Cutter head temperature control method, device, system and equipment of ultrasonic electrosurgical instrument

Abstract

The invention provides a tool bit temperature control method of an ultrasonic electrosurgical instrument. The method comprises the steps that an energy output mode of current operation is determined; determining an impedance value of the clamped tissue in a cutting mode of outputting the super-electric hybrid energy; determining a current cutting stage according to the change trend of the impedance value; and under the condition that the impedance value is larger than a set value, according to the current cutting stage, the output super-electric hybrid energy is reduced. According to the technical scheme, by means of the relation between the electrical impedance and the temperature of the biological tissue, a temperature measuring element and a corresponding circuit do not need to be additionally arranged, the current temperature of the biological tissue can be mastered by detecting the impedance in the output energy loop, the output energy is adjusted accordingly, and the probability of thermal damage is effectively reduced through a simple structure.

Description

Technical Field

[0001] The present disclosure relates to the field of ultrasonic electrosurgical instruments, and in particular to a method, device, system and equipment for controlling the temperature of a blade of an ultrasonic electrosurgical instrument. Background Art

[0002] Ultrasonic electrosurgery (hereinafter referred to as ultrasonic electrosurgery) combines the good cutting performance of ultrasonic scalpels and the good coagulation performance of high-frequency electrosurgery, and can achieve excellent coagulation and cutting performance in surgical operations. For example, two electrodes are set on the end effector of the ultrasonic scalpel to achieve the effects of ultrasonic scalpel and bipolar electrosurgery.

[0003] During clinical use, if the ultrasonic electrosurgical unit outputs excessive energy and generates excessive heat at the blade, it will cause irreparable thermal damage to the target tissue being treated and the surrounding non-target tissue. Therefore, preventing thermal damage to tissues caused by excessive temperatures during surgery is a very important issue. Summary of the invention

[0004] The present invention provides a method and device for controlling the temperature of a blade of an ultrasonic electrosurgical instrument, a surgical device and an electronic device, which are used to solve the problem that the existing ultrasonic electrosurgery device easily causes thermal damage to biological tissues during use.

[0005] In order to solve the above technical problems, one aspect of the present disclosure provides a method for controlling the temperature of a blade of an ultrasonic electrosurgical instrument, comprising:

[0006] determining the energy output mode of the current operation;

[0007] In the cutting mode of outputting ultra-electric hybrid energy, determining the impedance value of the clamped tissue;

[0008] Determining the current cutting stage according to the change trend of the impedance value;

[0009] When the impedance value is greater than the set value, the output superelectric hybrid energy is reduced according to the current cutting stage.

[0010] In another aspect, the present disclosure further provides a temperature control device for a blade of an ultrasonic electrosurgical instrument, comprising:

[0011] A mode determination module configured to determine an energy output mode of a current operation;

[0012] An impedance determination module is configured to determine the impedance value of the clamped tissue in a tissue cutting mode with mixed output ultra-electricity;

[0013] a cutting stage determination module, configured to determine a current cutting stage according to a change trend of the impedance value;

[0014] The control module is configured to reduce the output super-electric hybrid energy according to the current cutting stage when the impedance value is greater than a set value.

[0015] On the other hand, the present disclosure also provides an ultrasonic electrosurgery system, comprising a host end and an instrument end, wherein the host end includes an ultrasonic energy source and a high-frequency electric energy source, and also includes an impedance detection unit and a control unit, the impedance unit is used to detect the impedance in the energy circuit between the host and the blade, and the control unit is used to execute the various methods described above according to the detection results of the impedance detection unit to control the driving energy output by the ultrasonic energy source and the high-frequency energy source to the instrument end.

[0016] In another aspect, the present disclosure further provides an electronic device, comprising:

[0017] At least one processor; and a memory communicatively connected to the at least one processor; wherein the memory stores instructions executable by the at least one processor, and the instructions are executed by the at least one processor to enable the at least one processor to perform the various methods described above.

[0018] According to the technical solution disclosed in the present invention, the relationship between the electrical impedance and temperature of biological tissue is utilized, and there is no need to add additional temperature measurement elements and corresponding circuits. By detecting the impedance in the output energy circuit, the current temperature of the biological tissue can be grasped, and the output energy can be adjusted accordingly. The probability of thermal damage is effectively reduced using a simple structure. BRIEF DESCRIPTION OF THE DRAWINGS

[0019] In order to more clearly illustrate the embodiments of the present invention or the technical solutions in the prior art, the drawings required for use in the embodiments or the description of the prior art will be briefly introduced below. Obviously, the drawings described below are only some embodiments recorded in the present disclosure. For ordinary technicians in this field, other drawings can be obtained based on these drawings without paying creative work.

[0020] Figure 1 Schematic diagram of the impedance-temperature characteristic curve of biological tissue;

[0021] Figure 2 A flow chart of a method for controlling the temperature of a blade of an ultrasonic electrosurgical instrument provided in an embodiment of the present disclosure;

[0022] Figure 3 It is a schematic diagram of the acoustic impedance-time characteristic curve of general biological tissue;

[0023] Figure 4 It is a schematic diagram of the impedance-time characteristic curve of cutting pig stomach at different energy levels;

[0024] Figure 5 A flow chart of a method for controlling the temperature of a blade of an ultrasonic electrosurgical instrument provided in another embodiment of the present disclosure;

[0025] Figure 6 A block diagram of a temperature control device 200 for a blade of an ultrasonic electrosurgical instrument provided in an embodiment of the present disclosure;

[0026] Figure 7 A schematic diagram of a connection state of an ultrasonic electrosurgery system 300 provided in another embodiment of the present disclosure;

[0027] Figure 8 This is a structural block diagram of a host terminal 310 of an ultrasonic electrosurgery system provided in another embodiment of the present disclosure. DETAILED DESCRIPTION

[0028] In order to enable those skilled in the art to better understand the technical solutions in the present disclosure, the technical solutions of the present disclosure will be clearly and completely described below in conjunction with the drawings in the embodiments of the present disclosure. Obviously, the described embodiments are only part of the embodiments of the present disclosure, rather than all of the embodiments. Based on the embodiments of the present disclosure, all other embodiments obtained by ordinary technicians in this field without creative work should fall within the scope of protection of the present disclosure. In addition, for the sake of clarity, parts that are not related to the description of the exemplary embodiments are omitted in the drawings.

[0029] In the present disclosure, it should be understood that terms such as "including" or "having" are intended to indicate the existence of features, numbers, steps, behaviors, components, parts, or combinations thereof disclosed in the present disclosure, and are not intended to exclude the possibility that one or more other features, numbers, steps, behaviors, components, parts, or combinations thereof exist or are added. It should also be noted that the embodiments in the present disclosure and the features in the embodiments may be combined with each other if there is no conflict.

[0030] The ultrasonic scalpel converts high-frequency current into mechanical vibration through the ultrasonic transducer, causing the metal blade to produce mechanical vibration at a frequency of about 55.5KHz. This high-frequency mechanical friction will vaporize the water in the tissue, break the protein hydrogen bonds, disintegrate the cells, and denature the protein to form a viscous coagulation. At the same time, the friction heat generated by the vibration, coupled with the pressure formed by clamping the tissue, can achieve the purpose of cutting and stopping bleeding.

[0031] High-frequency electric knife provides high-frequency voltage and current to the local lesion to produce thermal effect, so as to achieve the effect of tissue cutting and hemostasis. When used alone, the electric knife can be used for electrocuting or electrocoagulation. Usually, the temperature for electrocuting is above 100℃, while the temperature for electrocoagulation is around 60~100℃. In actual application, the temperature control of the electric knife mainly depends on the operator's experience, and improper operation can easily cause thermal damage.

[0032] The ultrasonic electrosurgical unit combines the advantages of ultrasonic scalpel and electrosurgical unit, using the mechanical vibration of the ultrasonic scalpel to complete the cutting and the electrosurgical unit to stop bleeding by thermal coagulation. This mixed energy cutting mode reduces the risk of bleeding while cutting, and its cutting and hemostasis effects are better than those of ultrasonic scalpel or electrosurgical unit alone. The ultrasonic electrosurgical unit can also use only electrical energy for electrocoagulation, such as in the operation of blood vessel closure. Whether it is cutting or blood vessel closure, the temperature of the blade needs to be controlled to avoid thermal damage.

[0033] In order to control the temperature of the blade, one approach is to install a temperature sensor at the blade to collect the blade temperature in real time, control the output energy accordingly, and reduce the occurrence of excessive blade temperature. This method requires the installation of a temperature sensing device at the blade, the introduction of additional electronic circuits in the ultrasonic blade rod and ultrasonic transducer, and the need to change the existing component design of the ultrasonic knife, which is costly. In addition, due to the output of high-frequency electrical energy, the temperature sensing system will be severely interfered by high-power high-frequency current, the temperature measurement accuracy is low, and more isolation designs are required, which increases the complexity of the system.

[0034] The technical solution disclosed in the present invention adopts another approach, which does not require the addition of additional components. It utilizes the correspondence between bioimpedance and temperature, monitors temperature changes by detecting changes in bioimpedance, and controls the output energy accordingly, thereby achieving temperature control of the cutter head at a low cost.

[0035] Experiments have found that the electrical impedance of biological tissues will gradually increase as the temperature of cells rises, and the biological properties of the tissues will change. The electrical impedance of general biological tissues will be like this: Figure 1 The impedance-temperature characteristics shown in Figure 2 are slightly different for different biological tissues. Figure 1 As shown in Figure 2, between 37 and 60°C, as the temperature rises, the electrical impedance of biological tissues will gradually decrease and reach a minimum value around 60°C, corresponding to Figure 1 a and b in the figure; the weak bonds (hydrogen bonds, ionic bonds, hydrophobic bonds, etc.) of the spatial structure of tissue proteins will break when the temperature is higher than 60°C. Therefore, as the temperature continues to rise, the protein denatures, the biological tissue gradually becomes dry, and the impedance value of the tissue gradually increases. The coagulation temperature of biological tissue is between 60 and 90°C, corresponding to Figure 1 When the tissue temperature exceeds 70°, the tissue loses more water and becomes dry, and its impedance value rises rapidly. When the temperature continues to rise to 100°C, the impedance value rises rapidly, corresponding to Figure 1 Between points c, d, and e.

[0036] according to Figure 1The experimental results show that 60-90℃ is the stage of slow evaporation, contraction and coagulation of cell fluid. The thermal effect in this stage causes the cell fluid to slowly vaporize and the cells to contract to achieve hemostasis. This is also the appropriate temperature range for coagulation using an electric knife. When the tissue temperature reaches 100℃, the cell fluid vaporizes rapidly, causing the cells to rupture and the tissue to break. This is a temperature that needs to be avoided during the closure of blood vessels. In addition, biological tissues will carbonize at around 150℃, which is a situation that needs to be strictly avoided.

[0037] Based on this, the present disclosure provides a method for controlling the temperature of a blade of an ultrasonic electrosurgical instrument. The implementation methods of each technical solution of the present disclosure are described in detail below in conjunction with the accompanying drawings.

[0038] Figure 2 It is a flow chart of a method for controlling the temperature of a blade of an ultrasonic electrosurgical instrument provided in an embodiment of the present disclosure.

[0039] like Figure 2 As shown, the method includes S110 to S140.

[0040] S110: Determine the energy output mode of the current operation.

[0041] Ultrasonic knife can use two kinds of driving energy to perform operations, which can be set according to the needs in the application. For example, the mixed output of ultrasound + high-frequency electric energy (referred to as ultra-electric mixed output) is usually used to perform tissue cutting, and only high-frequency electric output is usually used to perform electrocoagulation operations, including hemostasis and vascular closure operations.

[0042] S120: In the cutting mode of outputting superelectric hybrid energy, determining the impedance value of the clamped tissue.

[0043] S130: Determine the current cutting stage according to the change trend of the impedance value.

[0044] S140: When the impedance value is greater than the set value, the output super-electric hybrid energy is reduced according to the current cutting stage.

[0045] By detecting the energy circuit between the host and the cutter head, the impedance value generated by the clamped tissue can be detected. In the cutting mode that outputs superelectric mixed energy, the host outputs a mixture of two energies to the cutter head to perform the cutting operation. The impedance value changes with the cutting process, showing a corresponding impedance change trend. According to the change trend of the impedance value, the current cutting stage can be determined, that is, the early, middle or late stage of the cutting. In different cutting stages, if the impedance value is greater than the set value, it indicates that the current tissue temperature exceeds the set temperature range, and it is necessary to reduce the heat absorbed by the tissue by reducing the output energy. In addition to the superelectric mixed energy cutting mode, there can also be an electrocoagulation mode that only outputs high-frequency electrical energy and a cutting mode that only outputs ultrasonic energy.

[0046] Specifically, the determined tissue impedance value includes an acoustic impedance value and an electrical impedance value. The acoustic impedance generated by the clamped tissue is detected through an ultrasonic circuit between the main unit and the cutter head; and the electrical impedance generated by the clamped tissue is detected through a high-frequency electrical circuit between the main unit and the cutter head.

[0047] The impedance detection circuit can be detected by using a dual-channel high-speed AD module of the Zhengdian Atom. The module has an on-chip sample-and-hold amplifier and adopts a multi-stage differential pipeline structure, which can prevent code loss in the entire operating temperature range. The impedance detection circuit sends the collected voltage and current information to the control unit for processing. The control unit can be an MCU and / or FPGA, which has computing power and can calculate the electrical impedance and acoustic impedance corresponding to the target tissue.

[0048] During implementation, the impedance of biological tissue can be continuously monitored to improve accuracy. The impedance value in the energy circuit can also be detected according to a set time interval, for example, once every 0.01 seconds, to obtain real-time impedance information in an efficient manner, and the output energy can be adjusted accordingly to avoid excessive temperature of the blade.

[0049] Specifically, S130 may be to determine the current cutting stage according to the change trend of the acoustic impedance value, and the cutting stage includes a first cutting stage and a second cutting stage. The first cutting stage corresponds to the cutting process, and the second cutting stage corresponds to the cutting end stage.

[0050] In surgical operations, the process of cutting biological tissues can be divided into different stages: the initial stage of cutting, the ongoing stage of cutting, and the end stage of cutting. Different cutting stages are adapted to different output energies. In some scenarios, the output energy of the super-electric knife device can be configured as follows: in the initial stage of cutting, the blade has not yet entered the tissue, and the temperature of the tissue is low. To allow the electric knife to start working quickly, the power of the electric knife can be output at a higher value, while the power of the ultrasonic knife only needs a lower value; in the ongoing stage of cutting, the blade has penetrated into the tissue and needs to cut and coagulate synchronously. At this time, the respective advantages of the ultrasonic knife and the electric knife should be utilized, and the two driving signal powers can be output at 50% of their respective total powers; when the cutting is about to be completed, the fast cutting advantage of the ultrasonic knife is fully utilized. At this time, the signal power driving the ultrasonic knife is also output at a higher value, while the signal power driving the electric knife only needs a lower value. Even if the mixed output energy is configured as above, it is inevitable that thermal damage will occur during the ongoing and late stages of cutting due to the continuous accumulation of heat absorbed by the target tissue. Therefore, it is also necessary to combine the temperature control solution for optimization.

[0051] When the blade cuts tissue, the resistance generated by the tissue changes with the state of the tissue, and this change can be reflected by the change of impedance. When the super-electric hybrid energy is output, the acoustic impedance and electrical impedance can be detected. In the embodiment of the present disclosure, the change characteristics of the acoustic impedance are used to determine the cutting stage. In addition, the electrical impedance can also be used to determine the cutting stage, and the acoustic impedance and electrical impedance can also be used together to determine the cutting stage.

[0052] The changing characteristics of acoustic impedance are as follows: at the beginning of cutting, the acoustic impedance value increases first and then decreases, and then there is a relatively long and constant stage, which is the cutting stage. At the final stage of cutting, the acoustic impedance value will increase rapidly again. Figure 3 An example of the acoustic impedance variation characteristic is given, according to Figure 3 The impedance characteristics in the acoustic impedance show that around time t1, the acoustic impedance first decreases and then changes steadily, and around time t2, the acoustic impedance increases rapidly.

[0053] The acoustic impedance characteristics are related to the tissue type and the amount of energy applied, and the overall presentation is as follows Figure 3 Therefore, the change of acoustic impedance value can be continuously monitored during the operation. If the acoustic impedance value rises first and then falls and maintains a stable change, it is determined to be the first cutting stage. If the acoustic impedance value rises rapidly after being stable, it is determined to be the second cutting stage. The first cutting stage corresponds to the cutting process, and the second cutting stage corresponds to the end of the cutting. For example, Figure 3 The period between t1 and t2 in the figure is the first cutting stage, and the period after t2 is the second cutting stage. Generally, the duration of the cutting process is related to the tissue type, and the duration of the first stage is related to the output energy. For example, Figure 4 In the animal experiment results data given, the pig stomach was cut with 5 energy levels respectively, and the impedance changes during the cutting process were recorded. It can be found that the energy levels 1 and 2 are more suitable, and the impedance changes of the protein structure from denaturation to separation are more obvious, and the first stage lasts for about 12 seconds.

[0054] S140 may specifically be: if it is the first cutting stage and the electrical impedance value is greater than the threshold Zu1, then the output ultrasonic energy is reduced; if it is the first cutting stage and the electrical impedance value is greater than the threshold Ze1, then the output high-frequency electrical energy is reduced.

[0055] If it is the second cutting stage and the electrical impedance value is greater than the threshold Zu2, the output high-frequency electrical energy is reduced; if it is the second cutting stage and the electrical impedance value is greater than the threshold Ze2, the output ultrasonic energy is reduced.

[0056] Herein, reducing the output energy includes temporarily stopping the output of the energy.

[0057] Thresholds Zu1, Ze1, Zu2, and Ze2 are determined according to the type of tissue, and Zu1>Ze1, Zu2>Ze2. This means that in the first cutting stage, if the temperature continues to rise, the ultrasonic energy is reduced first and then the high-frequency electric energy is reduced. In the second cutting stage, if the temperature continues to rise, the high-frequency electric energy is reduced first and then the ultrasonic energy is reduced.

[0058] The above threshold selection for different types of tissues can be determined through experiments. For example, different types of tissues such as fat, liver, and small intestine may be suitable for different threshold settings. Generally, the threshold of the first cutting stage corresponds to the impedance value of the tissue of this type at 70-85°C, and the threshold of the second stage corresponds to the impedance value of the tissue of this type at 90-115°C. Figure 1 From the above, Zu1 or Ze1 is Figure 1 The impedance values ​​corresponding to points a and c in the figure are combined with the determined first cutting stage. When the impedance value reaches the threshold, it can only correspond to the temperature of point c. At this time, the tissue is at the boundary of coagulation and in the cutting stage. Appropriately reducing the ultrasonic energy will not affect the cutting process. Therefore, the ultrasonic energy can be reduced to reduce the energy output by the cutter head. If the impedance continues to increase, it means that the temperature continues to rise. Then the high-frequency electric energy is reduced to reduce the heat absorbed by the clamped tissue. Zu2 or Ze2 is Figure 1 The impedance value corresponding to point d in the figure. When the impedance value reaches the threshold, the temperature of the tissue has entered the temperature range of cell rupture. At this time, the cutting is completed. Therefore, the heat output by the blade can be quickly reduced by reducing the output high-frequency electrical energy. If the impedance continues to increase, it means that the temperature continues to rise, and the ultrasonic energy is reduced again.

[0059] By setting different thresholds to adjust the ultrasonic energy and high-frequency electrical energy, more precise temperature control can be achieved while ensuring the progress of the operation.

[0060] Furthermore, the method of the embodiment of the present disclosure further includes operations S150 and S160 based on the above process.

[0061] Figure 5 This is a flow chart of a method for controlling the temperature of a blade of an ultrasonic electrosurgical instrument provided by another embodiment of the present disclosure, wherein operations S110 to S140 may be implemented with reference to the aforementioned embodiment, and there is no limitation on the order of operations S150 and S160 and operations S120 to S140.

[0062] S150: In the electrocoagulation mode that outputs only high-frequency electrical energy, determine the electrical impedance value of the clamped blood vessel.

[0063] S160: If the electrical impedance value is greater than the threshold value Z3, the output of high-frequency electrical energy is stopped.

[0064] In surgeries that operate on blood vessels, there are mainly electrocoagulation hemostasis and vascular closure operations, which utilize the electrocoagulation function of high-frequency electrosurgery. For example, when blood vessels are closed, when alternating current with a frequency of approximately 300-550kHz passes through vascular tissue with biological impedance, the thermal effect generated causes the protein in the tissue to denature. At the same time, the pressure applied to the vascular tissue causes the vascular lumen to adhere together to form a closure. Electrosurgical vascular closure technology based on the principle of electrothermal effect is a newer vascular closure technology, but the potential thermal damage to the tissue or nerves adjacent to the closure position caused by the heat generated during the operation is still a problem that needs to be solved. The electrocoagulation hemostasis process also faces the same problem. According to Figure 1 The thermal conductivity of biological tissues and their characteristics of changing with temperature can be used to determine the temperature of blood vessels by detecting the electrical impedance value of blood vessels, preventing the electrical impedance value from exceeding the threshold value Z3, thereby avoiding damage to tissues caused by excessive temperature and continuous heating.

[0065] In this embodiment, the threshold Z3 can be set at the electrical impedance value when the surface temperature of the blood vessel reaches about 80°C, to prevent the temperature of the inner wall of the blood vessel from being too high and causing irreversible damage, resulting in failure of blood vessel closure. Figure 1 curve, Z3 corresponds to the temperature of point d in the impedance-temperature curve of the blood vessel.

[0066] Here according to Figure 4 The experimental data shown gives examples of the above threshold settings: in the cutting of pig stomach, the minimum impedance value is detected to be around 200Ω. According to the impedance temperature curve, Zu1 is set to 280Ω, Ze1 is set to 300Ω, Zu2 is set to 380Ω, and Ze2 is set to 400Ω. According to the experimental data of pig blood vessels, Z3 can be set to 400Ω. When actually applied to the human body, corresponding adjustments can also be made. Accordingly, the host device can allow the operator to manually set the impedance threshold.

[0067] According to the control method of the embodiment of the present disclosure, the relationship between the electrical impedance and temperature of biological tissue is utilized. There is no need to add additional temperature measurement elements and corresponding circuits. By detecting the impedance in the output energy circuit, the current temperature of the biological tissue can be grasped, and the output energy can be adjusted accordingly. The probability of thermal damage is effectively reduced using a simple structure.

[0068] Based on the same inventive concept, the embodiment of the present disclosure also provides a temperature control device 200 for a blade of an ultrasonic electrosurgical instrument, as shown below. Figure 6 The control device 200 according to the embodiment of the present disclosure is described.

[0069] Figure 62 is a block diagram of a temperature control device 200 for a blade of an ultrasonic electrosurgical instrument provided in an embodiment of the present disclosure. The control device 200 can be implemented as part or all of an electronic device through software, hardware, or a combination of both.

[0070] like Figure 6 As shown, the control device 200 includes a mode determination module 210, an impedance determination module 220, a cutting stage determination module 230, and a control module 240. The control device 200 can execute the various methods described above.

[0071] The mode determination module 210 is configured to determine the energy output mode of the current operation.

[0072] The impedance determination module 220 is configured to determine the impedance value of the clamped tissue in the tissue cutting mode of the hybrid output ultra-electric.

[0073] The cutting stage determination module 230 is configured to determine the current cutting stage according to the variation trend of the impedance value.

[0074] The control module 240 is configured to reduce the output super-electric hybrid energy according to the current cutting stage when the impedance value is greater than the set value.

[0075] Specifically, the impedance determination module 220 is configured to determine the acoustic impedance value and electrical impedance value of the clamped tissue in the tissue cutting mode of the mixed output ultrasonic; the cutting stage determination module 230 is specifically configured to determine the current cutting stage according to the change trend of the acoustic impedance value; the control module 240 is configured to: if it is the first cutting stage and the electrical impedance value is greater than the threshold Zu1, then reduce the output ultrasonic energy; if it is the first cutting stage and the electrical impedance value is greater than the threshold Ze1, then reduce the output high-frequency electrical energy. The control module 240 is also configured to: if it is the second cutting stage and the electrical impedance value is greater than the threshold Zu2, then reduce the output high-frequency electrical energy; if it is the second cutting stage and the electrical impedance value is greater than the threshold Ze2, then reduce the output high-frequency electrical energy.

[0076] Furthermore, the impedance determination module 220 is also configured to determine the electrical impedance value of the clamped blood vessel in the electrocoagulation mode of only outputting high-frequency electrical energy, and the control module 240 is also configured to stop outputting high-frequency electrical energy if the electrical impedance value is greater than the threshold value Z3.

[0077] According to the control device of the embodiment of the present disclosure, the relationship between the electrical impedance and temperature of biological tissue is utilized, and no additional temperature measurement element and corresponding circuit are required. By detecting the impedance in the output energy circuit, the current temperature of biological tissue can be grasped, and the output energy can be adjusted accordingly, thereby effectively reducing the probability of thermal damage with a simple structure. The control device can be independently applied to ultrasonic electrosurgery equipment or combined with an existing main control system, and the present disclosure does not limit this.

[0078] On this basis, another embodiment of the present disclosure further provides an ultrasonic electrosurgery system 300, such as Figure 7 shown.

[0079] Figure 7 is a schematic diagram of a connection state of an ultrasonic electrosurgery system 300 provided in another embodiment of the present disclosure, Figure 8 It is a structural block diagram of the host side 310.

[0080] like Figure 7 , 8 As shown, the ultrasonic electrosurgery system 300 includes a host end 310 and an instrument end 320. The host end 310 includes an ultrasonic energy source 311 and a high-frequency electric energy source 312, and also includes an impedance detection unit 313 and a control unit 314. The impedance unit 313 is used to detect the impedance in the energy circuit between the host end and the instrument end blade. The control unit 314 is used to execute the various methods described above according to the detection result of the impedance detection unit to control the driving ability of the ultrasonic energy source 311 and the high-frequency energy source 312 to output to the instrument end 320. The instrument end 320 is connected to the host end 310 through an ultrasonic transducer 330. The ultrasonic transducer 330 converts the electric energy into mechanical vibration to drive the blade to vibrate.

[0081] The specific operations performed by the detection unit 313 and the control unit 314 in this embodiment can be referred to the description in the aforementioned embodiment, and will not be repeated here.

[0082] On this basis, an embodiment of the present disclosure also provides an electronic device, comprising: at least one processor; and a memory communicatively connected to the at least one processor; wherein the memory stores instructions executable by the at least one processor, and the instructions are executed by the at least one processor to enable the at least one processor to execute the various methods described above.

[0083] The above describes specific embodiments of the present invention. Other embodiments are within the scope of the appended claims. In some cases, the actions or steps recorded in the claims can be performed in an order different from that in the embodiments and still achieve the desired results. In addition, the processes depicted in the accompanying drawings do not necessarily require the specific order or continuous order shown to achieve the desired results. In some embodiments, multitasking and parallel processing are also possible or may be advantageous.

[0084] Each embodiment in the present disclosure is described in a progressive manner, and the same or similar parts between the embodiments can be referred to each other, and each embodiment focuses on the differences from other embodiments. In particular, for the embodiments of the control device, surgical equipment, and electronic equipment, since they are basically similar to the embodiments of the aforementioned control method, the description is relatively simple, and the relevant parts can be referred to the partial description of the method embodiment.

[0085] The above description is only an embodiment of the present disclosure and is not intended to limit the present disclosure. For those skilled in the art, the present disclosure may have various changes and variations. Any modification, equivalent substitution, improvement, etc. made within the spirit and principle of the present disclosure shall be included in the scope of the claims of the present disclosure.

Claims

1. A method for controlling the temperature of a blade of an ultrasonic electrosurgical instrument, characterized in that: include: determining the energy output mode of the current operation; In the cutting mode of outputting ultra-electric hybrid energy, determining the impedance value of the clamped tissue; Determining the current cutting stage according to the change trend of the impedance value; When the impedance value is greater than the set value, the output superelectric hybrid energy is reduced according to the current cutting stage.

2. The method according to claim 1, characterized in that The impedance value includes an acoustic impedance value and an electrical impedance value, and determining the current cutting stage according to the change trend of the impedance value includes: The current cutting stage is determined according to the variation trend of the acoustic impedance value, and the cutting stage includes a first cutting stage and a second cutting stage.

3. The method according to claim 2, characterized in that When the impedance value is greater than the set value, the output superelectric hybrid energy is reduced according to the current cutting stage, including: If it is the first cutting stage and the electrical impedance value is greater than the threshold Zu1, the output ultrasonic energy is reduced; if it is the first cutting stage and the electrical impedance value is greater than the threshold Ze1, the output high-frequency electrical energy is reduced.

4. The method according to claim 3, characterized in that The method also includes: If it is the second cutting stage and the electrical impedance value is greater than the threshold Zu2, the output high-frequency electrical energy is reduced; if it is the second cutting stage and the electrical impedance value is greater than the threshold Ze2, the output ultrasonic energy is reduced.

5. The method according to claim 3, characterized in that: The thresholds Zu1, Ze1, Zu2, and Ze2 are determined according to the type of tissue, and Zu1>Ze1, Zu2>Ze2.

6. The method according to claim 2, characterized in that The step of determining the acoustic impedance value and the electrical impedance value of the clamped tissue comprises: The acoustic impedance generated by the clamped tissue is detected through the ultrasonic circuit between the main unit and the cutter head; The electrical impedance generated by the clamped tissue is detected through a high-frequency electrical circuit between the main unit and the knife head.

7. The method according to claim 1, characterized in that The method further comprises: In the electrocoagulation mode of outputting only high-frequency electrical energy, the electrical impedance value of the clamped blood vessel is determined; If the electrical impedance value is greater than the threshold value Z3, the output of high-frequency electrical energy is stopped.

8. A temperature control device for a blade of an ultrasonic electrosurgical instrument, characterized in that: include: A mode determination module configured to determine an energy output mode of a current operation; An impedance determination module is configured to determine the impedance value of the clamped tissue in a tissue cutting mode with mixed output ultra-electricity; a cutting stage determination module, configured to determine a current cutting stage according to a change trend of the impedance value; The control module is configured to reduce the output super-electric hybrid energy according to the current cutting stage when the impedance value is greater than a set value.

9. An ultrasonic electrosurgery system, comprising a host end and an instrument end, characterized in that: The host end includes an ultrasonic energy source and a high-frequency electric energy source, and also includes an impedance detection unit and a control unit. The impedance unit is used to detect the impedance in the energy circuit between the host end and the cutting head of the instrument end, and the control unit is used to execute the method described in any one of claims 1 to 7 according to the detection result of the impedance detection unit to control the driving energy output by the ultrasonic energy source and the high-frequency energy source to the instrument end.

10. An electronic device, comprising: at least one processor; as well as, a memory communicatively connected to the at least one processor; wherein, The memory stores instructions that can be executed by the at least one processor, and the instructions are executed by the at least one processor to enable the at least one processor to perform the method according to any one of claims 1 to 7.

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