Electrosurgical System

Abstract

To provide an electrosurgical generator arranged to supply radio frequency (RF) energy to fuse tissue.SOLUTION: The generator is arranged to supply RF energy through an electrosurgical instrument to fuse tissue grasped by the removably coupled electrosurgical instrument. The generator monitors a phase angle of the supplied RF energy and adjusts or terminates the supplied RF energy based on the monitored phase angle in comparison to predetermined thresholds and conditions to optimally fuse the tissue. The electrosurgical instrument conducts radio frequency energy to fuse tissue captured between the jaws 222 and a blade to mechanically cut tissue between the jaws. A conductive post 281 is positioned on the jaw adjacent to the blade.SELECTED DRAWING: Figure 23

Description

Technical Field

[0001] The present invention generally relates to electrosurgical (electrosurgery) systems and methods, and more particularly to an electrosurgical generator and a novel bipolar electrosurgical instrument or device.

[0002] 〔Description of Related Applications〕 This application claims the benefit of U.S. Provisional Patent Application No. 61 / 994,192, filed May 16, 2014; U.S. Provisional Patent Application No. 61 / 994,185, filed May 16, 2014; U.S. Provisional Patent Application No. 61 / 994,415, filed May 16, 2014; and U.S. Provisional Patent Application No. 61 / 994,215, filed May 16, 2014, which are hereby incorporated by reference in their entirety and made a part hereof.

Background Art

[0003] Electrosurgical instruments that use electrical energy to perform certain surgical tasks have become available. Typically, an electrosurgical instrument includes a hand-held tool, such as a grasper, scissors, forceps, blade, needle, and other hand-held tools, that are configured to be supplied with electrical energy from an electrosurgical unit that includes a power source. The electrical energy can be used to coagulate, melt, or cut tissue to which the electrical energy is applied.

[0004] Electrosurgical instruments typically belong to two classifications: monopolar and bipolar. In monopolar instruments, electrical energy is supplied at a high current density to one or more electrodes of the instrument, and a separate return electrode is electrically coupled to the patient, often designed to minimize the current density. While monopolar electrosurgical instruments may be useful in certain procedures, they can pose a risk of trauma to certain types of patients, such as electrical burns, often due to the function of the return electrode, at least partially. In bipolar electrosurgical instruments, one or more electrodes are electrically coupled to an electrical energy source of a first polarity, and one or more other electrodes are electrically coupled to an electrical energy source of a second polarity opposite to the first. Thus, bipolar electrosurgical instruments, operating without a separate return electrode, can deliver concentrated electrical signals to tissue areas with reduced risk.

[0005] However, even when the surgical effect of bipolar electrosurgical instruments is relatively concentrated, surgical outcomes often depend heavily on the surgeon's skill. For example, if electrical energy is delivered for a relatively long period of time, or if a relatively high-power electrical signal is delivered for a short period of time, thermal tissue damage and necrosis may occur. The rate at which tissue achieves the desired coagulation or cutting effect when electrical energy is applied varies depending on the type of tissue and can also vary depending on the pressure applied to the tissue by the electrosurgical instrument. However, even highly experienced surgeons may find it difficult to assess how quickly a desired amount of tissue mass of a combined state, grasped by an electrosurgical instrument, can be melted. [Overview of the Initiative] [Problems that the invention aims to solve]

[0006] Efforts have been made to reduce the risk of tissue damage during electrosurgical processes. For example, conventional electrosurgical systems include a generator that monitors ohmic resistance or tissue temperature during the electrosurgical procedure and stops the electrical energy once a predetermined point is reached. However, these systems have the drawback of sometimes providing inconsistent results in determining tissue coagulation, fusion, or cutting endpoints for various types of tissue or tissue masses in various combination states. Furthermore, these systems do not provide consistent electrosurgical results between different instruments with different instrument and electrode geometric shapes. Typically, even a relatively minor upgrade to the instrument's geometric shape during the product's lifecycle requires recalibration for each type of instrument in which the electrosurgical unit is to be used. This is a costly and time-consuming procedure that may, undesirably, lead to the discontinuation of the use of the electrosurgical generator. [Means for solving the problem]

[0007] In certain embodiments, an electrosurgical system for performing electrosurgical procedures on a patient's body tissue includes an electrosurgical generator and a bipolar electrosurgical instrument or device. The generator controls the delivery of electrosurgical energy that melts the tissue in contact with the bipolar electrosurgical instrument. In various embodiments, the generator identifies a phase zero crossing, adjusts the RF energy output or voltage, and measures and monitors the phase angle and / or rate of change of the phase angle with respect to a predetermined threshold, where the predetermined threshold is identified at the identified phase zero crossing.

[0008] According to various embodiments, the electrosurgical melting device comprises a first jaw coupled to a second jaw, the first jaw having a first electrode, and the second jaw having a second electrode similar to the first electrode. The first and second electrodes are arranged to transmit radio frequency (RF) energy between the first and second electrodes, and the first and second electrodes are made of the same conductive material. The electrosurgical melting device further comprises an elongated shaft having a proximal end, a distal end, and a longitudinal axis extending from the proximal end to the distal end, with the first and second jaws rotatably mounted on the distal end of the elongated shaft. In one embodiment, the elongated shaft has an outer diameter of less than 5 mm so as to fit into a 5 mm cannula.

[0009] According to various embodiments, the electrosurgical melting device has a conductive post incorporated into a second jaw and extending from the second jaw toward the first jaw. The conductive post is stationary and is made of the same conductive material as the first and second electrodes. In various embodiments, the conductive post includes a plurality of conductive posts having varying heights.

[0010] According to various embodiments, the electrosurgical melting instrument has a first jaw equipped with a conductive pad, and a second jaw coupled to the first jaw. The second jaw has an inner surface facing the conductive pad, and the first and second jaws are arranged to trap tissue between the conductive pad and the inner surface of the second jaw. The conductive pad and the second jaw are arranged to be connected to an electrosurgical energy source and to transmit RF energy through the tissue held between the jaws. The electrosurgical melting instrument has a blade that can move along the longitudinal axis from a proximal to a distal position and return to the proximal position, and the blade is located within the outer circumference of the second jaw.

[0011] According to various embodiments, the electrosurgical melting instrument has a conductive post provided on a second jaw adjacent to the blade. The conductive post is positioned so as not to be connected to an electrosurgical energy source and is positioned to transmit RF energy between the conductive pad and the second jaw through tissue held between the jaws.

[0012] Many of the accompanying features of the present invention will be readily apparent when the present invention is viewed in conjunction with the accompanying drawings and the above and following descriptions.

[0013] The present invention will be best understood when described in conjunction with the accompanying drawings, in which reference numerals indicate the same parts throughout the drawings. [Brief explanation of the drawing]

[0014] [Figure 1] This is a perspective view of an electrosurgical system according to various embodiments of the present invention. [Figure 2] This is a perspective view of an electrosurgical generator as one of various embodiments of the present invention. [Figure 3] This flowchart illustrates the various operations of an electrosurgical system as an embodiment of the present invention. [Figure 4-1] This is a schematic block diagram of an embodiment of an electrosurgical system. [Figure 4-2] This is a schematic block diagram of an embodiment of an electrosurgical system. [Figure 5] This is a schematic block diagram of the components of an electrosurgical system as one embodiment of the present invention. [Figure 5-1] This is a schematic block diagram of the components of an electrosurgical system as one embodiment of the present invention. [Figure 5-2] This is a schematic block diagram of the components of an electrosurgical system as one embodiment of the present invention. [Figure 5-3] This is a schematic block diagram of the components of an electrosurgical system as one embodiment of the present invention. [Figure 5-4]Schematic block diagram of parts of an electrosurgical system as one embodiment of the present invention. [Figure 6] Schematic block diagram of parts of an electrosurgical system as another embodiment of the present invention. [Figure 6-1] Schematic block diagram of parts of an electrosurgical system as one embodiment of the present invention. [Figure 6-2] Signal diagram showing operations of an electrosurgical system as another embodiment of the present invention. [Figure 6-3] Schematic block diagram of parts of an electrosurgical system as another embodiment of the present invention. [Figure 6-4] Signal diagram showing operations of an electrosurgical system as another embodiment of the present invention. [Figure 6-5] Signal diagram showing operations of an electrosurgical system as another embodiment of the present invention. [Figure 6-6] Signal diagram showing operations of an electrosurgical system as another embodiment of the present invention. [Figure 6-7] Signal diagram showing operations of an electrosurgical system as another embodiment of the present invention. [Figure 6-8] Signal diagram showing operations of an electrosurgical system as another embodiment of the present invention. [Figure 6-9] Signal diagram showing operations of an electrosurgical system as another embodiment of the present invention. [Figure 6-10] Signal diagram showing operations of an electrosurgical system as another embodiment of the present invention. [Figure 6-11] Signal diagram showing operations of an electrosurgical system as another embodiment of the present invention. [Figure 6-12] Signal diagram showing operations of an electrosurgical system as another embodiment of the present invention. [Figure 7] Schematic block diagram of parts of an electrosurgical system as one embodiment of the present invention. [Figure 8] Schematic block diagram of parts of an electrosurgical system as another embodiment of the present invention. [Figure 9] This is a schematic block diagram of parts of an electrosurgical system as another embodiment of the present invention. [Figure 10] This flowchart illustrates the various operations of an electrosurgical system as an embodiment of the present invention. [Figure 11A] This is a flowchart illustrating the operation of an electrosurgical system as one embodiment of the present invention. [Figure 11B] This flowchart illustrates the various operations of an electrosurgical system as another embodiment of the present invention. [Figure 12] This is a graph of illustrative data or results provided by an electrosurgical system as one embodiment of the present invention. [Figure 13] This is an illustrative graph of data or results provided by an electrosurgical system as another embodiment of the present invention. [Figure 14] This is an illustrative graph of data or results provided by an electrosurgical system as another embodiment of the present invention. [Figure 15] This is an illustrative graph of data or results provided by an electrosurgical system as another embodiment of the present invention. [Figure 16] This is an illustrative graph of data or results provided by an electrosurgical system as another embodiment of the present invention. [Figure 17A] This is an illustrative graph of data or results provided by an electrosurgical system as another embodiment of the present invention. [Figure 17B] This is an illustrative graph of data or results provided by an electrosurgical system as another embodiment of the present invention. [Figure 18] This is an illustrative graph of data or results provided by an electrosurgical system as another embodiment of the present invention. [Figure 19] This is an illustrative graph of data or results provided by an electrosurgical system as another embodiment of the present invention. [Figure 20]This is an illustrative graph of data or results provided by an electrosurgical system as another embodiment of the present invention. [Figure 21] This is a perspective view of an electrosurgical melting device as one of various embodiments of the present invention. [Figure 22] This is a perspective view of a part of an electrosurgical melting device as one of various embodiments of the present invention. [Figure 23] This is a perspective view of the distal end of an electrosurgical instrument as one of various embodiments of the present invention. [Figure 24] This is a perspective view of the distal end of an electrosurgical instrument as one of various embodiments of the present invention. [Figure 25] This is a side cross-sectional view of the distal end of an electrosurgical instrument as one of various embodiments of the present invention. [Figure 26] This is a side view of the distal end of an electrosurgical instrument as one of various embodiments of the present invention. [Figure 27] This is a side cross-sectional view of an electrosurgical instrument as one of various embodiments of the present invention. [Figure 28] This is a side view of the distal end of an electrosurgical instrument as one of various embodiments of the present invention. [Figure 29] This is a side cross-sectional view of the distal end of an electrosurgical instrument as one of various embodiments of the present invention. [Figure 30] This is a side cross-sectional view of an electrosurgical instrument as one of various embodiments of the present invention. [Figure 31] This is a side cross-sectional view of a portion of an actuator for an electrosurgical instrument, which is one of various embodiments of the present invention. [Figure 32] This is a side cross-sectional view of an electrosurgical instrument as one of various embodiments of the present invention. [Figure 33] This is a side cross-sectional view of a portion of an actuator for an electrosurgical instrument, which is one of various embodiments of the present invention. [Figure 34] This is a side cross-sectional view of the distal end of an electrosurgical instrument as one of various embodiments of the present invention. [Figure 35] This is a front cross-sectional view of the distal end of an electrosurgical instrument as one of various embodiments of the present invention. [Figure 36] This is a perspective view of a post as one of various embodiments of the present invention. [Figure 37] This is a side view of a post as one of various embodiments of the present invention. [Figure 38] This is a front cross-sectional view of the distal end of an electrosurgical instrument as one of various embodiments of the present invention. [Figure 39] This is a front cross-sectional view of the distal end of an electrosurgical instrument as one of various embodiments of the present invention. [Figure 40] This is a front cross-sectional view of the distal end of an electrosurgical instrument as one of various embodiments of the present invention. [Modes for carrying out the invention]

[0015] According to various embodiments, an electrosurgical system is provided that includes an electrosurgical generator and an electrosurgical instrument configured to optimally melt tissue. According to various embodiments, the electrosurgical instrument is provided for use in laparoscopic surgery, having the ability to move, grasp, compress, and melt tissue by delivering RF energy. According to various embodiments, the electrosurgical instrument is a bipolar electrosurgical instrument that can be inserted through a 5 mm trocar and cuts tissue by the action of a mechanical cutting blade. RF energy is supplied by an electrosurgical generator, which is configured to deliver appropriate RF energy to melt tissue. According to various embodiments, the generator determines appropriate RF energy and the appropriate manner to deliver RF energy for an electrosurgical instrument in a particular connected state to the instrument and / or to specific tissue associated with a particular surgical procedure. According to various embodiments, information or data to help determine appropriate RF energy and the manner in which RF energy is delivered is provided or obtained externally from the generator. The external source is preferably one or more memory modules, which in various embodiments may be incorporated into the electrosurgical instrument via a connection (wired or wireless) to it, or via a separate tool, accessory and / or adapter and / or connection to them and / or via a separate port or generator connection. The generator retrieves and / or receives data and uses this data to issue commands or operate the generator to determine and supply appropriate RF energy in an appropriate manner.

[0016] In general, various embodiments provide a bipolar electrosurgical melting instrument or tool configured to melt tissue trapped between jaws. The jaws extend from elongated shafts coupled to actuators. The actuators are accessible to the user, thereby allowing the user to operate the jaws to open and close them and change their orientation or position. The user can also initiate the melting of tissue in contact with the jaws via the actuators. In various embodiments, each jaw is provided with an electrode, which can be connected to an electrosurgical energy source, such as an electrosurgical generator, thereby transmitting radio frequency (RF) energy between the jaws and the electrosurgical generator and to the tissue trapped between the jaws. A movable blade is also provided for cutting the tissue trapped between the jaws. In various embodiments, at least one jaw has at least one conductive post positioned between the blade and the electrode of this jaw. The conductive posts are made of the same conductive material as the jaw electrodes, but unlike the electrodes, they are not connected to or can not be connected to the electrosurgical generator to transmit RF energy between the conductive posts and the electrosurgical generator. However, according to various embodiments, the conductive posts are better involved in transmitting electrosurgical energy between the jaws and to the tissues between the jaws.

[0017] Referring to Figures 1 and 2, an exemplary embodiment of an electrosurgical system is shown, which includes an electrosurgical generator 10 and a detachably connectable electrosurgical instrument 20. The electrosurgical instrument 20 is preferably electrically coupled to the generator via a cable connection 30 to a tool or instrument port 12 provided on the generator. The electrosurgical instrument 20 is preferably provided with auditory, tactile, and / or visual indicators to inform the user of a specific predetermined state of the instrument, such as the start and / or end of a melting or cutting operation. In other embodiments, the electrosurgical instrument 20 is preferably reusable and / or connectable to another electrosurgical generator for another surgical procedure. In some embodiments, a manual control device, such as a hand or foot switch, is preferably connectable to the generator and / or instrument to enable predetermined selective control of the instrument, for example, to initiate a melting or cutting operation.

[0018] According to various embodiments, the electrosurgical generator 10 is configured to generate radio frequency (RF) electrosurgical energy and to receive data or information from an electrosurgical instrument 20 electrically coupled to the generator. In one embodiment, the generator 10 outputs RF energy (150V and 5A at 375VA, 350kHz), and in one embodiment, it is configured to calculate the phase angle or difference between the RF output voltage and the RF output current while operating or supplying RF energy. The generator adjusts the voltage, current and / or power and monitors the RF energy output (e.g., voltage, current, power and / or phase). In one embodiment, the generator 10 stops the RF energy output under predetermined conditions, for example, when an instrument switch is deasserted (e.g., when a fuse button is released), when a time value is met and / or when the active phase angle and / or phase change exceeds a certain phase and / or phase stop value.

[0019] The electrosurgical generator 10 has two novel bipolar tool ports 12, a standard bipolar tool port 16, and a power port 14. In other embodiments, the electrosurgical unit may have a different number of ports. For example, in some embodiments, the electrosurgical generator may have three or more or one or fewer novel bipolar tool ports, two or more or zero standard bipolar tool ports, and two or more or zero power ports. In one embodiment, the electrosurgical generator has only two novel bipolar tool ports.

[0020] According to various embodiments, each new type of bipolar tool port 12 is configured to be coupled to an electrosurgical instrument equipped with a mounted or integrated memory module. A standard bipolar tool port 16 is configured to accept non-specific bipolar electrosurgical tools, different from the new type of bipolar electrosurgical instruments that can be connected to the new type of bipolar tool port 12. A power port 14 is configured to accept or be connected to non-specific bipolar electrosurgical tools and DC accessory devices, different from the new type of electrosurgical instrument. The power port 14 is configured to supply a DC voltage. For example, in some embodiments, the power port 14 can provide about 12 volts DC. The power port 14 is preferably configured to supply power to surgical accessories, such as ventilators, pumps, lights, or other surgical accessories. Thus, in addition to replacing the electrosurgical generator for standard or non-specific bipolar tools, the electrosurgical generator can be replaced as a power source for surgical accessories. In some embodiments, replacing existing generators and power supplies with electrosurgical generators can reduce the amount of storage space required on storage racks, cards, or shelves for numerous trunk cords needed within a surgical or operating workspace.

[0021] In one embodiment, the generator does not actively check the tool when a non-specific bipolar tool is coupled to a standard bipolar port. However, the generator recognizes the connection so that it can display information about the non-specific bipolar tool. According to various embodiments, the generator recognizes the instrument connection status for each of the new tool ports 12, authenticates the connected instrument, and then receives RF energy activation requests (e.g., activation of instrument switches, e.g., fuse buttons). In one embodiment, the generator reads authenticated data from the connected instrument and also reads electrical control values ​​(e.g., voltage level setting, current level setting, power level setting, active phase angle level setting, RF energy output activation timing limit, instrument short-circuit limit, instrument open-circuit limit, instrument model / identification, RF energy output line configuration, switch state command configuration, and / or combinations thereof) from the authenticated and connected instrument.

[0022] In various embodiments, the electrosurgical generator 10 may have a display 15. The display may be configured to indicate the status of the electrosurgical system, such status may include, among other things, the status of one or more electrosurgical instruments and / or accessories, connectors or connections thereto. In some embodiments, the display may consist of a multiline display, such as an LCD panel display, which can provide text and graphic information, and in some embodiments, such an LCD panel display may be illuminated via a backlight or sidelight. In some embodiments, the display may consist of a multicolor display, which may be configured to display information about specific instruments electrically coupled to the electrosurgical generator and colors corresponding to specific surgical procedures (e.g., cutting operations indicated by yellow text and graphics, melting or welding operations indicated by purple, and coagulation operations indicated by blue, and bloodless dissection operations which may be indicated by yellow and blue).

[0023] In some embodiments, the display is preferably configured to simultaneously display status data for multiple instruments, which are divided to display status information for each instrument electrically coupled to and / or connected in correspondence to the tool port. Visual indicators, such as status bar graphs, can be used to illustrate the proportion of total effective electrical energy to be applied to a bipolar electrosurgical instrument during operation. In various embodiments, an electrosurgical instrument capable of cutting, coagulating, or melting tissue may have three color displays or bar graphs. In some embodiments, the user can switch the display between displaying the status of multiple electrically connected instruments and displaying the status of a single electrically connected instrument. According to various embodiments, once instruments and / or accessories are connected and / or detected, a window on the user interface display opens to show the instrument connection type and status.

[0024] The electrosurgical generator may, according to various embodiments, have a user interface, for example, a number of buttons 17. These buttons enable user interaction with the electrosurgical generator, allowing, for example, requests to increase or decrease the electrical energy supplied to one or more instruments coupled to the electrosurgical generator. In other embodiments, the display 15 may be a touchscreen display, thus incorporating data display and user interface functions. According to various embodiments, the surgeon can set the voltage setting value by selecting one to three levels via the user interface. For example, at level 1, the voltage is set to 110V; at level 2, the voltage is set to 100V; and at level 3, the voltage is set to 90V. For all three levels, the voltage is set to 5 amperes and the power is set to 300 VA. In other embodiments, the voltage is preset to a specific level, for example, level 2, or this is the default. In other embodiments, the voltage setting, like the current and power setting, is not user-adjustable to simplify the operation of the generator; therefore, a predetermined default voltage setting is used, for example, with the voltage set to 100V.

[0025] In one embodiment, the electrosurgical tool or instrument 20 may further have one or more memory modules. In some embodiments, the memory may include operational data relating to this instrument and / or other instruments. For example, in some embodiments, the operational data may include information regarding electrode configuration / reconfiguration, instrument usage, operating time, voltage, power, phase and / or current setting values, and / or information relating to specific operating states, conditions, scripts, processes or procedures. In one embodiment, the generator initiates reading from and / or writing to the memory modules.

[0026] In one embodiment, each new bipolar electrosurgical instrument is accompanied by a memory module and / or integrated circuitry that provides instrument authentication, configuration, expiration, and logging. The instrument verification and authentication process is initiated by coupling such instrument into a receptacle or port. Instrument authentication is provided, in one embodiment, via a challenge-response scheme and / or via a stored secret key also shared by the generator. Other parameters have a hash key for integrity checks. Usage is logged in the generator and / or instrument integrated circuitry and / or memory. In one embodiment, unlogged usage may occur as a result of errors. In one embodiment, the logging is set in binary and interpreted offline by the instrument or via the generator.

[0027] In one embodiment, the generator monitors the expiration of the instrument using a time measurement component. Such a component utilizes a polling oscillator, timer, or real-time calendar clock configured with the boot time. Timer interrupts are handled by the generator and can be used by a script for timeout events. Logging also displays logged events with their timestamps using a timer or counter.

[0028] According to various embodiments, the generator provides the ability to read the phase difference between the voltage and current of the RF energy sent to a connected electrosurgical instrument while the RF energy is active. While the tissue is being melted, the phase readings are used to detect different states during the melting process.

[0029] In one embodiment, the generator logs usage details in a downloadable internal log. The generator has memory for storing code and instrument performance. The generator has programmable memory containing instructions for specific instrument performance. The memory holds, for example, the serial number and instrument usage parameters. The generator stores information about the type of connected instrument. Such information includes, but is not limited to, the instrument identifier, such as the serial number of the connected instrument, the number of times the connected instrument has been used or the duration of use, and changes made to the power setting and default setting of each instrument. In one embodiment, the memory holds data for about two months, about 10,000 instrument uses or up to 150 logged startups, and this memory is configured to overwrite itself as needed.

[0030] According to various embodiments, the generator does not monitor or control current, power, or impedance. The generator can adjust and match voltage. The delivered electrosurgical power is a function of the applied voltage, current, and tissue impedance. The generator can influence the delivered electrosurgical power through voltage adjustment. However, increasing or decreasing the voltage does not necessarily increase or decrease the delivered electrosurgical power. Power reactions are caused not by the power-supplying generator, but by the power or tissue state interacting with the tissue without any control by the generator.

[0031] Once the generator starts supplying electrosurgical power, it does so continuously, for example, every 150 ms, until a failure occurs or a specific phase parameter is reached. In one embodiment, the jaws of the electrosurgical instrument are opened, so that the pressure can be released before, during, and at any point after the application of electrosurgical power. In another embodiment, the generator does not interrupt or wait for a specific duration or a predetermined time delay to initiate the cessation of electrosurgical energy.

[0032] In one embodiment, an electrosurgical process, such as a tissue melting process, is initiated by pressing a switch on the instrument or tool (51), thereby starting the initial measurement sequence as shown in Figure 3. With the switch on the tool turned on, the generator takes an initial measurement of the tissue (open circuit, short circuit, etc.) (52), and based on the initial measurement, starts or stops supplying RF energy (53). According to various embodiments, the generator measures the tool and / or tissue impedance and / or timing and / or determines whether the phase angle is within an acceptable range. In one embodiment, the generator performs tissue measurements between electrodes of an electrosurgical instrument connected to a generator that utilizes RF energy in a low energy range (e.g., a voltage of about 1 to 10 volts) that does not produce psychological effects (i.e., passive measurement). In various embodiments, the generator uses the initial impedance measurement to determine whether the instrument is short-circuited, faulty, open-circuited, etc. Based on the positive results of the initial check, the generator enables the supply of RF energy from the generator to the electrosurgical instrument and ultimately to the tissue (54). After the RF power has been turned on and the RF power is being supplied continuously by the generator, the generator monitors the phase angle or phase difference and / or change between the power and voltage of the supplied RF energy (55).

[0033] At a predetermined time, under predetermined conditions, or at a predetermined threshold (56), the supply of RF energy is stopped (57). In this case, an acoustic and / or visual signal is emitted indicating that tissue is melting (or that an error (e.g., a short circuit in the electrodes) has occurred and / or an unexpected condition (e.g., an acceptable condition despite an unexpected switch being released) has occurred). According to various embodiments, the predetermined time, condition, threshold, and / or initialization check are determined based on a provided instrument algorithm or script for the connected electrosurgical instrument, procedure, or preference. According to various embodiments, the measured tissue tolerance and the results of conductivity or initial phase shift are used to determine the endpoint for the connected instrument.

[0034] Referring to Figure 4-1, in one embodiment, the electrosurgical generator 10 is connected to the AC main input, and a power supply 41 converts the AC voltage from the AC main input to a DC voltage to power the various circuits of the generator. The power supply also supplies the DC voltage to an RF amplifier 42, which generates RF energy. In one embodiment, the RF amplifier 42 converts 100VDC from the power supply into a sine wave at a frequency of 350kHz, and this frequency is transmitted through the connected electrosurgical instrument. An RF sense circuit 43 measures / calculates the voltage, current, power, and phase at the output of the generator, and the RF energy in the generator is supplied to the connected electrosurgical instrument 20. The measured / calculated information is transmitted to a control device 44.

[0035] In one embodiment, the RF sense analyzes the measured AC voltage and current from the RF amplifier and generates a DC signal for control signals sent to the control device for further processing, such control signals include voltage, current, power, and phase. In one embodiment, the RF sense circuit 43 measures the output voltage and current and calculates the mean square (RMS) of the voltage and current, the apparent power of the RF output energy, and the phase angle of the voltage and current of the RF energy supplied through the connected electrosurgical instrument. In particular, the voltage and current of the output RF energy are processed by the analog circuit of the RF sense to generate real and imaginary components of both voltage and current. These signals are processed by the FPGA to give different measurements of voltage and current, such measurements include the AC signal, the phase difference between voltage and current, and the RMS measurement of power. Thus, in one embodiment, the output voltage and current are measured in analog form, converted to digital, processed by the FPGA to calculate the RMS voltage and current, apparent power, and phase angle between voltage and current, and then converted back to analog for the control device.

[0036] Next, referring again to Figure 4-2, for each instrument port 45a, 45b, there is a pair of signals for voltage and a pair of signals for current coming from the RF amplifier 42. In one embodiment, the generator has two redundant RF sense circuits 43a, 43b that measure voltage and current for each instrument at different locations on the RF amplifier. The first RF sense circuit detects currents 145a, 145b sent through the connected electrosurgical instrument on either instrument port 1 or instrument port 2 using sense resistors 141, 142, and also detects voltages 148a, 148b measured before and after the return to the output on either instrument port 1 or instrument port 2. The second RF sense circuit detects currents 147a and 147b returned from the connected electrosurgical instrument on either instrument port 1 or instrument port 2 using sense resistors 143 and 144, and also detects voltages 146a and 146b measured before and after the return output on either instrument port 1 or instrument port 2. The voltage input signal is a high-voltage sinusoidal waveform at 350 kHz that is attenuated and AC-coupled by a voltage divider and an inverting filter to remove DC bias from the signal. The reason for using an inverting filter is that the voltage and current inputs are 180° out of phase when measured with opposite polarities. For each voltage input signal, two separate inverted and non-inverted voltage sense signals are generated. In one embodiment, differential voltage measurements between the voltage input signals are performed to generate two separate pairs of inverted and non-inverted current sense signals. The current input signal represents the voltage across the shunt resistor on the RF amplifier, and within the RF amplifier, this voltage is proportional to the current flowing through the shunt resistor. The current input signal is a low-voltage sinusoidal waveform at 350 kHz, amplified using a non-inverting filter to remove DC bias from the signal. The RF sense generates a signal similar to the result obtained by multiplying each voltage and current signal by a predetermined reference signal. Therefore, the RF sense outputs non-inverting voltage and current sense signals when the waveform is positive, inverting voltage and current sense signals when the waveform is negative, and a ground signal when the waveform is zero.

[0037] The RF sense, according to various embodiments, receives four reference synchronization signals supplied by a control device via an RF amplifier. The synchronization signals are 350 kHz pulse signals having the same duty cycle but different phase shifts, and in one embodiment, they are 90° out of phase with each other. Two of the synchronization signals are used to produce in-phase waveforms to generate the real component of the input waveform, and the other two synchronization signals are used to produce quadrature waveforms to generate the imaginary component of the input. These signals are further processed to generate control signals to a plurality of switches. The outputs of the switches are coupled together to produce a signal output. In one embodiment, the control signals to the switches determine which input signals pass through to become the signal output. According to various embodiments, a first combination allows non-inverting voltage and current sense signals to pass through, which represents multiplying these sense signals by a positive pulse or similar. A second combination allows inverting voltage and current sense signals to pass through, which represents multiplying these sense signals by a negative pulse or similar. A third combination allows the ground signal to pass through, representing multiplying the sense signal by zero or generating a similar zero-voltage output. Each output is sent to a low-pass filter, which generates a DC voltage corresponding to the real or imaginary component of the detected signal. These signals are fed to an ADC, which then sends the digital signal to the FPGA.

[0038] In one embodiment, the control device 44 controls the RF amplifier 42 to affect the output RF energy. For example, the control device uses information provided by the RF sense 43 to determine whether RF energy should be output and to determine when to stop outputting the RF energy. In one embodiment, the control device determines when to stop outputting the RF energy by comparing a predetermined phase threshold based on the connected electrosurgical instrument 20 and the specific tissue in contact with it. In various embodiments, the control device performs a melting process, which is described in detail below, and in some embodiments, the control device receives commands and setpoints or script data for performing the melting process from data sent from the electrosurgical instrument.

[0039] According to various embodiments shown in Figure 4-2, the generator has six main subsystems or circuit modules, including a system power source or power supply 45, a control device 44, a front panel interface 46, a new bipolar instrument interface 47, an RF amplifier 42, and an RF sense 43. According to various embodiments, one or more of the circuits may be combined with or integrated with the other circuits. The power supply 45 is configured to control the power output by providing a DC voltage along with control signals to all other circuits or subsystems. The power supply receives an AC power input of 90-264VAC, 47-63Hz, and in one embodiment, the power supply has an integrated or separate switch configured to connect or disconnect the AC power input to the generator. The control device supports instrument connections for the user interface 21 and electrosurgical instruments 1,2 connected to the electrosurgical generator via the front panel interface (FPI) and the new bipolar instrument interface (ABDI).

[0040] The RF amplifier 42 generates high-power RF energy, which is passed through the connected electrosurgical instrument and, in one embodiment, an electrosurgical instrument for tissue melting. According to various embodiments, the RF amplifier converts a 100VDC power supply into a high-power sinusoidal waveform having a frequency of 350kHz, which is then sent into the ABDI 47 and ultimately into the connected electrosurgical instrument. The RF sense 43 interprets the measured AC voltage and current from the RF amplifier 42 and generates DC control signals, which are interpreted by the control device 44, and such DC control signals include voltage, current, power, and phase.

[0041] The generator has several dedicated connection receptacles, in the illustrated embodiment, instrument port 1 and instrument port 2, used solely for connection to new bipolar instruments, such as the electrosurgical melting instruments described in detail below. Each dedicated receptacle includes an array spring-pushed probe or a pogo pin. In various embodiments, the generator has a circuit to detect the presence of the new bipolar instrument prior to the energization of the active output terminals at the receptacle.

[0042] The front panel interface (FPI) 46 is configured to drive the display, instrument signals from the control unit, and LED backlights for the front panel buttons. The FPI is also configured to provide power isolation via a regulator and to provide functionality for the front panel switches / buttons. In one embodiment, the ABDI 47 is used as a pass-through connection that connects to the instrument via the FPI. The FPI also allows connection of the connected electrosurgical instrument to the control unit 44 via the ABDI. In one embodiment, this instrument interface is electrically isolated from the rest of the FPI. In various embodiments, the interface has lines for reading and writing to FRAM® on the new bipolar instrument, reading trigger switches and / or reading signals indicating that the instrument is connected. In one embodiment, an instrument memory circuit is provided that utilizes the SPI interface of the control unit to read and write to FRAM® on the new bipolar instrument. In one embodiment, a microcontroller is used instead of FRAM®, and the interface has interrupt lines, so that all information is transmitted between the electrosurgical instrument and the generator via a digital interface. FPI provides isolation for SPI signals to and from novel bipolar devices via ABDI. In one embodiment, the isolation interface for SPI signals is shared by two novel bipolar devices, and a port pin is used as a chip select.

[0043] According to various embodiments, the generator has an SPI communication bus that allows the control unit to have a bidirectional communication relationship with the CPLD and the RF sense FPGA. In various embodiments, the FPI provides an SPI interface between the control unit and the connected device via an ABDI connector to communicate with the FRAM® on the novel bipolar device. The FPI also provides electrical isolation for low-voltage signals from between the control unit and the ABDI. The device interface on the ABDI is configured to transmit RF energy to the connected device along with isolated interface communication for SPI signals. In one embodiment, the ABDI provides a connection for signals from the device indicating that the device is connected.

[0044] The FPI-ABDI interface provides power to the devices connected to the generator, enables SPI communication between the control unit and the devices, provides device switch signals from the devices to the control unit, and provides device connection signals from the devices to the control unit. ABDI provides RF energy to each connected new bipolar device via a separate pogo pin array. The FPI provides signals from the FPI and RF amplifier, low-voltage power and high-voltage RF power to connected devices via the ABDI connector through the pogo pin array.

[0045] Next, referring again to Figure 5, the RF amplifier has a transistor H-bridge circuit in which a pair of transistors within the transistor H-bridge circuit are switched ON or OFF according to a pulse-width modulated signal from a fault detection circuit 31, thereby generating a sinusoidal signal from the DC voltage supplied to the RF amplifier. The RF energy is supplied to the electrosurgical instrument via the instrument port 45. The sinusoidal signal is filtered by a filter circuit 32 and then sent to the connected, active electrosurgical instrument by a switching and tissue measurement circuit 33. Voltage, current, power, phase, and other measurement / calculation information are obtained by the voltage and current sense circuit 34 in conjunction with the RF sense 43. In one embodiment, the generator has a relay matrix that selectively switches or directs the RF energy from the RF amplifier to one of the instrument ports. In one embodiment, the switching and tissue measurement circuit 33 has a low-voltage network analyzer circuit used to measure instrument and / or tissue impedance before turning on the RF power. If successful, for example, if no short circuit or open circuit is detected with respect to the electrosurgical instrument, the RF energy is switched, and thus the RF amplifier 42 supplies RF energy to one of the instrument ports 45.

[0046] In one embodiment, the RF amplifier 42 receives voltage and current setting values ​​input by the user via a user interface to set the output level of the RF amplifier. The user setting values ​​are converted to operating levels by the RF amplifier's digital-to-analog converter. In one embodiment, the setting values ​​include a maximum voltage output, a maximum current output, and a maximum power output. According to various embodiments, the RF amplifier provides RF energy based on one or more of these setting values, and provides the output voltage of the RF amplifier such that it does not exceed one or more of the setting values.

[0047] According to various embodiments, the RF amplifier manages the DC-RF conversion process and certain system electrical measurements. Switching and structural measurement circuits route the RF transformer or measurement component to the output electrodes. According to various embodiments, volt-ampere (VA) is a unit used for the apparent power provided by the generator, and this VA is equal to the product of the mean square (RMS) voltage and the RMS current. In a direct current (DC) circuit, this product is equal to the actual power (active power) expressed in watts. Volt-ampere is useful in relation to alternating current (AC) circuits (sinusoidal voltage and sinusoidal current of the same frequency). Although volt-ampere and watt have dimensions of power (energy rate over time), they are still different from each other.

[0048] The control device FPGA has direct control of the RF output relay. The output relay configuration determines which drive signal (RF or tissue measurement) is sent to which instrument port, i.e., instrument port 1 or instrument port 2, as shown in Figures 5-1 and 5-4. During calibration, the relay is also connected to a predetermined load applied to the tissue measurement analyzer, such as a resistor with a set value, and this resistor can be calibrated before connecting the instrument load (the load of an electrosurgical instrument in contact with tissue). The RF output relay is arranged by or incorporated into the RF amplifier 42.

[0049] According to various embodiments, the control unit generates a pair of device 1 relay control signals for the device 1 relay pair 61 to connect the RF energy bus to device port 1. Similarly, the control unit generates a pair of device 2 relay control signals for the device 2 relay pair 62 to connect the RF energy bus to device port 2. The RF amplifier relay pair 63 controls whether the RF amplifier output is connected to the RF energy bus, and the tissue measurement relay pair 64 controls whether the tissue measurement analyzer is connected to the RF energy bus. The RF amplifier and tissue measurement analyzer are sources to the RF energy bus, and the device ports are destinations for the selected energy. The tissue measurement calibration relay 65 connects a predetermined calibration load to be applied to the RF energy bus.

[0050] Therefore, various embodiments are used to direct the flow of RF energy or the output of a tissue measurement circuit to one of the instrument ports. Four pairs of relay signals control four pairs of relays that change the flow of energy through the system. The first pair of relays allows a high-power RF signal to flow to the ABDI 47 and ultimately into the connected instrument. The second pair of relays allows the tissue measurement circuit to send a signal from the instrument through the ABDI and measure such a signal. The third and fourth pairs of relays allow a signal, whether it is a high-power RF signal or a tissue measurement signal, to flow through the ABDI to either instrument 1 or instrument 2. The signals that control the relays are controlled by the control device 44.

[0051] The calibration signal controls a fifth relay that enables a microstructure measurement circuit in the control unit to measure a predetermined load 66. The input signal to the relay circuit, which is HIGH when the relay is open, is inverted by a phase inverter. The output to the phase inverter is connected to a MOSFET, which controls the relay. When the relay must be closed, the input to the relay circuit becomes LOW, causing the output of the phase inverter and thus the input to the MOSFET to become HIGH. When the input to the MOSFET is HIGH, 5V flows through the coil, closing the relay and allowing the signal to pass through. The relays are opened and closed in a specific order or sequence determined by the control unit.

[0052] According to various embodiments, the device 1 active signal is asserted when the relay is configured to face RF on device port 1 or tissue measurement energy, the device 2 active signal is asserted when the relay is configured to face RF on device port 2 or tissue measurement energy, and the device 1 and device 2 RF ON signals are active only when the RF amplifier is ON and the relay is at the RF energy on the device 1 configuration or the RF energy on the device 2 configuration, respectively.

[0053] The control device FPGA controls the RF amplifier based on settings provided by the microcontroller. In one embodiment, the settings from the microcontroller are set by a script file retrieved from memory attached to the connected electrosurgical instrument 4. In one embodiment, the microcontroller sets the desired voltage, current, and power levels and enables the RF amplifier output.

[0054] In one embodiment, a low-power buffered voltage-out DAC provides voltage, current, and power setpoints to a control loop and an error amplifier. The control loop or system is shown in Figure 5-5. Voltage, current, and power feedback voltages 84, 85, 86 pass through a filter shown as a gain stage 87. This filtered feedback is summed with the respective setpoint parameters (88), and each error is then integrated into a circuit 89 tuned for each parameter. All error outputs combine with diode 80, resulting in the lowest output controlling the PWM circuit 90.

[0055] Each of the low-pass voltage, current, and power feedback signals, as well as the inverting set voltage, current, and power signals (VSET81, ISET82, PSET83), passes through a resistor and combines with each other to produce signals with amplitudes of (FVltFBT-Vset) / 2, (FCurFBT-Iset) / 2, and (FPwrFBT-Pset) / 2, which are considered error signals in each control loop. The next step is a proportional-integral control unit (PI), which produces DC signals (VError, IError, PError) as a result of changes in the error signals at its input. VError, IError, and PError are used in the summing junction to determine which of the voltage, current, or power is under the control of the main control loop to force a particular PWM duty cycle for the RF amplifier 42.

[0056] Next, referring again to Figure 6, the RF sense 43 has a synchronous detector that samples the RF energy being sent to the electrosurgical instrument. The RF sense removes undesirable harmonics from the RF energy by multiplying the supplied RF energy by one or more reference signals. From the product of the signals, RMS voltage, RMS current, apparent power, and phase information can be calculated. The RF sense includes an ADC circuit 36, an isolation component 37, an FPGA 38, and a DAC 39. The real and imaginary components of the raw current and voltage data are obtained by the analog-digital circuit, and these components are provided to the FPGA 38 via an isolation barrier or component 37 for processing by these components. In the illustrated embodiment, two instrument channels are provided for two novel bipolar electrosurgical tool ports and associated instruments. Fault detection data 35 is sent through the FPGA 38, and the digital form of the measured or calculated voltage, current, power, and phase is provided by the DAC circuit 39. In one embodiment, the FPGA is responsible for signal processing of the feedback signal from the synchronous detector, and such FPGA is also responsible for fault detection.

[0057] The ADC36 simultaneously samples the output from the synchronous detector, and this result represents the real and imaginary values ​​of the voltage and current of the output signals on each instrument port. After the ADC has sampled, the FPGA stores these values ​​in the ADC control module. The ADC error correction module corrects the sampling error by retrieving this data from the ADC control module via a multiplexer and applying offset and gain corrections.

[0058] The output of the ADC error correction module displays the real and imaginary components of voltage and current from both the active and inactive device ports. The output of the ADC correction module also outputs a sign bit for each signal from the active device port for phase calculation. A separate module receives the real and imaginary values ​​of voltage and current from the active device port and computer-calculates the magnitude of RMS voltage, RMS current, and apparent power, as well as the phase between voltage and current. Once these values ​​are computer-calculated, the DAC error correction module applies offset and gain correction to the scaled and encoded display of each signal. DAC error correction is performed sequentially on voltage, current, power, and phase. This data is sent to the DAC control module. The DAC control module sends the data to the DAC.

[0059] FPGA38 monitors real and imaginary values ​​for voltage and current, and generates a fault code if these values ​​deviate beyond a specific threshold on the inactive device port. Additionally, the FPGA will generate a fault code if the phase relationship between synchronization signals is lost. The synchronization monitor module has four inputs that are always 180° out of phase with each other. This module monitors whether there is a valid time relationship between the signals and flags an error if a violation occurs.

[0060] According to various embodiments, the RF sense FPGA is configured to correct errors in the RF feedback signals and to calculate the amplitude and phase of these signals. The RF sense synchronous detector uses the synchronous signals generated by the control device FPGA to generate in-phase (real) and quadrature (imaginary) components of the voltage and current feedback signals from the RF amplifier. The RF sense FPGA monitors the phase relationships between the synchronous signals generated by the control device and asserts a fault if the phase relationships are broken.

[0061] According to various embodiments, multiple synchronization signals are used as clock inputs for RF sensing. The synchronization signals have the same duty cycle and frequency. The only difference between the signals lies in their phase relationship. For example, in one embodiment, a first synchronization signal is used as a reference, a second synchronization signal is identical to the first but delayed by 180°, a third synchronization signal is delayed by 90° from the first synchronization signal, and a second synchronization signal is delayed by 270° from the first synchronization signal. The clock edges provided by these four signals provide the precise timing required by RF sensing for proper sampling of the RF output signal.

[0062] According to various embodiments, electrosurgical generators measure RF output voltage and current. However, due to the electrosurgical nature of the generator, measurements must be performed using isolated circuits. Voltage measurements are preferable because they have a relatively high signal-to-noise ratio. However, current measurements using current transformers present problems because a considerable level of PWM output stage switching noise exists in the circuit, and the isolation of a typical current transformer is insufficient to suppress this noise to achieve the desired or required accuracy. Directly sampling output voltage and current using a secondary-side reference (floating) analog-to-digital converter (ADC) and shunt resistors can also lead to other problems.

[0063] PWM switching noise is not harmonically related to the fundamental PWM carrier frequency, and this PWM switching noise has a wide bandwidth. To overcome this noise, it is best to significantly oversample the signal to achieve the desired or required accuracy. However, for a 350kHz PWM carrier frequency, 64 times the Nyquist sampling frequency, and 12-bit resolution, the required speed of the digital stream is 5.376 × 10⁻¹⁶ per ADC channel. 8 The performance is in bits / second. ADCs and digital isolators with this performance are difficult to source and relatively expensive.

[0064] According to various embodiments, the frequency requirements for digital streams can be reduced by using a high-precision analog preprocessor. Analog preprocessors take advantage of the fact that the time variation of RF output voltage and current is relatively slow, and that such signals generally have a narrow useful bandwidth.

[0065] In one embodiment, the analog preprocessor has a synchronous detector that enables the transport of the RF signal spectrum from a region concentrated around the carrier frequency down to zero. The narrow bandwidth significantly simplifies the complexity of the ADC and digital isolator. Consequently, the ADC sampling frequency may be low, and the digital isolator throughput is reduced. The digital isolator coupling capacitance is also reduced by reducing or minimizing the number of parallel channels. In general, the requirements for processing speed are reduced, thereby resulting in less expensive components.

[0066] Referring to Figures 6-1 to 6-4, according to various embodiments, the synchronous detector has an analog multiplier, which determines the overall accuracy of the circuit. However, due to the presence of off-band PWM noise and / or a 350 kHz carrier frequency, existing analog multipliers do not meet the accuracy requirement of 0.5% or higher.

[0067] The local oscillator (LO) required for spectral conversion should preferably be of the non-sinusoidal type. If the number of gain levels present in such a waveform is limited, the analog multiplier can be implemented using analog switches instead of a multiplier.

[0068] In one embodiment, as shown in Figures 6-1 and 6-2, the LO waveforms used 95, 96 are preferably square waves, and the gains 91, 92 are either +1 or -1. Low-pass filters (LPFs) 93, 94 located at the output of the switch are used for averaging and to suppress conversion components with high frequencies. The input signal 97 of the synchronous detector can be set as the fundamental frequency as follows. TIFF0007855626000001.tif13166 In the above equation, T is defined as the fundamental period, A is the fundamental amplitude, and p is the fundamental phase. The third harmonic frequency can be defined as follows: TIFF0007855626000002.tif13166 In the above equation, kA is defined as the amplitude of the third harmonic frequency, k is the ratio of the third harmonic amplitude to the fundamental amplitude, and q is the phase of the third harmonic frequency. The real (Re) and imaginary (Im) output voltages of the synchronous detector are as follows. TIFF0007855626000003.tif34166 TIFF0007855626000004.tif21166

[0069] If only the fundamental frequency is present in the input signal spectrum (k=0), the complex amplitude can be calculated as follows. TIFF0007855626000005.tif13166 TIFF0007855626000006.tif13166 If the amplitude of the third harmonic is not equal to zero, the complex amplitude may have a different result.

[0070] Next, referring to Figures 6-3 and 6-4, according to various embodiments, complex LO3 level waveforms 98 and 99 generated by a 3-level waveform local oscillator can be used. By using the LO3 level waveform, the real and imaginary output voltages become independent of the presence of third harmonics, although they may be distorted if higher harmonics are present. The real (Re) and imaginary (Im) output voltages of the synchronous detector are as follows. TIFF0007855626000007.tif34166 The reason for this is, TIFF0007855626000008.tif11170 Then, TIFF0007855626000009.tif11170 and TIFF0007855626000010.tif43170 In this case, the complex amplitude is as follows: TIFF0007855626000011.tif21170

[0071] Therefore, the dependence on the presence of any level of third harmonic is eliminated. According to various embodiments, the symmetry of the RF amplifier inevitably produces a signal with low levels of even harmonics. The low-pass filter can also, in one embodiment, suppress the high-frequency PWM carrier component and suppress the fifth harmonic to a sufficiently low level. Furthermore, an example of the operation of the synchronous detector is provided by the exemplary signal waveforms at the respective outputs (SynchDetRe and SynchDetIm) prior to filtering by the low-pass filter 93 for an exemplary input signal (Uin=cosωt), as shown in Figures 6-5 and 6-6. Figures 6 and 7 provide an exemplary signal waveform (e.g., Uin=cos(ωt+π / 4)) showing a phase-shifted input signal, and simultaneously show the exemplary signal waveforms at the respective outputs (SynchDetRe and SynchDetIm) prior to filtering by the low-pass filter 93 for such an input signal, as shown in Figures 6-8 and 6-9. Figures 6-10 provide exemplary input signals that, although significantly degraded, do not contain harmonics higher than the fourth harmonic, and similarly provide exemplary signal waveforms at their respective outputs (SynchDetRe and SynchDetIm) prior to filtering by the low-pass filter 93 for such input signals, as shown in Figures 6-11 and 6-12. Thus, as illustrated, the synchronous detector can accurately recover the fundamental amplitude and phase of such input signals according to various embodiments, and thus accurately provide real (Re) and imaginary (Im) output voltages with respect to phase detection and measurement or calculation and / or the rate of change of phase.

[0072] Next, referring to Figures 7 and 8, the control device 44 has an RF smoother or smoothing module or smoothing circuit 68 that removes noise and / or extrapolates a smooth modulated DC signal (e.g., voltage, current, power, and / or phase) representing the output RF energy. Illustrative RF energy before and after the RF smoother is shown in Figures 19 and 20. In one embodiment, a data sampler 69 collects raw, equally spaced data values ​​from analog-to-digital converter (ADC) phase, voltage, current, and power channels when measurements are taken, and then the RF smoother 68 applies a smoothing algorithm to filter the raw values ​​to obtain the resulting smoothed values. Further analysis is performed to determine various points or events of interest, such as phase minimum and zero crossing points. These points of interest are sent to an event handler 67 to trigger a state change. In one embodiment, the generator waits for a specific point or event of interest to be reached before changing the state.

[0073] In one embodiment, the RF smoother 68 detects a local minimum point in the smoothed phase data provided by the RF smoother, and this point of interest is sent to an event handler 67, which notifies the script operation engine 65. In another embodiment, the RF smoother detects a zero crossing indicated by an ADC reading equal to, for example, about half of the maximum ADC count, and this point of interest is sent to an event handler, which notifies the operation engine 65. Input commands, output commands, interrupts, and event detection are provided by the query / command interface 66.

[0074] According to various embodiments, the operating engine 65 allows the generator to be configured to accommodate various operation plans, which include, but are not limited to, a wide variety of electrosurgical instruments, surgical procedures, and preferences. The operating engine receives and interprets data from an external source and thereby specifically configures the operation of the generator based on the received data.

[0075] The operating engine receives configuration data from an appliance database script file 101, which is read from an appliance plug or a memory device on key 102. The script defines the state logic used by the generator. Based on the states defined by the generator and the measurements performed by the generator, the script can define or set the output level and the shut-off criteria. The script includes, for example, in one embodiment, trigger events or indicators that include an indication of a short circuit condition when the measurement phase is greater than 70° or an indication of an open circuit condition when the measurement phase is less than -50°.

[0076] In one embodiment, the operating engine provides system states and user states. System states are default states that control or manage specific default operations or operating conditions of the generator, such as states that successfully apply RF energy or indicate an error. In one embodiment, system states are a set of default configurations that indicate the system is working well (e.g., working as opposed to idle (not working)) and whose functions are hardcoded (coded to remain unchanged) within the electrosurgical generator. For example, RF Done (the state is a system state that indicates that the RF energy cycle has been completed without error). User states provide a framework as a means by which customized or specialized operations and values ​​can be established by instructions from an external source relating to a specific instrument, procedure, and / or preference.

[0077] In one embodiment, the script describes system states and their exit conditions, such as expiration times or commands to another state, and where the user state begins. For each user state, it describes the operating parameters for that specific state, such as power, voltage, and Current setting A user state can be defined or carried over from a previous state. In one embodiment, the user state can provide a specific state for the instrument, operator, or procedure, and in one embodiment, the user state may be provided for a specific state for testing or diagnostic purposes.

[0078] Two example user-state processes are shown in Figure 10 as examples. The process starts in the system state idle (71). When the switch is pressed (asserted) (78), the generator transitions to user state 1 (72). Based on the exit condition, the generator transitions to the next state, namely user state 2 (73), or to one of the system states (e.g., RF_completed (74) or error (75)). If no user states exist after user state 2, the process transitions back to a system state other than system state idle, thereby transitioning the generator back to system state idle.

[0079] An exit criterion or condition (79) for each state defines a logical path for the script based on measurements performed by the generator, and thus the generator transitions from one user state to another. However, if the exit condition does not match the expected logical path, the seal or operation cycle is deemed not to have completed successfully, and a system state error (75) is achieved. If the exit condition matches the expected logical path or indicates completion of the operation cycle, the operation cycle is deemed to have completed successfully, and the system state RF_Completed (74) is achieved. In one embodiment, if the switch is released before completion of the melting cycle, the system state Switch_Released (76) is achieved. According to various embodiments, additional system states may be predefined to handle other common system errors or unexpected deviations from the expected logical path, such as a timeout state indicating a maximum time to complete the melting or a maximum time or an operation cycle exceeding the limit. In addition, although only two user states are shown, the generator is expandable and can be configured to include additional user states to provide extended logical pathways for specific or a range of electrosurgical instruments, procedures, and / or preferences.

[0080] The script allows setting individual parameters or conditions related to the electrosurgical or melting process. For example, acceptable impedance levels, maximum voltage, maximum current, and maximum power setting values ​​for the electrosurgical instrument prior to RF energy activation (in one embodiment, for corresponding user-adjustable level setting values ​​(e.g., levels 1-3)), the switch asserting or deasserting dwell time for activation or deactivation, and the stack button error time following the completion of the initial connection and operating cycle.

[0081] In one embodiment, the operating engine provides at least 30 states, 5 system states, and 25 user states that provide operating control parameters and output characteristics. These characteristics define the voltage, current, and power output ranges, which are preferably at or below the full scale of the generator's output range. Each state, in one embodiment, has the ability to enable or disable the RF output, adjust the RF output level, and recognize and act on different events or control indicators based on, for example, time, voltage, current, power, or phase (φ) or combinations thereof, and to transition to another user state, error condition, or completion state. In one embodiment, the data received by the operating engine from the event handler or RF smoother is smoothed according to a dual exponential smoothing algorithm or an exponential moving average algorithm. Voltage, current, power, and phase smoothing parameters can be set individually in the device script.

[0082] In one embodiment, every 1ms, the data sampler reads and stores ADC channel measurements, such as voltage, current, power, and phase angle. After processing the ADC measurements, the data sampler calls an RF smoother. The RF smoother smooths or filters the ADC measurements and then notifies an event handler. When the event handler (for example, by checking every 15ms) determines that a particular event or metric has occurred, the event handler notifies the operation engine 65. After the operation engine processes the event, it sets up the event handler for the next series of event evaluations.

[0083] In one embodiment, the event handler is configured to evaluate a set of script events defined by an instrument script. A script event is a grouping of postfix (Reverse Polish Notation (RPN)) tokens that describe a logical expression (Boolean expression). The operation engine 65 provides the event handler with a port and script state 68 corresponding to the instrument script database. The event handler evaluates this state and each event within this state, each event within this state being described by a logical expression. The event handler calculates the value of the logical expression. If any event evaluation within the state is found to be true, the event handler notifies the script operation engine, indicating that an event in a particular state has been encountered and providing the next location in the instrument script database where the script should continue execution. If no event is found, the event handler does not notify the script operation engine. In one embodiment, the event handler is configured to evaluate up to 10 events per given sample time, with the events being evaluated sequentially.

[0084] The event handler obtains timer values ​​from the system timer 70, switch events (press, release) 72 from the connected device, and simulated switch events from the diagnostic port 71. The event handler also checks for time-based events, such as global timeouts or state timeouts, and other recoverable errors, such as overvoltage or overcurrent conditions. In one embodiment, this check is performed by reading various ADC values ​​and comparing them to limits set by the device script.

[0085] In one embodiment, the operating engine receives an instrument script database file and installs it into a default instrument script database storage location in memory. During script development, the script compiler compiles the script source file into the instrument script database, which includes, among other things, RPN notation and event data stored in state instructions. Prior to installation, the operating engine checks the instrument script database, i.e., the compiled script, for errors. In one embodiment, the operating engine checks each token in the RPN data for "out-of-range" values, where a boolean value is returned and only one RPN token remains on the stack when the token count is at the end of the RPN data.

[0086] Next, referring to Figure 9, according to various embodiments, the device is plugged into the generator's tool port. The operating engine authenticates this device, thereby indicating that the integrity of the device memory and scripts has not been compromised. Once the device is authenticated, the operating engine checks the script database, thereby confirming that the script database is correctly constructed. If the script database is confirmed to be valid, the operating engine begins script execution. (The start section of the IDLE state is set as the column number in the script table from which execution begins).

[0087] To describe the operation, the operation engine reads instructions from the script database. If the operation engine needs to wait for an event, it instructs the event handler to identify which event to identify and then waits. When an event is identified by the event handler, i.e., when the event evaluation is true, the event handler notifies the operation engine, and the event handler is prevented from performing any further event evaluations for the toolport until the operation engine instructs the event handler again. In one embodiment, the event handler is interrupted at least once every 20ms from a timer or from ADC data evaluating the event. The operation engine resumes execution when the event handler informs the operation engine that an event has been triggered.

[0088] The melting process can be stopped at (a) a fixed and absolute resistance (e.g., 2 k ohms) that does not take into account both the size and type of tissue, (b) a certain number of times when the ohmic resistance is minimal, (c) a certain number of times when the ohmic resistance is the same as the initial ohmic resistance, or (d) a certain number of times when the ohmic resistance is a certain coefficient of the minimum ohmic resistance. However, considering the rupture pressure and thermal spread of the artery in the molten state, the termination of the melting process is determined to be at the flattened portion of the impedance curve. However, as can be seen in Figures 12-20, this region is also an inaccurate range of impedance measurement. Similarly, each of the consecutively aligned (a) through (d) is good in determining the endpoint of the melting time (resulting in the highest desired rupture pressure being achieved with the least desired thermal spread). Imperfect results may result from using ohmic resistance alone as the termination criterion. This may be particularly noticeable when melting tissues of different sizes (even if identical in nature).

[0089] From one perspective, the determination of the endpoint of the melting process is given by monitoring the phase shift of voltage and current during the melting process. Unlike impedance, the phase shift changes very significantly at the point when tissue melting is complete, and therefore yields a more sensitive control value than impedance. However, for various tissues, reaching the high end of the phase range may result in an excessively long melting time. Therefore, as will be described in detail below, initiating an electrosurgical generator and applying RF energy in conjunction with measuring or monitoring the phase shift is done to melt blood vessels and tissues according to various embodiments of the electrosurgical system.

[0090] Therefore, instruments that cause tissue sealing, melting, or bonding provide non-traumatic contact with connective tissue while also providing sufficient bursting pressure, tensile strength, or fracture strength within the tissue.

[0091] In one embodiment, the generator initially determines the initial instrument impedance and / or capacitance (e.g., during the plugging-in of the instrument connector to the electrosurgical generator), in which case tolerances / variations in the instrument characteristics are taken into consideration in the tissue measurement and endpoint determination process. It is preferable to take into account tissue measurements that are independent of the ohm value and capacitive value and / or tolerance of the specific electrosurgical instrument.

[0092] Exemplary RF energy control processes relating to electrosurgical generators and associated electrosurgical instruments for melting tissue according to various embodiments are shown in Figures 11A and 11B. In one embodiment, the generator supplies RF energy through a connected electrosurgical instrument or tool (101). The generator monitors at least the phase and / or phase change of the supplied RF energy (102). If it encounters a phase zero crossing or a polarity change from positive to negative or negative to positive (103), it determines a phase stop (104). In one embodiment, the phase stop includes a predetermined phase angle and / or phase angle change based on determined tissue properties, e.g., size, dielectric constant, conductivity and / or applied voltage, current and / or power. The generator continues to monitor at least the phase and / or phase change of the supplied RF energy (106). When a phase stop (105) is reached or exceeded, the process is terminated or a termination procedure is initiated and / or the RF energy supplied by the generator is stopped (107).

[0093] In one embodiment, prior to the start of the process, impedance is measured and a low-voltage measurement signal is sent to the connected electrosurgical instrument to determine whether it is short-circuited or open-circuited. In one embodiment, passive impedance measurement is used to determine whether the grasped tissue is within the operating range of the electrosurgical instrument (e.g., 2 to 200 Ω). If the initial impedance check is passed, RF energy is supplied to the electrosurgical instrument. In one embodiment, the RF energy voltage is applied in a ramping manner starting from 25% to at most 80% of the global set value, or in one embodiment, at a user-selected level (e.g., 27.5 to 88 V for level 1, 25.0 to 80 V for level 2, and 22.5 to 72 V for level 3) (111).

[0094] The voltage and phase of the applied RF energy are continuously measured (112). When the phase measurement is equal to zero or a transition value from positive to negative (113), the voltage at that point is kept constant at that voltage or a predetermined voltage. In one embodiment, the tissue size is determined using zero crossing or polarity crossing and an appropriate path is selected to complete the melting cycle. In one embodiment, the tissue size is determined using the voltage level of the ramp at zero crossing, and then an appropriate path is selected. It has been noted that the time required to reach the phase zero crossing is preferably related to or correlated with the amount of water or moisture extracted from the tissue at that point and the tissue size.

[0095] According to various embodiments, if the voltage level is less than 50% of the selected level at the zero crossing (e.g., Level 1: Voltage < 55V, Level 2: Voltage < 50V, Level 3: Voltage < 45V), the tissue size is determined to be small (114). If the voltage level is less than 60% but greater than 50% of the selected level at the zero crossing (e.g., Level 1: 55V < Voltage < 66V, Level 2: 50V < Voltage 60V, Level 3: 45V < Voltage < 54V), the tissue size is determined to be medium (115). If the voltage level is 60% or more of the selected level at the zero crossing (e.g., Level 1: Voltage ≥ 66V, Level 2: Voltage ≥ 60V, Level 3: Voltage ≥ 54V), the tissue size is determined to be large (116). Based on the determination of the tissue size as medium or large, the voltage of the applied RF energy is kept constant at that level at the zero crossing. According to various embodiments, based on the determination of a small tissue size, the applied RF energy voltage is set to a predetermined voltage, which in one embodiment is set to 22V. In one embodiment, the predetermined voltage is below that voltage level based on the determination of a medium or large tissue size.

[0096] If the monitored phase and / or phase change is less than or equal to a selected predetermined phase and / or phase change, the electrosurgical energy is stopped (121). In one embodiment, if the calculated phase does not reach this phase stop within a set time, for example, 3 seconds, 3.25 seconds, or 4 seconds, the electrosurgical energy is stopped. In one embodiment, if the tissue size is determined to be small, the phase stop and / or phase stop change is set to phase <-7.0° and / or phase change <-2.3° / s (117). An example graph of RF energy to successfully melt tissue when the tissue size is determined to be small is shown in Figure 12. Also, as shown, the phase 12b is shown relative to other tissue readings or indicators, such as current 12a, power 12c, impedance 12d, temperature 12e, energy 12f, and voltage 12g. If the tissue size is determined to be moderate, the phase stop and / or phase stop change is set to phase <-23.0° and / or phase change <-7.1° / s (118). If the tissue size is determined to be small, an example graph of the RF energy required to successfully melt the tissue is shown in Figure 13. Also, as shown in the figure, the phase 13b is shown relative to other tissue readings or indicators, such as current 13a, power 13c, impedance 13d, temperature 13e, energy 13f, and voltage 13g. If the tissue size is determined to be large, the phase stop and / or phase stop change are set to phase <-32.0° and / or phase change <-8.0° / s (119). If the tissue size is determined to be small, an example graph of the RF energy required to successfully melt the tissue is shown in Figure 14. Also, as shown in the figure, the phase 14b is shown relative to other tissue readings or indicators, such as current 14a, power 14c, impedance 14d, temperature 14e, energy 14f, and voltage 14g. In addition, as shown in Figures 12 to 14, in various embodiments, the generator is configured not to measure or calculate one or more of the indicators or readings, such as temperature or energy, thereby reducing the generator's operation, power components, cost, and consumption. Additional information or readings are generally provided or shown for contextual purposes.

[0097] According to various embodiments, while RF energy is applied, and in one embodiment, after evaluating or determining whether a phase and / or phase stop change or endpoint has been reached and an incorrect indicator for melting (caused by an open circuit or short circuit) has been reached, the phase is monitored in relation to the current for open circuit and short circuit events, while the energy is monitored on the other hand.

[0098] According to various embodiments, the generator is configured to provide additional adjustments to various parameters or functions associated with the output of RF energy, voltage, current, power, and / or phase, and the operating engine is configured to adjust the output of RF energy using the various parameters or functions. In one exemplary embodiment, the control circuit provides additional adjustment controls for direct phase adjustment, which adjust the voltage, current, and / or power outputs to satisfy a specified phase adjustment setpoint provided by the operating engine.

[0099] In various embodiments, the generator recognizes and acts upon or executes operating conditions using measured values ​​of voltage, power, current, and / or phase, such as control indicators. In various embodiments, additional measurements or calculations based on measurements associated with the RF output adjustment circuit are performed by a script or operating engine, thereby recognizing and acting upon additional or different events associated with or triggered by other measurements or thresholds. The additional measurements include, in one embodiment, an error signal combined with a pulse-width modulation (PWM) duty cycle used to adjust the output of voltage, current, and / or power or other similar adjustment parameters. In various embodiments, the different or additional events or indicators identified and triggered are preferably transitions from one adjustment control to another (e.g., from current adjustment to power adjustment).

[0100] According to various embodiments, the generator provides or performs calculations for directly measuring the rate of change of voltage, current, power, and / or phase. For example, Figure 15 is an illustrative graphical representation of the phase 15a of RF energy relative to the phase change of RF energy 15b. In one embodiment based on these calculations or direct measurements, the generator can recognize and act upon different events associated with the RF output and electrical characteristics of the tissue during the melting cycle.

[0101] According to various embodiments, a predetermined completion indicator can be varied or modified by the operating engine. In one embodiment, during a given melting cycle, a sound (or other indicator) is triggered at a phase threshold determined to be equivalent to a 7 psi (3 × systolic pressure) seal 161, and then RF energy is continued to be applied to the vessel up to a phase threshold determined to be equivalent to a higher burst pressure (e.g., 20 psi) 163, at which point the RF energy is automatically stopped. A graphical diagram illustrating an example of RF energy used to melt tissue using seal pressure determination is shown in Figure 16. Also, as shown, the phase 16g is shown for other tissue readings or indicators, e.g., voltage 16a, power 16b, impedance 16c, energy 16d, temperature 16e, and current 16f. According to various embodiments, instead of or in addition to the use of a phase angle as a predetermined completion indicator, or with respect to other thresholds, time, voltage, current, and power, as well as conditional combinations thereof, can be used.

[0102] In one embodiment, the user can release the activation button at any point between the first and last tones. This gives the surgeon some control over the amount of RF energy being applied to the tissue. For example, in the case of thin, non-vascular tissue, the surgeon can release the button near the first tone rather than waiting for the next tone. Similarly, in the case of large tissue, the surgeon can release the button much later than the first tone or near the next cycle tone or the end of the cycle tone, thereby allowing the RF energy to be applied for a longer period.

[0103] In one embodiment, the phase angle setting is user-accessible and adjustable. By adding a phase level setting parameter, the phase trigger threshold can be coupled to a percentage or multiple (positive or negative) of the phase threshold. Thus, the user can adjust the melting cycle time, for example, by shortening or lengthening the melting cycle (e.g., level 1 (171), level 2 (172), and level 3 (173)). TIFF0007855626000012.tif35167

[0104] Figure 17A shows an illustrative graph of RF energy used to melt tissue using user-adjusted phase levels 171, 172, and 173. As shown in the figure, phase 17g is shown relative to other tissue readings or indicators, such as voltage 17a, power 17b, impedance 17c, energy 17d, temperature 17e, and current 17f.

[0105] An additional way to provide an alternative endpoint or alternative RF output path is to provide an additional or alternative script logic path based on an output level setting. This also allows for adjustment of the melt cycle time, for example, shortening or lengthening the user-adjustable seal cycle (e.g., level 1 (175), level 2 (176), level 3 (177)). An illustrative graph of the RF energy used to melt the tissue using the additional or user-level-adjustable script logic paths 175, 176, 177 is shown in Figure 17B. Also, as shown, the phase 17g1 is shown relative to other tissue readings or indicators, e.g., voltage 17a1, power 17b1, impedance 17c1, energy 17d1, temperature 17e1, and current 17f1. In addition, as shown in Figures 16 to 17B, in various embodiments the generator is configured not to measure or calculate one or more of the indicators or readings, e.g., temperature or energy, thereby reducing the operation and power components, cost, and consumption of the generator. Additional information or readings are generally provided or indicated for contextual purposes.

[0106] As provided in various embodiments, the operating engine provides the ability for the generator to operate between two or more states 18e. State transitions can be triggered by time, voltage, current, power, or phase 18a, 18b, 18d, and such state transitions can also be used for exit states 18c. In one embodiment, maintaining a running state count of how many states have been cycled through can serve as an additional trigger for exiting a particular state. Another melting cycle can also be defined using additional states or state counts, which may include, for example, tissue cutting, depending on the RF output level and electrosurgical instrument geometry. An illustrative graph of RF energy used to melt tissue using script states is shown in Figure 18.

[0107] According to various embodiments, the RF amplifier is configured to convert a 100VDC signal from the power supply into a high-power sinusoidal waveform with a frequency of 350kHz, which is sent to the ABDI and ultimately to the connected electrosurgical tool. In one embodiment, the amplitude of this signal is determined by the duty cycle of multiple input signals from the control unit.

[0108] In one embodiment, the RF amplifier includes circuitry to ensure a dead time exists between the PWM signals to prevent both PWM signals from the control unit from being ON simultaneously. A 1:2 transformer in the RF amplifier provides isolation between the PWM signals driving the H-bridge and two-stage low-pass filter. The output of the filter is a continuous 350 kHz sine wave. The RF amplifier includes a number of relays configured by the control unit to direct the 350 kHz signal from the output of the filter circuit to the ABDI's instrument port.

[0109] The RF amplifier, according to various embodiments, has multiple shunt resistors, for example, two shunt resistors for each instrument port. Voltage and current are measured across the resistors and, in one embodiment, supplied to two independent RF senses. Relays in the RF amplifier are configured by the control device FPGA to direct the tissue measurement signals from the control device to the instrument ports. In addition, transformers are provided to isolate the tissue measurement signals from the instrument ports. Power control signals pass through the RF amplifier to the control device, and in one embodiment, the RF amplifier has an overcurrent detection circuit for determining whether the supplied current exceeds a certain threshold and / or a voltage monitor circuit for determining whether the supplied voltage exceeds a certain threshold. PWM signals, RF energy shutdown signals, RF sense control signals and relay control signals are sent from the control device to the RF amplifier. RF sense analog signals, various RF sense fault signals, power control signals, passive measurement signals and standby power signals are sent from the RF amplifier to the control device.

[0110] In one embodiment, the RF amplifier has a gate drive circuit that receives at least two 180° phase-shifted 350kHz PWM signals from a control device to generate a non-overlapping PWM signal, which is then fed to a gate driver located in the power stage to generate an output RF signal or energy. The non-overlapping signal prevents damage to components in the power stage. Before the signal enters the power stage, these signals are isolated to separate the noisy power ground from the noise-free signal ground. The PWM signal in the power stage is fed into the gate driver, which receives a low-power PWM signal and sends a high-current drive input signal to a MOSFET.

[0111] The control unit outputs two PWM signals with a specific pulse width corresponding to this RF output. The H-bridge topology utilizes at least four gate drive signals to drive the MOSFETs in the circuit. These four signals are obtained by generating inverted corresponding signals for the two PWM signals. In addition, the RF amplifier prevents a pair of signals (i.e., the first PWM signal and the inverted / second PWM signal) from being HIGH simultaneously. By providing both signals HIGH at the same time, a shoot-through condition may occur, which may potentially damage the generator components.

[0112] In one embodiment of the RF amplifier, the two RC circuits ensure that there is a dead time when both signals are off. Similarly, the other pair of these signals also has two RC circuits to ensure a dead time. The RC circuits have short time constants to account for propagation delay.

[0113] In one embodiment, separate and independent signals are provided that can stop the propagation of PWMA and PWMB (i.e., the first PWM signal and the inverted PWM signal) to the gate driver. For example, one such signal is generated by a control device FPGA, and the other by a microcontroller. The PWM signals continue to propagate through an isolator, which isolates a noisy ground from a noise-free ground, in this case referring to a high-power switching circuit. These signals control a gate driver that converts the low-power PWM signals and generates signals with a current large enough to saturate the MOSFET. Resistor and diode circuits located at the output of the gate driver are adjusted to achieve desired rise and fall times.

[0114] The control FPGA can communicate with the PWM DAC via the PWM DAC SPI line. The PWM DAC uses a DAC with an SPI interface to produce a 4.452 volt output. This output passes through an operational amplifier buffer and is then switched at 700 kHz with a 50% duty cycle to produce a 700 kHz square wave. Thus, the PWM DAC initially sets a DC level, for example during power-up, and this DC level is switched at 700 kHz to produce a square wave output. This signal is then sent to an integrator stage, resulting in a 700 kHz triangular wave at the output. In particular, the integrator circuit produces a slope proportional to the input voltage. The amplifier is the other half of this. This converts the square wave into a triangular wave. The output is a 700 kHz wave with a duty cycle proportional to the error output. This signal becomes an FPGA-coupled PWM input, and the FPGA alternates these pulses to produce first and second PWM outputs, which operate the FETs on the input side of the RF transformer.

[0115] Specifically, by combining the resulting triangular wave with the error signal from the RF control loop, the resulting signal becomes a pulse-width modulated signal used to drive the RF amplifier. Since the RF amplifier has a full H-bridge output stage, two drive signals are used, each 180° out of phase with the other. The PWM signal controller within the control FPGA takes in the combined PWM signal and splits it into two signals. During the first half of the 350kHz output cycle, the FPGA sends the combined PWM signal to the first PWM output, and the second PWM output is held at 0V. During the second half, the FPGA sends the combined PWM signal to the second PWM output, and the first PWM output is held at 0V.

[0116] In one embodiment, the first and second PWM outputs driving the RF amplifier are enabled only when the microcontroller requests that the RF energy be turned ON, for example when the RF amplifier output is enabled. If a fault is detected while the RF energy is active or being supplied, it is preferable to immediately disable the PWM signal and warn the microcontroller.

[0117] The microcontroller can control the RF amplifier output level by sending desired voltage, current, and power levels to the control FPGA. These levels or set values ​​are used by an analog RF control loop circuit, which adjusts the amplifier's output power to match the set values.

[0118] The power stage circuit is configured to receive a PWM signal generated by the gate drive circuit and produce a continuous sinusoidal signal, which is then transmitted to the relay circuit. The PWM signal drives the MOSFETs in the H-bridge configuration. The output of the H-bridge is connected to a 1:2 transformer via a decoupling capacitor and fuse. The transformer isolates the +100V power supply from the energy output to the patient. The circuit operates to produce a rectangular pulse train with a 0V offset, where the first state is followed by the second state. When the first state occurs, current flows through the transformer and out, producing the positive portion of the resulting waveform. When the second state occurs, current flows through the transformer in the reverse direction, producing the negative portion of the resulting waveform. When PWMA and PWMB are simultaneously either HIGH or LOW, the resulting waveform is 0V. After the transformer, this signal is sent to a two-stage LC filter to produce a continuous sinusoidal waveform.

[0119] The two-stage LC filter is a low-pass filter designed to produce a 0dB gain at 350kHz. The load resistor is the resistance of the sealed tissue. A series capacitor is positioned in one embodiment to minimize the possibility of neuromuscular stimulation.

[0120] In various embodiments, the control system generally includes a microcontroller responsible for monitoring the RF energy configuration and startup, as well as the user interface. The control system further includes a field-rewritable gate array (FPGA) responsible for assisting the microcontroller by inspecting access to analog data and managing the control circuit. In one embodiment, the control system further includes a plurality of composite programmable logic devices (CPLDs) for health monitoring.

[0121] In one embodiment, the microcontroller has an interface to an FPI that provides a user interface and indicates fault conditions / alarms, an interrupt input to indicate that a fault condition has been detected, and an interrupt input to indicate that the front panel switch has changed state. The control device FPGA has parallel access to analog and control data, access to the front panel switch, outputs to indicate changes in their states, and access to device 1 and 2 inputs and outputs. In one embodiment, the control device FPGA has an active serial configuration interface for programming the FPGA, and in one embodiment, is a master for the system SPI communication bus that enables read and write access to the control device CPLD and RF sense FPGA.

[0122] The control FPGA measures feedback voltage, current, power, and phase, and interfaces with the ADC circuit, which reads voltage and current setpoints and errors. Voltage, current, power, and phase feedback voltages are precisely measured by two groups of ADCs powered by different voltage references. The control FPGA controls the DAC circuit, which generates analog setpoints for voltage, current, and power.

[0123] The control device FPGA provides inputs for a clock, an SPI DAC interface, a 700kHz switch signal for a triangular wave generator, and a 700kHz PWM circuit that generates a 350kHz ± 350kHz output to the RF amplifier driver circuit. The control device FPGA also detects when an instrument is connected. In various embodiments, the control device FPGA detects an output indicating which instrument is active and a 90° phase-shifted (sine and cosine) PWM composite signal and provides these to the RF sense. In various embodiments, the control device FPGA has an output to a microcontroller indicating that a fault condition has occurred, as well as an output for controlling an output / tissue measurement relay.

[0124] In one embodiment, the control device has an analog control circuit that enables closed-loop control of the RF energy output using the DAC output as a setpoint and the maximum voltage, current, and power RF sense outputs as feedback. The output would be a coupled PWM input to an FPGA.

[0125] In one embodiment, the control device includes a redundant composite rewritable logic device (CPLD) circuit that generally detects error conditions and shuts off the output when an error condition occurs. Each CPLD circuit is configured to have an output that activates an independent circuit (gate power control circuit) that disables the RF output. In addition, each CPLD circuit is configured to have a digital display (ADC) of RF sense 1 and RF sense 2 voltage, current, power, and phase outputs from the RF sense. If any of these signals exceeds a minimum or maximum limit, the CPLD circuit will disable the RF output.

[0126] In one embodiment, the control unit CPLD controls a load switch that allows the control unit to independently turn off the supply voltage to the gate driver and ultimately turn off the supply of RF energy.

[0127] The control unit has multiple CPLDs to detect fault / error conditions. The CPLDs monitor the same signal redundantly or for complete reliability. The analog input from the RF sense passes through a filtering stage, then enters a multiplexed state, and the output is sent to the ADC. From there, the output goes to a digital isolator, which is used as a voltage level shifter. The output of the digital isolator goes directly into the bidirectional I / O of the CPLD.

[0128] The CPLD detects the difference between the analog voltages or values ​​(voltage, current, power, and phase) obtained from multiple RF sense circuits, such as RF sense 1 and RF sense 2. If the magnitude of the difference between RF sense 1 and RF sense 2 exceeds the maximum error value, the CPLD will cause a local fault. Examples of this fault include when either the voltage feedback signal or the current feedback signal for RF sense 1 or RF sense 2 exceeds a predetermined limit, or when the phase relationship between the synchronization signals is not valid for RF sense 1 or RF sense 2.

[0129] In one embodiment, the control device has a passive measuring circuit configured to computer-process the absolute impedance and phase of the connected electrosurgical tool and the tissue in contact with it. In one embodiment, the passive measuring circuit includes a calibration resistor circuit, which is a transformer isolated from the patient.

[0130] The control device comprises a passive measuring circuit including multiple branch circuits, an impedance analyzer, a voltage reference, a low-pass filter, and a measuring amplifier. This circuit is electrically isolated from the patient by a transformer, and it is preferable that this circuit be connected to a resistor of known value for calibration.

[0131] The impedance converter and network analyzer have an AC output set to 100 kHz, which passes through a filter circuit that removes harmonics from the 100 kHz signal and acts as a current source capable of driving a low-impedance load. The passive measuring amplifier uses the impedance of the tissue as feedback to ensure that the output is proportional to the impedance of the tissue.

[0132] Referring to Figure 9, when the electrosurgical instrument or device 20 is connected, the generator 10 receives script information from the electrosurgical instrument or device 20. The generator uses this script information to determine the number of states and the execution order of the states.

[0133] Script source files or script information written by instrument script creator 100 and not present on the instrument or generator 10 are text or user-readable. The script information is compiled using a script compiler 105 to produce an instrument script database or binary file (SDB) 101. The binary file is transferred to a memory module by an instrument key programmer 107, which is connectable to or embeddable in an electrosurgical instrument 20 by an instrument key 102. When an electrosurgical instrument is connected to an electrosurgical generator, the generator authenticates the script binary file and / or the instrument (108). The generator verifies the script binary file (109), and if verified, the operating engine utilizes the script to be started by the operation of the connected instrument (110). In one embodiment, the script source file is a text file containing instrument scripts specific to a particular electrosurgical instrument, generator and / or surgical procedure. In one embodiment, the script source file for the device contains information including parameters and scripts (states, functions, events) related to the electrosurgical generator and / or electrosurgical instrument. After successful verification, the script compiler assembles the data into a binary format, which constitutes the state machine used by the electrosurgical generator. In one embodiment, the script compiler, as shown in Figure 9, is separate from the electrosurgical generator and is responsible for reading the script source file as text and verifying its contents.

[0134] When a memory module is inserted into the generator, the generator downloads a binary file stored in the ferromagnetic read / write memory (FRAM®) or microcontroller located within the module. The binary contains the logic to execute the treatment algorithm described above. The generator includes firmware / software responsible for processing the binary, authenticating the connected instrument, and executing the binary to implement the treatment algorithm. Thus, the generator is configured to operate only with certified, compliant hand tools.

[0135] In one embodiment, an instrument script or script database represents an instrument process relating to a specific or given instrument. The instrument script is stored in memory connected to or integrated with the instrument, control unit, or a combination thereof. An event handler responds to specific events, such as switch activation / deactivation, instrument position, or exceeding a measurement threshold. An action engine, based on the detected event when applicable in a given event, produces an output to the connected instrument. In one embodiment, the event is a distinct change when a switch is asserted or deasserted.

[0136] A script state is a block or a set of script functions or operating conditions and a script event or indicator. A script function is a configurable instruction for controlling a generator and / or instrument. A script operator is a logical and comparative action performed during script event evaluation. Script parameters are configuration data used by all states and events of the script, and in one embodiment, they are declared within their own dedicated section of the script file. A script event is a distinct change in electrosurgical generator measurement. When a script event occurs, for example, a sequence of script functions is executed.

[0137] In one embodiment, the control device has a specific or predetermined fixed instrument script for a particular input receptacle. Therefore, only this instrument script is used for instruments connected to a particular input receptacle. An event handler receives and identifies instrument events or indicators, such as switch activation / deactivation events or measurement events (e.g., phase threshold exceedance). The operation engine makes requests or actions to the RF amplifier to control RF output, output selection, and / or selection of several outputs. Other detected events or indicators include detection of hand and foot switches, jaw switches, phase over and under-after-over events, short circuits and open circuits, and instrument script state detection. Keywords in the script help the operation engine extract operation commands and data for instrument operation based on the detected events identified by the event handler.

[0138] In one embodiment, the script controls voltage and current output setpoints and the sequence of voltage and current setpoints. Generally, small blood vessels melt very quickly, while larger blood vessels may take several seconds. Applying a large amount of current to small blood vessels may result in excessive tissue damage, while using a small amount of current may result in an unacceptably long time to perform the melting function. In one embodiment of modifying instrument performance, the script may initially command a small amount of RF current, and then, if the melting endpoint is not reached, for example, in less than one second, command a larger current to accelerate the melting of larger blood vessels. Another use of the script to modify instrument performance, in one embodiment, is to switch from one operation (melting) to another (cutting), for example, a multi-step process, or to reconfigure instrument electrodes and ESG outputs to simplify melting and cutting. When the clinician starts the process, the script first sets up the unit for melting and measures the tissue phase angle that indicates the melting endpoint. It then delivers RF power until the melting endpoint is reached. Next, the unit turns off the RF power to indicate that melting is complete. The unit then switches the electrodes to the cutting configuration, sets the RF output for cutting, and restarts the RF output. The cutting process is stopped by the clinician when cutting is complete.

[0139] In one embodiment, when a switch coupled to the instrument is activated, the control unit detects the switch is closed, authenticates the instrument or device, checks the instrument's expiration status, and / or initializes the internal data structure representing the instrument on the receptacle. The next activation of the instrument switch initiates an event in which a script instructs the generator to supply RF energy. The control unit logs usage information for both the instrument and the generator. When the instrument is disconnected from the generator's receptacle, the control unit resets the receptacle-related information. In one embodiment, the control unit constantly monitors the generator to ensure proper operation. Irrecoverable errors and failures are reported, and further operation of the system is prevented. All failures are stored in the control unit's memory and / or the instrument's memory.

[0140] Data from a specific procedure (e.g., from power-up to power-down) is stored on each instrument. The instrument also retains data from the procedure, namely the number of times the instrument has been used, power settings, and faults. In one embodiment, each instrument also retains information from all other instruments. The instrument memory includes, but is not limited to, some of the following parameters: the generator serial number, timestamp, tissue assertion and endpoint settings for each instrument use, cutting, melting, power settings, RF duration, and endpoints (auto-stop, fault, manual stop, etc.).

[0141] According to various embodiments, the script engine controls RF activation via a script database-driven state machine. When the instrument is plugged into or through the diagnostic port, the script database can be loaded into the script engine via the tool port. The script engine waits for events to be recognized by script event handlers and then executes functions associated with the received and recognized events. In one embodiment, after initially executing a sequence of functions that constitute a state setup or state event action, the script engine issues commands to event handlers to check for events and then waits for notification from the event handler that the event has occurred. Thus, the event handler checks whether there are any events or combinations of events that would cause the script engine to transition from the current state to a new state.

[0142] The script engine, according to various embodiments, performs runtime checks to ensure that the execution script cannot damage the generator. In one embodiment, the script database is a binary data block containing tokenized encoding of script files. The script database is loaded by an external job into one of two partitions of FRAM® or SRAM memory (an area for each toolport). The script binary database is a binary file generated from script files by the script compiler and executed by the operation engine to control the operation of the electrosurgical generator and / or electrosurgical instrument.

[0143] As described above and throughout this application, the electrosurgical generator ultimately supplies RF energy to a connected electrosurgical instrument. The electrosurgical generator ensures that the supplied RF energy does not exceed specified parameters and detects fault or error conditions. However, in various embodiments, the electrosurgical instrument provides commands or logic used to appropriately apply RF energy for surgical procedures. The electrosurgical instrument includes a memory containing commands and parameters that, in conjunction with the electrosurgical generator, determine the operation of the instrument. For example, in a simple case, the generator can supply RF energy, but the connected instrument determines how much energy to apply. However, the generator ensures that the supply of RF energy cannot exceed a set threshold, even if determined by the connected instrument, thereby providing a check or guarantee against fault instrument commands.

[0144] As outlined above and described in detail below, various handheld electrosurgical instruments or other instruments can be used in the electrosurgical systems described herein. For example, electrosurgical grippers, scissors, forceps, probes, needles, and other instruments including one, some, or all of the features described herein can provide various advantages in an electrosurgical system. Embodiments relating to various electrosurgical instruments are described below. Generally, it is assumed that one, some, or all of the features described below can be included in any of the embodiments of the instruments described below. For example, it may be desirable for each of the instruments described below to have memory for interaction with the generator described above. However, in other embodiments, the instruments described below may be configured to interact with a standard bipolar power supply without interaction with instrument memory. However, it is also assumed that certain features of these embodiments can be combined with certain features of other electrosurgical instruments within the scope of the present application.

[0145] As described above with reference to Figure 1, electrosurgical instruments are preferable to have memory. The memory is preferable to include a configuration instrument module. The configuration instrument module can store a certain type of instrument data. For example, the configuration instrument module can store operating parameters for the instrument, such as software to be transferred to the electrosurgical unit when the electrosurgical unit is successfully electrically connected. These operating parameters are preferable to include data on various electrosurgical procedures to be performed by the instrument and the corresponding energy level ranges and durations of these operations, data on the electrode configuration of the instrument, and data on switching between electrodes to perform different electrosurgical procedures on the instrument. Advantageously, it is preferable to quickly make changes to the instrument profile and periodic instrument updates to the electrosurgical generator without downtime, because the data for instrument operation may reside within the electrosurgical instrument itself rather than in the generator. Therefore, updates are preferable to be made during instrument manufacturing.

[0146] The configuration instrument module may further store a data log, which may include, for example, a record of information regarding each of the previous machine uses. For example, in some embodiments, the data log may include timestamp data that identifies the electrosurgical unit, a log of the electrosurgical procedures performed by the instrument, and a log of the duration and energy applied to the instrument. In some embodiments, it may be desirable that the use of a particular instrument be limited to a maximum usage period or number of procedures, especially if the electrosurgical instrument is not configured for sterilization and reuse. Therefore, in some embodiments, the configuration instrument module may be configured to prevent the instrument from operating after a predetermined number of uses or procedures. In some embodiments, the instrument may have a mechanical lockout, such as a breakaway single-use connector, in addition to or instead of a data log, to reduce the possibility of unintended reuse.

[0147] In one embodiment, the electrosurgical instrument has two separate electrodes capable of carrying RF energy (375 VA, 150 V, 5 A at 350 kHz ± 5 kHz). The maximum output RF voltage is 150 Vrms ± 7.5 Vrms. The maximum output RF current is 5 Arms ± 0.25 Arms. The maximum output RF power is 375 VA ± 18.75 VA.

[0148] According to various embodiments, an electrosurgical instrument 20 is provided. This instrument 20 has an actuator coupled to a rotatable shaft. The elongated shaft has a proximal end and a distal end, with a central longitudinal axis defined between the proximal and distal ends. A jaw is provided at the distal end of the shaft, and an actuator is provided at the proximal end. In one embodiment, the actuator is a handle similar to the grip of a pistol. In one embodiment, the shaft and jaw are dimensioned and shaped to fit into a 5 mm diameter trocar cannula or access port.

[0149] The actuator has a movable handle and a stationary handle or housing, the movable handle being able to move relative to the stationary housing while coupled to it. According to various embodiments, the movable handle is slidably and rotatably coupled to the stationary housing. In operation, a user, such as a surgeon, operates the movable handle to actuate the jaws, for example, to selectively open and close the jaws. In various embodiments, the instrument has a forward-moving cutting blade, which is preferably coupled to a blade actuator, such as a blade trigger of the actuator. It is preferable that the blade actuating mechanism operatively couples the blade trigger to the cutting blade.

[0150] A jaw is attached to the distal end of an elongated shaft, and these jaws consist of a first jaw and a second jaw. In one embodiment, a pivot pin of the jaws rotatably connects the first jaw and the second jaw, so that the first jaw can move and rotate relative to the second jaw. In various embodiments, one jaw is fixed to the elongated shaft so that the opposing jaw rotates relative to a fixed jaw between an open position and a closed position. In other embodiments, both jaws are preferably rotatably connected to the elongated shaft so that both jaws can rotate relative to each other.

[0151] A conductive pad is attached to the first jaw. In one embodiment, an insulated wire is routed to electrically couple the conductive pad provided on the first jaw to a wiring harness in the actuator. The insulated wire extends from the distal end of a protective sleeve, which is housed at the proximal end of the second jaw and extends into the first jaw. The first jaw preferably has a slot sized to receive the insulated wire. The insulated wire then passes through a hole provided in the first jaw and falls into a slot provided in the non-conductive portion. The insulated wire then extends to the distal end of the non-conductive portion and down through it to the conductive pad.

[0152] Next, referring to some of the operational aspects of the electrosurgical instruments described herein, once a bundle of blood vessels or tissue is identified for sealing, the first jaws and the second jaws are positioned around this tissue. The movable handle is squeezed to move it proximal to the stationary housing. As the movable handle moves proximal, it pushes the pull block. The pull block engages with the pull tube, causing the pull tube to move proximal. The proximal movement of the pull tube causes the first jaw to rotate toward the second jaw, effectively clamping the tissue. The force applied to the tissue by the first jaw is transmitted to the movable handle through the pull tube and the pull block. Once the pre-applied force is overcome, the movable handle begins to move the sliding pin distally. Once the pre-load on the spring is overcome, the pivot point of the movable handle shifts from the sliding pin to the rear portion of the pull block, where the pull block contacts the movable handle. The sliding pin can advance distally because the force acting on it is greater than the pre-applied force on the trigger spring.

[0153] Continuing to operate the movable handle causes it to rotate to a position where it engages with the latch mechanism, which holds the handle in the engaged position and prevents it from returning to the open position. Pressing the power-activation button applies sealing high-frequency energy from the engaged position to the tissue. Once the tissue has been melted, the movable handle can be opened again by continuing to advance proximally to a position where the latch mechanism can disengage.

[0154] The force regulation mechanism reduces the risk of excessive force being applied to the tissue. If too much force is applied to a blood vessel or tissue bundle, potential damage may occur. Thus, when clamping very thin blood vessels or thin tissue bundles within the jaws, the instrument applies the minimum force necessary to achieve good tissue fusion. The same applies to very thick blood vessels or tissue bundles.

[0155] Once the tissue has been melted, the user should activate the blade trigger. Moving the blade trigger proximal causes the blade lever to rotate, moving the push bar and cutting blade distally. The cutting blade moves forward and severs the melted portion of the tissue. When the user releases the blade trigger, the blade spring resets the cutting blade to its original position. Returning the blade trigger to its original or initial position allows the user to continue to squeeze the movable handle to open the upper jaws. Continued movement of the movable handle proximal leads to a position where the latch mechanism disengages and the movable handle can be released.

[0156] The dimensions of the sealing surfaces are appropriately proportional to the optimal pressure applied to the tissue between the jaws due to the potential forces that the instrument mechanism can generate. The surface area is also electrically significant with respect to the surface area in contact with the tissue. This proportion of the surface area and the tissue thickness are optimized in relation to the relative electrical properties of the tissue. The jaws are positioned to maintain an electrically significant distance between them with respect to the thickness of the tissue held between them.

[0157] As described above with respect to electrosurgical systems, in some embodiments, the electrosurgical melting instrument can be used in a system that monitors various operating parameters and determines a high-frequency endpoint based on the phase angle.

[0158] Referring to Figures 21 to 40, various embodiments provide an electrosurgical melting apparatus or device, which, according to various embodiments, can be detachably connected to an electrosurgical generator. In the illustrated embodiments, the apparatus has an actuator 224, which is coupled to a shaft 226 rotatable with respect to the actuator. The elongated shaft 226 has a proximal end and a distal end, with a central longitudinal axis defined between the proximal and distal ends. A jaw 222 is provided at the distal end of the shaft 226, and an actuator is provided at the proximal end. In one embodiment, the actuator is a handle resembling the grip of a pistol. In one embodiment, the shaft 226 and the jaw 222 are dimensioned and shaped to fit into a 5 mm diameter trocar cannula or access port.

[0159] The actuator 224 has a movable handle 223 and a stationary handle or housing 28, the movable handle 223 being able to move relative to the stationary housing while coupled to it. According to various embodiments, the movable handle 223 is slidably and rotatably coupled to the stationary housing. In operation, a user, such as a surgeon, operates the movable handle 223 to activate the jaws, for example, to selectively open and close the jaws.

[0160] According to various embodiments, the actuator 224 has a force adjustment mechanism configured such that, in the closed position, the jaws 222 deliver a gripping force between a predetermined minimum force and a predetermined maximum force.

[0161] As part of the force adjustment mechanism, the movable handle 223 is coupled to the stationary handle at two sliding pivot locations to form the force adjustment mechanism. The movable handle has a first end with a gripping surface and a second end 258 opposite the first end. The movable handle is coupled to a pin 256 adjacent to the second end. In some embodiments, the movable handle is preferably formed integrally with a projection extending from the movable handle to constitute the pin surface. In other embodiments, the pin is preferably pressure-fitted into a hole provided in the movable handle. The pin is preferably housed in a slot provided in the stationary housing, for example, in corresponding slots formed in the right and / or left handle frames of the stationary housing. In some embodiments, the slots are preferably configured to define a desired operating handle path, such as a curved or V-shaped path, when the operating handle is moved from a first position corresponding to an open jaw to a second position corresponding to a closed jaw.

[0162] The force adjustment mechanism includes a biasing member, such as a tension spring 257, that biases the pin in the proximal direction. In operation, when a predetermined force is applied by the movement of the movable handle 223, it overcomes the biasing force applied by the spring, and the second end of the movable handle is able to translate distally as a whole, guided by the pin in the slot.

[0163] According to various embodiments, the movable handle is slidably and rotatably coupled to the stationary housing 228 at a location between the first and second ends of the operating handle. An actuator member, such as a pull block 251, is coupled to the operating handle. When the movable handle is moved proximal, the pull block also moves proximal and longitudinally, closing the jaws 222 and thereby clamping the tissue between the jaws. According to various embodiments, the pull block 251 is a rectangle having open top and bottom faces and a closed proximal end. The movable handle passes through the top and bottom faces of the pull block. The edge of the movable handle abuts the proximal end of the pull block so that the pull block moves longitudinally as the movable handle moves relative to the stationary housing. In one embodiment, the distal end of the pull block is coupled to an operating shaft, such as a pull tube, bar, or rod, which preferably extends longitudinally along an elongated shaft 226. Thus, to describe the operation, the movement of the movable handle from the first position to the second position causes the pull block 251 to translate longitudinally within the stationary housing, and consequently, the pull tube as a whole translates linearly along its longitudinal axis relative to the elongated shaft 226. This movement of the pull tube can control the relative movement of the jaws 222.

[0164] According to various embodiments, the actuator 224 has a latch mechanism that positions the movable handle 223 in a second position relative to the stationary housing 228. In the illustrated embodiment, the movable handle has a latch arm 265 which engages with a matching latch 267 housed within the stationary handle to hold the movable handle in the second or closed position.

[0165] In various embodiments, the machine has a forward-moving cutting blade 271, which is preferably coupled to a blade actuator of an actuator 224, such as a blade trigger 225. The blade actuation mechanism preferably couples the blade trigger to the cutting blade. In one embodiment, the blade actuation mechanism includes a rotating blade advance link, which transmits the proximal movement of the blade trigger 225 to a blade actuation shaft assembly, such as a push bar, coupled to the cutting blade, or vice versa. To describe the operation, the user can move the blade trigger 225 toward the metal side to advance the cutting blade 271 from the retracted position to the extended position. The blade actuation mechanism preferably includes a biasing member, such as a blade return spring 263, which biases the cutting blade to the retracted position.

[0166] By selectively moving the cutting component between a proximal and distal location, tissue compressed between the jaws of the jaw assembly can be cut. In various embodiments, the cutting blade 271 may be a sharp blade, hook, knife, or other cutting element sized and shaped to cut tissue between the jaws. In some embodiments, the cutting blade has a first pointed edge and a second pointed edge provided on the proximal and distal edges of the cutting blade, respectively, so that tissue can be cut by moving the cutting blade either proximal or distal along a slot or channel provided in the jaw.

[0167] The actuator has a wire harness containing individual insulated wires or leads housed in a single sheath. The wire harness can exit the stationary housing at its underside and form part of a cable connection. The wires within the harness can provide electrical communication between the instrument and the electrosurgical generator and / or its accessories or attachments.

[0168] According to various embodiments, the actuator has one or more beads attached to a rotary coupling clip configured to allow infinite rotation of the shaft. In various embodiments, a switch is connected to a user-operated activation button 229, which is activated when the activation button is pressed. In one view, once activated, the switch forms a circuit by electrically coupling at least two leads to each other. Thus, an electrical path is then established from the electrosurgical generator to the actuator to supply RF energy to the leads attached to the rotary coupling clip.

[0169] In one embodiment, the actuator has a rotating shaft assembly that includes a rotating knob 227 mounted on an outer cover tube of an elongated shaft 226. The rotating knob allows the surgeon to rotate the shaft of an instrument while gripping the actuator 224.

[0170] According to various embodiments, the elongated shaft 226 has an actuator tube that connects the jaws 222 to an actuator and a blade actuator shaft assembly that connects the actuator to a cutting blade 271. In various embodiments, the blade actuator shaft assembly includes a two-piece (consisting of two parts) shaft having a proximal portion and a distal portion. The proximal portion of the blade shaft assembly terminates at a proximal end located at an interface node. The interface node consists of a spherical projection as a whole that engages with a blade advance lever. In other embodiments, the interface node may consist of a projection of another geometric shape, such as a cubic or rectangular columnar shape. The proximal portion of the blade shaft is operationally coupled to the distal portion of the blade shaft assembly. The distal portion of the blade shaft may have a mount at its distal end for attaching a cutting blade. In certain embodiments, both the proximal and distal portions of the blade shaft are at least partially positioned within a tubular section as a whole of the actuator tube.

[0171] In various embodiments, the actuation tube is housed within the outer cover tube. The actuation tube is shown as a tubular member that can be fitted into the outer cover tube, and in which case the blade actuation shaft can be fitted. In other embodiments, non-tubular actuation members, such as a shaft, a rigid band, or a link, can be used, and in certain embodiments, such non-tubular actuation members can be positioned parallel as a whole to the blade actuation shaft within the outer cover tube.

[0172] In various embodiments, a rotating shaft assembly is attached to the distal end of the outer cover tube, and this rotating shaft assembly includes two paired hubs and a conductive sleeve. The hubs engage with the outer cover tube in a snap-fit ​​relationship with each other. In other embodiments, the hubs may be integrally constructed, and these hubs are configured to interface with paired features on the outer cover tube. The conductive sleeve is preferably attached to the proximal portion of the assembled hub after they have been attached to the outer cover tube. When the conductive sleeve is attached to the rear of the assembled hub, the sleeve captures the exposed end of the insulated wire. In the illustrated embodiment, the insulated wire extends from its capture point below the conductive sleeve through a slot provided in the operating tube and then into a protective sleeve. The protective sleeve and the insulated wire extend distally toward the jaws within the operating tube. In other embodiments, the insulated wire may be formed integrally with the protective sheath, and there is no separate protective sleeve present within the operating tube.

[0173] A jaw 222 is attached to the distal end of an elongated shaft, and the jaw 222 includes a first jaw 270 and a second jaw 280. In one embodiment, a jaw pivot pin rotatably connects the first jaw and the second jaw to each other, so that the first jaw can move relative to the second jaw and rotate relative to it. In various embodiments, one jaw is fixed to the elongated shaft so that the opposing jaw rotates relative to a fixed jaw between an open position and a closed position. In other embodiments, both jaws are preferably rotatably connected to the elongated shaft so that both jaws can rotate relative to each other.

[0174] A conductive pad 272 is attached to the first jaw. In one embodiment, an insulated wire 273 is routed to electrically couple the conductive pad provided on the first jaw to a wiring harness in the actuator. The insulated wire extends from the distal end of a protective sleeve housed at the proximal end of the second jaw and then into the first jaw. The first jaw preferably has a slot positioned to receive the insulated wire. The insulated wire then passes through a hole provided in the first jaw and falls into a slot provided in the non-conductive portion. The insulated wire then extends to the distal end of the non-conductive portion and down through it to the conductive pad.

[0175] In some embodiments, the electrode geometric shape on the conductive pad of the jaw assembly is such that the sealing area completely encloses the distal portion of the blade cutting path. In embodiments, the conductive pad 272 and the second jaw 280 are curved at the edges to maintain a unique sealing surface in contact with the tissue between the jaws, reducing undesirable concentrated current density and / or assisting in the cutting of the tissue between the jaws. In some embodiments, with respect to certain surgical procedures, the jaw shape is preferably curved such that the distal end of the jaw is offset from the proximal end of the jaw with respect to the longitudinal axis to improve visibility for the user, e.g., the surgeon.

[0176] According to various embodiments, the dimensions of the jaw surfaces are appropriately proportional to the optimal pressure applied to the tissue between the jaws due to the potential forces that the instrument mechanism can generate. The surface area is also electrically significant with respect to the surface area in contact with the tissue. This proportion of the surface area and the thickness of the tissue are optimized in relation to the relative electrical properties of the tissue.

[0177] The jaws are positioned to maintain an electrically meaningful distance between them with respect to the thickness of the tissue held between them. In one embodiment, at least one jaw has a conductive post 281 extending laterally with respect to the longitudinal direction of the jaw. In various embodiments, this post protrudes through the inner surface of the second jaw or lower jaw assembly toward the inner surface of the first jaw or conductive pad.

[0178] In one embodiment, the conductive post is made of a conductive material, such as stainless steel. In one embodiment, a conductive post made of stainless steel provides high compressive strength and / or long-post strength. Thus, the conductive post can withstand large operational wear and tear, and such a conductive post is preferably dimensionally small relative to the dimensions of the jaws, with little concern for breakage or detachment, or occupying excessive space on the jaws. In one embodiment, the conductive post is made of the same material as the conductive pads on the first and / or second jaws.

[0179] According to various embodiments, a number of posts are provided, which support the inner edges of the conductive surfaces of the jaws adjacent to the blade channels within the jaws. According to various embodiments, the posts also provide additional surface texture to help capture and grasp tissue trapped within the jaws of the instrument. However, the conductive posts do not have edges or other non-traumatic surfaces that puncture, penetrate, or otherwise pierce the grasped tissue between the jaws.

[0180] In one embodiment, the conductive post supports the inner edge of a conductive surface located adjacent to the blade channel. The post is biased to be positioned at the edge of the blade channel. When the jaws are closed and RF energy is supplied, the conductive post is at the same potential as the conductive surface. Due to the configuration of the conductive post relative to the conductive surface and the fact that the conductive post is at the same potential as the upper conductive surface, in one embodiment a continuous microstructure-treated surface is obtained along the jaws. In one embodiment, this configuration and potential allow RF energy to be applied, thereby enabling heating and sealing around the conductive post, and further improving the quality of the microstructure seal or microstructure treatment between the jaws.

[0181] In addition, to improve sealing quality and reduce the risk of high current density at the edges of the upper and lower conductive surfaces, the upper and lower conductive surfaces have, in one embodiment, a retraction angle of 274 and / or radii of 275, 283. In addition to addressing current density, the radii also provide a non-traumatic rounded edge to blood vessels located adjacent to the area affected by the application of RF energy, thereby helping to prevent severance at the edges of the jaw surface.

[0182] In one embodiment, the conductive posts are positioned along the jaws and at different heights relative to each other, so that the conductive posts are not located on the same plane. Thus, in one embodiment, the conductive posts ensure that the first or most distal conductive post makes contact with the tissue first, followed by one or more intermediate conductive posts, and finally the most proximal conductive post makes contact with the tissue. In one embodiment, the most distal post is 0.005 inches (0.127 mm), the intermediate posts are 0.004 inches (0.102 mm), and the most proximal post is 0.003 inches (0.076 mm). This staggered arrangement ensures that the jaws or inner surfaces remain relatively parallel to the tissue and to each other, compensating for the deflection of the first and / or second jaws when force is applied. In one embodiment, the difference in height of the post relative to the jaws allows for lifting or raising portions of tissue located near or adjacent to the blade channel, thereby assisting in gripping the tissue as it is being cut, resulting in a smoother cut and facilitating the cutting process.

[0183] In one embodiment, the first jaw or upper jaw assembly includes a press-formed sheet metal conductive pad 272, which is held at a distance from the machined upper metal jaw 275 by a heat-resistant non-conductive plastic material 276. The press-formed sheet metal, the non-conductive plastic material, and the machined upper metal jaw are placed in a mold, and the mold is then filled with thermoplastic resin. The result of the process is an overmolded upper machined or MIM (metal injection molded) jaw, a press-formed conductive pad, and heat-resistant plastic, which are fixed or held together by thermoplastic resin overmolding to produce the first or upper jaw. In one embodiment, the upper jaw has an injection-molded component instead of the heat-resistant non-conductive plastic material.

[0184] In one embodiment, the second jaw or lower jaw assembly includes a machined or MIM jaw and a machined or MIM conductive post 281. In one embodiment, the post and jaw are made of the same material. The jaw and post are placed in a mold, and then thermoplastic resin is filled into this mold. The result of this process is an overmolded lower jaw, an overmolded lower jaw and a conductive post, which are fixed or held together by thermoplastic resin overmolding to produce the lower jaw. The strength and / or stability of the conductive post is increased relative to the jaw and / or structure by the post extending from the lower jaw assembly and through the inner surface of the jaw. Thus, in one embodiment, the post has a height of at least twice the thickness of the conductive pad. In one embodiment, the post has a bottom portion that extends into about half the thickness or depth of the first and / or second jaw. During assembly, the jaw gap is set in the fixture and laser welded, which in one embodiment is facilitated by slotted holes and dwells provided in the lower jaw.

[0185] Referring to Figures 38 to 40, in one embodiment, a return path connection 285 is provided for connecting a conductive post to the generator. In such an embodiment, the conductive post can provide additional feedback information, such as applied voltage, current, power, and phase or tissue characteristics. In one embodiment, the return path connection acts as an indicator or cutoff switch, so that when a cutting blade enters the jaw, a circuit is created or an intentional short circuit is triggered to stop the RF energy, thereby preventing the supply of RF energy while the blade is operating. In one embodiment, a thermistor or temperature sensor 286 is positioned below or in line with the conductive post and is connected in a return state to the wire or return connection via the lower jaw to monitor the temperature, for example, by a change in the thermistor caused by a temperature change. In one embodiment, the electrosurgical generator can then take into account jaws that can provide tissue temperature and tissue melting and / or apply RF energy. In one embodiment, the second or lower jaw has a plate or capacitance structure or sensor 287, and in one embodiment, in this case the electrosurgical generator can measure the capacitance between the bottom surface of the conductive post and a portion of the jaw in order to take into account the tissue capacitance or instrument that can melt and / or apply RF energy to the tissue.

[0186] According to various embodiments, the electrosurgical system may include an electrosurgical generator and an electrosurgical instrument. The electrosurgical instrument is used in laparoscopic procedures where ligation and division of blood vessels and tissue bundles are desired. The electrosurgical instrument melts blood vessels by delivering radio frequency (RF) energy to tissue trapped between the jaws of the instrument, and then divides the sealed tissue with a user-operated blade. The generator can provide an electrosurgical endpoint by determining the phase endpoint of the tissue to be treated. The electrosurgical system may include two or more electrosurgical instruments for different electrosurgical tasks, and the electrosurgical system may include various user interface features and audio / visual indicators. The electrosurgical system can also power conventional bipolar electrosurgical instruments and DC surgical instruments.

[0187] Next, referring to some of the operational aspects of the electrosurgical instrument or the instrument described herein according to various embodiments, once a bundle of blood vessels or tissue is identified for melting, the first jaws and the second jaws are positioned around the tissue. The movable handle 223 is squeezed to move the movable handle proximal to the stationary handle 228. As the movable handle moves proximal, it pushes the pull block. The pull block engages with the pull tube, thereby moving the pull tube proximal. The proximal movement of the pull tube causes the first jaw to rotate toward the second jaw, thereby effectively clamping the tissue. In Figures 27 and 28, the actuator 224 is shown in a first or initial position, in which the jaws 222 are in an open position, and in one embodiment, the opening of the first and second jaws determines an angle of about 30°.

[0188] Continuing to operate the movable handle causes it to rotate to a position where it engages with the latch mechanism, which holds the handle in the engaged position and prevents it from returning to the open position. High-frequency energy is applied to the tissue from the engaged position by pressing the activation button. Once the tissue has been melted, the movable handle is opened again by continuing to advance proximally to a position where the latch mechanism can disengage. In Figures 30 and 31, the actuator 224 is shown in the engaged position, in which the jaws 222 are closed and the movable handle is latched.

[0189] Alternatively or additionally, the user can activate the blade trigger 225. Moving the blade trigger proximal rotates the blade lever, thereby moving the push bar and cutting blade distally. The cutting blade moves forward and severs the sealed portion of the tissue. When the user releases the blade trigger, the blade spring resets the cutting blade to its original position. Returning the blade trigger to its original or initial position allows the user to continue to squeeze the movable handle to open the upper jaws. In Figures 32 and 33, the actuator 224 is shown in the cutting position, where the jaws 222 are in the closed position and the blade trigger is pressed, thereby advancing the cutting blade to its most distal position. Continued movement of the movable handle proximal leads to a position where the latch mechanism disengages and the movable handle can be released. Figure 29 shows an intermediate position where the jaws are in the closed position and the movable handle is not latched. In one embodiment, activating the blade trigger can cut the tissue between the jaws, and / or activating the melt button or switch can melt the tissue between the jaws.

[0190] Electrosurgical units, instruments and connections thereto, and other embodiments of their operation and / or function are described in U.S. Patent Application No. 12 / 416,668 (Title of Invention: Electrosurgical System), filed April 1, 2009, U.S. Patent Application No. 12 / 416,751 (Title of Invention: Electrosurgical System), filed April 1, 2009, U.S. Patent Application No. 12 / 416,695 (Title of Invention: Electrosurgical System), filed April 1, 2009, U.S. Patent Application No. 12 / 416,765 (Title of Invention: Electrosurgical System), filed April 1, 2009, and U.S. Patent Application No. 12 / 416,128 (Title of Invention: Electrosurgical System), filed March 31, 2009. These patent documents are incorporated herein by reference, and their entire contents are incorporated as part of this specification.

[0191] The above description is provided to enable those skilled in the art to manufacture and use surgical instruments and to carry out the methods described herein, and such description describes the optimal embodiment envisioned by the inventors carrying out the invention. However, various modifications remain obvious to those skilled in the art. These modifications are intended to fall within the scope of the invention. Various embodiments or aspects of such embodiments are shown in various figures and described throughout the specification. However, it should be noted that each embodiment and its aspects, whether illustrated or described separately, can be combined with one or more other embodiments and their aspects unless otherwise specified. Each combination is not explicitly described only for the sake of readability of this specification.

[0192] Although the present invention has been described in a particular manner, many additional modifications and variations will be apparent to those skilled in the art. Therefore, it should be understood that the present invention can be implemented in forms other than those specifically described, such as various deviations in dimensions, shape, and materials, which do not depart from the spirit and scope of the invention. Thus, the embodiments of the present invention should be considered in all respects to be illustrative and not limiting. Next, preferred embodiments of the present invention will be shown. 1. An electrosurgical generator configured to supply radio frequency (RF) energy to melt tissue, wherein the generator is: An RF amplifier that supplies RF energy via a detachably coupled electrosurgical instrument, A generator comprising a control device configured to monitor the phase angle of the supplied RF energy, wherein the control device signals the RF amplifier to adjust the voltage of the supplied RF energy when the monitored phase angle is equal to or less than a predetermined phase value. 2. The generator according to item 1 above, wherein the predetermined phase value is zero degrees. 3. The generator according to 1 or 2 above, wherein the predetermined phase value is the rate of change of the phase angle. 4. The generator according to any one of 1 to 3 above, wherein the adjustment of the voltage is to reduce the voltage of the supplied RF energy. 5. The generator according to any one of 1 to 4 above, wherein the adjustment of the voltage is to maintain the voltage of the supplied RF energy at its current voltage level. 6. The generator according to any one of items 1 to 5 above, wherein the adjustment of the voltage is to set the voltage of the supplied RF energy to a predetermined voltage. 7. The control device is a generator according to any one of 1 to 6 above, wherein the control device determines a second predetermined phase value based on and after the adjustment of the voltage. 8. The generator according to any one of 1 to 7 above, wherein the control device sends a signal to the RF amplifier to stop supplying the RF energy when the monitored phase angle is less than the second predetermined phase value. 9. The generator according to any one of 1 to 8 above, wherein the control device sends a signal to the RF amplifier to stop supplying the RF energy when the rate of change of the monitored phase angle is smaller than the second default phase value, and the second default phase value is the rate of change of the monitored phase angle. 10. An electrosurgical generator configured to supply radio frequency (RF) energy to melt tissue, wherein the generator is: An RF amplifier that supplies RF energy via a detachably coupled electrosurgical instrument, A generator having a control device configured to monitor the phase angle of the supplied RF energy, wherein the control device is configured to determine the voltage of the supplied RF energy when the monitored phase angle is equal to or less than a predetermined phase value. 11. The control device is the generator according to 10 above, which calculates the size of the tissue by comparing the determined voltage with a predetermined voltage value. 12. The generator according to 10 or 11 above, wherein the control device calculates a second predetermined phase value using the calculated tissue size. 13. The control device is a generator according to any one of 10 to 12 above, which calculates a second predetermined phase value using the voltage determined above. 14. The generator according to any one of 10 to 13 above, wherein the control device sends a signal to the RF amplifier to stop supplying the RF energy when the monitored phase angle is smaller than the second predetermined phase value. 15. The generator according to any one of 10 to 14, wherein the control device sends a signal to the RF amplifier to stop supplying the RF energy when the rate of change of the monitored phase angle is smaller than the second predetermined phase value. 16. The generator according to any one of items 10 to 15 above, wherein the control device sends a signal to the RF amplifier to stop supplying the RF energy when the monitored phase angle remains constant. 17. An electrosurgical system, An electrosurgical instrument configured to grasp tissue and melt the tissue using radio frequency (RF) energy, The system includes an electrosurgical generator that is connectable to the electrosurgical instrument and configured to supply the RF energy via the electrosurgical instrument, An electrosurgical system wherein the generator can identify at least one control index and at least one operating condition, and can be reconfigured to adjust the supply of RF energy based on the identified operating condition in response to the identified control index being satisfied. 18. The electrosurgical system according to 17, wherein the identified control index includes a measured phase angle, and the identified operating condition includes an RF output adjustment value. 19. The electrosurgical system according to 17 or 18, wherein the RF output adjustment value is at least one of voltage, current, power, or phase value. 20. The electrosurgical system according to any one of 17 to 19, wherein the generator further comprises an RF sense configured to measure the phase angle of the output of the generator via a connected electrosurgical instrument and to send the measured phase angle to the control device. 21. The electrosurgical system according to any one of 17 to 20, wherein the generator further comprises an RF amplifier configured to adjust the supply of RF energy by an amount specified by the RF output adjustment value. 22. The electrosurgical system according to any one of 17 to 21, wherein the control device is configured to determine a second control indicator and to stop supplying the RF energy when the second control indicator is met. 23. An electrosurgical system according to any one of 17 to 22 above, wherein the identified control index includes a measured rate of change of the phase angle, and the identified operating condition includes an RF output adjustment value. 24. The electrosurgical system according to any one of items 17 to 23 above, wherein the generator is reconfigured when an electrosurgical instrument is connected to the generator. 25. The electrosurgical system according to any one of 17 to 24, wherein the generator is configured to identify a second control indicator and to adjust the voltage of the supplied RF energy when the second control indicator is met. 26. The electrosurgical system according to any one of 17 to 25, wherein the generator further comprises a control device configured to determine the time when a control index is satisfied by evaluating a logical expression. 27. An electrosurgical system according to any one of 17 to 26 above, wherein a binary decision is made as a result of the evaluation of the logical formula. 28. The electrosurgical system according to any one of 17 to 27 above, wherein the at least one control index is predetermined by the script source being located remotely and being disconnected from the generator and the connectable surgical instrument. 29. An electrosurgical system according to any one of items 17 to 28 above, wherein the script source is converted into a script database file prior to the connection of the electrosurgical instrument. 30. The electrosurgical system according to any one of items 17 to 29 above, wherein the script database file contains a set of tokens that can be joined to form a logical expression. 31. Electrosurgical instruments, Having a first jaw equipped with a first electrode, The first jaw has a second jaw coupled to the first jaw and having a second electrode facing the first electrode, the first electrode and the second electrode being arranged to transmit radio frequency (RF) energy between the first electrode and the second electrode, and the first and second electrodes being made of the same conductive material. It has an elongated shaft having a proximal end, a distal end, and a longitudinal axis extending from the proximal end to the distal end, and the first and second jaws are rotatably connected to the distal end of the elongated shaft. An electrosurgical instrument having a conductive post incorporated in the second jaw and extending from the second jaw toward the first jaw, wherein the conductive post is stationary and made of the same conductive material as the first and second electrodes. 32. The electrosurgical instrument according to 31, wherein the conductive post has an upper portion extending from the upper surface of the second jaw and a lower portion enclosed within an insulating material provided in the second jaw, the insulating material separating the conductive post from the conductive material in the second jaw, and the conductive post is not connectable to the conductive material extending from the elongated shaft. 33. The electrosurgical instrument according to 31 or 32, wherein the conductive post has a smaller surface area than the first electrode. 34. The electrosurgical instrument according to any one of 31 to 33 above, wherein the conductive post has a smaller surface area than the second electrode. 35. An electrosurgical instrument according to any one of 31 to 34, further comprising a single wire made of a conductive material extending from the elongated shaft and connected to the first electrode. 36. The electrosurgical instrument according to any one of 31 to 35 above, wherein the conductive post is in contact with the first jaw, and the first and second jaws are in the closed position. 37. The electrosurgical instrument according to any one of 31 to 36, wherein the conductive post has an outer circumference limited to the outer circumference of the second jaw. 38. The electrosurgical instrument according to any one of the above 31 to 37, wherein the conductive posts include a plurality of conductive posts having various heights. 39. The electrosurgical instrument according to any one of 31 to 38 above, wherein the plurality of conductive posts include the distal conductive post having a height greater than the height of the proximal conductive post. 40. The electrosurgical instrument according to any one of 31 to 39, wherein the conductive post has a flat upper surface positioned to match the flat lower surface of the first jaw. 41. An electrosurgical instrument according to any one of 31 to 40 above, wherein the conductive post is non-adjustable and rigid. 42. Electrosurgical instruments, Having a first jaw equipped with a conductive pad, It has a second jaw coupled to the first jaw and having an inner surface facing the conductive pad, the first and second jaws are arranged to trap tissue between the conductive pad and the inner surface of the second jaw, the conductive pad and the second jaw are arranged to be connected to an electrosurgical energy source and to transmit RF energy through the tissue held between the jaws, It has a blade that can move along the longitudinal axis from a proximal position to a distal position and return to the proximal position, the blade being positioned within the outer circumference of the second jaw, An electrosurgical instrument having a conductive post provided on the second jaw adjacent to the blade, wherein the conductive post is arranged not to be connected to the electrosurgical energy source and to transmit RF energy between the conductive pad and the second jaw through the tissue held between the jaws. 43. It further has an elongated shaft having a proximal end, a distal end, and a longitudinal axis extending from the proximal end to the distal end, and the first and second jaws are rotatably connected to the distal end of the elongated shaft. The electrosurgical instrument according to 42, further comprising an actuator provided at the proximal end of the elongated shaft, wherein the actuator is positioned to be more accessible to the user when the actuator is operated to move the first and second jaws, thereby initiating the supply of RF energy to the conductive pad and the second jaw or initiating the translational motion of the blade. 44. The electrosurgical instrument according to 42 or 43, wherein the electrosurgical energy source is an electrosurgical generator configured to supply high-frequency energy only to the conductive pad and the second jaw, and not to the conductive post and the blade. 45. The electrosurgical instrument according to any one of 42 to 44, wherein the second jaw has a channel through which the blade is inserted, and the conductive post is provided adjacent to the channel of the second jaw and below the lower surface of the conductive pad, and the conductive post is positioned to contact the lower surface of the conductive pad. 46. ​​The electrosurgical instrument according to any one of 42 to 45 above, wherein the conductive post is made of a conductive material, and the second jaw is made of the same conductive material as the conductive post. 47. The electrosurgical instrument according to any one of 42 to 46 above, wherein the conductive pad is made of the same conductive material as the conductive post. 48. An electrosurgical instrument according to any one of 42 to 47 above, wherein the blade is made of the same conductive material as the conductive material of the conductive post. 49. The electrosurgical instrument according to any one of 42 to 48, wherein the entire surface of the second jaw and the first jaw facing the conductive pad is smooth and flat, and the entire surface is free from depressions or pockets. 50. The electrosurgical instrument according to any one of 42 to 49, wherein the conductive post has a flat and smooth inner surface that faces the first jaw and is positioned to contact a portion of the inner surface of the first jaw. 51. An electrosurgical instrument according to any one of 42 to 50, further comprising an RF sense configured to receive a supplied RF waveform, wherein the RF sense further comprises a synchronous detector configured to calculate the real and imaginary components of the supplied RF waveform. 52. An electrosurgical generator configured to supply radio frequency (RF) energy to melt tissue, wherein the generator is: An RF amplifier configured to supply an RF waveform of RF energy, An electrosurgical generator comprising an RF sense configured to receive the supply RF waveform, wherein the RF sense includes a synchronous detector configured to calculate the real and imaginary components of the supply RF waveform by multiplying the supply RF waveform to at least one reference signal.

Claims

1. It is an electrosurgical system, Equipped with an electrosurgical instrument configured to grasp tissue and melt it using radio frequency (RF) energy, The aforementioned electrosurgical instrument is A first jaw having a first electrode, A second jaw having a second electrode opposite to the first electrode, wherein the first and second electrodes are configured to conduct the RF energy between them, and the first and second jaws are positioned at the distal end of the electrosurgical instrument such that the first jaw is movable relative to the second jaw. The second jaw includes a conductive post that is stationary with respect to the second jaw, having an upper portion extending from the upper surface of the second jaw and a lower portion disposed within the insulating material within the second jaw, wherein the insulating material separates the lower portion of the conductive post from the conductive material within the second jaw. The second jaw further comprises a channel, and the electrosurgical instrument further comprises a blade movable within the channel of the second jaw along the longitudinal axis, the blade being movable from a proximal position to a distal position and back to the proximal position. The electrosurgical system further includes, The electrosurgical device comprises an electrosurgical generator that is detachably connected to the electrosurgical instrument and configured to supply the RF energy only to the first and second electrodes and not to the conductive post, system.

2. The system according to claim 1, wherein the first electrode, the second electrode, the conductive post, and the blade are made of the same conductive material.

3. The system according to claim 2, wherein the entire surface of the first jaw facing the second jaw is smooth and flat, and the entire surface is free from recesses or pockets.

4. The system according to claim 3, wherein the electrosurgical instrument further comprises an actuator accessible to a user and positioned to move a blade along a longitudinal axis.

5. The system according to claim 4, wherein the electrosurgical generator is configured not to supply RF energy to the blade.

6. The system according to claim 5, wherein the electrosurgical instrument further comprises a switch that supplies RF energy to the electrosurgical generator.

7. The system according to claim 6, wherein the electrosurgical generator further comprises a control device arranged to record the usage status of both the electrosurgical instrument and the electrosurgical generator.

8. The system according to claim 7, wherein the conductive post is fixed to the second jaw by a thermoplastic material.

9. The system according to claim 8, wherein the conductive post has a flat upper non-traumatic surface.

10. The system according to claim 1, 2, or 9, wherein the conductive post is positioned between the distal end and the intermediate portion of the second jaw.

11. The system according to claim 10, further comprising a second conductive post positioned between the proximal end and the intermediate portion of the second jaw.

12. The system according to claim 11, further comprising a third conductive post disposed between the conductive post and the second conductive post.

13. The system according to claim 1, 2, or 9, wherein the conductive posts include a plurality of conductive posts having varying heights, and the plurality of conductive posts include a distal conductive post having a height greater than the height of the most proximal conductive post.

14. The electrosurgical generator is configured to receive script information from the electrosurgical instrument when the electrosurgical instrument is connected to the electrosurgical generator, and the script information defines a state and the sequence of transitions between states. The system according to claim 1, 2, or 9, wherein the states include a system state and a user state, in which a predefined operation of the electrosurgical generator is performed, and in which a framework is provided for establishing customized operations and values ​​for a particular electrosurgical instrument in the user state.

15. The system according to claim 14, wherein for each user state, a power, voltage, or current setting value for the electrosurgical generator is determined or carried over from the state before transitioning to the current state.

16. The system according to claim 15, wherein the script information provides termination conditions for a system state, instructions to transition to another state, and instructions to transition to a user state.

17. The system according to claim 1, 2, or 6, wherein the electrosurgical generator comprises a control device including an action engine configured to enable the generator to be configured to correspond to a plurality of action plans and electrosurgical instruments, the action engine being configured to receive and interpret data from an external source and to specifically configure the operation of the generator based on the received data.

18. The system according to claim 1, 2, or 6, wherein the electrosurgical generator includes a control device that includes an operating engine configured to receive configuration data from an instrument script database file read from a memory device, check for errors in the instrument script database, and start script execution.

Images