Temperature control method and device of ultrasonic high-frequency instrument and multi-output-energy surgical equipment

Abstract

The invention provides a temperature control method for an ultrasonic high-frequency instrument, and the method comprises the steps: collecting the temperature of a tool bit, and enabling the temperature of the tool bit to be obtained through a temperature sensor disposed at the tool bit; collecting a feedback signal in the energy output loop; calculating an energy adjustment coefficient according to the temperature of the tool bit and the feedback signal; and correspondingly adjusting the output ultrasonic energy and high-frequency electric energy according to the energy adjustment coefficient. According to the technical scheme, the temperature sensor is used for monitoring the temperature of the scalpel head, the output energy is adjusted in a self-adaptive mode according to the scalpel head temperature collected in real time and the feedback signal in the energy loop, the requirement of an operation can be met, and the situation that the scalpel head is overheated, and consequently thermal damage to biological tissue is caused can be effectively prevented; therefore, the dependence on operation experience is reduced, and the safety and the universality of the ultrasonic high-frequency instrument are improved.

Description

Technical Field

[0001] The present disclosure relates to the field of ultrasonic electrosurgical instruments, and in particular to a temperature control method and device for ultrasonic high-frequency instruments and a multi-output energy surgical device. Background Art

[0002] Ultrasonic high-frequency instruments combine the good cutting performance of ultrasonic scalpels and the good coagulation performance of high-frequency electric scalpels, and can achieve excellent coagulation and cutting performance in surgical operations. For example, after two electrodes are set at the jaws end of the ultrasonic scalpel, the effects of ultrasonic scalpel and bipolar electric scalpel can be achieved.

[0003] During clinical use, if the output energy of ultrasonic high-frequency devices is excessive and the blade generates too much heat, it will cause irreparable thermal damage to the target tissue being treated and the surrounding non-target tissue. For ultrasonic high-frequency devices, how to safely and effectively use the two energies to avoid thermal damage is an urgent problem to be solved. Summary of the invention

[0004] The present invention provides a temperature control method and device for an ultrasonic high-frequency instrument and a multi-output energy surgical device, which are used to solve the problem of how existing ultrasonic high-frequency instruments can safely and effectively utilize two energies to reduce thermal damage to biological tissues.

[0005] In order to solve the above technical problems, one aspect of the present disclosure provides a temperature control method of an ultrasonic high-frequency device, comprising:

[0006] Collecting the temperature of the cutter head, wherein the temperature of the cutter head is obtained by a temperature sensor arranged on the cutter head;

[0007] Collect feedback signals in the energy output loop;

[0008] Calculating an energy adjustment coefficient according to the temperature of the cutter head and the feedback signal;

[0009] According to the energy adjustment coefficient, the output ultrasonic energy and high-frequency electric energy are adjusted accordingly.

[0010] In another aspect, the present disclosure further provides a temperature control device for an ultrasonic high-frequency instrument, comprising:

[0011] A temperature acquisition module is used to acquire the temperature of the cutter head, and the temperature of the cutter head is obtained by a temperature sensor arranged on the cutter head;

[0012] A feedback module, used for collecting feedback signals in an energy output loop;

[0013] A calculation module, used for calculating an energy adjustment coefficient according to the temperature of the cutter head and the feedback signal;

[0014] The adjustment module is used to adjust the output ultrasonic energy and high-frequency electric energy accordingly according to the energy adjustment coefficient.

[0015] On the other hand, the present disclosure also provides a multi-output energy surgical device, including an ultrasonic energy source and a high-frequency electrical energy source, which are used to output driving energy to the instrument end of the ultrasonic high-frequency instrument, and also includes a control device capable of executing the various control methods mentioned above.

[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, a temperature sensor is used to monitor the temperature of the blade, and the output energy is adaptively adjusted based on the real-time collected blade temperature and the feedback signal in the energy circuit. This can not only meet the energy requirements of the operation but also effectively prevent the blade from overheating and causing thermal damage to biological tissues, thereby reducing dependence on operating experience and improving the safety and universality of ultrasonic high-frequency instruments. 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 This is a schematic diagram of an application scenario of the temperature control method of an ultrasonic high-frequency device in an embodiment of the present disclosure;

[0021] Figure 2 A flow chart of a temperature control method for an ultrasonic high-frequency device provided by 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 Schematic diagram of impedance-time characteristic curve for cutting different types of tissues;

[0024] Figure 5 A block diagram of a temperature control device for ultrasonic high-frequency equipment provided by an embodiment of the present disclosure;

[0025] Figure 6 A structural block diagram of a multi-output energy surgical device provided by an embodiment of the present disclosure;

[0026] Figure 7 A schematic diagram of the functional structure of a multi-output energy surgical device implementing an embodiment of the present disclosure. DETAILED DESCRIPTION

[0027] It should be noted that the embodiments described in the present disclosure 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 belong to 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 accompanying drawings. 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, in the absence of conflict, the embodiments in the present disclosure and the features in the embodiments can be combined with each other.

[0028] The working principle of ultrasonic scalpel is to convert high-frequency current into mechanical vibration through ultrasonic transducer, so that the metal blade produces mechanical vibration, and the vibration frequency is 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 hemostasis. The high-frequency electric knife produces a thermal effect by providing high-frequency voltage and current to the local lesion to achieve the purpose of tissue cutting and hemostasis. When used alone, the high-frequency electric knife can be used for electric cutting or electric coagulation. Under normal circumstances, the temperature for electric cutting is above 100℃, and the temperature for electric coagulation is about 60-100℃. In practical applications, the temperature control of the electric knife mainly depends on the operator's experience, and improper operation can easily cause thermal damage.

[0029] Ultrasonic high-frequency devices combine the advantages of ultrasonic scalpels and electric scalpels: using the mechanical vibration of ultrasonic scalpels to complete cutting, and using electric scalpels to stop bleeding by thermal coagulation. Ultrasonic high-frequency devices use mixed energy to cut, reducing the risk of bleeding while cutting, and their cutting and hemostasis effects are better than those of ultrasonic scalpels or electric scalpels alone. Ultrasonic high-frequency devices can also be operated using only one type of energy, such as using only high-frequency electrical energy to perform vascular closure operations. Whether it is cutting or vascular closure operations, the temperature of the blade needs to be controlled to avoid thermal damage to the target tissue or surrounding tissue.

[0030] In order to control the temperature of the cutter head, a temperature sensor can be installed at the cutter head to accurately sense the changes in the cutter head temperature in real time. The host device appropriately reduces the output energy according to the temperature of the cutter head, which can effectively reduce the occurrence of excessive cutter head temperature.

[0031] The technical solution of the present disclosure will be clearly and completely described below in conjunction with the drawings in the embodiments of the present disclosure.

[0032] Figure 1 It is a schematic diagram of an application scenario of the temperature control method of an ultrasonic high-frequency instrument in an embodiment of the present disclosure.

[0033] like Figure 1 As shown, in surgical applications, the ultrasonic high-frequency instrument 100 is connected to the host device 300 through the transducer 200. The ultrasonic high-frequency instrument 100 is the instrument end, and a temperature sensor is provided at its blade head, and a corresponding temperature measurement signal transmission line is provided at the host end and the device end. The temperature control method provided by the present disclosure is executed by the host device 300.

[0034] Figure 2 It is a flow chart of the temperature control method of the ultrasonic high-frequency instrument provided in the embodiment of the present disclosure.

[0035] like Figure 2 As shown, the method includes S110 to S140.

[0036] S110: Collecting the temperature of the cutter head. The temperature of the cutter head is obtained by a temperature sensor disposed on the cutter head.

[0037] The blade head is the main component for performing surgical operations. It is usually integrated with the blade rod and forms a jaw with the clamp to complete the operations of tissue stripping, clamping and applying energy. A schematic diagram of the blade head is shown in Figure 2 As shown. When working, the blade will vibrate mechanically at the ultrasonic frequency. This high-frequency mechanical friction can achieve the purpose of cutting. On the other hand, the jaws of the ultrasonic high-frequency instrument are also a discharge area of ​​a bipolar electric knife, which can provide high-frequency voltage and current to the clamped tissue to produce a thermal effect, causing the protein to denature and form a viscous coagulant to achieve the purpose of hemostasis. When using ultrasonic high-frequency instruments, depending on the purpose of the operation, ultrasonic energy and high-frequency electrical energy may be used at the same time. For example, during the cutting process, the two energies will be output at the same time to obtain better surgical results.

[0038] The temperature sensor is set at the blade head to sense the temperature of the blade head in real time and accurately, so as to determine whether the target tissue at the blade head is overheated. If the temperature of the blade head is too high or the continuous heat exceeds the threshold, the temperature of the blade head is reduced by reducing the output energy to prevent the blade head from causing irreparable thermal damage to the target tissue and surrounding tissue.

[0039] The temperature sensor can be a surface thermocouple, a probe thermocouple, or a temperature resistor, which can be fixed on the surface or inside the cutter head. For example, the thermocouple of the Capeson T-type ultra-fine temperature measuring wire has a temperature measuring wire diameter of less than 0.2mm. Both the temperature sensing head and the temperature measuring wire can be attached to the surface of the cutter bar, which will not affect the opening and closing of the jaws and the transfer of energy. This type of temperature sensor has mature technology, controllable costs, and a wide temperature measurement range and high accuracy.

[0040] When a temperature sensor is installed at the cutter head, it is necessary to receive the temperature measurement signal generated by the temperature sensor when collecting the temperature of the cutter head. The temperature measurement signal varies according to the temperature sensor. For example, for thermocouples, a voltage signal is generated, and for thermal resistors, a resistance signal is generated. The temperature measurement signal generated by the temperature sensor when the temperature changes is usually very small. For example, when measuring temperature with a thermocouple, the voltage difference between each degree Celsius is only a few tens of microvolts. Therefore, it needs to be amplified and linearly adjusted before it can be properly sampled by most ADC modules. The temperature measurement can be preliminarily compensated and amplified at the handle of the ultrasonic high-frequency instrument before it reaches the host.

[0041] The temperature measurement signal starts from the handle of the ultrasonic high-frequency instrument and can reach the host device through a separate line. For example, a line channel is opened on the handle to connect directly to the host device. This method does not require the modification of the transducer, but the added line connection will affect the flexibility of the surgical operation. The temperature measurement signal can also reach the host through the transducer, and the transducer may need to be modified, including the interface between the transducer and the handle and the wire connection inside the transducer housing.

[0042] The disclosed embodiment provides a method for allowing the temperature measurement signal to reach the host through the transducer without modifying the transducer, that is, the temperature measurement signal and the manual control signal generated by the handle share the same cable path. In the existing ultrasonic high-frequency instruments, there is already a line for transmitting control signals from the handle to the host, which is used to transmit the manual control signal generated by the manual operation button. The temperature measurement signal can be transmitted using the control line. The host device separates the temperature measurement signal generated by the temperature sensor through the line that transmits the control signal between the instrument end and the host end, and then determines the temperature of the blade according to the temperature measurement signal. Furthermore, the temperature measurement signal can be synthesized into a mixed signal with the manual control signal, and still reaches the host through the original transmission line for transmitting the control signal. The host obtains the mixed signal from the line and then separates the temperature measurement signal from the mixed signal. The synthesis method of the two signals can adopt a line multiplexing method such as time division, frequency division, or amplitude modulation, frequency modulation, etc. A circuit board is set inside the handle to control the output of the two signals in a predetermined manner.

[0043] During the operation, high-frequency electrical energy can be output continuously or according to a certain duty cycle. In this case, the cycle is generally between 0.5s and 1s, and the duty cycle is about 50%. Since high-power high-frequency current has a greater interference with the temperature measurement circuit, temperature measurement is performed during intervals without energy output, which can effectively reduce high-frequency interference and improve temperature measurement accuracy. Therefore, the method of the disclosed embodiment also includes controlling the interval output of high-frequency electrical energy so that the temperature measurement signal is transmitted during the time interval when the high-frequency electrical energy is not output. Due to the characteristics of the extremely short interval time and the temperature not changing instantly, the temperature result obtained by this temperature measurement method can also reflect the temperature changes at the blade head, and this structure is simpler, without the need to modify the transducer, only the circuit board in the handle needs to be upgraded, and it has more flexible applicability.

[0044] Before collecting the temperature of the cutter head, the method of the embodiment of the present disclosure also includes a process for processing the temperature measurement signal, including first amplifying the millivolt-level temperature measurement signal, then filtering out the high-order harmonics carried by the signal through a second-order low-pass filter, and finally performing electrical isolation through a photoelectric coupling circuit. The isolated signal is then sent to a DAQ acquisition card for data acquisition.

[0045] S120: Collecting feedback signals in the energy output loop.

[0046] While outputting driving energy to the ultrasonic high-frequency instrument, the feedback signals in these energy output circuits must also be collected. The types of feedback signals include feedback current and feedback voltage. The feedback signals can reflect the state changes of the target tissue, which are manifested by changes in bioimpedance. Therefore, the bioimpedance of the target tissue can be calculated based on the feedback signal, and the type of target tissue and the cutting stage can be determined based on the change characteristics of the bioimpedance of the target tissue.

[0047] The impedance characteristics of different types of biological tissues and the impedance characteristics of different cutting stages are briefly described below.

[0048] As an example, Figure 3 A characteristic curve of bioimpedance changing with time is given, which can reflect the progress of cutting: at the beginning of cutting, the impedance value increases first and then decreases, and then a relatively gentle stage (t1) appears, at which time the blade enters the tissue, which is the cutting stage, and at the end of the cutting (t2), the impedance value will increase rapidly again.

[0049] The study of the impedance characteristics of different tissues revealed that the tissue impedance curves of different tissue parts at different energies are significantly different, and the cutting process of tissue parts can be roughly divided into three stages: start-denaturation-separation. Figure 4The impedance characteristic curve detected by the blade when cutting pig stomach, small intestine and blood vessels at the same energy is shown. It can be seen that the impedance characteristics of different types of tissues are significantly different at the initial stage, which can be used to determine the type of tissue and determine the cutting stage based on the impedance change trend.

[0050] The feedback signal in the energy output loop includes an ultrasonic feedback signal and an electrical feedback signal. When collecting the feedback signal, the ultrasonic feedback signal and the electrical feedback signal can be collected through independent feedback circuits. Such a structure can reduce the interference between the two feedback signals, thereby ensuring the accuracy of various parameters calculated from the feedback signal. The ultrasonic impedance obtained using the ultrasonic feedback signal and the electrical impedance obtained using the electrical feedback signal are different, and can be used separately or in combination. For example, the ultrasonic impedance and the electrical impedance are used to obtain the comprehensive impedance, and then the comprehensive impedance is used for judgment.

[0051] On this basis, the bioimpedance of the target tissue is calculated according to the feedback signal, and the type of target tissue and the cutting stage are determined according to the change characteristics of the bioimpedance of the target tissue. There are three calculation schemes:

[0052] The first method is to calculate the ultrasonic impedance of the target tissue based on the ultrasonic feedback signal and determine the type of the target tissue based on the changing characteristics of the ultrasonic impedance; the electrical impedance of the target tissue is calculated based on the electrical feedback signal and determine the cutting stage based on the changing characteristics of the electrical impedance.

[0053] The second method is to calculate the electrical impedance of the target tissue based on the electrical feedback signal and determine the type of the target tissue based on the changing characteristics of the electrical impedance; calculate the ultrasonic impedance of the target tissue based on the ultrasonic feedback signal and determine the cutting stage based on the changing characteristics of the ultrasonic impedance.

[0054] The third method is to calculate the electrical impedance of the target tissue according to the electrical feedback signal, calculate the ultrasonic impedance of the target tissue according to the ultrasonic feedback signal, obtain the comprehensive impedance according to the ultrasonic impedance and the electrical impedance, and determine the type of target tissue and the cutting stage according to the change characteristics of the comprehensive impedance.

[0055] During implementation, different computing solutions can be adapted according to specific environments and individual differences.

[0056] Different types of tissues and different cutting stages require different energies, and the energy output of the driving ultrasonic high-frequency instrument can be adapted to this. For example, in the initial stage of cutting, the blade has not yet entered the tissue, and the temperature of the tissue is low. In order to allow the electrosurgical knife to start working quickly, the power of the driving electrosurgical knife can be output at a higher value, while the power of the ultrasonic scalpel only needs to be lower; in the ongoing cutting stage, the blade has penetrated into the tissue and needs to cut and coagulate synchronously. At this time, the respective advantages of the ultrasonic scalpel and the electrosurgical 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 scalpel is fully utilized. At this time, the signal power driving the ultrasonic scalpel is output at a higher value, while the signal power driving the electrosurgical knife only needs to be lower. Under such an energy configuration, once the temperature of the blade is too high and the energy needs to be adjusted, in addition to reducing the two energies in proportion, the following more precise and more adaptive energy adjustments can also be made.

[0057] S130: Calculate the energy adjustment coefficient according to the temperature of the cutter head and the feedback signal.

[0058] Research has found that 60-90°C is the stage where the cell fluid slowly evaporates, shrinks and coagulates. The thermal effect at this stage causes the cell fluid to slowly vaporize and the cells to shrink to achieve a hemostatic effect. This is also the appropriate temperature range for electrosurgical coagulation. When the tissue temperature reaches 100°C, the cell fluid rapidly vaporizes, causing the cells to rupture and the tissue to break. This is a temperature that needs to be avoided during the vascular closure process. In addition, biological tissues will carbonize at around 150°C, which is a situation that needs to be strictly avoided. During implementation, the temperature threshold for triggering energy adjustment can be set according to these temperature ranges, tissue types, and surgical operations performed. For example, the temperature threshold for vascular closure operations is set at 90°C, the temperature threshold for liver cutting operations is set at 100°C, and the temperature threshold for cutting adipose tissue is set at 110°C. The total heat applied to the tissue can also be calculated based on the temperature and duration of the blade, and the threshold for the total heat can be set.

[0059] Based on the determined tissue type and cutting stage, combined with the real-time collected blade temperature, the output energy can be adjusted to better suit the current surgical operation.

[0060] Still taking the aforementioned configuration of ultra-electric hybrid energy output as an example, during the cutting stage, the blade has penetrated deep into the tissue and needs to be cut and coagulated synchronously. At this time, if the blade temperature exceeds the threshold, the electric knife energy is reduced by 5% based on the original output, and the ultrasonic energy is reduced by 10% based on the original output. When the cutting is about to be completed, the fast cutting advantage of the ultrasonic knife is fully utilized. At this time, if the blade temperature exceeds the threshold, the ultrasonic energy is not reduced, and the high-frequency electric energy is reduced by 10% based on the original output. If the blade temperature does not exceed the threshold, there is no need to adjust the energy output, and it can still be output according to the original energy configuration. In addition, the reduction of high-frequency electric energy can be achieved by reducing the power of the output signal or reducing the duration of the output signal, that is, the output duty cycle of the high-frequency electric energy can be reduced.

[0061] Specifically, the energy adjustment coefficient can be determined according to the amount by which the current cutter head temperature exceeds the threshold. One implementation method is to determine the energy reduction ratio using the ratio of (T-Ts) / Ts, where T is the current cutter head temperature and Ts is the set temperature threshold. In another implementation method, different temperature thresholds are set for ultrasonic energy and high-frequency electric energy, and then the ultrasonic energy and high-frequency electric energy are determined based on the feedback signal, and then the reduction ratio of ultrasonic energy is calculated based on (T-Tu) / Tu; the reduction ratio of high-frequency electric energy is calculated based on (T-Te) / Te; where T is the current cutter head temperature, Tu is the temperature threshold to be reduced for ultrasonic energy, and Te is the temperature threshold to be reduced for high-frequency electric energy. For example, Tu is 80°C and Te is 105°C. By setting different temperature thresholds, the ultrasonic energy and high-frequency electric energy can be adjusted independently, which is more convenient when using only one energy to perform operations.

[0062] S140: According to the energy adjustment coefficient, the output ultrasonic and high-frequency electrical energy is adjusted accordingly.

[0063] The energy adjustment coefficient at this time is applied on top of the original energy output configuration scheme and has a higher priority. If the calculated energy adjustment coefficient needs to be reduced, the energy output must be reduced accordingly. The energy adjustment coefficient includes the adjustment coefficient for ultrasonic energy and the adjustment coefficient for high-frequency electric energy. If the coefficient is 0, the corresponding energy does not need to be adjusted.

[0064] According to the method of the embodiment of the present disclosure, by monitoring the temperature of the blade and energy feedback, the output energy is adaptively adjusted, which can not only meet the energy requirements of the operation but also effectively prevent the blade from overheating and causing thermal damage, thereby reducing the dependence on operating experience and improving the safety and universality of ultrasonic high-frequency instruments.

[0065] Based on the same inventive concept, the embodiment of the present disclosure also provides a temperature control device 200 for an ultrasonic high-frequency instrument, as shown below. Figure 5The control device 200 according to the embodiment of the present disclosure is described.

[0066] Figure 5 2 is a block diagram of a temperature control device 200 for an ultrasonic high-frequency instrument head 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.

[0067] like Figure 5 As shown, the control device 200 includes a temperature acquisition module 210, a feedback module 220, a calculation module 230, and an adjustment module 240. The control device 200 can execute the various methods described above.

[0068] A temperature acquisition module 210 is used to acquire the temperature of the cutter head, and the temperature of the cutter head is obtained by a temperature sensor arranged on the cutter head;

[0069] Feedback module 220, used for collecting feedback signals in the energy output loop;

[0070] A calculation module 230, configured to calculate an energy adjustment coefficient according to the temperature of the cutter head and the feedback signal;

[0071] The adjustment module 240 is used to adjust the output ultrasonic energy and high-frequency electric energy accordingly according to the energy adjustment coefficient.

[0072] Furthermore, the temperature acquisition module 210 is also used to separate the temperature measurement signal generated by the temperature sensor through the line for transmitting control signals between the instrument end and the host end; the separation method includes obtaining a mixed signal through the line for transmitting control signals between the instrument end and the host end, and the mixed signal includes the temperature measurement signal returned by the temperature sensor and the manual control signal generated by the manual operation of the instrument end; and then separating the temperature measurement signal based on the mixed signal.

[0073] Furthermore, the feedback module 220 obtains an ultrasonic feedback signal and a high-frequency electric feedback signal from two independent energy feedback circuits. When the operation module 230 calculates the energy adjustment coefficient, the bioimpedance of the target tissue is calculated according to the feedback signal, and the type and cutting stage of the target tissue are determined according to the change characteristics of the bioimpedance of the target tissue; and the energy adjustment coefficient is calculated according to the temperature of the blade and the type and cutting stage of the target tissue. To specifically determine the type and cutting stage of the target tissue, the ultrasonic feedback signal and the high-frequency electric feedback signal can be used separately, or the two feedback signals can be used in combination.

[0074] According to the control device of the embodiment of the present disclosure, by monitoring the temperature of the blade and the feedback signal in the energy circuit, the output energy is adaptively adjusted, which can not only meet the energy requirements of the operation but also effectively prevent the blade from overheating and causing thermal damage, further reduce the dependence on operating experience, and improve the universality of ultrasonic high-frequency instruments. The control device can be independently applied to ultrasonic electrosurgery equipment or implemented in combination with an existing main control system, and the present disclosure does not limit this.

[0075] On this basis, another embodiment of the present disclosure further provides a multi-output energy surgical device 300 .

[0076] Figure 6 is a structural block diagram of a multi-output energy surgical device 300 provided in an embodiment of the present disclosure.

[0077] like Figure 6 As shown, the multi-output energy surgical device 300 includes an ultrasonic energy source 310 and a high-frequency electrical energy source 320, which are used to output driving energy to the ultrasonic high-frequency instrument end, and also includes a control module 330. The control module can execute the various control methods mentioned above, so that it can adaptively adjust the output driving energy according to the temperature, tissue type, and cutting stage, thereby improving the surgical efficiency and reducing the probability of thermal damage.

[0078] Furthermore, the multi-output energy surgical device 300 also includes a display module for displaying the real-time temperature of the blade head, so that the operator can manually adjust the duration of the excitation energy.

[0079] Figure 7 It is a schematic diagram of the functional structure of the multi-output energy surgical device in the above embodiment.

[0080] like Figure 7 As shown, in the multi-output energy surgical device, the ultrasonic (US) energy end and the high-frequency electric (ES) energy end are respectively provided with a signal feedback module, and the feedback signal is sampled and filtered by ADC in the control module, and then sent to the operation unit; the temperature acquisition unit also sends the temperature measurement signal to the operation unit after filtering. The operation unit calculates the adapted energy and energy adjustment coefficient according to the feedback signal and the current temperature, and then adjusts the two energy power adjustment modules accordingly and outputs them through the I / O port. The result of the operation can also be output through the display module for the convenience of the operator to view.

[0081] 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.

[0082] 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.

[0083] 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 device, surgical equipment, and electronic device, 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.

[0084] 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 temperature control method for ultrasonic high-frequency equipment, characterized in that: include: Collecting the temperature of the cutter head, wherein the temperature of the cutter head is obtained by a temperature sensor arranged on the cutter head; Collect feedback signals in the energy output loop; Calculating an energy adjustment coefficient according to the temperature of the cutter head and the feedback signal; According to the energy adjustment coefficient, the output ultrasonic energy and high-frequency electric energy are adjusted accordingly.

2. The control method according to claim 1, characterized in that: The calculating the energy adjustment coefficient according to the temperature of the cutter head and the feedback signal comprises: Calculating the bioimpedance of the target tissue according to the feedback signal; Determining the type and cutting stage of the target tissue according to the change characteristics of the bioimpedance of the target tissue; An energy adjustment factor is calculated according to the temperature of the cutting head and the type and cutting stage of the target tissue.

3. The control method according to claim 2, characterized in that: Calculating the energy adjustment coefficient according to the temperature of the cutting head and the type and cutting stage of the target tissue includes: Determining the magnitude of ultrasonic energy and high-frequency electrical energy according to the type of target tissue and the cutting stage; Calculating the reduction ratio of the ultrasonic energy according to (T-Tu) / Tu; Calculating the reduction ratio of the high-frequency electric energy according to (T-Te) / Te; Wherein, T is the current temperature of the cutter head, Tu is the temperature threshold at which the ultrasonic energy needs to be reduced, and Te is the temperature threshold at which the high-frequency electrical energy needs to be reduced.

4. The control method according to claim 2, characterized in that: The feedback signal includes an ultrasonic feedback signal and a high-frequency electrical feedback signal; the bioimpedance of the target tissue is calculated according to the feedback signal, and the type and cutting stage of the target tissue are determined according to the change characteristics of the bioimpedance of the target tissue, including: Calculating the acoustic impedance of the target tissue according to the ultrasonic feedback signal, and determining the type of the target tissue according to the change characteristics of the acoustic impedance; The electrical impedance of the target tissue is calculated according to the electrical feedback signal, and the cutting stage is determined according to the change characteristics of the electrical impedance.

5. The control method according to claim 2, characterized in that: The feedback signal includes an ultrasonic feedback signal and a high-frequency electrical feedback signal; the bioimpedance of the target tissue is calculated according to the feedback signal, and the type and cutting stage of the target tissue are determined according to the change characteristics of the bioimpedance of the target tissue, including: Calculating the electrical impedance of the target tissue according to the electrical feedback signal, and determining the type of the target tissue according to the change characteristics of the electrical impedance; The acoustic impedance of the target tissue is calculated according to the ultrasonic feedback signal, and the cutting stage is determined according to the change characteristics of the acoustic impedance.

6. The control method according to claim 1, characterized in that: The temperature of the collecting blade includes: Separate the temperature measurement signal generated by the temperature sensor through the line that transmits the control signal between the instrument end and the host end; The temperature of the cutter head is determined according to the temperature measurement signal.

7. The control method according to claim 6, characterized in that: The temperature measurement signal generated by the temperature sensor is separated through the transmission control signal line between the instrument end and the host end, including: A mixed signal is obtained through a line for transmitting control signals between the instrument end and the host end, wherein the mixed signal includes a temperature measurement signal generated by a temperature sensor and a manual control signal generated by manual operation of the instrument end; The temperature measurement signal is separated based on the mixed signal.

8. The control method according to claim 6, characterized in that: The method also includes controlling the interval output of the high-frequency electric energy so that the temperature measurement signal is transmitted within the time interval when the high-frequency electric energy is not output.

9. A temperature control device for ultrasonic high-frequency equipment, characterized in that: include: A temperature acquisition module is used to acquire the temperature of the cutter head, and the temperature of the cutter head is obtained by a temperature sensor arranged on the cutter head; A feedback module, used for collecting feedback signals in an energy output loop; A calculation module, used for calculating an energy adjustment coefficient according to the temperature of the cutter head and the feedback signal; The adjustment module is used to adjust the output ultrasonic energy and high-frequency electric energy accordingly according to the energy adjustment coefficient.

10. A multi-output energy surgical device, comprising an ultrasonic energy source and a high-frequency electric energy source, for outputting driving energy to an ultrasonic instrument and a high-frequency electric instrument, characterized in that: It also includes a temperature control system for executing the temperature control method according to any one of claims 1 to 8.

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