     In another embodiment, the module  108  may introduce impedance into the electrode circuitry to provide predetermined, machine-selected, fixed, or user-selected impedance matching or compensation. In other words, the module  108  contains a mechanism to electrically introduce impedance into a circuit containing the power supply, the outputs  108   b - 108   c , and the electrodes  103 - 104 . 
     More particularly, the module  108  includes capacitors, inductors, and/or other impedance elements that can be adjusted or selectively introduced to control the amount of impedance in the circuit containing the power supply and electrodes  103 - 104 . These impedance elements may comprise discrete elements, integrated circuit features, or other constructs suitable for the purposes described herein. The module  108  establishes this impedance matching or compensation according to directions from a user, machine-implemented analysis, and/or default setting. 
     One example of an adjustable impedance is an adjustable inductor that may comprise any known inductance, such as a coil of conducting material wrapped around an adjustable ferromagnetic core or discrete inductors. In this example, the overall inductance is selectively increased by closing a switch that may be activated manually, mechanically, electrically, or by any means suitable to the purposes of this disclosure, for example, via the user interface  110 . 
       FIG. 2  illustrates an electrode arrangement having an inductance in series with each electrode of an upper electrode surface (as illustrated).  FIG. 3  shows a different example, including an inductance in series with each electrode of the lower electrode surface (as illustrated). In a different example still,  FIG. 4  contains “T” type network where a capacitor is placed in series with each electrode of the upper electrode surface. Additionally, a different inductor is placed in parallel with each pair of electrodes that are designed to be activated together. The examples of  FIGS. 2-4  may employ impedance elements that are fixed, adjustable, or a combination of fixed and adjustable. Furthermore, in connection with the electrodes having a dielectric coating on their surface, a nearly limitless number of additional circuitry configurations for impedance matching and/or compensation will be apparent to ordinarily skilled artisans having the benefit of this disclosure. 
     In addition to the arrangement for introducing impedance into the electrode circuits, another consideration is the value of such impedance elements. In one example, the impedance is selected to achieve maximum power transfer and to make accurate power measurements. In this regard, the impedance is chosen to maintain an impedance match between the RF generator, namely, the power supply  106 , and the tissue. Impedance matching is achieved when the phase-angle between applied voltage and current is zero. Namely, additional inductance is increased to compensate for the increased capacitive reactance. In one example, this is carried out with a continuously variable inductor, with a finite range and nearly infinite resolution. Such an inductor can be adjusted to a near zero phase. In a different example, impedance matching is carried out by using discrete inductive elements in an appropriate arrangement, such as shown in  FIGS. 2-4 , to find the least possible phase angle, though this may not be exactly zero. 
     Having described the structural features of the invention, the operational aspects of the invention will be described. The steps of any method, process, or algorithm described in connection with the embodiments disclosed herein may be embodied directly in hardware, in a software module executed by hardware, human-performed steps, or a combination of these. 
     A sequence for performing an electrocautery procedure uses an electrocautery system that includes an electrode structure and a mechanism for automated or user-selected operation or compensation of the electrodes. For ease of explanation, but without any intended limitation, this example is described in the specific context of the system  100  of  FIG. 1 . 
     In a first step, different parameters for operating the system  100  are selected. In one example, one or more human users select these parameters and convey them to the system  100  via the user interface  110 . In a different example, the parameters for operating the system  100  are selected by digital data processing equipment aboard the module  108 . In this case, the parameters are set according to user input, default values, measurements gathered by the various sensors installed in the system  102 , programming of the module  108 , etc. 
     Without any intended limitation, the following are some non-exclusive examples of parameters that may be selected in the first step:
         (1) Identity of individual electrodes to be activated e.g.,  FIG. 5  in order to focus energy of the electrodes  103 - 104  on a specific region of tissue.   (2) Firing order of electrodes.   (3) Assessment or measurement of magnitude of impedance, e.g.  FIGS. 2-4 , to be used in compensating and/or impedance matching between the power supply  106  and electrodes  103 - 104 .   (4) Parameters of electrical power to be applied in electrocautery, such as magnitude, frequency, phase, or other characteristics of voltage, current, power, etc.   (5) Any other parameter by which the operation of the system  100  can be varied.       

     In a next step appropriately trained personnel apply the electrodes  103 - 104  to a targeted tissue region to be electrocauterized. The manner of applying the electrodes  103 - 104 , varies according to the construction of the electrodes  103 - 104 , the nature of the targeted body part, the procedure to be performed, and other such factors. There may be circumstances where both electrode structures  103 - 104  are used within the body, and other embodiments where one electrode is inserted into the body and the other electrode used externally, i.e. bipolar or monopolar applications, as is know in the art. 
     In a specific example of this next step, there are multiple electrodes of one surface, such as  104 , corresponding to one electrode of the other surface, such as  103 . Optionally, personnel arrange the first and second electrode surfaces  103 - 104  so that the electrode surfaces are substantially parallel, and each one of the second electrodes is aligned with its corresponding first electrodes, although alignment is preferably obtained during manufacture of the device.  FIGS. 2-5  show examples of the final arrangement. 
     In a further step, directions are given to begin electrocautery. This occurs by user input submitted via the interface  110 . For example, a user may press a start button, utter a start command, press a foot pedal, trip a lever, or perform other action. In a different example, electronically occurs upon expiration of a user-initiated timer. 
     In a still further step, the system  100  responds to the start command and electrocautery is conducted. Here, the system  100  directs bipolar RF power at target tissue regions defined by spaced-apart placement of the electrode structures  103 - 104 . The use of opposed, bipolar electrodes concentrates energy between the electrodes and limits the effect on adjacent tissue that is not confined within the opposed electrodes. In practice, power may be applied for a time sufficient to raise the tissue temperature in the tissue mass being treated to above a threshold level required for cauterization or necrosis, such as 60-80° C., or even higher. 
     More specifically, electrocautery is conducted according to the configuration set. For instance, the power supply  106  operates according to the power settings established. Moreover, the module  108  acts to invoke individual ones of the electrodes according to the electrode combination selected. In other words, the module  108  applies voltage from the power supply  106  across the first and second electrode surfaces  103 - 104 , such that voltage is applied exclusively to the electrodes selected in. In the case of computer control, this is achieved by the module  108  selectively applying power to the selected electrodes. 
     As a further enhancement to the use of selected electrodes, the electrodes may be activated using a selected firing order. In this example, the module  108  applies voltage from the power supply  106  across the first and second electrode surfaces  103 - 104 , such that voltage is applied to one or more of the first electrodes  102  and one or more of the second electrodes  103  at any one time, and the module  108  prevents firing of adjacent electrodes of the same electrode surface concurrently or sequentially. The module  108  may further implement a predetermined or user-selected firing order. 
     For example, one way of preventing interaction, either thermal or electrical, between two or more multiple electrodes in an RF device with multiple electrodes is to alter the firing sequence of electrodes so that adjacent electrodes are never sequentially charged. For example, instead of sequential firing a four electrode system, where the electrodes are sequentially numbered 1, 2, 3, 4, the invention fires them in an order such as 3, 1, 4, 2, 4, 2, 4, 1, 3, 1, 3, etc. so that adjacent electrodes are not fired sequentially. Firing times may be different for each electrode to balance the energy delivered in such a sequence where some electrodes fire more frequently than others. This prevents cross-talk during the transmission from one electrode to another as well as cumulative effects of sequential heat build-up in the transition area between the two electrodes. Additionally, rounded electrodes can minimize the edge effect that occurs between electrodes and at any transition surface. 
     Additionally, if one electrode surface or both opposing surface of conductive, typically metal, electrodes are coated with dielectric, non-conductive materials, RF energy may still be transmitted through tissue between them via capacitive coupling.  FIG. 6  is a block diagram showing an electrode having a dielectric coating according to the invention. However, due to the non-conductive nature of the surface coating the electrode surfaces does not create a short circuit if brought into close proximity or contact. In this way, if a portion of an electrode pair only partially captures tissue, i.e. there is a small, 5 mm air gap between a portion of the electrodes, the RF energy still passes through the tissue, as opposed to going around the tissue and flowing directly between the close proximity electrodes. This is especially important late in the sealing cycle as the tissue impedance rises. When the tissue impedance is high the energy seeks alternate pathways of lower resistance, such as between exposed electrode sections. These dielectric layers can be thin coats of polymers, such as Teflon, metal oxides, such as titanium, tungsten, or tantalum or ceramics. To obtain adequate capacitance these layers may be in the micron range of thickness. 
     In an alternative embodiment, a variety of different tissue cauterization patterns can be achieved with the system  100  by selectively energizing different ones of the electrode surfaces or regions. By selectively energizing two adjacent electrodes, while leaving all other electrodes non-energized, a limited tissue region is cauterized. In contrast, by energizing other multiple electrode surfaces, a larger region is cauterized. Slightly different patterns are achieved depending on the precise pattern of electrode surface polarity. In other embodiments, the electrode surfaces can be energized in an alternating pattern of polarity to produce a tissue cauterization pattern. Different patterns may also be used to produce somewhat different patterns of cauterized tissue. 
     A different approach for selected firing is employed to prevent local areas of high impedance from impacting the overall system impedance along the entire electrode, and thus potentially reducing the power output of the entire system as voltage reaches its maximal capacity. Here, electrodes are activated to prevent one area that has already been well sealed and has thus reached high impedance value from affecting other regions in which the tissue is not yet sealed, and is thus at a lower impedance. Optionally, the module  108  may employ unique power and energy delivery profiles for each electrode or electrode pair, based on the properties of the tissue in a specific electrode location/position. 
     The performance of electrocautery employs the selected impedance compensation and/or matching selected. As a result, power delivered from the power supply  106  is delivered to the targeted tissue region with less electrical loss. 
     The system  100  may further sense and automatically adjust conjugate matching impedance. In response, the module  108  adjusts the impedance applied to the conductive path containing the electrode surfaces  103 - 104  and power supply  106 . Alternatively, the sensors may provide raw data to the module  108 , which analyzes whether and how to adjust impedance. In a different instance, the module  108  may adjust impedance responsive to direction or data from the sensors. This can be carried out by changing the frequency of RF energy delivered by the power supply  106 . For example, in one embodiment the module  108  senses whether or not tissue is present at each electrode at the beginning of a cauterization cycle by measuring any of impedance, pressure, or any combination of these and/or other parameters. If tissue is not present at any electrode, then such electrode pair is idle; the module  108  deactivates firing of this electrode, and/or provides a warning to an operator via the user interface  110 . The module  108  may also provide a status indicator for each electrode pair that indicates whether the sealing cycle is active or completed with regard to each electrode pair. In this embodiment, each electrode pair may include a mode status indicator, such as an LED for example, that indicates any of an idle, active, or complete condition, once a cauterization cycle is commenced. 
     The invention also addresses the problem of determining the area of tissue coverage of one or more electrodes through the use of dielectric coated electrode surfaces (See  FIG. 6 ). With a suitable RF generator and with electrode surfaces coated with a dielectric coating, determination of tissue coverage may be obtained by measuring phase-angle of RF voltage and current. Because a dielectric coating essentially forms a capacitive coupling to tissue, for a given dielectric material thickness, the capacitance is a function of the area of coverage. 
     The basic formula for a capacitor is:
 
 C=ε   0 ε r   A/d  
 
     Expressed in Farads, where ε 0  is the permittivity of free-space (8.854E-12), ε r , is the relative permittivity of the dielectric, A/d is the ratio of the area and the dielectric thickness. 
     At a given frequency, the reactance is expressed as
 
 Xc= 1 /ωC  
 
where ω is 2*Pi*Frequency.
 
     A suitable RF generator is required to insert a conjugate impedance inductance in this case to cancel out the capacitive reactance with a fully covered electrode and to measure the phase-angle of RF voltage and current. When an electrode is only partially covered, the capacitance changes i.e. becomes smaller, because the effective area is smaller. As a result, the reactance and, ultimately, the phase-angle of RF voltage and current change. While the magnitude of change is affected in part by the tissue resistance, it is believed that this methodology allows the greatest degree of determination of electrode coverage by tissue. 
     A further advantage of such a methodology may signal the RF generator&#39;s control algorithm to change frequency, e.g. increase, with smaller surface areas, thus maintaining maximum power transfer while minimizing chances for electrical arcing and tissue charring. Potential electrical arcing and tissue charring conditions may be detected rapidly by rapid changes in phase and/or impedance and by appreciating that electrodes which are only partially covered by tissue may be used to signal the RF generator control algorithm to shorten or change treatment parameters. 
     To achieve maximum power transfer and to make accurate power measurements, it is desirable to maintain an impedance match between the RF generator and the tissue. Impedance matching is achieved when the phase-angle is zero. Several methodologies may be used to attain near-zero phase. One such methodology uses additional reactive elements e.g. greater inductance, to compensate for the increased capacitive reactance. This approach can be achieved in two different ways:
         (1) Via the insertion of a continuously variable inductor with a finite range and nearly infinite resolution, such an inductor can be adjusted to a near zero phase; or   (2) Via the insertion of discrete elements, e.g. inductors to find the lowest phase, though this may not be near-zero phase.       

     In both cases, electromechanical devices are required within the RF generator. 
     Another methodology of achieving maximum power-transfer, e.g. zero phase, is by changing the RF frequency. Given that the reactance is frequency dependent, this methodology allows the RF generator to compensate for phase discrepancy by electronically changing frequency. This may not require any mechanical devices such as relays, servos, etc. Further, the RF generator can change frequency during operation rather than first interrupting RF power to change elements. Thus, this may be the most desirable methodology. 
     Although the invention is described herein with reference to the preferred embodiment, one skilled in the art will readily appreciate that other applications may be substituted for those set forth herein without departing from the spirit and scope of the present invention. Accordingly, the invention should only be limited by the Claims included below.