CN116831719A

CN116831719A - Electrosurgical device and energy output control method thereof

Info

Publication number: CN116831719A
Application number: CN202210292283.6A
Authority: CN
Inventors: 代建; 周康; 任健; 黄旭; 左鹏飞
Original assignee: Shenzhen Mindray Bio Medical Electronics Co Ltd
Current assignee: Shenzhen Mindray Bio Medical Electronics Co Ltd
Priority date: 2022-03-23
Filing date: 2022-03-23
Publication date: 2023-10-03

Abstract

The application provides electrosurgical equipment and an energy output control method thereof. The controller obtains the minimum value of the impedance according to the impedance of the target tissue obtained by the measuring unit at a plurality of different moments; after the minimum value of the impedance and/or the impedance meet the preset condition, the rising rate of the impedance is obtained according to the impedance of the target tissue, whether the rising rate of the impedance is larger than or equal to a preset rising rate threshold value is judged, and if yes, the energy output module is controlled to reduce the voltage rising rate of the energy signal. According to the application, through the minimum value of the impedance and/or the condition that the impedance meets the preset condition and the impedance rising rate is greater than or equal to the rising rate threshold value, when tissue moisture begins to evaporate, the rising rate of the output voltage is timely controlled to avoid the uncontrolled impedance rising rate, and the output of the electrosurgical equipment is accurately controlled, so that tissue fusion is promoted, and a better coagulation effect is obtained.

Description

Electrosurgical device and energy output control method thereof

Technical Field

The application relates to the field of medical appliances, in particular to electrosurgical equipment and an energy output control method thereof.

Background

The electrotome is a device which introduces high-frequency (> 300 KHZ) alternating current into human tissues, and realizes the functions of cutting and hemostasis of the tissues and coagulation of large blood vessels by utilizing the generated thermal effect, thus being widely applied to surgical operations.

The tissue fusion and the large blood vessel coagulation are realized by transmitting high-frequency energy to the tissue or the blood vessel through a special bipolar electrocoagulation device, generating a thermal effect to denature and inactivate elastin and collagen in the tissue, and liquefying and recombining the elastin and collagen into a fusion substance, thereby achieving the aim of closing the blood vessel to stop bleeding; therefore, the accurate control of the energy in the coagulation process is very important, is a necessary condition for obtaining consistent and reliable coagulation effect, and can cause unpredictable effects if the output energy is not controlled properly, for example, the impedance change is very rapid when the tissue moisture begins to evaporate, and the judgment of the end point is very important for the control of the coagulation process; if the end is too late, the coagulation time is too long, the output energy is too much, eschar is generated at the operation position, heat damage is caused, and the operation efficiency is reduced. If the end is too early, the tissue fusion can not be effectively caused, the hemostatic effect is reduced, the damage to the patient is caused, and the operation time is prolonged.

Currently, intelligent bipolar devices generally adopt phased control, and impedance rising speed needs to be controlled (not too fast or too slow, and with a certain opportunity) during the period, so that overheating or energy shortage of tissues is avoided.

Different manufacturers control the impedance rising rate at different time points, and the time points represent the time when the tissue moisture begins to evaporate rapidly; the choice of this timing for impedance rate control is important because the impedance changes relatively rapidly after the water begins to evaporate, and improper timing of rate control can easily cause excessive or insufficient heating of the tissue. For the control of the impedance rising rate, the main method is currently target impedance curve feedback control, and the output voltage is feedback controlled by the difference between the target impedance and the actual measured impedance. However, the target impedance curve is not necessarily very accurate, and the characteristics (e.g., water content) of different tissues are different, and the use scenarios are also diverse, which results in poor accuracy of output control of the existing electrosurgical devices.

Disclosure of Invention

The application mainly provides electrosurgical equipment and an energy output control method thereof, aiming at improving the accuracy of output control and improving the effect.

One embodiment provides an electrosurgical device comprising:

the energy output module is used for generating an energy signal and outputting the energy signal to a target tissue;

the measuring unit is used for measuring the electrical parameter in real time and obtaining the impedance of the target tissue according to the electrical parameter; the electrical parameter is an electrical parameter in a circuit formed by the energy output module and the target tissue;

a controller for:

obtaining an minimum value of the impedance according to the impedance of the target tissue obtained by the measuring unit at a plurality of different moments, and judging whether the minimum value of the impedance meets a preset extremum condition; and/or judging whether the impedance meets the preset extremum condition according to the impedance of the target tissue obtained in real time by the measuring unit;

if the minimum value of the impedance and/or the impedance meets the preset extremum condition, the rising rate of the impedance is obtained according to the impedance of the target tissue, whether the rising rate of the impedance is greater than or equal to a preset rising rate threshold value is judged, and if yes, the energy output module is controlled to reduce the voltage increasing rate of the energy signal.

In the case of the electrosurgical device described above,

the preset extremum condition corresponding to the minimum value of the impedance comprises: the minimum value is smaller than a preset extreme value threshold, or the minimum value is smaller than the initial impedance, and the minimum value is always the minimum value of the impedance in a preset time period after the minimum value appears;

the preset extremum condition corresponding to the impedance comprises: the impedance is less than a preset extremum threshold, or the impedance is less than the initial impedance, and the impedance is always the minimum value of the impedance within a preset time period after the impedance appears.

In an embodiment, the controller is further configured to, before the impedance of the target tissue obtained by the measurement unit at a plurality of different times,:

controlling the energy output module to output an initial pulse signal, and acquiring initial impedance of the target tissue, which is measured by the measurement unit based on the initial pulse signal; wherein the extremum threshold is less than the initial impedance;

and according to the initial impedance, obtaining a corresponding voltage increasing rate, controlling the energy output module to generate and output an energy signal, wherein the voltage of the energy signal increases according to the voltage increasing rate.

In the electrosurgical device provided in an embodiment, the controller is further configured to control the energy output module to stop generating the energy signal and/or stop outputting the energy signal when the impedance of the target tissue meets a preset end condition; wherein, the preset ending condition comprises: the impedance is greater than or equal to a preset ending impedance threshold, and/or the rate of rise of the impedance is greater than or equal to a preset ending rate threshold.

In an electrosurgical device provided by an embodiment, the controller is further configured to control the voltage of the energy signal output by the energy output module to be maintained at a preset voltage threshold after the voltage of the energy signal increases to the voltage threshold.

In an electrosurgical device provided by an embodiment, the controller obtains a corresponding voltage increase rate according to the initial impedance, controls the energy output module to generate and output an energy signal, and the voltage of the energy signal increases according to the voltage increase rate, including:

determining a target impedance interval in which the initial impedance is located in a plurality of preset impedance intervals according to the initial impedance; each preset impedance interval is pre-associated with a voltage increasing rate, and the impedance interval and the voltage increasing rate are in direct proportion or positive correlation;

and controlling the energy output module to generate and output an energy signal according to the voltage increasing rate related to the target impedance interval, wherein the voltage of the energy signal increases according to the voltage increasing rate related to the target impedance interval.

In one embodiment, the electrosurgical device is provided wherein the output instrument comprises a dual electrode.

An embodiment provides the electrosurgical device, further comprising a display;

the controller is further configured to: and obtaining the change trend of the electric parameter along with the time according to the electric parameter measured by the measuring unit in real time, and displaying the change trend on the display.

In the electrosurgical device provided in an embodiment, the trend of the change of the electrical parameter with time is a change curve chart of the change of the electrical parameter with time; the controller is further configured to: and marking the moment when the energy output module starts to generate an energy signal and the moment when the voltage of the energy signal increases to a preset voltage threshold value on the change curve chart.

One embodiment provides an energy output control method of an electrosurgical device, including:

obtaining the minimum value of the impedance according to the impedance of the target tissue obtained at a plurality of different moments, and judging whether the minimum value of the impedance meets a preset extremum condition; and/or judging whether the impedance meets the preset extremum condition according to the impedance of the target tissue;

and if the minimum value of the impedance and/or the impedance meets the preset extremum condition, obtaining the rising rate of the impedance according to the impedance of the target tissue, judging whether the rising rate of the impedance is greater than or equal to a preset rising rate threshold, and if so, reducing the voltage increasing rate of the energy signal applied to the target tissue.

An embodiment provides a computer-readable storage medium having stored thereon a program executable by a processor to implement a method as described above.

The electrosurgical device and the energy output control method thereof according to the above embodiments include an energy output module, a measurement unit, and a controller. The controller obtains the minimum value of the impedance according to the impedance of the target tissue obtained by the measuring unit at a plurality of different moments; after the minimum value of the impedance and/or the impedance meet the preset condition, the rising rate of the impedance is obtained according to the impedance of the target tissue, whether the rising rate of the impedance is larger than or equal to a preset rising rate threshold value is judged, and if yes, the energy output module is controlled to reduce the voltage rising rate of the energy signal. According to the application, through the minimum value of the impedance and/or the condition that the impedance meets the preset condition and the impedance rising rate is greater than or equal to the rising rate threshold value, when tissue moisture begins to evaporate, the rising rate of the output voltage is timely controlled to avoid the uncontrolled impedance rising rate, and the output of the electrosurgical equipment is accurately controlled, so that tissue fusion is promoted, and a better coagulation effect is obtained.

Drawings

FIG. 1 is a block diagram of one embodiment of an electrosurgical device in accordance with the present application;

FIG. 2 is a flow chart of an embodiment of a method for controlling energy output of an electrosurgical device in accordance with the present application;

FIG. 3 is a flow chart of another embodiment of a method for controlling energy output of an electrosurgical device in accordance with the present application;

fig. 4 is a schematic diagram of a voltage profile of an energy signal and an impedance profile of a target tissue during an electrocoagulation process.

Detailed Description

The application will be described in further detail below with reference to the drawings by means of specific embodiments. Wherein like elements in different embodiments are numbered alike in association. In the following embodiments, numerous specific details are set forth in order to provide a better understanding of the present application. However, one skilled in the art will readily recognize that some of the features may be omitted, or replaced by other elements, materials, or methods in different situations. In some instances, related operations of the present application have not been shown or described in the specification in order to avoid obscuring the core portions of the present application, and may be unnecessary to persons skilled in the art from a detailed description of the related operations, which may be presented in the description and general knowledge of one skilled in the art.

Furthermore, the described features, operations, or characteristics of the description may be combined in any suitable manner in various embodiments. Also, various steps or acts in the method descriptions may be interchanged or modified in a manner apparent to those of ordinary skill in the art. Thus, the various orders in the description and drawings are for clarity of description of only certain embodiments, and are not meant to be required orders unless otherwise indicated.

The numbering of the components itself, e.g. "first", "second", etc., is used herein merely to distinguish between the described objects and does not have any sequential or technical meaning. The term "coupled" as used herein includes both direct and indirect coupling (coupling), unless otherwise indicated.

Electrosurgical devices have become an indispensable device in the operating room, which can utilize high frequency electrical energy to achieve the surgical purposes of cutting, separating, hemostasis, etc. of tissue. Electrosurgical devices are particularly diverse types such as electrotomes, vascular electrocoagulation devices, and the like.

As shown in fig. 1, the electrosurgical apparatus provided by the present application includes: an energy output module 10, a measurement unit 40 and a controller 30.

The energy output module 10 is used to generate an energy signal and output the energy signal to the target tissue. The energy signal may be, for example, a high frequency alternating current, which may have a frequency between 300khz and 5 Mhz.

The measurement unit 40 is used for measuring an electrical parameter in real time, wherein the electrical parameter is an electrical parameter in a circuit formed by the energy output module 10 and the target tissue. For example, the electrical parameter in the circuit may be the electrical parameter at the output of the energy output module 10, i.e. the electrical parameter of the energy signal, or the electrical parameter of the target tissue. Typically, the electrical parameter at the output of the energy output module 10 in this circuit is the electrical parameter of the target tissue. The electrical parameter may be voltage and/or current. The measurement unit 40 is also used to derive the impedance of the target tissue from the electrical parameters.

The controller 30 is configured to obtain the impedance of the target tissue obtained by the measurement unit 40 at a plurality of different times, and obtain a minimum value of the impedance according to the impedance at the plurality of different times; judging whether the minimum value of the impedance meets a preset extremum condition, if so, obtaining the rising rate of the impedance according to the impedance of the target tissue, judging whether the rising rate of the impedance is larger than or equal to a preset rising rate threshold value, and if so, controlling the energy generator 110 to reduce the voltage rising rate of the energy signal. And/or, the controller 30 is configured to obtain the impedance of the target tissue obtained in real time by the measurement unit 40, and determine whether the impedance meets a preset extremum condition according to the impedance of the target tissue; if so, the energy generator 110 is controlled to reduce the voltage increase rate of the energy signal.

According to the application, through the two conditions that the minimum value or the impedance meets the preset condition and then the rising rate of the impedance is greater than or equal to the rising rate threshold value, when tissue moisture begins to evaporate, the rising rate of the output voltage is timely controlled to avoid out-of-control of the rising rate of the impedance, and the output of electrosurgical equipment is accurately controlled, so that tissue fusion is promoted, and a better coagulation effect is obtained.

In this embodiment, energy output module 10 includes an energy generator 110 and an output instrument 120.

The energy generator 110 is used to generate an energy signal, for example, for outputting a voltage and delivering a current, which in this embodiment is high frequency, which may be between 300khz-5 Mhz. The energy generator 110 may include an amplitude adjustable switching power supply and a high frequency power amplifier. The 220V/50Hz low-voltage low-frequency current is converted into high-frequency alternating current with the frequency of 0.3-5 MHz through the frequency conversion and transformation of the energy generator 110. The output of the energy generator 110 is connected to the output device 120, and the energy signal generated by the energy generator is output to the output device 120.

The output device 120 is configured to output an energy signal to the target tissue, and may be a bipolar electrode (e.g., a conventional bipolar electrode, a plasma bipolar electrode, a smart bipolar electrode, etc.), such as a bipolar electrocoagulation device, etc., or a single electrode (e.g., a conventional monopolar electrode, an argon plasma, etc.), such as illustrated by a bipolar electrode, where current flows from one electrode to the other electrode through the target tissue. The double electrodes can realize the electric coagulation (clamp coagulation) by clamping human tissues, and can also realize the electric coagulation (leaning coagulation) by leaning against the human tissues. For example, the output device 120 outputs the high frequency current generated by the energy generator 110 to the contacted target tissue to heat the target tissue, thereby achieving separation or coagulation of the body tissue for the purpose of cutting or hemostasis. The high-frequency alternating current energy only generates a thermal effect after acting on the tissues, achieves the effects of cutting and coagulating the tissues, and does not generate electric shock risks to human bodies.

The control 30 controls the energy output of the electrosurgical device, as shown in fig. 4, in three stages: a start phase (initial phase) (1), a tissue dehydration phase (2) and a tissue fusion phase (3). The control modes corresponding to each stage are different, and the specific process can be shown in fig. 2, and the method comprises the following steps:

the specific process by which the controller 30 controls the energy output of the electrosurgical device may be as shown in fig. 2, including the steps of:

in step 1, in the beginning stage, the controller 30 triggers the energy output module 10 to output an initial pulse signal, and obtains an initial impedance measured by the measurement unit 40 based on the initial pulse signal. Specifically, controller 30 controls energy generator 110 to generate an initial pulse signal and output by output device 120 to the target tissue. The measurement unit 40 measures the resulting initial impedance R0 based on the initial pulse signal. The initial pulse signal is used to measure an initial impedance R0 that does not substantially alter the physical characteristics of the target tissue. The initial pulse signal may be a small amplitude voltage signal (e.g., 30 v) of a very short duration (e.g., 100 ms). After the initial pulse signal is applied to the target tissue through the output device 120, the measurement unit 40 measures an electrical parameter of the target tissue, calculates an initial impedance R0 based on the electrical parameter, for example, measures a voltage and a current of the initial pulse signal, divides the measured voltage by the current to obtain the initial impedance R0, and may measure only a current (current in a circuit) of the target tissue, and divides a theoretical voltage of the initial pulse signal by the measured current to obtain the initial impedance R0 of the target tissue. The initial impedance R0 of the target tissue may reflect the size, type, moisture content, etc. of the target tissue. After acquiring the initial impedance R0 of the target tissue, the measurement unit 40 transmits to the controller 30, and then proceeds to the next stage (tissue dehydration stage).

The start phase may be triggered by a user, for example, the user pressing a designated switch, thereby entering the start phase.

Step 2, the controller 30 controls the energy output module 10 to generate an energy signal of voltage step-up. The controller 30 measures the electrical parameters of the target tissue in real time through the measurement unit 40. The initial pulse signal of the initial stage has no influence on the target tissue basically, so that the electric parameters of the target tissue can be measured in real time from the tissue dehydration stage. The present embodiment is described taking as an example electrical parameters including voltage and current. The voltage of the energy signal output by the output device 120 is the voltage applied to the target tissue, and the embodiment is described taking the measurement unit 40 as an example for measuring the voltage (the voltage of the energy signal) output by the output device 120 and measuring the current corresponding to the voltage (the current in the circuit), where the measurement unit 40 calculates the impedance in real time according to the electrical parameter, and the real-time impedance of the target tissue is obtained by dividing the real-time measured voltage by the real-time measured current. In some embodiments, the real-time impedance of the target tissue may also be obtained by dividing the theoretical voltage of the energy signal by the current measured in real-time.

Specifically, during the tissue dehydration phase, the controller 30 obtains a corresponding voltage increase rate based on the initial impedance, thereby controlling the energy generator 110 to generate an energy signal having a voltage that increases at the voltage increase rate. The controller 30 may control the energy generator 110 to intermittently generate the energy signal, or may control the energy generator 110 to continuously generate the energy signal, the latter is described as an example in this embodiment. The voltage increase rate corresponding to the initial impedance may be one or more (two or more), for example, the controller 30 is preset with a plurality of impedance intervals, and each impedance interval is pre-associated with one voltage increase rate or a plurality of voltage increase rates; when a plurality of voltage increasing rates are associated with one impedance interval in advance, each voltage increasing rate is also associated with a maintaining time period (namely, the impedance interval is associated with a voltage increasing rate curve in advance), when the voltage of the subsequent energy signal increases according to the voltage increasing rate corresponding to the initial impedance, the voltage of the energy signal can be sequentially increased according to the plurality of voltage increasing rates associated with the impedance interval, the time of increasing the voltage of the energy signal according to the voltage increasing rate is the associated maintaining time period, namely, the voltage of the energy signal increases according to the voltage increasing rate A in the maintaining time period A, and then increases according to the voltage increasing rate B in the maintaining time period B … …; the greater the impedance value, the greater the voltage increase rate associated with the impedance interval, e.g., the impedance interval is proportional or positively correlated to the voltage increase rate. In this embodiment, taking an example that one impedance section is associated with one voltage increasing rate in advance, the controller 30 determines, according to the initial impedance R0, a target impedance section in which the initial impedance R0 is located in a plurality of preset impedance sections, that is, the target impedance section is one of the plurality of impedance sections. For example, one impedance interval is [0,300] ohms (ohm), with an associated voltage increase rate of 100V/s, i.e., the corresponding voltage increase rate is 100V/s for an initial impedance R0 < 300 Ω; another impedance interval is >500 ohms with an associated voltage increase rate of 120V/s, i.e. the initial impedance R0>500 Ω corresponds to a voltage increase rate of 120V/s.

Controller 30 controls energy generator 110 to generate an energy signal having a voltage that increases according to the rate of voltage increase associated with the target impedance interval and is applied to the target tissue via output device 120 according to the rate of voltage increase associated with the target impedance interval. According to the embodiment, different voltage increasing rates are adopted according to different initial impedances, so that the method can be well adapted to different human tissues, and the success rate and effect of coagulation are improved.

In the prior art, because the control is not very accurate, the coagulation operation needs to be carried out for a plurality of times to realize the coagulation of the tissue, namely, the coagulation is repeated until the aim is fulfilled, which needs to depend on the experience of doctors. The application can realize the coagulation of the tissue only by one-time electrocoagulation, so that the dehydration stage and the fusion stage are important. When the dehydration stage is dehydrated, the temperature is too high and scabs are formed during constant pressure output in the subsequent fusion stage, and when the dehydration stage is not dehydrated, high power is required during constant pressure output. The embodiment adopts different voltage increasing rates according to different initial impedances, can be well adapted to different human tissues, has good dehydration effect, and can form a constant temperature environment in target tissues during subsequent constant voltage output.

Different manufacturers control the impedance rising rate at different time, and when the tissue reacts (when the tissue impedance is rising to the initial impedance again after falling), the impedance is falling, and the rising slope exceeds the threshold again; the control timing is the timing when the tissue moisture starts to evaporate quickly, and the impedance rate control is important to select the control timing, because the impedance change is relatively rapid after the moisture starts to evaporate, and the overheating or insufficient heating of the tissue is easily caused by the improper rate control timing. In burst pressure tests, it is found that there are some situations, such as strong elasticity of blood vessels or wall thickness of blood vessels, where the initial impedance is high, and especially for a coagulation-dependent scene, the impedance will not rise for a long period of time, and the actual impedance change may deviate greatly from the ideal impedance change curve; in this case, if the subsequent control is performed according to the conventional impedance feedback control, control hysteresis is likely to occur, resulting in failure of the coagulation. Meanwhile, the water frying in the condensation process causes interference, a transient sudden change of sudden impedance rise is generated at the moment, and the control advance is judged possibly by means of the existing judgment mode of target impedance feedback control.

The application can accurately control the output of the electrosurgical equipment by judging the impedance and the rising rate of the impedance so as to adjust the voltage rising rate. There are various ways to implement this process, as shown in fig. 2 and 3, and several examples are described below.

In the mode shown in fig. 2, as shown in step 3, in the tissue dehydration stage, the controller 30 acquires the impedance of the target tissue calculated by the measurement unit 40 at a plurality of different times, and obtains the minimum value of the impedance according to the impedance at the plurality of different times. In this embodiment, the measurement unit 40 continuously calculates the impedance, and the controller 30 obtains the impedance in real time, so as to obtain the minimum value of the impedance according to the impedance at different moments.

Step 4, the controller 30 determines whether the minimum value of the impedance meets a preset extremum condition, where the extremum condition is a condition for determining that the minimum value is a minimum value, for example, the extremum condition is: the minimum value is smaller than a preset extreme value threshold value, and the extreme value threshold value is smaller than the initial impedance R0. The extremum threshold may be derived from the initial impedance R0 minus an empirical value ranging within 0,50 ohms. As another example, the extremum condition is: the minimum value is smaller than the initial impedance R0, and is always the minimum value of the impedance within a preset period after the minimum value occurs. After the minimum value of the impedance satisfies the preset extremum condition, the measurement unit 40 continues to calculate to obtain the impedance, and the controller 30 obtains the rising rate Δr/Δtof the impedance according to the impedance calculated by the measurement unit 40, for example, calculates the difference value between the impedance at the previous and the next time, and divides the absolute value of the difference value by the time interval between the two times, thereby obtaining the rising rate of the impedance at the current time.

Step 5, the controller 30 determines whether the rising rate of the impedance is greater than or equal to the preset rising rate threshold, if yes, the energy generator 110 is controlled to decrease the voltage increasing rate of the output energy signal, i.e. decrease the voltage increasing rate of the energy signal applied to the target tissue, for example, decrease the voltage increasing rate from 100V/s to 50V/s. The purpose of reducing the rate of voltage increase of the energy signal is not to cause the impedance to rise too fast, so the rate of rise of the impedance can be reduced below a predetermined rate of rise threshold. The rate of voltage increase for the energy signal may be reduced once instead of continuously. The ramp-up rate threshold may be set as desired or may be an empirical value, such as 150 ohms/second (ohm/s).

As described above, the impedance rising rate is controlled by detecting that the impedance of the tissue has fallen to the minimum value and then the rising rate of the impedance has reached the rising rate threshold; so as to ensure that when the moisture of the tissues begins to evaporate, the output voltage increasing rate is controlled in time to avoid the uncontrolled impedance rising rate and promote the tissue fusion, thereby obtaining better coagulation effect.

In the manner shown in fig. 3, as shown in step 3', during the tissue dehydration phase, the controller 30 acquires the impedance of the target tissue calculated in real time by the measurement unit.

And step 4', the controller 30 judges whether the impedance meets the preset extremum condition according to the impedance of the target tissue calculated by the measuring unit in real time. The extremum condition may be: the impedance is smaller than a preset extreme value threshold value, and the extreme value threshold value is smaller than the initial impedance; the extremum condition may also be: the impedance is smaller than the initial impedance R0, and the impedance is always the minimum value of the impedance within a preset period of time after the occurrence of the impedance. After the impedance satisfies the preset extremum condition, the measurement unit 40 continues to calculate the impedance, and the controller 30 obtains the rising rate Δr/Δtof the impedance according to the impedance calculated by the measurement unit 40.

In step 5, after the impedance meets the preset extremum condition, the controller 30 determines whether the rising rate of the impedance is greater than or equal to the preset rising rate threshold, and if so, controls the energy generator 110 to reduce the voltage increasing rate of the output energy signal. The specific process is the same as the above manner, and will not be described here.

In some embodiments, the controller 30 may further determine whether the minimum value of the impedance meets the corresponding preset extremum condition, determine whether the impedance meets the corresponding preset extremum condition, and execute the step 5 if both the minimum value and the preset extremum condition are met.

After the above steps, step 6 (not shown in the figure) may be further included: after the voltage of the energy signal or the impedance of the target tissue reaches a certain condition, the controller 30 controls the voltage of the energy signal output by the energy generator 110 to be maintained at the voltage threshold. The voltage threshold may be set as required, for example, one of 120V to 160V, and this embodiment is illustrated with a voltage threshold of 150V. The voltage of 150V is output to the target tissue at a constant voltage, so that a good coagulation effect can be achieved.

Specifically, the controller 30 further obtains the impedance calculated by the measuring unit 40 in real time, and after the impedance calculated by the measuring unit 40 in real time meets the preset impedance condition, the next stage (tissue fusion stage) is entered, so as to control the energy generator 110 to increase the voltage of the generated energy signal to the preset voltage threshold, and maintain the voltage threshold for a preset period of time. The preset time period may be set as required, and in this embodiment, the preset time period is long enough for the energy output module to stop generating the energy signal and/or stop outputting the energy signal. That is, in the present embodiment, the voltage of the energy signal output by the energy generator 110 is constant to the voltage threshold during the tissue fusion phase. The preset impedance condition is that the impedance is greater than or equal to a preset first impedance threshold value, and/or the rising rate of the impedance is greater than or equal to a preset first rate threshold value. The first impedance threshold may be related to the initial impedance R0, e.g. the first impedance threshold is equal to the sum of the initial impedance R0 and a preset first tested value, i.e. the first impedance threshold = initial impedance r0+ first tested value, which may be summed up by an experimental process, e.g. the first tested value may be 300 Ω, it being seen that the first impedance threshold is larger than the initial impedance R0. The first rate threshold is greater than the ramp-up rate threshold, which may also be an empirical value, such as one of 150-200 ohms/second.

Of course, the controller 30 may enter the next stage (tissue fusion stage) after the voltage of the energy signal increases to the preset voltage threshold, so as to control the voltage of the energy signal generated by the energy generator 110 to be maintained at the voltage threshold for a preset period of time, as shown in fig. 4, so that the output voltage and the impedance of the target tissue are both maintained at a constant value. The voltage of the energy signal may be obtained from the energy generator 110 or may be obtained by measuring the voltage of the target tissue by the measuring unit 40.

In the prior art, electrosurgical equipment also adopts phased control, and controllable and good-consistency coagulation effect is realized by performing phased energy regulation and control on the tissue fusion process. In the initial stage, measuring initial impedance of tissue, and calculating and outputting electric parameters such as target voltage; during the tissue desiccation and fusion phase, the energy output is controlled by the rate of rise of the target impedance. The application discovers that the low protective explosion pressure is sometimes caused in the process of electric coagulation, and the conditions of incomplete coagulation and the like can sometimes occur if the coagulation surface is not dried in the case of contact coagulation. The constant-temperature environment is maintained by constant-pressure output in the tissue fusion stage, so that protein fusion is promoted to be firmer, and the coagulation effect is better. And the voltage output by the constant voltage is a preset voltage threshold, the threshold can limit the energy signal in the tissue dehydration stage, even if the voltage of the energy signal in the tissue dehydration stage does not reach the voltage threshold, the voltage of the energy signal is directly raised to the voltage threshold after entering the tissue fusion stage, and then the constant voltage is output, so that no matter what condition occurs in the electrocoagulation process, a proper constant temperature environment can be provided for the target tissue.

After the above steps, step 7 (not shown in the figure) may be further included: the controller 30 controls the energy output module 10 to stop generating the energy signal and/or to stop outputting the energy signal, i.e., to end the electrocoagulation, when the current impedance of the target tissue satisfies the preset end condition. In particular, the controller 30 may control the energy generator 110 to cease generating the energy signal and/or may control the output device 120 to cease outputting the energy signal.

The preset end condition may be set as required, for example, it may include: in this step, after entering the tissue fusion stage, the controller 30 may obtain the impedance measured by the measuring unit 40 in real time, and determine whether the real-time impedance is greater than or equal to the preset ending impedance threshold, if so, control the energy output module 10 to stop generating the energy signal and/or stop outputting the energy signal. The constant pressure output can ensure that the target tissue is in a constant temperature environment, and the end condition can ensure that the heat energy obtained by the target tissue is not too high, so that the electric coagulation is accurately and properly ended.

The end condition may also include a rate of rise of impedance greater than or equal to a predetermined end rate threshold, or may include a duration of the tissue fusion phase greater than or equal to a predetermined time (e.g., one of 4-6 s), in which case, one of the three end conditions described above is met to end the electrocoagulation. In some embodiments, the impedance is greater than or equal to a preset ending impedance threshold, the rate of rise of the impedance is greater than or equal to a preset ending rate threshold, and the duration of the tissue fusion phase is greater than or equal to a preset time, and multiple of these three conditions may be considered an ending condition. The ending impedance threshold may be determined by the initial impedance R0 of the target tissue, with the larger the initial impedance R0, the larger its corresponding ending impedance threshold, e.g., the ending impedance threshold is proportional or positively correlated with the initial impedance R0. In some embodiments, the ending impedance threshold may also be derived from the initial impedance R0 and an empirical value, e.g., ending impedance threshold = r0+ a second empirical value; wherein the second empirical value may be within [ 300, 500 ] ohms. The ending impedance threshold is greater than the first impedance threshold, and the ending impedance threshold may also be equal to a sum of the first impedance threshold and a preset third empirical value, which may be, for example, 100 ohms. The end rate threshold is greater than or equal to the first rate threshold, which may also be an empirical value, such as 300 ohms/s.

The electrosurgical device may also include a display. The controller 60 may obtain a trend of the electrical parameter over time according to the electrical parameter measured by the measuring unit 40 in real time, and then send the trend to the display, and display the trend through the display. The trend of the change of the electrical parameter with time is a graph of the change of the electrical parameter with time, as shown in fig. 4, which shows a voltage change curve (shown by a solid line) and an impedance change curve (shown by a broken line). Therefore, the user can conveniently and quickly see the change condition of various current parameters and can quickly judge or intervene. The controller 30 may also mark on the variation graph the time at which the energy generator starts generating the energy signal and the time at which the voltage of the energy signal increases to a preset voltage threshold, as indicated by the vertical dashed line between (1) and (2) and the vertical dashed line between (2) and (3).

Reference is made to various exemplary embodiments herein. However, those skilled in the art will recognize that changes and modifications may be made to the exemplary embodiments without departing from the scope herein. For example, the various operational steps and components used to perform the operational steps may be implemented in different ways (e.g., one or more steps may be deleted, modified, or combined into other steps) depending on the particular application or taking into account any number of cost functions associated with the operation of the system.

Additionally, as will be appreciated by one of skill in the art, the principles herein may be reflected in a computer program product on a computer readable storage medium preloaded with computer readable program code. Any tangible, non-transitory computer readable storage medium may be used, including magnetic storage devices (hard disks, floppy disks, etc.), optical storage devices (CD-ROMs, DVDs, blu-Ray disks, etc.), flash memory, and/or the like. These computer program instructions may be loaded onto a general purpose computer, special purpose computer, or other programmable data processing apparatus to produce a machine, such that the instructions which execute on the computer or other programmable data processing apparatus create means for implementing the functions specified. These computer program instructions may also be stored in a computer-readable memory that can direct a computer or other programmable data processing apparatus to function in a particular manner, such that the instructions stored in the computer-readable memory produce an article of manufacture including means which implement the function specified. The computer program instructions may also be loaded onto a computer or other programmable data processing apparatus to cause a series of operational steps to be performed on the computer or other programmable apparatus to produce a computer implemented process such that the instructions which execute on the computer or other programmable apparatus provide steps for implementing the functions specified.

While the principles herein have been shown in various embodiments, many modifications of structure, arrangement, proportions, elements, materials, and components, which are particularly adapted to specific environments and operative requirements, may be used without departing from the principles and scope of the present disclosure. The above modifications and other changes or modifications are intended to be included within the scope of this document.

The foregoing detailed description has been described with reference to various embodiments. However, those skilled in the art will recognize that various modifications and changes may be made without departing from the scope of the present disclosure. Accordingly, the present disclosure is to be considered as illustrative and not restrictive in character, and all such modifications are intended to be included within the scope thereof. Also, advantages, other advantages, and solutions to problems have been described above with regard to various embodiments. The benefits, advantages, solutions to problems, and any element(s) that may cause any benefit, advantage, or solution to occur or become more pronounced are not to be construed as a critical, required, or essential feature. The terms "comprises," "comprising," or any other variation thereof, are intended to cover a non-exclusive inclusion, such that a process, method, article, or apparatus that comprises a list of elements does not include only those elements but may include other elements not expressly listed or inherent to such process, method, system, article, or apparatus. Furthermore, the term "couple" and any other variants thereof are used herein to refer to physical connections, electrical connections, magnetic connections, optical connections, communication connections, functional connections, and/or any other connection.

Claims

1. An electrosurgical apparatus, comprising:

a controller for:

2. The electrosurgical device of claim 1, wherein the surgical instrument is configured to,

3. The electrosurgical device of claim 2, wherein the controller is further configured to, prior to the impedance of the target tissue obtained at a plurality of different times from the measurement unit:

4. Electrosurgical apparatus according to claim 1 or 2, wherein the controller is further configured to control the energy output module to cease generating the energy signal and/or to cease outputting the energy signal when the impedance of the target tissue meets a preset end condition; wherein, the preset ending condition comprises: the impedance is greater than or equal to a preset ending impedance threshold, and/or the rate of rise of the impedance is greater than or equal to a preset ending rate threshold.

5. The electrosurgical device of claim 1 or 2, wherein the controller is further configured to control the voltage of the energy signal output by the energy output module to remain at a preset voltage threshold after the voltage of the energy signal increases to the voltage threshold.

6. The electrosurgical device of claim 3, wherein the controller obtains a corresponding rate of voltage increase from the initial impedance, controls the energy output module to generate and output an energy signal, the voltage of the energy signal increasing according to the rate of voltage increase, comprising:

7. Electrosurgical apparatus according to claim 1 or claim 2, wherein the output instrument comprises a double electrode.

8. The electrosurgical device of claim 5, further comprising a display;

9. The electrosurgical device of claim 8, wherein the trend of the change in the electrical parameter over time is a plot of the change in the electrical parameter over time; the controller is further configured to: and marking the moment when the energy output module starts to generate an energy signal and the moment when the voltage of the energy signal increases to a preset voltage threshold value on the change curve chart.

10. A method of controlling energy output of an electrosurgical device, comprising:

11. A computer readable storage medium having stored thereon a program executable by a processor to implement the method of claim 10.