Breast surgery electrotome and thermal radiation fine control system

Abstract

The invention relates to the technical field of medical equipment control, in particular to a breast surgery electrotome and a thermal radiation fine control system. The system comprises a memory and a processor, and the processor executes a computer program stored in the memory so as to realize the following steps: acquiring instantaneous impedance data between a working electrode and a loop electrode in a current time period, according to the change characteristics of the instantaneous impedance data in the current time period and the instantaneous impedance data of the initial state of the period in which each moment in the current time period is located, obtaining heat effect damage risk factors of each moment in the current time period; obtaining a dynamic thermal safety margin according to the fluctuation characteristics of the thermal effect damage risk factors, the change condition of the instantaneous impedance data and the duration of energy output; determining an operation efficiency coefficient based on the output power at the current moment; the power is adjusted by integrating the thermal effect injury risk factor, the dynamic thermal safety margin and the operation efficiency coefficient at the current moment. The low-heat injury risk in the mammary gland operation process is reduced.

Description

TECHNICAL FIELD

[0001] The present application relates to the technical field of medical equipment control, in particular to a breast surgery electrotome and a heat radiation fine control system. BACKGROUND

[0002] A high-frequency electrotome (high-frequency surgical instrument) is an electric surgical instrument that replaces a mechanical surgical knife to cut tissues. It realizes the separation and coagulation of body tissues by the high-frequency high-voltage current generated at the tip of the active electrode when it contacts the body, so as to achieve the purpose of cutting and hemostasis.

[0003] There are many problems in using a high-frequency electrotome in breast surgery. There are many types of breast tissues, and the impedance characteristics are significantly different due to the heterogeneity of breast tissues. The traditional fixed power mode is easy to cause fat carbonization or insufficient cutting of the breast. The reference impedance of the tissue changes greatly in different surgical environments, and the heat-sensitive structure is closely adjacent to the diseased tissue, so the heat radiation diffusion may cause irreversible damage. When a monopolar mode is used, although the current can realize the cutting and coagulation of the tissue, the traditional adjustment method does not fully consider the sensitivity of the tissue to heat, the influence of heat accumulation and the surgical efficiency, which is easy to cause serious heat damage to the tissue and slow down the surgical progress. SUMMARY

[0004] In order to solve the problem of heat radiation risk in the existing method for adjusting the power of the electrotome in the breast surgery process, the purpose of the present application is to provide a breast surgery electrotome and a heat radiation fine control system, and the technical scheme adopted is as follows:

[0005] The present application provides a breast surgery electrotome and a heat radiation fine control system, which comprises a memory and a processor. The processor executes the computer program stored in the memory to realize the following steps:

[0006] Obtain the instantaneous impedance data between the working electrode and the return electrode in the current period, wherein the current period is a period in the breast surgery process, and the current time is the last time in the current period;

[0007] According to the change characteristics of the instantaneous impedance data in the current period and the initial state of the instantaneous impedance data of each time in the current period, the heat effect damage risk factor of each time in the current period is obtained. According to the fluctuation characteristics of the heat effect damage risk factor in the current period, the change of the instantaneous impedance data and the duration of the energy output, the dynamic heat safety margin is obtained. The surgical efficiency coefficient is determined based on the output power of the current time;

[0008] The linear adjustment coefficient of the electrotome power is obtained by comprehensively considering the heat effect damage risk factor, the dynamic heat safety margin and the surgical efficiency coefficient of the current time. The electrotome power is adjusted by using the linear adjustment coefficient.

[0009] Preferably, the thermal effect damage risk factor of each time point in the current period is obtained according to the change feature of the instantaneous impedance data in the current period and the initial state of the instantaneous impedance data of each time point in the current period, comprising:

[0010] Based on the impedance feature value of each time point in the current period, the instantaneous change rate of each time point is obtained; wherein the process of obtaining the impedance feature value is: calculating the first difference value between the instantaneous impedance data of each time point and the initial time point of the same period of the initial time point, and taking the ratio between the first ratio and the instantaneous impedance data of the initial time point of the same period as the impedance feature value of each time point;

[0011] Based on the instantaneous change rate of each time point in the current period, the thermal effect damage risk factor of each time point in the current period is determined.

[0012] Preferably, the thermal effect damage risk factor of each time point in the current period is determined based on the instantaneous change rate of each time point in the current period, comprising:

[0013] Based on the instantaneous change rate of each time point, the symbol function value corresponding to each time point is obtained by means of the symbol function; the absolute value of the ratio between the cumulative sum of the symbol function values corresponding to all time points in the current period and the total number of time points in the current period is recorded as the continuous change state value;

[0014] The product of the instantaneous change rate of each time point and the continuous change state value is taken as the actual impedance change rate of each time point; the normalized result of the product between the actual impedance change rate of each time point and its impedance feature value is determined as the thermal effect damage risk factor of each time point.

[0015] Preferably, the dynamic thermal safety margin is obtained according to the fluctuation feature of the thermal effect damage risk factor in the current period, the change of the instantaneous impedance data and the duration of the energy output, comprising:

[0016] Based on the fluctuation feature of the thermal effect damage risk factor of all time points in the current period, the thermal sensitivity is obtained;

[0017] The sum of the absolute values of the actual impedance change rates of all time points in the current period is recorded as the first sum value; the range of the actual impedance change rates of all time points in the current period is obtained; the first ratio between the first sum value and the range is calculated; the product of the reciprocal of the sampling frequency and the first ratio is recorded as the heat dissipation factor;

[0018] According to the duration of the energy output of the current time point and the heat dissipation factor, the time accumulation factor is obtained;

[0019] The normalized product of the time accumulation factor and the heat sensitivity is determined as the dynamic heat safety margin.

[0020] Preferably, the heat effect damage risk factor is obtained by determining the standard deviation of the heat effect damage risk factor at all time points in the current period as the heat sensitivity, and the standard deviation is used to represent the fluctuation characteristics of the heat effect damage risk factor.

[0021] Preferably, the time accumulation factor is obtained according to the duration of the energy output at the current time point and the heat dissipation factor, and the time accumulation factor is obtained according to the duration of the energy output at the current time point and the heat dissipation factor.

[0022] The second ratio of the duration of the energy output at the current time point and the heat dissipation factor is calculated.

[0023] The time accumulation factor is obtained based on the second ratio, and the second ratio is positively correlated with the time accumulation factor.

[0024] Preferably, the surgical efficiency coefficient is determined based on the output power at the current time point, and the surgical efficiency coefficient is determined based on the output power at the current time point.

[0025] The ratio between the output power at the current time point and the preset reference power is taken as the surgical efficiency coefficient.

[0026] Preferably, the linear adjustment coefficient of the electrosurgical power is obtained by comprehensively considering the heat effect damage risk factor at the current time point, the dynamic heat safety margin and the surgical efficiency coefficient, and the linear adjustment coefficient of the electrosurgical power is obtained by comprehensively considering the heat effect damage risk factor at the current time point, the dynamic heat safety margin and the surgical efficiency coefficient.

[0027] The second difference between the preset first value and the surgical efficiency coefficient is calculated.

[0028] The product of the heat effect damage risk factor at the current time point, the dynamic heat safety margin and the second difference is taken as the linear adjustment coefficient of the electrosurgical power.

[0029] Preferably, the linear adjustment coefficient of the electrosurgical power is adjusted, and the linear adjustment coefficient of the electrosurgical power is adjusted.

[0030] The product of the normalized value of the output power at the current time point and the linear adjustment coefficient is taken as a third product.

[0031] The third difference between the preset second value and the third product is calculated.

[0032] The third difference is used to adjust the electrosurgical power at the current time point.

[0033] Preferably, the third difference is used to adjust the electrosurgical power at the current time point, and the product of the output power at the current time point and the third difference is taken as the adjusted power of the electrosurgical power.

[0034] The present application has at least the following advantages:

[0035] The application first evaluates the damage risk caused by heat radiation according to the change characteristics of the instantaneous impedance data in the current period and the initial state of the instantaneous impedance of each time in the current period, obtains the thermal effect damage risk factor of each time in the current period, and accurately quantifies the real-time thermal damage risk; then, the time cumulative effect is evaluated by combining the fluctuation characteristics of the thermal effect damage risk factor in the current period, the change of the instantaneous impedance data and the duration of the energy output, and the dynamic thermal safety margin of the current time is obtained; the surgical efficiency coefficient is introduced to establish the flexible balance between safety and efficiency, and the surgical efficiency coefficient is obtained to optimize the power output while ensuring the basic cutting performance; the linear adjustment coefficient is determined by comprehensively considering the thermal effect damage risk factor, the dynamic thermal safety margin and the surgical efficiency coefficient of the current time, and the power of the electrotome in the breast surgery is controlled based on the linear adjustment coefficient to avoid step response and ensure the safety of the surgery. The breast surgery electrotome and heat radiation fine control system provided by the application significantly reduces the low thermal damage risk in the breast surgery process, ensures the breast surgery effect, and provides more reliable energy equipment support for breast surgery. BRIEF DESCRIPTION OF DRAWINGS

[0036] In order to more clearly illustrate the technical solutions in the embodiments of the present application or the prior art, and the advantages thereof, below, a brief introduction will be given to the drawings needed to be used in the embodiments or the prior art description. Obviously, the drawings in the following description are only some embodiments of the present application, and for those skilled in the art, other drawings can also be obtained without creative labor.

[0037] Figure 1 The flow chart of the method executed by the breast surgery electrotome and heat radiation fine control system provided by the embodiments of the present application. DETAILED DESCRIPTION

[0038] In order to further illustrate the technical means and effects adopted by the present application to achieve the predetermined invention purpose, the breast surgery electrotome and heat radiation fine control system according to the present application is described in detail below by combining the drawings and the preferred embodiments.

[0039] Unless otherwise defined, all technical and scientific terms used herein have the same meaning as commonly understood by one of ordinary skill in the art to which the present application belongs.

[0040] The specific scheme of the breast surgery electrotome and heat radiation fine control system provided by the present application is specifically described below by combining the drawings.

[0041] Embodiment of a breast surgery electrotome and heat radiation fine control system:

[0042] The embodiment provides a breast surgery electrotome and a fine control system for thermal radiation. Figure 1 As shown in the figure, the method performed by the breast surgery electrotome and the fine control system for thermal radiation comprises the following steps:

[0043] In step S1, instantaneous impedance data between the working electrode and the return electrode in a current period is acquired, wherein the current period is a period in the breast surgery process, and the current moment is the last moment in the current period.

[0044] In the surgery process, the high-frequency electrotome usually adopts a monopolar mode, in which a complete circuit is used to cut and coagulate tissues, and the circuit is composed of a high-frequency generator in the high-frequency electrotome, a patient plate, a connecting wire and an electrode. In most applications, the current passes through the patient through the effective wire and the electrode, and then returns to the generator of the high-frequency electrotome through the patient plate and the wire thereof. The heating effect of the high-frequency electrotome capable of destroying the lesion tissues is not caused by the heating electrode or the knife head, but the high-frequency current with high current density is gathered to directly destroy the tissues under the point in contact with the effective electrode tip. When the temperature of the tissues or cells in contact with or adjacent to the effective electrode rises to the point at which the proteins in the cells are denatured, coagulation is generated. The precise surgical effect is determined by the waveform, voltage, current, type of tissue and shape and size of the electrode.

[0045] The use of the electrotome for the surgical operation on the breast part can reduce bleeding and the size of the wound, and since the fat content of the breast part is high, the vaporization efficiency of the fat tissues by the electrotome is higher than that of mechanical cutting, thereby reducing postoperative fat liquefaction. The breast surgery includes various types of surgeries, such as open resection, breast conservation and axillary cleaning. Before the subsequent operation, the surgeon should select and confirm the type of surgery. Since the reference impedance range of different tissues is different for the breast and various types of surgeries.

[0046] In the breast surgery process, the voltage and the current between the working electrode and the return electrode are monitored in real time, and the master control system calculates the instantaneous impedance data according to the monitored voltage and current. The calculation method of the instantaneous impedance is a prior art, and will not be described in detail herein. In the embodiment, the data acquisition frequency is 0.01 seconds per acquisition, and in specific applications, the implementer can set it according to the specific circumstances. The instantaneous impedance data between the working electrode and the return electrode at each moment in the current period is acquired. The current period is a set of all historical moments and the current moment, wherein the time interval between the current moment and the current period is less than or equal to the preset time length, that is, the current moment is the last moment in the current period. In the embodiment, the preset time length is 1 second, and in specific applications, the implementer can set it according to the specific circumstances.

[0047] Then, the instantaneous impedance data of all time points in the current period is processed by using the moving average method to remove high-frequency noise and obtain smoothed instantaneous impedance data. It should be noted that the instantaneous impedance data mentioned in the subsequent description is the smoothed instantaneous impedance data unless otherwise specified.

[0048] At this point, the instantaneous impedance data of each time point in the current period is collected, and the instantaneous impedance data is stored in the control terminal of the electrotome for subsequent analysis and processing.

[0049] In step S2, the thermal effect damage risk factor of each time point in the current period is obtained according to the change characteristics of the instantaneous impedance data in the current period and the initial state of the instantaneous impedance data of each time point in the current period. The dynamic thermal safety margin is obtained according to the fluctuation characteristics of the thermal effect damage risk factor, the change of the instantaneous impedance data and the duration of the energy output. The operation efficiency coefficient is determined based on the output power of the current time point.

[0050] For the same type of tissue or structure, it has approximately consistent impedance value during cutting by the electrotome. Therefore, by analyzing the change of the impedance value and regulating the power of the electrotome during the operation, the negative impact of heat radiation on the tissue structure can be reduced.

[0051] The system shows a complete energy output cycle during cutting. The instantaneous impedance data is obtained at the beginning of each cutting cycle, that is, the initial impedance of the tissue corresponding to the current contact point is obtained.

[0052] For any time point in the current period, the difference between the instantaneous impedance data of the time point and the initial time point of the period is calculated, which is recorded as the first difference. The ratio between the first difference and the instantaneous impedance data of the initial time point of the period is taken as the impedance characteristic value of the time point. By using this method, the impedance characteristic value of each time point in the current period can be obtained. There is an impedance characteristic value for each time point in the current period. The impedance characteristic value directly reflects the change degree relative to the initial state. A positive value indicates that the impedance increases, which means that the probability of dehydration, coagulation and carbonization of the tissue corresponding to the position increases. A negative value indicates that the impedance decreases, which means that the probability of tissue fluid increase and small blood vessel rupture increases, thereby eliminating the influence of the difference in the basic impedance of different patients and different tissue parts. It should be noted that in continuous operation, if the instantaneous impedance data of the initial time point of the adjacent time point changes significantly, it means that the tissue type has changed, for example, the cutting position of the electrotome moves from the fat area to the gland area, and then the initial state calculation reference of the impedance characteristic value also changes.

[0053] Based on the impedance characteristic value of each time in the current period, the instantaneous change rate of the impedance characteristic value of each time is calculated, and the instantaneous change rate is recorded as the instantaneous change rate of each time. The positive and negative signs of the instantaneous change rate represent the change direction of the impedance. The calculation method of the instantaneous change rate of the data is prior art, and will not be described in detail here.

[0054] Based on the instantaneous change rate of each time in the current period, the sign function value corresponding to each time is obtained by means of the sign function, that is, if the instantaneous change rate is negative, the sign function value corresponding to it is -1; if the instantaneous change rate is 0, the sign function value corresponding to it is 0; if the instantaneous change rate is positive, the sign function value corresponding to it is 1. By using this method, the sign function value corresponding to each time in the current period is obtained, the cumulative sum of the sign function values corresponding to all times in the current period is calculated, and the ratio between the cumulative sum and the total number of times in the current period is calculated. The value of the ratio is in the range of [-1, 1], and the closer the value is to -1 or 1, the more it indicates that there is a continuous change process of the impedance value; the closer the value is to 0, the more it indicates that the impedance value is in a stable state, so the absolute value of the ratio is recorded as the continuous change state value.

[0055] The tissue at the current position is effectively cut by the electrotome and the coagulation is normal, so the corresponding impedance characteristic value rises rapidly and continuously; the instantaneous change rate is positive and the value is relatively small, indicating that the blood vessel protein is denatured and dehydrated closed. When the tissue at the current position is cut or coagulated by the electrotome, the impedance characteristic value rises sharply and greatly, and the instantaneous change rate is a continuously increasing positive value, indicating that the tissue may be excessively dehydrated and carbonized, and the risk probability of damage caused by heat radiation is high.

[0056] Therefore, the product of the instantaneous change rate of each time and the continuous change state value is taken as the actual change rate of the impedance of each time; the normalized result of the product between the actual change rate of the impedance of each time and its impedance characteristic value is determined as the heat effect damage risk factor of each time. The heat effect damage risk factor represents the risk probability of damage caused by heat radiation, and the larger the heat effect damage risk factor, the higher the risk probability. However, direct power adjustment needs to consider three constraints, that is, when adjusting the power, the effective cutting efficiency should be maintained, and the accumulation of heat radiation should be avoided to cause damage to the deep tissue. In this embodiment, the maximum and minimum value normalization method is used to normalize the product between the actual change rate of the impedance and its impedance characteristic value. The maximum and minimum value normalization method is prior art, and will not be described in detail here. As other embodiments, other existing data normalization methods can also be used for processing.

[0057] Different types of breast tissue, such as adipose tissue, glandular tissue, etc., have different physical properties, such as thermal conductivity, and different responses to the energy of the electrotome. For example, blood vessel walls and nerve bundles are more sensitive to heat during the cutting process. The closer the distance to the heat-sensitive structure during the cutting process, the greater the unexpected fluctuation range of the thermal effect damage risk factor, indicating that the heat-sensitive structure is closer.

[0058] The standard deviation of the thermal effect damage risk factor at all times in the current period is determined as the heat sensitivity. The standard deviation is used to characterize the fluctuation characteristics of the thermal effect damage risk factor. The greater the standard deviation, the more violent the fluctuation of the thermal effect damage risk factor, and the higher the heat sensitivity of the current cutting position.

[0059] Next, the sum of the absolute values of the impedance actual change rates at all times in the current period is recorded as a first sum; the range of the impedance actual change rates at all times in the current period is obtained; the ratio between the first sum and the range is recorded as a first ratio; the product of the reciprocal of the sampling frequency and the first ratio is recorded as a heat dissipation factor; the heat dissipation factor is used to reflect the heat dissipation speed of the tissue at the current position, and the smaller the value, the slower the heat dissipation of the tissue. Calculate the ratio between the duration of the energy output at the current time and the heat dissipation factor, and record the ratio as a second ratio; the duration of the energy output at the current time is the duration between the first time of the period in which the current time is located and the current time. Then, obtain a time accumulation factor based on the second ratio, and the second ratio and the time accumulation factor are in a positive correlation.

[0060] Wherein, the positive correlation means that the dependent variable will increase with the increase of the independent variable, and the dependent variable will decrease with the decrease of the independent variable, which can be an additive relationship, a multiplicative relationship, etc., determined by actual application.

[0061] In this embodiment, the specific calculation formula of the time accumulation factor is given, which can be represented as:

[0062]

[0063] Wherein, μ represents the time accumulation factor, e represents the natural constant, Δt represents the duration of the energy output at the current time, and τ represents the heat dissipation factor.

[0064] When the duration of the energy output is longer, and the heat dissipation speed is slower, it means that more heat is accumulated at the current time, i.e. the time accumulation factor is larger. The closer the time accumulation factor is to 1, the smaller the safety margin of the cutting process at the current position.

[0065] Further, the product of the time accumulation factor and the heat sensitivity is calculated, and the normalized result of the product is determined as the dynamic thermal safety margin. The greater the value, the higher the demand for regulation of thermal radiation, that is, the greater the power reduction amplitude for the current position should be.

[0066] In view of the fact that the efficiency of the operation is directly related to the power of the electrotome, the higher the power, the higher the efficiency of the operation. For different breast tissue types, the minimum power value is ensured when the basic cutting efficiency, such as the cutting depth per unit time, reaches the minimum value required by the clinic. Through power gradient experiments on different breast tissue types, including adipose tissue, glandular tissue, and fibrous connective tissue, the minimum stable working power corresponding to each type of tissue is recorded under the premise that the cutting depth per unit time meets the clinical requirements. The working power is the preset reference power. The data will be integrated into the intelligent database of the surgical instrument, supporting the doctor to confirm the tissue type through the touch display or voice command before the operation starts, and the system automatically matches the corresponding preset reference power.

[0067] The ratio between the output power at the current time and the preset reference power is taken as the operation efficiency coefficient η. When η is greater than 1, it indicates that the current power is higher than the reference efficiency power, and the operation efficiency is redundant, so the power can be appropriately reduced. When η is less than 1, there may be a risk of insufficient efficiency.

[0068] At this point, the thermal effect damage risk factor, the dynamic thermal safety margin, and the operation efficiency coefficient at the current time are obtained in the embodiment.

[0069] Step S3: The thermal effect damage risk factor, the dynamic thermal safety margin, and the operation efficiency coefficient at the current time are integrated to obtain the linear adjustment coefficient of the electrotome power; and the linear adjustment coefficient is used to adjust the electrotome power.

[0070] In the embodiment, the thermal effect damage risk factor, the dynamic thermal safety margin, and the operation efficiency coefficient at the current time are obtained in step S2. Next, the three parameters are integrated to determine the linear adjustment coefficient of the electrotome power, and then the real-time adjustment of the electrotome power is realized.

[0071] Specifically, the difference between the preset first value and the operation efficiency coefficient η is calculated, and the difference is denoted as a second difference. In the embodiment, the preset first value is 2, that is, the second difference is 2-η. When η is at a low level, that is, the system efficiency is insufficient, the value of 2-η increases, which preferentially guarantees the operation energy output efficiency when weakening the power reduction amplitude caused by the dynamic thermal safety margin and the damage risk probability caused by thermal radiation, thereby avoiding affecting the operation process due to excessive power reduction. When the value of η is too large, it indicates that the system has efficiency redundancy, and the value of 2-η decreases, allowing a larger amplitude of power reduction, giving priority to safety, and preventing potential tissue damage risks caused by excess energy.

[0072] Based on the above characteristics, the product of the thermal effect damage risk factor, the dynamic thermal safety margin and the second difference at the current time is taken as the linear adjustment coefficient of the electrotome power.

[0073] To achieve precise regulation of the electrotome power, the linear adjustment coefficient and the power adaptation range of the breast surgery are combined to construct a regulation formula, wherein the power adaptation range corresponding to different breast surgery types and tissues is determined through clinical data statistics. For different surgery types such as open resection, breast conservation, axillary dissection, and different tissues such as fat, gland, and fibrous connective tissue, a large number of safe and efficient power output intervals in surgery cases are collected, and finally the minimum safe power and the maximum safe power in each scenario are determined and stored in the system database.

[0074] Then, the minimum safe power and the maximum safe power in the current breast surgery scenario are used to normalize the output power at the current time by using the range normalization method, the product of the normalized value of the output power at the current time and the linear adjustment coefficient is calculated, and the product is recorded as the third product; the difference obtained by subtracting the third product from the preset second value is recorded as the third difference. When the linear adjustment coefficient increases, the thermal safety demand increases, and the third difference decreases. At this time, the power should be reduced, and when the safe power range is wide, the power corresponding to the same linear adjustment coefficient decreases more gently, avoiding excessive adjustment; when the safe range is narrow, the adjustment is more sensitive, ensuring that the power does not exceed the safe interval. Further, the product of the output power at the current time and the third difference is taken as the adjusted power of the electrotome, and the adjusted power is adjusted. In this embodiment, the preset second value is 1, which can be set according to specific circumstances in specific applications.

[0075] It should be noted that based on the response speed of the electrotome power adjustment and the frequency of tissue state changes, the adjusted power is calculated synchronously, and the output power at the current time is linearly and smoothly transitioned to the adjusted power. At the same time, the system monitors whether it is in the specified interval in real time. If it exceeds the specified interval, it is automatically clamped to the nearest boundary value, ensuring that the power is always within the safe range.

[0076] In the process of controlling the electrotome during breast surgery, in order to discover potential risks in the surgery in time and ensure the safety of the surgery, the system can trigger an early warning by monitoring the deviation of key parameters, as follows:

[0077] (1) Power out-of-range early warning: when the actual output power of the electrotome exceeds the safe interval for 0.05 seconds continuously for 3 consecutive sampling periods, the system determines that the power is out of range; at this time, the master control unit drives the audible and visual alarm device to issue intermittent prompt sound, the corresponding area of the display screen flashes red light, and the deviation of the current power value and the safe interval is displayed in real time on the display screen, reminding the doctor to check the working state of the electrotome or adjust the operation.

[0078] (2) Thermal safety margin sudden change warning: calculate the change amount of dynamic thermal safety margin within 0.5 seconds, if the change amount is greater than the safety threshold, it indicates that the thermal safety margin changes rapidly, and the organization faces the risk of sudden thermal injury, the system immediately issues a continuous alarm sound, and at the same time triggers a vibration feedback on the handle controller, prompting the doctor to pause the operation and evaluate the tissue state. In this embodiment, the safety threshold is set to 0.5, and in specific applications, the implementer can set it according to the specific circumstances.

[0079] All the above warning information is stored synchronously to the log system of the control terminal, including trigger time, parameter value, processing result, etc., which is convenient for postoperative tracing and system optimization. The warning mechanism covers common risk scenarios such as power abnormalities, thermal risk mutations, and physical contact problems through multi-dimensional parameter monitoring, achieving comprehensive safety monitoring of the surgical process.

[0080] At this point, the method provided in this embodiment has completed the fine control of the electrotome and thermal radiation in the breast surgery process.

[0081] This embodiment first evaluates the damage risk caused by thermal radiation according to the change characteristics of the instantaneous impedance data in the current period and the initial state of the instantaneous impedance of each time in the current period, obtains the thermal effect damage risk factor of each time in the current period, and accurately quantifies the real-time thermal damage risk; then, combined with the fluctuation characteristics of the thermal effect damage risk factor in the current period, the change of the instantaneous impedance data and the duration of the energy output, the time cumulative effect is evaluated, and the dynamic thermal safety margin of the current time is obtained; At the same time, the surgical efficiency coefficient is introduced to establish a flexible balance between safety and efficiency, and the surgical efficiency coefficient is obtained, which optimizes the power output while ensuring the basic cutting efficiency; the linear adjustment coefficient is determined by comprehensively considering the thermal effect damage risk factor, the dynamic thermal safety margin and the surgical efficiency coefficient at the current time, and then the linear adjustment coefficient is used to control the power of the electrotome in the breast surgery process, avoiding step response and ensuring the safety of the surgery. The breast surgery electrotome and thermal radiation fine control system provided in this embodiment significantly reduces the low thermal damage risk in the breast surgery process, ensures the effect of breast surgery, and provides more reliable energy instrument support for breast surgery.

[0082] It should be noted that: the above only describes the preferred embodiments of the present application, and does not limit the present application, any modification, equivalent replacement, improvement, etc. within the principles of the present application shall be included in the protection scope of the present application.

Claims

1. A breast surgery electrotome and heat radiation fine control system, characterized by, The system comprises a memory and a processor, and the processor executes a computer program stored in the memory to realize the following steps: Obtaining the instantaneous impedance data between the working electrode and the return electrode in the current period, wherein the current period is a period in the breast surgery process, and the current time is the last time in the current period; According to the change characteristics of the instantaneous impedance data in the current period and the initial state of the instantaneous impedance data of each time in the current period, the thermal effect damage risk factor of each time in the current period is obtained; according to the fluctuation characteristics of the thermal effect damage risk factor in the current period, the change of the instantaneous impedance data and the duration of the energy output, the dynamic thermal safety margin is obtained; the surgical efficiency coefficient is determined based on the output power of the current time; Comprehensive thermal effect damage risk factor, dynamic thermal safety margin and surgical efficiency coefficient of the current time, obtain the linear adjustment coefficient of the electrosurgical power; adjust the electrosurgical power by using the linear adjustment coefficient.

2. The breast surgery electrosurgical and thermal radiation fine control system of claim 1, wherein, According to the change characteristics of the instantaneous impedance data in the current period and the initial state of the instantaneous impedance data of each time in the current period, the thermal effect damage risk factor of each time in the current period is obtained, including: Based on the impedance characteristic value of each time in the current period, the instantaneous change rate of each time is obtained; wherein the impedance characteristic value is obtained by calculating the first difference value between the instantaneous impedance data of each time and the initial time of the same period, and the ratio between the first ratio and the instantaneous impedance data of the initial time of the same period is taken as the impedance characteristic value of each time; Based on the instantaneous change rate of each time in the current period, the thermal effect damage risk factor of each time in the current period is determined.

3. The breast surgery electrosurgical and thermal radiation fine control system of claim 2, wherein, Based on the instantaneous change rate of each time in the current period, the thermal effect damage risk factor of each time in the current period is determined, including: Based on the instantaneous change rate of each time, the corresponding sign function value of each time is obtained by means of sign function; the absolute value of the ratio between the cumulative sum of the sign function values of all times in the current period and the total number of times in the current period is recorded as the continuous change state value; The product of the instantaneous change rate of each time and the continuous change state value is taken as the actual impedance change rate of each time; the normalized result of the product between the actual impedance change rate of each time and its impedance characteristic value is determined as the thermal effect damage risk factor of each time.

4. The breast surgery electrosurgical and thermal radiation fine control system of claim 3, wherein, According to the fluctuation characteristics of the thermal effect damage risk factor in the current period, the change of the instantaneous impedance data and the duration of the energy output, the dynamic thermal safety margin is obtained, including: Based on the fluctuation characteristics of the thermal effect damage risk factor of all times in the current period, the heat sensitivity is obtained; The sum of the absolute values of the actual impedance change rates of all times in the current period is recorded as the first sum value; the range of the actual impedance change rates of all times in the current period is obtained; the first ratio between the first sum value and the range is calculated; the product of the reciprocal of the sampling frequency and the first ratio is recorded as the heat dissipation factor; According to the duration of the energy output of the current time and the heat dissipation factor, the time accumulation factor is obtained; The normalized product of the time accumulation factor and the thermal sensitivity is determined as the dynamic thermal safety margin.

5. The breast surgery electrosurgical and thermal radiation fine control system of claim 4, wherein, The thermal sensitivity is obtained based on fluctuation characteristics of the thermal effect damage risk factor at all time points in the current period, and the thermal sensitivity is determined as a standard deviation of the thermal effect damage risk factor at all time points in the current period, the standard deviation being used to represent the fluctuation characteristics of the thermal effect damage risk factor.

6. The breast surgery electrosurgical and thermal radiation fine control system of claim 4, wherein, The time accumulation factor is obtained according to the duration of the energy output at the current time point and the heat dissipation factor, and the time accumulation factor is determined as a ratio of the duration of the energy output at the current time point to the heat dissipation factor. A second ratio of the duration of the energy output at the current time point to the heat dissipation factor is calculated. The time accumulation factor is obtained based on the second ratio, and the second ratio is in positive correlation with the time accumulation factor.

7. The breast surgery electrosurgical and thermal radiation fine control system of claim 1, wherein, The surgical efficiency coefficient is determined based on the output power at the current time point, and the surgical efficiency coefficient is determined as a ratio between the output power at the current time point and a preset reference power. The surgical efficiency coefficient is determined based on the output power at the current time point, and the surgical efficiency coefficient is determined as a ratio between the output power at the current time point and a preset reference power.

8. The breast surgery electrosurgical and thermal radiation fine control system of claim 1, wherein, The linear adjustment coefficient of the electrosurgical power is obtained by comprehensively considering the thermal effect damage risk factor at the current time point, the dynamic thermal safety margin and the surgical efficiency coefficient, and the linear adjustment coefficient of the electrosurgical power is determined as a product of the thermal effect damage risk factor at the current time point, the dynamic thermal safety margin and a second difference between a preset first value and the surgical efficiency coefficient. The second difference between the preset first value and the surgical efficiency coefficient is calculated. The linear adjustment coefficient of the electrosurgical power is obtained by comprehensively considering the thermal effect damage risk factor at the current time point, the dynamic thermal safety margin and the surgical efficiency coefficient, and the linear adjustment coefficient of the electrosurgical power is determined as a product of the thermal effect damage risk factor at the current time point, the dynamic thermal safety margin and a second difference between a preset first value and the surgical efficiency coefficient.

9. The breast surgery electrosurgical and thermal radiation fine control system of claim 1, wherein, The third difference between the preset second value and the third product is calculated. The electrosurgical power at the current time point is adjusted by using the third difference. The electrosurgical power at the current time point is adjusted by using the third difference, and the product of the output power at the current time point and the third difference is used as the adjusted electrosurgical power. ​ 10. The breast surgery electrosurgical and thermal radiation fine control system of claim 9, wherein, ​

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