Abstract:
An electrosurgical system includes an electrosurgical generator, an electrosurgical instrument, an optical clarity sensor and a control component. The electrosurgical generator generates electrosurgical energy for use during electrosurgery. The electrosurgical instrument is coupled to the electrosurgical generator and treats tissue. The optical clarity sensor is coupled to the electrosurgical generator and is adapted to measure tissue with at least two optical frequencies. The control component is operatively coupled to the optical clarity sensor and receives sensor data therefrom. The control component communicates control instructions to the electrosurgical generator to control the generation of the electrosurgical energy.

Description:
CROSS REFERENCE TO RELATED APPLICATION 
       [0001]    This application is related to U.S. application Ser. No. 10/427,832, filed on May 1, 2003 by Buysse et al., now U.S. Pat. No. 7,137,980 entitled “Method and system for controlling output of RF medical generator”, the entire contents thereof are hereby incorporated by reference in its entirety herein. 
     
    
     BACKGROUND 
       [0002]    1. Technical Field 
         [0003]    The present disclosure relates to an electrosurgical system and method and more particularly, the present disclosure relates to an electrosurgical system and method that includes an electrosurgical instrument with a sensor, such as a temperature sensor, a tissue hydration sensor, and an optical clarity sensor. 
         [0004]    2. Description of Related Art 
         [0005]    Electrosurgery is the application of electricity and/or electromagnetic energy to cut or modify biological tissue during a surgical procedure. Generally, electrosurgery utilizes an electrosurgical generator, a return electrode, and a source electrode. The electrosurgical generator produces an electromagnetic wave (referred to herein as “electrosurgery energy”) typically above 100 kilohertz, between the return and source electrodes when applied to tissue. The electromagnetic wave created therebetween dissipates energy as heat as it travels from one electrode to the other. Electromagnetic frequencies above  100  kilohertz are employed to avoid muscle and/or nerve stimulation. 
         [0006]    During electrosurgery, current generated by the electrosurgical generator is conducted through the patient&#39;s tissue disposed between the two electrodes. The current causes the tissue to heat up as the electromagnetic waves overcome the tissue impedance. Although many other variables affect the total heating of the tissue, usually more current density directly correlates to increased heating. Electrosurgical energy is typically used for cutting, dissecting, ablating, coagulating, and/or sealing tissue. 
         [0007]    The two basic types of electrosurgery employed are monopolar and bipolar electrosurgery; however, both types use an “active” and a “return” electrode. In bipolar electrosurgery, the surgical instrument has an active electrode and a return electrode on the same instrument or in very close proximity, usually causing current to flow through a smaller amount of tissue. In monopolar electrosurgery, the return electrode is located elsewhere on the patient&#39;s body and is usually not part of the electrosurgical instrument itself. In monopolar electrosurgery, the return electrode is part of a device usually referred to as a return pad. 
         [0008]    The effectiveness of the application of electrosurgical energy is affected by a variety of factors, including the patient&#39;s age, weight, the type of tissue being modified, and the desired tissue effect. Different voltages, currents, duty cycles and frequencies are used to cause a variety of tissue effects. For example, coagulation requires the application of different electrosurgical energy compared to cutting. 
         [0009]    Many electrosurgical procedures require cutting or ligating blood vessels or vascular tissue. A surgeon can cauterize, coagulate, desiccate, and/or reduce bleeding by controlling the intensity, frequency and duration of the electrosurgical energy applied to the tissue between the electrodes of the electrosurgical instrument. 
         [0010]    The process of coagulating vessels is different from electrosurgical vessel sealing. For the purposes herein, “coagulation” is defined as a process of desiccating tissue wherein the tissue cells are ruptured and dried. “Vessel sealing” or “tissue sealing” is defined as the process of liquefying the collagen in the tissue so that it reforms into a fused mass. Coagulation of small vessels is sufficient to permanently close them, while larger vessels need to be sealed to assure permanent closure. 
         [0011]    A way to achieve effective operation of the electrosurgical instrument is to monitor the electrosurgical energy directly. Additionally or alternatively, the tissue being acted upon can be monitored. This monitoring can be used in a feedback loop of a control component that controls the generation of the electrosurgical energy. 
       SUMMARY 
       [0012]    The present disclosure relates to an electrosurgical system and method and more particularly, the present disclosure relates to an electrosurgical system and method that includes an electrosurgical instrument with a sensor, such as a temperature sensor, a tissue hydration sensor, and an optical clarity sensor. 
         [0013]    In one embodiment of the present disclosure, an electrosurgical system includes an electrosurgical generator, an electrosurgical instrument, an optical clarity sensor and a control component. The electrosurgical generator generates electrosurgical energy for use during electrosurgery. The electrosurgical instrument is coupled to the electrosurgical generator and treats tissue. The optical clarity sensor is coupled to the electrosurgical generator and is adapted to measure tissue with at least two optical frequencies. The control component is operatively coupled to the optical clarity sensor and receives sensor data therefrom. The control component communicates control instructions to the electrosurgical generator to control the generation of the electrosurgical energy. 
         [0014]    In another embodiment of the present disclosure, the sensor data includes optical clarity measurements of tissue. The control component instructs the electrosurgical generator to generate the electrosurgical energy corresponding to the optical clarity measurements which corresponds to tissue being less than about 60 degrees Celsius or less than about 100 degrees Celsius. 
         [0015]    In another embodiment of the present disclosure, the control component instructs the electrosurgical generator to generate the electrosurgical energy corresponding to at least one optical clarity measurement being in a predetermined range and/or tissue hydration being within a predetermined range. Additionally or alternatively, the control component instructs the electrosurgical generator to generate the electrosurgical energy when the at least one optical clarity measurement falls within a predetermined range. 
         [0016]    In another embodiment of the present disclosure, the electrosurgical instrument includes a shaft, a drive assembly, and a movable handle. The shaft has first and second jaw members at a distal end thereof. One or both of the jaw members include an electrode disposed thereon which applies the electrosurgical energy to tissue. One (or both) of the jaw members includes the optical clarity sensor disposed thereon. The drive assembly is operatively coupled to the shaft and moves one of the jaw members relative to the other from a first position to a second position. In the first position, the first jaw member is disposed in spaced relation relative to the second jaw member and in the second position, the first jaw member grasps tissue. The movable handle actuates the drive assembly. 
         [0017]    In another embodiment of the present disclosure, the electrosurgical instrument includes first and second shafts having first and second jaw members, respectively. The second shaft is pivotally connected to the first shaft. One (or both) of the jaw members includes an electrode disposed thereon configured to apply the electrosurgical energy to tissue. One of the jaw members includes the optical clarity sensor disposed thereon. 
         [0018]    In another embodiment of the present disclosure, one or more of the optical frequencies of the at least two optical frequencies is adapted to be a reference, is adapted to be substantially absorbed by water and/or is adapted such that water is substantially translucent to the optical frequency. The at least two optical frequencies may include first and second optical frequencies such that the first optical frequency is adapted to be substantially absorbed by water and the second optical frequency is adapted such that water is substantially translucent to the second optical frequency. The sensor data may include a first measurement of the first optical frequency and second measurement of the second optical frequency. The electrosurgical generator can compare the first measurement to the second measurement, e.g., such that at least one of tissue hydration, tissue temperature, optical clarity and tissue thickness is determined. 
         [0019]    In yet another embodiment of the present disclosure, an electrosurgical generator includes a control component. The control component includes a receiving module, a waveform controller and a control algorithm. The control component is at least partially implemented by an operative set of processor executable instructions configured for execution by at least one processor. The receiving module is operatively connected to a optical clarity sensor and receives sensor data therefrom. The optical clarity sensor is adapted to measure tissue with at least two optical frequencies and the sensor data includes a tissue temperature sensor measurement, a tissue hydration sensor measurement, and/or an optical clarity sensor measurement utilizing the at least two optical frequencies. The waveform controller communicates control instructions to the electrosurgical generator to control the generation of electrosurgical energy. The control algorithm is in operative communication with the receiving module and the waveform controller. The control algorithm processes the data to calculate the control instructions and communicates the control instructions to the waveform controller. 
         [0020]    The control algorithm may be a proportional-integral-derivative control algorithm. The control module may include one or more microcontrollers to execute the operative set of processor executable instructions. The receiving module may include an analog to digital conversion circuit configured to convert the data from an analog signal to a digital signal and/or the waveform controller includes a digital-to-analog conversion circuit configured to convert the control instructions from a digital signal to an analog signal. The waveform controller may includes an electronic signal amplifier configured to amplify the analog signal of the control instructions such that the amplified analog signal instructs the electrosurgical generator. 
         [0021]    In another embodiment of the present disclosure, a method for controlling generation of electrosurgical energy includes: providing an electrosurgical system; activating an optical clarity sensor of the electrosurgical system to communicate with the control component; and monitoring sensor data from the optical clarity sensor. 
     
    
     
       BRIEF DESCRIPTION OF THE DRAWINGS 
         [0022]    These and other advantages will become more apparent from the following detailed description of the various embodiments of the present disclosure with reference to the drawings wherein: 
           [0023]      FIG. 1  is a schematic block diagram of an electrosurgical system that includes an electrosurgical instrument with a sensor according to the present disclosure; 
           [0024]      FIGS. 2A-2B  are schematic block diagrams of an electrosurgical system according to the present disclosure; and 
           [0025]      FIG. 3  is a flow chart diagram illustrating a method for using an electrosurgical system that includes an electrosurgical instrument with a sensor according to the present disclosure. 
       
    
    
     DETAILED DESCRIPTION 
       [0026]    Referring to the drawings,  FIG. 1  is a block diagram depicting an electrosurgical system  100 . Electrosurgical system  100  includes electrosurgical generator  102  that generates electrosurgical energy. The electrosurgical energy is used to perform electrosurgery on a patient using electrosurgical instrument  104 . 
         [0027]    Electrosurgical generator  102  may have several user interface devices (e.g., touch screens, switches, dials, and the like) to assist a surgeon to achieve the desired results. The surgeon can use the user interface devices to input various data parameters into electrosurgical generator  102 . However, not all factors can be known and/or are readily known to the surgeon. For example, the specific physiology of patient P (e.g., age, weight, electrolyte density, PH, osmolarity, fluid volume and pressure, diseases and the like), temperature, humidity, and other factors that may influence electrosurgery, may not be readily know to the surgeon. 
         [0028]    Thus, to better assist in ensuring an effective electrosurgical procedure, electrosurgical generator  102  may use several techniques to adjust the applied electrosurgical energy. Some such techniques include calculating or monitoring the tissue impedance, current, voltage, duty cycle, tissue resistance and the like. Electrosurgical generator  102  can use these calculated or monitored properties to make adjustments to the electrosurgical energy applied to tissue by electrosurgical instrument  104 . Additionally or alternatively, as is discussed in more detail below, feedback data may be provided to electrosurgical generator  102  by electrosurgical instrument  104 . 
         [0029]    Electrosurgical instrument  104  can be a monopolar electrosurgical instrument or a bipolar electrosurgical instrument. For example, electrosurgical instrument  104  may be forceps, a vessel sealing electrosurgical instrument, a cutting electrosurgical instrument, or the like. The electrosurgical energy generated by electrosurgical generator  102  is transferred to electrosurgical instrument  104  via cable  106 . Cable  106  includes an active path and a return path. The active and/or return paths may be made out of a sufficiently conductive material having an appropriate geometry. For example, cable  106  may be a coaxial cable having a geometry that mitigates attenuation losses within the frequency range of the electrosurgical energy. 
         [0030]    Electrosurgical generator  102  may be powered by Alternating Current or Direct Current (referred to herein as “AC” and “DC”, respectively); however, it is preferable that electrosurgical generator  102  is powered by a power source via a standardized receptacle outlet, e.g., a 110 volt outlet as typically found within the United States. Although electrosurgical generator  102  is connected to an external power source, power supply  108  conditions and converts the external power source (e.g., AC power from a outlet) to sufficiently power various parts of electrosurgical generator  102 . 
         [0031]    For example, consider that control component  110  includes microcontroller  112 ; microcontrollers typically need a DC power source, such as a 5-Volt DC power source. Thus, power supply  108  can also include circuitry to ensure that microcontroller  112  is sufficiently powered, e.g., circuitry that includes transformers, rectifiers, capacitors, voltage regulators, or the like. Additionally, power supply  104  supplies power to control component  110  and electrosurgical energy source  114 . 
         [0032]    Electrosurgical energy source  114  includes circuitry sufficient to translate instructions from waveform controller  118  from one form to another form more conducive for interpretation by RF output stage  116 . RF output stage  116  includes circuitry to safely and efficiently transfer the electrosurgical energy to electrosurgical instrument  104 . For example, RF output stage  116  may include an output transformer providing an isolated ground, an output amplifier, impedance matching circuitry to facilitate efficient power transfer, or the like, while electrosurgical energy source  114  may include a variable output power supply connection, voltage scaling circuitry, a buffer such as a voltage follower, or the like. 
         [0033]    RF output stage  116  may be connected to cable  106  using an RF connector, such as an coaxial cable female connector, facilitating low attenuation injection of the electrosurgical energy into cable  106 . Also, electrosurgical energy source  114  implements the instructions received from waveform controller  118  while ensuring that RF output stage  116  properly complies with the instructions. For example, waveform controller  118  may send multiple signals regarding the desired characteristics of the electrosurgical energy to be injected into cable  106 , and electrosurgical energy source  114  translates those signals to ensure that RF output stage  116  complies with the instructions by comparing a voltage sense to an RF drive (not depicted in  FIG. 1 ). Additionally or alternatively, electrosurgical energy source  114  may include safety and/or isolation circuitry. 
         [0034]    Electrosurgical component  102  also includes control component  110 . Control component  110  may be implemented in hardware, software, firmware, or some combination thereof, and includes waveform controller  118 , control algorithm  124 , and receiving module  126 . For example, control algorithm  124  may be implemented in software processed by microcontroller  112 . 
         [0035]    Waveform controller  118  instructs electrosurgical energy source  114  to maintain a particular amplitude, voltage, current, frequency, duty cycle, and/or other properties of the electrosurgical energy for application to tissue. Waveform controller  118  includes a digital to analog converter (referred to herein as a “DAC”)  120  and electronic signal amplifier  122 . Additionally or alternatively, waveform controller  118  may include output relays, scaling relays, and/or an output waveform microcontroller (not depicted). Waveform controller  118  can also instruct the electrosurgical energy source  114  using an analog or a digital signal. For example, waveform controller  118  may have a digital waveform stored therein for converting the waveform to analog form via DAC  120 . Electrosurgical signal amplifier  112  may amplify the analog waveform by a scalar value, e.g., 10, before sending the waveform to electrosurgical energy source  114 . 
         [0036]    However, control component  110  determines what properties the electrosurgical energy should have based upon sensor data, specifically, control component  110  can form a feed-back loop with sensor  128 . Sensor  128  may include tissue temperature sensor  130 , tissue hydration sensor  132 , and/or optical clarity sensor  134 . The sensor data is received by receiving module  126  via cable  136 . The sensor data may be in analog or digital form. Additionally or alternatively, the sensor data may be converted from analog to digital form via analog to digital converter (referred to herein as “ADC”)  138 . 
         [0037]    The sensor data is processed by control algorithm  124  to calculate the control instructions. The calculated control instructions are communicated to waveform controller  118 . Control algorithm  124  may be a proportional-integral-derivative control algorithm and/or some other control algorithm to facilitate application of the electrosurgical energy to achieve the desired tissue effect. 
         [0038]    Referring simultaneously to  FIGS. 1 ,  2 A, and  2 B, sensor  128  may be located on electrosurgical instrument  104  and is shown in two embodiments by  FIGS. 2A and 2B . Electrosurgical instrument  104  may include an active and/or a return electrode, and sensor  128  may be disposed on or near at least one of the electrodes, or otherwise positioned to take at least one tissue measurement of Patient P of  FIGS. 2A and 2B . Cable  106  may include an active path and a return path for apply electrosurgical energy to patient P while electrosurgical generator  102  receives sensor data through cable  136 . 
         [0039]    Referring to the drawings,  FIG. 2A  shows an open electrosurgical instrument  104  that includes shaft  202  with jaw member  204  on the end. Electrosurgical instrument  104  also includes shaft  206  with jaw member  208  on the end as well. Shaft  206  is attached to shaft  202  via pivot  210  making them pivotally connected. Pivot  210  may be formed from pins, bearings, axels, or the like to assist in the movement of jaws  204  and  208  relative to each other. Grips  212  and  214  move shafts  206  and  202 , respectively, allowing a surgeon to grip and/or compress tissue of patient P between jaw members  204  and  208 . For example, a surgeon may apply pressure to force grips  212  and  214  together when a vessel is positioned between jaw members  204  and  208 , gripping the vessel. Electrosurgical energy may then be applied between jaw members  204  and  208  by electrodes, sealing the vessel. Sensor  128  may be used by electrosurgical generator  102  to assist in the vessel sealing (discussed in more detail below). Further details relating to open instrument vessel sealing are discussed in commonly-owned U.S. application Ser. No. 10/962,116. 
         [0040]    Referring now to  FIG. 2B , another embodiment is shown of electrosurgical system  100  for use with an electrosurgical instrument  104 ′. Electrosurgical instrument  104 ′ includes a shaft  216 ′ that has a distal end that includes jaw members  218 ′ and  220 ′. Within electrosurgical instrument  104 ′, a drive assembly (not shown) actuates jaw members  219 ′ and  220 ′ so that initially they are spaced by a distance, and, when actuated, move relative to each other. Actuation assembly includes handle  220 ′ that when “squeezed” causes jaw members  218 ′ and  220 ′ to move closer together pivotally, approximately pivoting along their attachment point to the distal end of shaft  216 ′. Trigger  226 ′ causes the electrosurgical generator  102  to apply the electrosurgical energy. Jaw members  220 ′ and  218 ′ may each have an active and/or a return electrode. Sensor  128  may be disposed on or near one of the electrodes. Additionally or alternatively, sensor  128  can be positioned to take at least one measurement of tissue of patient P and send the measurement to electrosurgical generator via cable  138 . 
         [0041]    Referring again to  FIG. 1 , as mentioned previously, sensor  128  may include tissue temperature sensor  130 , tissue hydration sensor  132 , and optical clarity sensor  134 , and can communicate data through cable  136  to electrosurgical generator  102 ; the data may include a tissue temperature measurement, a tissue hydration measurement, and an optical clarity measurement of tissue. 
         [0042]    Tissue temperature sensor  130  can measure tissue temperature and communicate one or more tissue temperature measurements to electrosurgical generator  102 . The biology of tissue is highly sensitive to temperature. For example, above 60 degrees Celsius, collagen protein denatures causing the tissue bond strength to be reduced. Above 100 degrees Celsius, the water within the cell vaporizes leading to cell destruction. Electrosurgical generator  102  can monitor the tissue temperature via temperature measurements received by receiving module  126  through cable  136 , and adjust the electrosurgical energy based upon the received measurements to achieve a desired result, e.g., by keeping the tissue temperature measurements below a value, above a value, and/or within a predetermined range. 
         [0043]    For example, for tissue cutting, it may be desirable to generate electrosurgical energy to ensure that the tissue is above about 100 degrees Celsius. In other applications, such as vessel sealing, it is more desirable to maintain a tissue temperature of less than about 60 degrees Celsius. Also, a predetermined range may be used to ensure that the temperature is high enough to cause tissue fusion but low enough to prevent loss of tissue strength. Programming of the tissue temperature desired (or range desired) may be preprogrammed within electrosurgical generator  102 , or may manually be set by the operator. 
         [0044]    Tissue temperature sensor  130  may include a contact or a non-contact temperature sensor. Tissue temperature sensor  130  also include a ratio or optical pyrometer, a thermal imager temperature sensor, fiber optic based temperature sensor, thermocouples, thermistors, resistance temperature detector (“RTD”), semiconductor, or the like to measure temperature. Note that cable  136  may include one or more conductive cable paths (i.e., wires) and/or may include a fiber optic cable path (also referred to herein as a “fiber optic cable”). Additionally or alternatively, sensor  128  may include additional components or circuitry to aide in the communication of measurements to electrosurgical generator  102 . For example, electrosurgical generator  102  may provide power to circuitry within sensor  128  via cable  136  to enable the circuitry to communicate measurements to electrosurgical generator  102  using a pulsed width modulation based communication technique. Also, cable  106  may be bundled with cable  136  (not depicted). 
         [0045]    Tissue hydration sensor  132  can communicate to electrosurgical generator  102  a tissue hydration measurement of some tissue of patient P (see  FIGS. 2A and 2B ). For example, tissue hydration sensor  132  can approximate tissue hydration of the tissue between jaw members  204  and  208  of  FIG. 2A , and/or between jaw members  218 ′ and  220 ′ of  FIG. 2B . The measurement of the tissue hydration may be accomplished using an optical based sensor, electrical based sensor, or other sufficient tissue hydration sensor. As tissue is heated the water therein may evaporate slowly. The tissue hydration sensor  132  may measure this decreasing tissue hydration and communicate a series of tissue hydration measurements to receiving module  126  via cable  136 . Control Algorithm  126  may instruct waveform controller  118  to continue to apply the electrosurgical energy until the tissue hydration sensor  132  falls within a predetermined threshold. 
         [0046]    For example, during electrosurgery a surgeon may use surgical instrument  216  of  FIGS. 2A  to clamp onto a vessel between jaw members  204  and  208 . The surgeon may then activate the electrosurgical energy (e.g., by a foot pedal) to start the vessel sealing. The initial tissue hydration measurement of tissue hydration sensor  132  may be, for exemplary purposes only, about 60% water content, and control algorithm  124  may have a predetermined threshold of 30% water content. As the electrosurgical energy is applied, consecutive tissue hydration measurements measured by tissue hydration sensor  132  measures the reducing water content and instructs waveform controller  118  to continue to apply the electrosurgical energy until control algorithm  124  detects an approximate  30 % water content tissue hydration measurement. When the 30% water content tissue hydration measurement is detected, control algorithm  124  may instruct waveform controller  118  to stop applying electrosurgical energy to electrosurgical instrument  104 . An alarm and/or an indicator may indicate to the surgeon that the vessel is sealed. 
         [0047]    Referring simultaneously to  FIGS. 1 ,  2 A, and  2 B, sensor  128  includes optical clarity sensor  134 . Optical clarity sensor  134  may use optical frequencies which may be visible or outside of visual perception to make an optical clarity measurement. 
         [0048]    Referring to  FIG. 2A , an optical source may inject photons from jaw member  204  through tissue and to jaw member  208  where an absorption and/or transparency measurement can be made. Jaw member  204  may include an LED, a laser, a fiber optical coupling lens, or the like. Additionally or alternatively, cable  136  may include a fiber optic cable that carries light from electrosurgical generator  102  that is focused to travel from jaw member  204  thorough tissue and to jaw member  208 . Jaw member  208  may include a fiber optic coupling lens to gather the photons and carry them back to electrosurgical generator  102  through a fiber optic cable located within cable  136 . 
         [0049]    For example, electrosurgical generator  102  may include a semiconductor based laser that injects photons into a fiber optic cable within cable  136 . The photons travel down the core of the fiber optic cable to jaw member  204 , where a lens injects the photons into tissue contained within jaw members  204  and  208 . Jaw member  208 , in this example, contains a lens that couples the photons back into a fiber optic cable that carries the photons to electrosurgical generator  102 . Receiving module  126  may include photodetector that measures the amount of photons that are received, and converts received photons into an electronic signal. Referring to  FIG. 2B , jaw members  218 ′ and  220 ′ may behave similarly to the jaw members  204  and  208  of  FIG. 2A , with regards to optical clarity sensor  134 . 
         [0050]    Optical clarity sensor  132  may utilize a broadband optical wavelength that has a relatively large bandwidth, e.g., a wavelength produced by a LED source. Additionally or alternatively, optical clarity sensor  134  may utilize several optical wavelengths to measure wavelength-dependant optical clarity of the tissue. 
         [0051]    For example, optical clarity sensor  134  may use a first wavelength that is more readily absorbed by water than by other molecules found within the tissue, and a second wavelength that is more readily absorbed by a particular protein found throughout human tissue. When the electrosurgical energy is applied to the tissue, the absorption characteristics of the two wavelengths may be compared. If a surgeon is applying too much pressure to the tissue causing the tissue to be “squeezed out” of the jaw members, both wavelengths should have an increase in optical transmissibility because the tissue is “thinning” between the jaw members. However, if only the first wavelength (the one that is more readily absorbed by the water) has an increase of optical transmissibility while the second wavelength maintains its optical transmissibility measurement, the reasons for the changes to the optical transmissibility of the first wavelength is more likely to be due to the evaporation of water. Therefore, optical clarity sensor  132  may use multiple optical wavelengths to communicate a optical clarity sensor measurement to electrosurgical generator  102  to measure wavelength-dependant optical clarity, e.g., by using wave division multiplexing. 
         [0052]    Referring to the drawings,  FIG. 3  is a flow chart diagram illustrating a method  300  for using an electrosurgical system that includes an electrosurgical instrument with a sensor. Method  300  starts at step  302  and includes providing an electrosurgical system  304 . The electrosurgical system of step  302  may be electrosurgical system  100  as shown in  FIGS. 1 ,  2 A,  2 B, a monopolar electrosurgical system, or a bipolar electrosurgical system. The electrosurgical system of step  304  includes an optical clarity sensor and a control component. Method  300  further includes step  306  which is activating the optical clarity sensor of the electrosurgical system (of step  304 ) to communicate with a control component of the electrosurgical system (of step  304 ). The sensor of step  306  may be sensor  128  of  FIG. 1  and includes optical clarity sensor  132 . Also, the control component may be control component  110  of  FIG. 1 . Additionally, method  300  includes monitoring the sensor data  308 . The sensor data of step  308  may be communicated via cable  136  to control component  124 , that is received by receiving module  126  of  FIG. 1 . 
         [0053]    While several embodiments of the disclosure have been shown in the drawings, it is not intended that the disclosure be limited thereto, as it is intended that the disclosure be as broad in scope as the art will allow and that the specification be read likewise. Therefore, the above description should not be construed as limiting, but merely as exemplifications of particular embodiments. Those skilled in the art will envision other modifications within the scope and spirit of the claims appended hereto.