Methods, devices, systems, and apparatuses for tip temperature control of ultrasonic electrosurgical instruments

Abstract

The disclosure provides a method for controlling the temperature of a blade of an ultrasonic electrosurgical instrument, comprising: determining the current energy output mode of operation; in the cutting mode outputting ultracapacitor hybrid energy, determining the impedance value of the clamped tissue; determining the current cutting stage according to the change trend of the impedance value; in the case where the impedance value is greater than a set value, reducing the output ultracapacitor hybrid energy according to the current cutting stage. According to the technical scheme of the disclosure, the relationship between the electrical impedance of biological tissue and temperature is utilized, without the need for additional temperature measurement elements and corresponding circuits, by detecting the impedance in the output energy loop, the temperature of the current biological tissue can be grasped, and the output energy is adjusted accordingly, thereby effectively reducing the probability of thermal damage with 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 apparatus for controlling the temperature of the blade of an ultrasonic electrosurgical instrument. BACKGROUND

[0002] An ultrasonic electrosurgical instrument (hereinafter referred to as an ultrasonic electrotome) combines the good cutting performance of an ultrasonic knife and the good coagulation performance of a high-frequency electrotome, and can achieve good coagulation and cutting performance in a surgical operation. For example, two electrodes are provided on the end effector of the ultrasonic knife to achieve the functions of the ultrasonic knife and the bipolar electrotome.

[0003] In clinical use, if the output energy of the ultrasonic electrotome is excessive, too much heat is generated in the blade part, which can cause irreparable thermal damage to the target tissue and the surrounding non-target tissue during processing. Therefore, it is very important to prevent thermal damage to tissue caused by excessive temperature during surgery. SUMMARY

[0004] The present disclosure provides a method, device, surgical apparatus and electronic apparatus for controlling the temperature of the blade of an ultrasonic electrosurgical instrument to solve the problem that the existing ultrasonic electrotome is prone to cause thermal damage to biological tissue in use.

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

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

[0007] determining the impedance value of the clamped tissue in the cutting mode of mixed output of ultrasonic and electric energy;

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

[0009] reducing the output of the mixed ultrasonic and electric energy according to the current cutting stage when the impedance value is greater than a set value.

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

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

[0012] an impedance determination module configured to determine the impedance value of the clamped tissue in the cutting mode of mixed output of ultrasonic and electric energy;

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

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

[0015] In another aspect, the present disclosure also provides an ultrasonic electrosurgical system including a host end and an instrument end, wherein the host end includes an ultrasonic energy source and a high-frequency electric energy source, and further includes an impedance detection unit for detecting impedance in an energy loop between the host and the blade head, and a control unit for performing various methods as described above 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.

[0016] In another aspect, the present disclosure also provides an electronic device including:

[0017] at least one processor; and a memory connected with the at least one processor in communication; 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 various methods as described above.

[0018] According to the technical solution of the present disclosure, by utilizing the relationship between the electrical impedance of biological tissue and temperature, without additional temperature measurement elements and corresponding circuits, the current temperature of biological tissue can be grasped by detecting the impedance in the output energy loop, and the output energy is adjusted accordingly, thereby effectively reducing the probability of thermal damage with a simple structure. BRIEF DESCRIPTION OF DRAWINGS

[0019] In order to more clearly illustrate the technical solutions of the embodiments of the present disclosure or the prior art, the drawings needed in the embodiments or prior art description will be briefly introduced as follows. Obviously, the drawings in the following description are only some embodiments described in the present disclosure, and those skilled in the art can also obtain other drawings according to these drawings without creative labor.

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

[0021] Figure 2 is a flowchart of the blade head temperature control method of the ultrasonic electrosurgical instrument provided by the embodiments of the present disclosure;

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

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

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

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

[0026] Figure 7 A connection state diagram of an ultrasonic electrosurgical system 300 is provided for another embodiment of the present disclosure;

[0027] Figure 8 A structural block diagram of a host end 310 of an ultrasonic electrosurgical system is provided for 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 described clearly and completely in combination with the drawings in the embodiments of the present disclosure. Obviously, the described embodiments are only a part of the embodiments of the present disclosure, rather than all the embodiments. Based on the embodiments of the present disclosure, all other embodiments obtained by those skilled in the art without making creative efforts should fall within the scope of protection of the present disclosure. In addition, in order to be clear, parts irrelevant 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 "include" or "have" are intended to indicate the presence of features, numbers, steps, actions, components, parts or combinations thereof disclosed in the present disclosure, and do not exclude the presence or addition of one or more other features, numbers, steps, actions, components, parts or combinations thereof. In addition, it should be further pointed out that the embodiments in the present disclosure and the features in the embodiments can be combined with each other without conflict.

[0030] The ultrasonic blade converts high-frequency current into mechanical vibration through an ultrasonic transducer, so that the metal blade generates mechanical vibration with a frequency of about 55.5 KHz. This high-frequency mechanical friction can vaporize water in the tissue, break hydrogen bonds of proteins, and cause cells to disintegrate, and proteins to denature and form viscous coagulum. At the same time, due to the friction heat generated by vibration, and the pressurizing effect formed by clamping the tissue, the purpose of cutting and hemostasis can be achieved.

[0031] The high-frequency electrotome generates a thermal effect by providing a high-frequency voltage and current to the lesion site to achieve the effect of tissue cutting and hemostasis. When used alone, the electrotome can be used for electrocision or electrocoagulation. In general, the temperature for electrocision is above 100℃, and the temperature for electrocoagulation is about 60-100℃. In actual application, the temperature control of the electrotome mainly depends on the experience of the operator, and improper operation can easily cause thermal damage.

[0032] The ultrasonic electrotome combines the advantages of the ultrasonic knife and the electrotome, uses mechanical vibration of the ultrasonic knife to complete cutting, and uses the electrotome to heat and coagulate blood. This mixed energy cutting mode reduces the risk of bleeding while cutting, and the cutting and hemostasis effect is better than that of the ultrasonic knife or the electrotome alone. The ultrasonic electrotome can also use only electric energy for coagulation, for example, in a blood vessel closure operation. Whether it is cutting or a blood vessel closure operation, the temperature of the knife head needs to be controlled to avoid causing thermal damage.

[0033] In order to control the temperature of the knife head, one way is to install a temperature sensor at the knife head to collect the temperature of the knife head in real time, and accordingly control the output energy to reduce the occurrence of excessively high temperature of the knife head. This method needs to set a temperature sensing device at the knife head, introduce additional electronic circuits in the ultrasonic knife rod and the ultrasonic transducer, and change the existing component design of the ultrasonic electrotome, which is high in cost. Moreover, when high-frequency electric energy is output, the temperature sensing system will be seriously disturbed by high-power high-frequency current, the temperature measurement accuracy is low, and more isolation design is needed, which increases the system complexity.

[0034] The technical solution of the present disclosure adopts another way, which does not need to increase additional components, uses the corresponding relationship between the bioimpedance and the temperature, monitors the temperature change by detecting the change of the bioimpedance, and accordingly controls the output energy to realize the temperature control adjustment of the knife head at low cost.

[0035] Experiments have found that the electrical impedance of biological tissue will gradually increase as the temperature of cells rises, and the biological characteristics of the tissue will change. As shown in Figure 1 , the impedance-temperature characteristics of general biological tissue will be different. As shown in Figure 1 , between 37-60℃, the electrical impedance of biological tissue will gradually decrease as the temperature rises, and reaches a minimum value near 60℃, corresponding to points a and b in Figure 1 . The weak bonds (hydrogen bonds, ionic bonds, hydrophobic bonds, etc.) of the spatial structure of tissue proteins will break under the condition of a temperature higher than 60℃, so as the temperature continues to rise, the proteins will denature, the biological tissue will gradually become dry, and the impedance value of the tissue will gradually increase. The coagulation temperature of the biological tissue is between 60-90℃, corresponding to points b and c in Figure 1 . When the temperature of the tissue exceeds 70°, the tissue becomes dry due to a large amount of water loss, and the impedance value rises rapidly. After the temperature continues to rise to 100℃, the impedance value rises rapidly, corresponding to points c, d and e in Figure 1 .

[0036] According to Figure 1The experimental results show that 60-90 DEG C is the stage of slow evaporation, shrinkage and coagulation of cell liquid, the thermal effect of this stage makes the cell liquid slowly vaporize, the cell shrinkage reaches the hemostasis effect, which is also the suitable temperature interval for using the electrotome to coagulate blood, and when the tissue temperature reaches 100 DEG C, the cell liquid rapidly vaporizes to make the cell rupture and the tissue break, which is a temperature that needs to be avoided in the blood vessel closure process. In addition, the biological tissue will be carbonized at about 150 DEG C, which is a condition that needs to be strictly avoided.

[0037] Based on this, the present disclosure provides a method for controlling the temperature of the blade head of an ultrasonic electrosurgical instrument.

[0038] Figure 2 The flow chart of the method for controlling the temperature of the blade head of the ultrasonic electrosurgical instrument provided by the embodiments of the present disclosure is shown in the figure.

[0039] As shown in the figure, the method comprises S110-S140. Figure 2

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

[0041] The ultrasonic electrotome can perform operations by using two driving energies, which are set according to the requirements in the application. For example, ultrasonic + high-frequency electric energy mixed output (referred to as ultrasonic-electric mixed output) is usually used to perform tissue cutting, and only high-frequency electric output is usually used to perform electric coagulation operation, including hemostasis and blood vessel closure operation.

[0042] S120: In the cutting mode of outputting ultrasonic-electric mixed energy, determine 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: In the case where the impedance value is greater than the set value, reduce the output ultrasonic-electric mixed energy according to the current cutting stage.

[0045] By detecting the energy loop between the host and the blade head, the impedance value generated by the clamped tissue can be detected. In the cutting mode of outputting ultrasonic-electric mixed energy, the host outputs mixed two kinds of energy to the blade head for performing cutting operation, and the impedance value changes with the cutting process, showing the corresponding impedance change trend. According to the change trend of the impedance value, the current cutting stage can be determined, i.e. the initial, middle or final stage of cutting. In different cutting stages, if the impedance value is greater than the set value, it indicates that the temperature of the current tissue exceeds the set temperature range, and then the output energy needs to be reduced to reduce the heat absorbed by the tissue. In addition to the cutting mode of outputting ultrasonic-electric mixed energy, there can also be an electric coagulation mode of outputting only high-frequency electric energy and a cutting mode of outputting only ultrasonic energy. ​

[0046] Specifically, the determined impedance value of the tissue 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 host and the blade, and the electrical impedance generated by the clamped tissue is detected through a high-frequency electrical circuit between the host and the blade.

[0047] The impedance detection circuit can use a positive point atomic dual-channel high-speed AD module for detection. The module has a sampling and holding amplifier on a chip, uses a multi-stage differential pipeline structure, and can not lose code in the entire working temperature range. The impedance detection circuit gives the collected voltage and current information to the control unit for processing. The control unit can be an MCU and / or an FPGA, has computing power, and can calculate the electrical impedance and acoustic impedance corresponding to the target tissue, respectively.

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

[0049] Specifically, S130 can be determining the current cutting stage according to the change trend of the acoustic impedance value. 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 a surgical operation, the cutting process of the biological tissue can be divided into different stages: a cutting initial stage, a cutting process stage, and a cutting end stage. Different cutting stages adapt to different output energies. In some scenarios, the output energy of the ultrasonic knife device can be configured as follows: in the cutting initial stage, the blade has not yet entered the tissue, and the temperature of the tissue is relatively low. The power of the electrotome can be output at a high value, while the power of the ultrasonic knife only needs to be output at a low value. In the cutting process stage, the blade has penetrated into the tissue and needs to be cut and coagulated at the same time. At this time, the advantages of the ultrasonic knife and the electrotome are utilized, and the power of the two driving signals can be output at 50% of the respective total power. In the cutting end stage, the fast cutting advantage of the ultrasonic knife is fully utilized, and the power of the driving signal of the ultrasonic knife is output at a high value, while the power of the driving signal of the electrotome only needs to be output at a low value. Even if the output energy is configured as above, heat damage may still occur due to the continuous accumulation of heat absorbed by the target tissue in the cutting process stage and the cutting late stage. Therefore, a temperature control scheme needs to be combined for optimization.

[0051] As the resistance generated by the cutting head changes with the state of the tissue during cutting, this change can be reflected by changes in impedance. When the superelectric hybrid energy is output, acoustic impedance and electrical impedance can be detected. In this embodiment, the cutting stage is determined using the characteristics of changes in acoustic impedance. Alternatively, electrical impedance can be used to determine the cutting stage, or both acoustic impedance and electrical impedance can be used together to determine the cutting stage.

[0052] The characteristics of acoustic impedance variation are as follows: at the beginning of cutting, the acoustic impedance value first increases and then decreases, and then there is a relatively long and constant stage, which is the cutting stage. In the final stage of cutting, the acoustic impedance value will increase rapidly again. Figure 3 An example of acoustic impedance variation characteristics is given, based on Figure 3 The impedance characteristics of the instrument show that the acoustic impedance first decreases and then stabilizes near time t1, and then increases rapidly near time t2.

[0053] Acoustic impedance characteristics are related to tissue type and the amount of energy applied, and generally present as follows: Figure 3 The trend shown indicates that the acoustic impedance value can be continuously monitored during the surgery. If the acoustic impedance value first rises and then falls and remains stable, it is determined to be the first cutting stage. If the acoustic impedance value stabilizes and then rises rapidly, 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 cutting end stage. For example... Figure 3 The first cutting stage occurs between t1 and t2, and the second cutting stage occurs after t2. Generally, the duration of the cutting process is related to the tissue type, and the duration of the first stage is related to the amount of energy output. For example, Figure 4 The animal experiment data provided showed that pig stomach was cut using five different energy levels, and the changes in impedance during the cutting process were recorded. It can be found that the energy levels 1 and 2 are more suitable, and the impedance changes during the process of protein structure denaturation and separation are more obvious. The first stage lasts for about 12 seconds.

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

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

[0056] Reducing the output energy includes temporarily stopping the output of that energy.

[0057] The thresholds Zu1, Ze1, Zu2, and Ze2 are determined based on the tissue type, with Zu1 > Ze1 and Zu2 > Ze2. This means that in the first cutting stage, if the temperature continues to rise, the ultrasonic energy is reduced first, followed by the high-frequency electrical energy; in the second cutting stage, if the temperature continues to rise, the high-frequency electrical energy is reduced first, followed by the ultrasonic energy.

[0058] The threshold selection for different types of tissues can be determined experimentally. For example, different threshold settings may be suitable for different types of tissues such as fat, liver, and small intestine. Generally, the threshold for the first cutting stage corresponds to the impedance value of this type of tissue at 70–85°C, and the threshold for the second stage corresponds to the impedance value of this type of tissue at 90–115°C. Figure 1 It appears that Zu1 or Ze1 is... Figure 1 The impedance values ​​near points a and c, combined with the determined first cutting stage, indicate that when the impedance reaches the threshold, it can only correspond to the temperature at point c. At this point, the tissue is at the boundary of coagulation and is in the cutting stage. Appropriately reducing the ultrasonic energy will not affect the cutting process. Therefore, the ultrasonic energy can be reduced first to decrease the energy output of the cutting head. If the impedance continues to increase, indicating a continued temperature rise, then the high-frequency electrical energy can be further reduced to decrease the heat absorbed by the clamped tissue. Zu2 or Ze2 is... Figure 1 The impedance value near point d in the diagram indicates that when the impedance value reaches the threshold, the tissue temperature has entered the temperature range of cell rupture. At this time, the cutting is in the completion stage. Therefore, the heat output of the cutting head can be quickly reduced by first reducing the output high-frequency electrical energy. If the impedance continues to increase, it means that the temperature continues to rise, so the ultrasonic energy is reduced again.

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

[0060] Furthermore, the method of this disclosure embodiment further includes operations S150 and S160 in addition to the foregoing process.

[0061] Figure 5 This is a flowchart of a method for controlling the tip temperature of an ultrasonic electrosurgical instrument according to another embodiment of this disclosure. Operations S110 to S140 can be implemented with reference to the foregoing embodiments, and there is no specific order between operations S150 and S160 and operations S120 to S140.

[0062] S150: Determine the impedance value of the clamped blood vessel in electrocoagulation mode where only high-frequency electrical energy is output.

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

[0064] In the operation of performing operation on blood vessels, there are mainly the operations of electric coagulation hemostasis and blood vessel closure, which utilize the electric coagulation function of the high-frequency electric knife. For example, in blood vessel closure, the heat effect generated when the alternating current with a frequency of about 300-550 kHz passes through the blood vessel tissue with biological impedance makes the protein in the tissue denature, at the same time, the blood vessel lumen is adhered together by means of the pressure applied on the blood vessel tissue to make the blood vessel form closure. The electric surgical blood vessel closure technology based on the principle of electric heat effect is a relatively new blood vessel closure technology, but the potential thermal damage to the adjacent tissue or nerve of the closure position generated in the operation process is still a problem to be solved. The electric coagulation hemostasis process also faces the same problem. According to Figure 1 Based on the heat conduction performance of the biological tissue and the characteristics thereof changing with temperature as shown in the figure, the temperature of the blood vessel can be determined by detecting the electrical impedance value of the blood vessel, and the damage to the tissue caused by excessive temperature and continuous heating can be avoided by avoiding that the electrical impedance value exceeds the threshold Z3.

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

[0066] Here, examples of the above several threshold settings are given according to the experimental data shown in Figure 4 : In the cutting of pig belly, it is found by detection that the minimum impedance value is about 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 be made, and accordingly, the host device can allow the operator to manually set the impedance threshold.

[0067] According to the control method of the embodiments of the present disclosure, the relationship between the electrical impedance of the biological tissue and the temperature is utilized, without the need for additional temperature measurement elements and corresponding circuits, by detecting the impedance in the output energy loop, the temperature of the current biological tissue can be grasped, and accordingly the output energy is adjusted, and the probability of thermal damage is effectively reduced by using a simple structure.

[0068] Based on the same inventive concept, the embodiments of the present disclosure also provide a knife head temperature control device 200 for an ultrasonic electric surgical instrument, which will be described below with reference to Figure 6 The control device 200 of the embodiments of the present disclosure will be described.

[0069] Figure 6is a block diagram of a blade temperature control device 200 for an ultrasonic electrosurgical instrument provided by embodiments of the present disclosure. The control device 200 can be implemented by software, hardware, or a combination of both to be part or all of an electronic device.

[0070] As shown in Figure 6 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 perform 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 mixed output ultrasonic electrosurgical tissue cutting mode.

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

[0074] The control module 240 is configured to reduce the output of the ultrasonic electrosurgical mixed energy according to the current cutting stage when the impedance value is greater than a set value.

[0075] Specifically, the impedance determination module 220 is configured to determine the acoustic impedance value and the electrical impedance value of the clamped tissue in the mixed output ultrasonic electrosurgical tissue cutting mode; 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; and the control module 240 is configured to reduce the output of the ultrasonic energy when the electrical impedance value is greater than a threshold Zu1 in the first cutting stage, and reduce the output of the high-frequency electrical energy when the electrical impedance value is greater than a threshold Ze1 in the first cutting stage. The control module 240 is further configured to reduce the output of the high-frequency electrical energy when the electrical impedance value is greater than a threshold Zu2 in the second cutting stage, and reduce the output of the high-frequency electrical energy when the electrical impedance value is greater than a threshold Ze2 in the second cutting stage.

[0076] Further, the impedance determination module 220 is further configured to determine the electrical impedance value of the clamped blood vessel in the electrical coagulation mode that only outputs high-frequency electrical energy, and the control module 240 is further configured to stop the output of the high-frequency electrical energy when the electrical impedance value is greater than a threshold Z3.

[0077] According to the control device of the embodiment of the present disclosure, the relationship between the electrical impedance of the biological tissue and the temperature is utilized, without additional temperature measuring elements and corresponding circuits, the current temperature of the biological tissue can be mastered by detecting the impedance in the output energy loop, and the output energy is adjusted accordingly, so that the probability of thermal damage is effectively reduced by using a simple structure. The control device can be independently applied to the ultrasonic electrosurgical equipment or combined with the existing master control system, and the present disclosure does not limit this.

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

[0079] Figure 7 is a schematic diagram of the connection state of the ultrasonic electrosurgical system 300 provided by another embodiment of the present disclosure, Figure 8 is a structural block diagram of the host end 310.

[0080] As shown in Figure 7 , 8 the ultrasonic electrosurgical 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 electrical energy source 312, and further includes an impedance detection unit 313 and a control unit 314. The impedance detection unit 313 is used to detect the impedance in the energy loop between the host end and the instrument end. The control unit 314 is used to execute various methods according to the detection results of the impedance detection unit, so as to control the driving capability of the ultrasonic energy source 311 and the high-frequency energy source 312 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 electrical energy into mechanical vibration to drive the blade to vibrate.

[0081] The specific execution operations of the detection unit 313 and the control unit 314 in the embodiment can refer to the description in the foregoing embodiments, which will not be described here.

[0082] On this basis, the embodiment of the present disclosure further provides an electronic device, including: at least one processor; and a memory in communication connection with 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 various methods as described above.

[0083] The foregoing description of specific embodiments of the application has been presented with reference to particular embodiments. Other embodiments are within the scope of the following claims. In some instances, the actions or steps described in the claims can be performed in a different order and still achieve the desired results. In addition, the process depicted in the accompanying figures does not necessarily require the particular order shown or sequential order to achieve the desired results. In certain implementations, multitasking and parallel processing can be advantageous or necessary.

[0084] The various embodiments in the present disclosure are described in a progressive manner, and the same or similar parts between the various embodiments can be referred to each other. Each embodiment focuses on the difference from other embodiments. In particular, the embodiments of the control device, the surgical apparatus, and the electronic device are described simply because they are basically similar to the embodiments of the control method described above, and the relevant parts can be referred to the description of the method embodiments.

[0085] The above only describes the embodiments of the present disclosure and is not intended to limit the present disclosure. The present disclosure can have various modifications and changes for those skilled in the art. Any modification, equivalent replacement, improvement, etc. 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 tip temperature control device for an ultrasonic electrosurgical instrument, comprising: The temperature control device comprises: a mode determination module configured to determine an energy output mode of current operation; an impedance determination module configured to determine an impedance value of clamped tissue in a hybrid output ultracapacity tissue cutting mode, the impedance value comprising an acoustic impedance value and an electrical impedance value; a cutting stage determination module configured to determine a current cutting stage according to a variation trend of the acoustic impedance value, the cutting stage comprising a first cutting stage and a second cutting stage; a control module configured to reduce output ultracapacity hybrid energy according to the current cutting stage when the impedance value is greater than a set value, comprising: if the first cutting stage, reducing output ultrasonic energy when the electrical impedance value is greater than a threshold Zu1, and reducing output high-frequency electric energy when the electrical impedance value is greater than a threshold Ze1; if the second cutting stage, reducing output high-frequency electric energy when the electrical impedance value is greater than a threshold Zu2, and reducing output ultrasonic energy when the electrical impedance value is greater than a threshold Ze2, the thresholds Zu1, Ze1, Zu2, and Ze2 being determined according to the type of tissue, and Zu1<Ze1 and Zu2<Ze2.

2. The apparatus of claim 1, wherein, The impedance determination module determines the acoustic impedance value and the electrical impedance value of the clamped tissue, comprising: detecting the acoustic impedance generated by the clamped tissue through an ultrasonic circuit between the host and the tool head; detecting the electrical impedance generated by the clamped tissue through a high-frequency electric circuit between the host and the tool head.

3. The apparatus of claim 1, wherein, The control module is further configured to: determine the electrical impedance value of the clamped blood vessel in an electrocoagulation mode in which only high-frequency electric energy is output; stop outputting high-frequency electric energy when the electrical impedance value is greater than a threshold Z3.

4. An ultrasonic electrosurgical system comprising a host end and an instrument end, characterized in that: the host end comprises an ultrasonic energy source and a high-frequency electric energy source, and further comprises an impedance detection unit and a control unit, the impedance detection unit being configured to detect impedance in an energy circuit between the host end and the tool head of the instrument end, and the control unit being configured to realize the functions of the temperature control device according to any one of claims 1-3, and being configured to control driving energy output from the ultrasonic energy source and the high-frequency energy source to the instrument end according to the detection result of the impedance detection unit.

5. An electronic device comprising: at least one processor; and a memory connected to the at least one processor in communication; 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 realize the functions of the temperature control device according to any one of claims 1-3.

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