System And Method For Measuring Initial Tissue Impedance

Abstract

An electrosurgical system and method are disclosed. The system includes an electrosurgical generator adapted to supply electrosurgical energy to tissue. The generator is further adapted to supply an electrical signal having at least one substantially constant value to tissue to determine initial tissue impedance response. The generator includes sensor circuitry adapted to continuously monitor initial tissue impedance response, wherein the initial tissue impedance response includes one of an initial impedance, an impedance drop, an impedance minimum and a first impedance rise. The generator also includes a microprocessor adapted to generate at least one tissue parameter based as a function of the initial impedance, the impedance drop, the impedance minimum and the first impedance rise. The system also includes an electrosurgical instrument including at least one active electrode adapted to apply electrosurgical energy to tissue for treatment.

Description

BACKGROUND

1. Technical Field

The present disclosure relates to a system and method for performing electrosurgical procedures. More particularly, the present disclosure relates to a system and method for measuring tissue properties during tissue sealing procedures.

2. Background of Related Art

Electrosurgery involves application of high radio frequency electrical current to a surgical site to cut, ablate, coagulate, cauterize, desiccate or seal tissue. Tissue or vessel sealing is a process of liquefying the collagen, elastin and ground substances in the tissue so that they reform into a fused mass with significantly-reduced demarcation between the opposing tissue structures. Cauterization involves the use of heat to destroy tissue and coagulation is a process of desiccating tissue wherein the tissue cells are ruptured and dried.

In bipolar electrosurgery, one of the electrodes of the hand-held instrument functions as the active electrode and the other as the return electrode. The return electrode is placed in close proximity to the active electrode such that an electrical circuit is formed between the two electrodes (e.g., electrosurgical forceps). In this manner, the applied electrical current is limited to the body tissue positioned between the electrodes. When the electrodes are sufficiently separated from one another, the electrical circuit is open and thus inadvertent contact with body tissue with either of the separated electrodes does not cause current to flow.

A forceps is a pliers-like instrument which relies on mechanical action between its jaws to grasp, clamp and constrict vessels or tissue. So-called “open forceps” are commonly used in open surgical procedures whereas “endoscopic forceps” or “laparoscopic forceps” are, as the name implies, are used for less invasive endoscopic surgical procedures. Electrosurgical forceps (open or endoscopic) utilize mechanical clamping action and electrical energy to effect hemostasis on the clamped tissue. The forceps includes electrosurgical sealing plates which apply the electrosurgical energy to the clamped tissue. By controlling the intensity, frequency and duration of the electrosurgical energy applied through the sealing plates to the tissue, the surgeon can coagulate, cauterize and/or seal tissue. Selecting the appropriate energy parameters during the sealing procedure allows for efficient application of energy to tissue. Thus, a need exists to develop an electrosurgical system which effectively and consistently seals tissue.

SUMMARY

The present disclosure relates to a system and method for performing electrosurgical procedures. The system includes an electrosurgical generator and an instrument (e.g., electrosurgical forceps). The generator supplies an initial interrogatory signal at constant voltage to tissue and measures initial tissue impedance response. Thereafter, the generator analyzes the initial tissue impedance response and selects corresponding treatment parameters that are used to select corresponding output of the generator.

According to one aspect of the present disclosure an electrosurgical system is disclosed. The system includes an electrosurgical generator adapted to supply electro surgical energy to tissue. The generator is further adapted to supply an electrical signal having at least one substantially constant value to tissue to determine initial tissue impedance response. The generator includes sensor circuitry adapted to continuously monitor tissue impedance response, wherein the tissue impedance response includes an initial impedance, an impedance drop, an impedance minimum and a first impedance rise. The generator also includes a microprocessor adapted to generate at least one tissue treatment parameter as a function of one of the initial impedance, the impedance drop, the impedance minimum and the first impedance rise. The system also includes an electrosurgical instrument including at least one active electrode adapted to apply electrosurgical energy to tissue for treatment.

According to another aspect of the present disclosure, a method for performing electrosurgical procedures is disclosed. The method includes the steps of supplying an electrical signal having at least one substantially constant value to tissue to determine initial tissue impedance response, wherein the initial tissue impedance response includes at least one of an initial impedance, an impedance drop, an impedance minimum and a first impedance rise. The method also includes the step of continuously monitoring initial tissue impedance response. The method further includes the step of generating at least one tissue treatment parameter as a function of one of the initial impedance, the impedance drop, the impedance minimum and the first impedance rise.

According to a further aspect of the present disclosure, an electrosurgical generator is disclosed. The electrosurgical generator includes an RF output stage adapted to supply electrosurgical energy to tissue and to supply an electrical signal having at least one substantially constant value to tissue to determine initial tissue impedance response. The generator also includes sensor circuitry adapted to continuously monitor initial tissue impedance response, wherein the initial tissue impedance response includes at least one of an initial impedance, an impedance drop, an impedance minimum and a first impedance rise. The generator further includes a microprocessor adapted to generate at least one tissue treatment parameter as a function of the initial impedance, the impedance drop, the impedance minimum and the first impedance rise.

BRIEF DESCRIPTION OF THE DRAWINGS

Various embodiments of the present disclosure are described herein with reference to the drawings wherein:

FIG. 1 is a perspective view of an electrosurgical system according to the present disclosure;

FIG. 2 is a side, partial internal view of an endoscopic forceps according to the present disclosure;

FIG. 3 is a schematic block diagram of a generator system according to the present disclosure;

FIG. 4 is a flow diagram illustrating a method according to the present disclosure; and

FIGS. 5A-B are illustrative graphs showing impedance values over time.

DETAILED DESCRIPTION

Particular embodiments of the present disclosure are described hereinbelow with reference to the accompanying drawings. In the following description, well-known functions or constructions are not described in detail to avoid obscuring the present disclosure in unnecessary detail. Those skilled in the art will understand that the invention according to the present disclosure may be adapted for use with either monopolar or bipolar electrosurgical systems

FIG. 1 shows an endoscopic bipolar electrosurgical system according to the present disclosure which includes an electrosurgical forceps 10. Those skilled in the art will understand that the invention according to the present disclosure may be adapted for use with either an endoscopic instrument as shown in FIG. 1 or an open instrument. More particularly, forceps 10 generally includes a housing 21, a handle assembly 40, a rotating assembly 80, and a trigger assembly 70 which mutually cooperate with the end effector assembly 100 to grasp and treat tissue. The forceps 10 also includes a shaft 12 which has a distal end 14 that mechanically engages the end effector assembly 100 and a proximal end 16 which mechanically engages the housing 21 proximate the rotating assembly 80. Handle assembly 40 includes a fixed handle 50 and a movable handle 42. Handle 42 moves relative to the fixed handle 50 to actuate the end effector assembly 100 and enable a user to grasp and manipulate tissue. Electrosurgical RF energy is supplied to the forceps 10 by generator 20 via a supply line connected to the active electrode and returned through a return line connected to the return electrode. The supply and return lines are enclosed within a cable 23.

The generator 20 includes input controls (e.g., buttons, activators, switches, touch screen, etc.) for controlling the generator 20. In addition, the generator 20 may include one or more display screens for providing the surgeon with a variety of output information (e.g., intensity settings, treatment complete indicators, etc.). The controls allow the surgeon to adjust the RF energy, waveform, and other parameters to achieve the desired waveform suitable for a particular task (e.g., coagulating, tissue sealing, intensity setting, etc.). It is also envisioned that the forceps 10 may include a plurality of input controls which may be redundant with certain input controls of the generator 20. Placing the input controls at the forceps 10 allows for easier and faster modification of RF energy parameters during the surgical procedure without requiring interaction with the generator 20.

The end effector assembly 100 includes opposing jaw members 110 and 120 having electrically conductive sealing plate 112 and 122, respectively, attached thereto for conducting electrosurgical energy through tissue. More particularly, the jaw members 110 and 120 move in response to movement of the handle 42 from an open position to a closed position. In open position the sealing plates 112 and 122 are disposed in spaced relation relative to one another. In a clamping or closed position the sealing plates 112 and 122 cooperate to grasp tissue and apply electrosurgical energy thereto. Further details relating to one envisioned endoscopic forceps is disclosed in commonly-owned U.S. application Ser. No. 10/474,169 entitled “VESSEL SEALER AND DIVIDER” the entire contents of which is incorporated by reference herein.

The jaw members 110 and 120 are activated using a drive assembly (not shown) enclosed within the housing 21. The drive assembly cooperates with the movable handle 42 to impart movement of the jaw members 110 and 120 from the open position to the clamping or closed position. Examples of a handle assemblies are shown and described in the above identified application as well as commonly-owned U.S. application Ser. No. 10/369,894 entitled “VESSEL SEALER AND DIVIDER AND METHOD MANUFACTURING SAME” and commonly owned U.S. application Ser. No. 10/460,926 entitled “VESSEL SEALER AND DIVIDER FOR USE WITH SMALL TROCARS AND CANNULAS” which are both hereby incorporated by reference herein in their entirety.

Jaw members 110 and 120 also include insulators 116 and 126 which together with the outer, non-conductive plates of the jaw members 110 and 120 are configured to limit and/or reduce many of the known undesirable effects related to tissue sealing, e.g., flashover, thermal spread and stray current dissipation.

The handle assembly 40 of this particular disclosure may include a four-bar mechanical linkage which provides a unique mechanical advantage when sealing tissue between the jaw members 110 and 120. For example, once the desired position for the sealing site is determined and the jaw members 110 and 120 are properly positioned, handle 42 may be compressed fully to lock the electrically conductive sealing plates 112 and 122 in a closed position against the tissue. The details relating to the inter-cooperative relationships of the inner-working components of forceps 10 are disclosed in the above-cited commonly-owned U.S. patent application Ser. No. 10/369,894. Another example of an endoscopic handle assembly which discloses an off-axis, lever-like handle assembly, is disclosed in the above-cited U.S. patent application Ser. No. 10/460,926.

As shown in FIGS. 1-2, the forceps 10 also includes a trigger 70 which advances a knife (not explicitly shown) disposed within the end effector assembly 100. Once a tissue seal is formed, the user activates the trigger 70 to separate the tissue along the tissue seal. Knife preferably includes a sharpened edge for severing the tissue held between the jaw members 110 and 120 at the tissue sealing site. A longitudinally-oriented channel (not explicitly shown) is defined in an electrically conductive sealing plate 112 extending from the proximal end to the distal end thereof. The channel facilitates longitudinal reciprocation of the knife along a preferred cutting plane to effectively and accurately separate the tissue along a formed tissue seal.

The forceps 10 also includes a rotating assembly 80 mechanically associated with the shaft 12 and the drive assembly (not shown). Movement of the rotating assembly 80 imparts similar rotational movement to the shaft 12 which, in turn, rotates the end effector assembly 100. Various features along with various electrical configurations for the transference of electrosurgical energy through the handle assembly 20 and the rotating assembly 80 are described in more detail in the above-mentioned commonly-owned U.S. patent application Ser. Nos. 10/369,894 and 10/460,926.

As best seen with respect to FIGS. 1 and 2, the end effector assembly 100 attaches to the distal end 14 of shaft 12. The jaw members 110 and 120 are pivotable about a pivot 160 from the open to closed positions upon relative reciprocation, i.e., longitudinal movement, of the drive assembly (not shown). Again, mechanical and cooperative relationships with respect to the various moving elements of the end effector assembly 100 are further described by example with respect to the above-mentioned commonly-owned U.S. patent application Ser. Nos. 10/369,894 and 10/460,926.

It is envisioned that the forceps 10 may be designed such that it is fully or partially disposable depending upon a particular purpose or to achieve a particular result. For example, end effector assembly 100 may be selectively and releasably engageable with the distal end 14 of the shaft 12 and/or the proximal end 16 of the shaft 12 may be selectively and releasably engageable with the housing 21 and handle assembly 40. In either of these two instances, the forceps 10 may be either partially disposable or reposable, such as where a new or different end effector assembly 100 or end effector assembly 100 and shaft 12 are used to selectively replace the old end effector assembly 100 as needed.

FIG. 3 shows a schematic block diagram of the generator 20 having a controller 24, a high voltage DC power supply 27 (“HVPS”) and an RF output stage 28. The HVPS 27 provides high voltage DC power to an RF output stage 28 which then converts high voltage DC power into RF energy and delivers the RF energy to the active electrode 24. In particular, the RF output stage 28 generates sinusoidal waveforms of high frequency RF energy. The RF output stage 28 is configured to generate a plurality of waveforms having various duty cycles, peak voltages, crest factors, and other parameters. Certain types of waveforms are suitable for specific electrosurgical modes. For instance, the RF output stage 28 generates a 100% duty cycle sinusoidal waveform in cut mode, which is best suited for dissecting tissue and a 25% duty cycle waveform in coagulation mode, which is best used for cauterizing tissue to stop bleeding.

The controller 24 includes a microprocessor 25 operably connected to a memory 26 which may be volatile type memory (e.g., RAM) and/or non-volatile type memory (e.g., flash media, disk media, etc.). The microprocessor 25 includes an output port which is operably connected to the HVPS 27 and/or RF output stage 28 allowing the microprocessor 25 to control the output of the generator 20 according to either open and/or closed control loop schemes.

A closed loop control scheme is a feedback control loop wherein sensor circuitry 22, which may include a plurality of sensors measuring a variety of tissue and energy properties (e.g., tissue impedance, tissue temperature, output current and/or voltage, etc.), provides feedback to the controller 24. Such sensors are within the purview of those skilled in the art. The controller 24 then signals the HVPS 27 and/or RF output stage 28 which then adjust DC and/or RF power supply, respectively. The controller 24 also receives input signals from the input controls of the generator 20 or the forceps 10. The controller 24 utilizes the input signals to adjust power outputted by the generator 20 and/or performs other control functions thereon.

FIG. 4 shows a method according to the present disclosure for controlling output of the generator in response to monitored tissue impedance. In step 300, the forceps 10 is positioned to grasp tissue using jaw members 110 and 120. In step 310, the sealing plates 112 and 122 are activated and are in contact with the tissue but may not be fully closed. A constant voltage signal is applied for a predetermined period of time (e.g., first 2 to 3 seconds) to determine initial tissue impedance response. This occurs prior to treatment of tissue via electrosurgical energy. Other electrical signals having one or more substantially constant values, such as constant power, current, and energy, may also be applied to tissue to determine initial tissue impedance response.

The initial tissue impedance response describes the natural tissue state and is used in subsequent calculations to determine a variety of seal parameters (e.g., duration of energy application, amount of energy to be applied, etc.). The impedance is monitored by the sensor circuitry 22. In particular, voltage and current signals are monitored and corresponding impedance values are calculated with the sensor circuitry 22 and/or with the microprocessor 25. Power and other energy properties may also be calculated based on collected voltage and current signals. The microprocessor 25 stores the collected voltage, current, and impedance within the memory 26.

Exemplary impedance response is illustrated in FIGS. 5A-B which show a graph of impedance versus time. In particular, FIG. 5A shows changes in impedance during an entire tissue sealing procedure. As shown, the initial tissue impedance drops reaching a minimum impedance then rises at a first rate and then continues rising at a second rate which is generally slower than the first rate. FIG. 5B shows in more detail initial tissue impedance response that is represented by an impedance dip 400 that includes an initial impedance 402 followed by an impedance drop 404 that reaches an impedance minimum 406 and subsequently transitions into a first impedance rise 408.

In step 320, the initial tissue impedance response values, i.e., initial impedance 402, the impedance drop 404 (e.g., rate of drop), the impedance minimum 406 and the first impedance rise 40 (e.g., rate of rise) are recorded and analyzed. Impedance measurements as low as 50 Ohms or below are detected. The recorded initial tissue impedance response values provide detailed information concerning tissue between the jaws. For instance, the impedance drop 404 may be used to calculate the relationship between the gap distance between the electrodes and the amount of energy being supplied to tissue. Further, the impedance drop 404 may also be used to determine the type of tissue being grasped and the hydration levels thereof.

In step 330, the initial tissue impedance response values are used to determine treatment parameters (e.g., pressure to be applied to tissue, duration of energy application, amount of energy to be supplied, target impedance trajectory, etc.) for subsequent treatment of the tissue. This may be accomplished by populating a look up table that may be stored in the memory 26 with the impedance values. Based on these values corresponding tissue treatment parameters are loaded. The microprocessor 25 utilizes the loaded tissue treatment parameters to adjust output of the generator 20 as well as rate of closure and pressure exerted by the jaw members 110 and 120 on the tissue.

Those skilled in the art will appreciate that the measurement of initial impedance values and analysis thereof may be performed on a real-time basis providing for a system which is adaptive to various types of tissue.

While several embodiments of the disclosure have been shown in the drawings and/or discussed herein, 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.

Claims

1. An electrosurgical system comprising: an electrosurgical generator configured to supply electrosurgical energy and an electrical signal having at least one substantially constant value to tissue to determine an initial tissue impedance response;wherein, in response to application of the electrosurgical energy, the generator controls the tissue impedance response such that the tissue exhibits a non-linear impedance profile having a first phase wherein the initial tissue impedance response drops to reach a minimum impedance, a second phase wherein the tissue impedance rises at a first rate, and a third phase wherein the tissue impedance rises at a second rate, the second rate being less than the first rate and the second rate stabilizing over a period of time.

2. The electrosurgical system as in claim 1, wherein the initial tissue impedance response is used to determine an amount of the electrosurgical energy to the tissue prior to tissue treatment.

3. The electrosurgical system as in claim 1, wherein the electrosurgical generator further includes sensor circuitry adapted to continuously monitor the initial tissue impedance response.

4. The electrosurgical system as in claim 1, wherein the electrosurgical generator further includes a controller adapted to generate at least one tissue treatment parameter as a function of the initial tissue impedance response.

5. The electrosurgical system as in claim 4, wherein the controller is in electrical communication with a memory to store collected impedance and tissue information, the memory including at least a look up table for storing collected impedance values from a plurality of uses of the electrosurgical system.

6. The electrosurgical system as in claim 4, wherein the controller is further adapted to adjust an output of the electrosurgical generator based on the at least one tissue treatment parameter.

7. The electrosurgical system as in claim 4, wherein the at least one tissue treatment parameter is selected from a group consisting of pressure to be applied to tissue, duration of energy application, amount of energy to be supplied, and target impedance trajectory.

8. The electrosurgical system as in claim 1, wherein an electrosurgical instrument is configured to be connected to the electrosurgical generator for transmitting electrosurgical energy to be supplied to the tissue.

9. The electrosurgical system as in claim 8, wherein the electrosurgical instrument is an electrosurgical forceps including at least one shaft member having an end effector assembly disposed at a distal end thereof, the end effector assembly including jaw members movable from a first position in spaced relation relative to one another to at least one subsequent position wherein the jaw members cooperate to grasp the tissue therebetween.

10. The electrosurgical system as in claim 9, wherein the electrosurgical forceps includes a sealing plate attached to each of the jaw members in opposing relation thereto, the sealing plates adapted to connect to the electrosurgical generator such that the sealing plates communicate electrosurgical energy through the tissue held therebetween.

11. An electrosurgical generator adapted to supply electrosurgical energy to tissue, the electrosurgical generator comprising: an RF output stage configured to supply an electrical signal having at least one substantially constant value to tissue to determine an initial tissue impedance response;sensor circuitry adapted to continuously monitor the initial tissue impedance response; anda controller adapted to generate at least one tissue treatment parameter as a function of the initial tissue impedance response;wherein, in response to application of the electrosurgical energy, the generator controls the tissue impedance response such that the tissue exhibits a non-linear impedance profile having a first phase wherein the initial tissue impedance response drops to reach a minimum impedance, a second phase wherein the tissue impedance rises at a first rate, and a third phase wherein the tissue impedance rises at a second rate, the second rate being less than the first rate and the second rate stabilizing over a period of time.

12. The electrosurgical generator as in claim 11, wherein the initial tissue impedance response is used to determine an amount of the electrosurgical energy to the tissue prior to tissue treatment.

13. The electrosurgical generator as in claim 11, wherein the electrosurgical generator is connected to an electrosurgical instrument including at least one active electrode adapted to apply electro surgical energy to the tissue.

14. The electrosurgical generator as in claim 11, wherein the controller is further adapted to adjust an output of the electrosurgical generator based on the at least one tissue treatment parameter.

15. The electrosurgical generator as in claim 11, wherein the at least one tissue treatment parameter is selected from a group consisting of pressure to be applied to tissue, duration of energy application, amount of energy to be supplied, and target impedance trajectory.

16. The electrosurgical generator as in claim 11, wherein the controller is in electrical communication with a memory to continuously store collected impedance and tissue information, the memory including at least a look up table for storing collected impedance values from a plurality of uses of an electrosurgical instrument.

17. The electrosurgical generator as in claim 16, wherein the electrosurgical instrument is an electrosurgical forceps for sealing the tissue.

18. The electrosurgical generator as in claim 17, wherein the electrosurgical forceps includes at least one shaft member having an end effector assembly disposed at a distal end thereof, the end effector assembly including jaw members movable from a first position in spaced relation relative to one another to at least one subsequent position wherein the jaw members cooperate to grasp the tissue therebetween.

19. The electrosurgical generator as in claim 18, wherein the electrosurgical forceps includes a sealing plate attached to each of the jaw members in opposing relation thereto, the sealing plates adapted to connect to the electrosurgical generator such that the sealing plates communicate electrosurgical energy through the tissue held therebetween.

20. The electrosurgical generator as in claim 11, wherein the constant value of the electrical signal is selected from a group consisting of constant voltage, constant current, constant power, and constant energy.