Control device, method and system for an ultrasonic hemostatic surgical system

Abstract

The application relates to the technical field of medical equipment, and discloses a control device, method and system of an ultrasonic hemostasis operation system, the control device comprising: a current parameter value acquisition module, which is used for acquiring a current parameter value collected in an energy output process of the ultrasonic hemostasis operation system, the current parameter value comprising a current impedance value and a current frequency value; a current tissue state indication value determination module, which is used for determining a current tissue state indication value based on the current parameter value; and a power adjustment module, which is used for determining a current target power value based on the current tissue state indication value and the current impedance value, and adjusting a power value to the target power value. The application can make the energy output of the ultrasonic hemostasis operation system during blood vessel closure match actual demand.

Description

Technical Field

[0001] This invention relates to the field of medical equipment technology, and specifically to a control device, method and system for an ultrasonic hemostasis surgical system. Background Technology

[0002] Ultrasonic hemostasis surgery systems are medical devices that use high-frequency ultrasonic energy for surgical cutting and hemostasis, playing a crucial role in vascular closure. The probe of an ultrasonic hemostasis surgery system vibrates at extremely high frequencies. When it comes into contact with tissue, it creates a cavitation effect, causing rapid vaporization of water within the tissue, breakage of protein hydrogen bonds, and protein denaturation and coagulation, thereby achieving blood vessel closure and hemostasis. When using ultrasonic hemostasis surgery systems for vascular closure, related technologies generally employ impedance or frequency threshold plus time control during energy output to achieve different levels of energy (i.e., power) at different times. However, blood vessels of different diameters, thicknesses, and tissue compositions require different energy profiles. Simply adjusting the output energy according to impedance or frequency thresholds may lead to a mismatch between energy output and actual needs. This mismatch mainly includes two situations: 1. Insufficient energy, which leads to incomplete vascular closure and a higher risk of postoperative bleeding; 2. Excessive energy, which can cause tissue carbonization and adhesion, increasing the risk of complications. Summary of the Invention

[0003] In view of this, the present invention provides a control device, method and system for an ultrasonic hemostasis surgical system to solve the problem of mismatch between energy output and actual needs when the ultrasonic hemostasis surgical system performs vascular closure.

[0004] In a first aspect, the present invention provides a control device for an ultrasonic hemostasis surgical system, the device comprising:

[0005] The current parameter value acquisition module is used to acquire the current parameter values ​​collected during the energy output process of the ultrasonic hemostasis surgery system. The current parameter values ​​include the current impedance value and the current frequency value.

[0006] The current organization status indicator value determination module is used to determine the current organization status indicator value based on the current parameter value;

[0007] The power adjustment module is used to determine the current target power value based on the current tissue status indication value and the current impedance value, and adjust the power value to the target power value.

[0008] In one optional implementation, the current organization status indicator value determination module includes:

[0009] The first acquisition unit is used to acquire the first and second derivatives of the current impedance value and to acquire the impedance spectrum characteristics of the tissue.

[0010] The current tissue status indication value calculation unit is used to determine the current tissue status indication value based on the first and second derivatives of the current impedance value, the impedance spectrum characteristics, and the current frequency value.

[0011] In one optional implementation, the current tissue state indicator value is used to indicate the current tissue state, which includes four types, corresponding to the four stages of blood vessel closure: the initial stage, the protein denaturation stage, the fusion stage, and the solidification stage.

[0012] In one optional implementation, the current tissue state indication value calculation unit is specifically used to perform a weighted summation of the first and second derivatives of the current impedance value, the impedance spectrum characteristics, and the current frequency value to obtain the current tissue state indication value.

[0013] In one optional implementation, the weighting coefficients for the weighted summation of the first and second derivatives of the current impedance value, the impedance spectral characteristics, and the current frequency value are determined based on the ratio of the duration of the four stages to the total duration during the experiment.

[0014] In one optional implementation, the power adjustment module includes:

[0015] The second acquisition unit is used to acquire the first and second derivatives of the current impedance value and to acquire the initial startup power value.

[0016] The target power value determination unit is used to determine the target power value based on the first and second derivatives of the current impedance value, the initial startup power value, and the current tissue status indication value.

[0017] In one optional implementation, the target power value determination unit is specifically used for:

[0018] Calculate the first product of the first control parameter and the first derivative of the current impedance value; calculate the second product of the second control parameter and the second derivative of the current impedance value.

[0019] Calculate the sum of the first product, the second product, and 1, and use it as the first value;

[0020] Multiply the first value by the initial startup power value to obtain the second value;

[0021] Calculate the product of the third control parameter and the current tissue state indication value, and use it as the third value;

[0022] Calculate the value of the exponential function with the negative third value as the exponent;

[0023] The target power value is obtained by multiplying the second value by the exponential function value.

[0024] In one optional implementation, the values ​​of the first control parameter, the second control parameter, and the third control parameter are determined by an in vitro burst pressure experiment. During the in vitro burst pressure experiment, one of the first control parameter, the second control parameter, and the third control parameter is selected as the target control parameter each time by using the controlled variable method, and the target control parameter is changed to obtain the value corresponding to the peak burst pressure when the blood vessel closure is completed as the value of the target control parameter.

[0025] In one optional embodiment, the control device of the ultrasonic hemostasis surgical system further includes:

[0026] A phase difference acquisition module is used to acquire the current-voltage phase difference during the energy output process of the ultrasonic hemostasis surgical system;

[0027] The frequency adjustment module is used to adjust the driving frequency so that the phase difference between the current and voltage is reduced.

[0028] In one alternative implementation, the step size for adjusting the driving frequency is determined based on the current current-voltage phase difference and the phase margin, wherein the phase margin is determined based on the difference between the anti-resonant frequency and the resonant frequency of the ultrasonic hemostasis surgical system.

[0029] The resonant frequency and the anti-resonant frequency are the frequencies corresponding to the first detection of a current-voltage phase difference of 0° and the second detection of a current-voltage phase difference of 0° during the process of the driving frequency increasing from low to high.

[0030] In one alternative implementation, the step size is determined based on the current-voltage phase difference, the phase margin, and the difference calibration coefficient.

[0031] The difference calibration coefficient is determined based on the ratio of the difference between the first resonant frequency and the second resonant frequency to the preset duration. The first resonant frequency and the second resonant frequency are the initial resonant frequency and the end resonant frequency of the ultrasonic hemostasis surgery system before and after the preset duration of no-load output.

[0032] In one optional embodiment, the control device of the ultrasonic hemostasis surgical system further includes:

[0033] The first acquisition module is used to acquire the first and second derivatives of the current impedance value, and to acquire the current resonant frequency and the initial resonant frequency of the ultrasonic hemostasis surgery system.

[0034] The second acquisition module is used to acquire a condensation indication value based on the first and second derivatives of the current impedance value, the current resonant frequency, and the initial resonant frequency.

[0035] The stop module is used to determine that condensation is complete and stop energy output if the condensation indicator value meets the condensation completion judgment condition.

[0036] In one optional implementation, the second acquisition module is specifically used for:

[0037] Calculate the difference between the current resonant frequency and the initial resonant frequency, and calculate the absolute value of the ratio of the difference to the initial resonant frequency;

[0038] The fourth value is obtained by multiplying the absolute value of the ratio by the first threshold parameter.

[0039] The fifth value is obtained by multiplying the absolute value of the second derivative with the second threshold parameter.

[0040] The sum of the absolute value of the first derivative, the fourth value, and the fifth value is used as the condensation indicator value.

[0041] In one optional implementation, the condensation completion judgment condition is that the condensation indication value is less than a first preset threshold and the duration is greater than a second preset threshold.

[0042] Secondly, the present invention provides a control method for an ultrasonic hemostasis surgical system, the method comprising:

[0043] During the energy output process of the ultrasonic hemostasis surgical system, the current parameter values ​​collected include the current impedance value and the current frequency value;

[0044] Based on the current parameter values, determine the current organization status indication value;

[0045] Based on the current tissue status indication value and the current impedance value, the current target power value is determined, and the power value is adjusted to the target power value.

[0046] In some optional implementations, determining the current organization status indication value based on the current parameter value includes:

[0047] The first acquisition unit is used to acquire the first and second derivatives of the current impedance value and to acquire the impedance spectrum characteristics of the tissue.

[0048] The current tissue status indication value calculation unit is used to determine the current tissue status indication value based on the first and second derivatives of the current impedance value, the impedance spectrum characteristics, and the current frequency value.

[0049] Thirdly, the present invention provides an ultrasonic hemostasis surgical system, comprising: a control device for the ultrasonic hemostasis surgical system of the second aspect above or any corresponding embodiment thereof.

[0050] Fourthly, the present invention provides an ultrasonic hemostasis surgical system, comprising: a memory and a processor, wherein the memory and the processor are communicatively connected to each other, the memory stores computer instructions, and the processor executes the computer instructions to perform the control method of the ultrasonic hemostasis surgical system of the second aspect above or any corresponding embodiment thereof.

[0051] Fifthly, the present invention provides a computer-readable storage medium storing computer instructions for causing a computer to perform the control method of the ultrasonic hemostasis surgical system of the second aspect or any corresponding embodiment described above.

[0052] In a sixth aspect, the present invention provides a computer program product, including computer instructions for causing a computer to execute the control method of the ultrasonic hemostasis surgical system of the second aspect or any corresponding embodiment described above.

[0053] The control device, method, and system of the ultrasonic hemostasis surgical system provided in this invention simultaneously analyze tissue impedance and frequency, that is, through multi-parameter fusion analysis, identify the closure state of the tissue, thereby dynamically adjusting the power (i.e., energy output value) of the ultrasonic hemostasis surgical system during the vascular closure process, so as to continuously adjust the output energy level according to the changes in the tissue state and complete the reliable closure of the blood vessel. Attached Figure Description

[0054] To more clearly illustrate the technical solutions in the specific embodiments or related technologies of the present invention, the drawings used in the description of the specific embodiments or related technologies will be briefly introduced below. Obviously, the drawings described below are some embodiments of the present invention. For those skilled in the art, other drawings can be obtained from these drawings without creative effort.

[0055] Figure 1 This is a schematic diagram of the components of an ultrasonic hemostatic scalpel head;

[0056] Figure 2 This is a schematic block diagram of the control device of the ultrasonic hemostasis surgical system according to an embodiment of the present invention;

[0057] Figure 3This is a schematic diagram comparing the temperature change curve during the vascular coagulation process according to an embodiment of the present invention with the temperature change curve of a conventional method.

[0058] Figure 4 This is a hardware schematic block diagram of an ultrasonic hemostasis surgical system according to an embodiment of the present invention;

[0059] Figure 5 This is a schematic block diagram of a circuit structure for obtaining phase difference according to an embodiment of the present invention;

[0060] Figure 6 This is a schematic diagram of the delay N between two square wave signals obtained by passing a current signal and a voltage signal through a zero-comparison circuit according to an embodiment of the present invention.

[0061] Figure 7 This is a schematic diagram of the driving frequency tracking process according to an embodiment of the present invention;

[0062] Figure 8 This is a schematic flowchart of the control method for an ultrasonic hemostasis surgical system according to an embodiment of the present invention;

[0063] Figure 9 This is a schematic diagram of the overall flow of the control method of the ultrasonic hemostasis surgical system according to an embodiment of the present invention;

[0064] Figure 10 This is a schematic diagram of the hardware structure of the ultrasonic hemostasis surgical system according to an embodiment of the present invention. Detailed Implementation

[0065] To make the objectives, technical solutions, and advantages of the embodiments of the present invention clearer, the technical solutions of the embodiments of the present invention will be clearly and completely described below with reference to the accompanying drawings. Obviously, the described embodiments are only some embodiments of the present invention, not all embodiments. Based on the embodiments of the present invention, all other embodiments obtained by those skilled in the art without creative effort are within the scope of protection of the present invention.

[0066] Ultrasonic hemostasis surgical systems include ultrasonic hemostatic knives, such as... Figure 1 As shown, the ultrasonic hemostatic knife head includes a handle 1, a gasket 2, and a clamp 3.

[0067] When using an ultrasonic hemostasis surgical system to close blood vessels, the clamp 3 closes, and the tissue is clamped between the pad 2 and the blade (also known as a waveguide rod) 1. The blade generates a high-frequency vibration of 55kHz, which simultaneously produces cavitation, thermal, and mechanical effects. This causes the tissue being cut (such as blood vessels) to emulsify into an emulsion, while generating a large amount of local heat, which denatures the tissue proteins, thus achieving the effect of cutting and coagulating the tissue.

[0068] This embodiment provides a control device for an ultrasonic hemostasis surgical system. As used below, the term "module" can refer to a combination of software and / or hardware that implements a predetermined function. Although the device described in the following embodiments is preferably implemented in software, hardware implementation, or a combination of software and hardware, is also possible and contemplated.

[0069] This embodiment provides a control device for an ultrasonic hemostasis surgical system, such as... Figure 2 As shown, it includes:

[0070] The current parameter value acquisition module 201 is used to acquire the current parameter values ​​collected during the energy output process of the ultrasonic hemostasis surgery system. The current parameter values ​​include the current impedance value and the current frequency value.

[0071] Specifically, during the energy output process of the ultrasonic hemostasis surgical system, the current impedance value Z(t), frequency value F(t), phase difference Phase(t), and power value P(t) can be periodically acquired. The periodic acquisition period can be, for example, 10 ms. The current impedance value can refer to the current impedance value of the tissue, such as the current impedance value of a blood vessel. The current frequency value can be the frequency value after resonant frequency tracking. Resonant frequency tracking refers to adjusting the driving frequency of the ultrasonic hemostasis surgical system in real time to make it as close as possible to the current resonant frequency. During the operation of the ultrasonic hemostasis surgical system (i.e., during energy output), such as during tissue cutting, the resonant frequency changes in real time due to factors such as the temperature rise of the cutting head and changes in load.

[0072] The current organization status indication value determination module 202 is used to determine the current organization status indication value based on the current parameter value.

[0073] The power adjustment module 203 is used to determine the current target power value based on the current tissue state indication value and the current impedance value, and adjust the power value to the target power value. Adjusting the power of the ultrasonic hemostasis surgical system means adjusting the output energy of the ultrasonic hemostasis surgical system.

[0074] A key aspect of vascular closure using an ultrasonic hemostasis system is controlling the energy level during the closure process. Single impedance or frequency threshold methods are easily affected by tissue fluid, the thickness of the clamped tissue, the force applied, and the amount of tissue grasped, resulting in a high misjudgment rate. Furthermore, when using an ultrasonic hemostasis system for vascular closure, if energy control does not correspond to the tissue state during the process, vascular closure will fail, failing to meet clinical burst pressure requirements.

[0075] In this embodiment of the invention, tissue impedance and frequency are analyzed simultaneously. That is, through multi-parameter fusion analysis, the closure state of the tissue is identified, thereby dynamically adjusting the power (i.e., energy output value) of the ultrasonic hemostasis surgical system during the vascular closure process. This enables the output energy level to be continuously adjusted according to the changes in the tissue state, thus completing the reliable closure of the blood vessel.

[0076] Specifically, such as Figure 3 As shown, the control scheme of the ultrasonic hemostasis surgical system provided in this embodiment of the invention, compared with the conventional control scheme, can achieve the following:

[0077] 1. At the beginning of coagulation, the energy applied to the tissue can be adjusted according to the tissue's condition, so that the temperature rises relatively quickly to near the temperature required for vascular coagulation.

[0078] 2. During the coagulation process, the energy can be continuously adjusted to maintain the tissue temperature near a level conducive to vascular coagulation, preventing it from rising too high until coagulation is complete. Conventional control methods, on the other hand, can cause the tissue temperature to rise continuously, affecting the coagulation effect and even posing a risk of charring and blackening of the tissue.

[0079] In some optional embodiments, the current organization status indicator value determination module 202 includes:

[0080] The first acquisition unit is used to acquire the first and second derivatives of the current impedance value and to acquire the impedance spectrum characteristics of the tissue.

[0081] The current tissue status indication value calculation unit is used to determine the current tissue status indication value based on the first and second derivatives of the current impedance value, the impedance spectrum characteristics, and the current frequency value.

[0082] Specifically, the formulas for calculating the first and second derivatives of the current impedance value are as follows:

[0083] First derivative:

[0084] Second derivative:

[0085] in, It is the impedance value at the current time t (i.e., the current impedance value). This refers to the sampling time interval. As mentioned above, the current impedance value Z(t), frequency value F(t), phase difference Phase(t), and power value P(t) can be periodically collected during the energy output process of the ultrasonic hemostasis surgical system. The periodic collection period can be, for example, 10ms. The corresponding time is 10ms.

[0086] Furthermore, the impedance spectrum characteristics of tissues can be extracted using the Discrete-Time Fourier Transform (DTFT), which maps discrete-time sequences to periodic spectra in the continuous frequency domain. This paper utilizes the Discrete-Time Fourier Transform to extract the impedance spectrum characteristics of tissues. The calculation formula is:

[0087]

[0088] in, It is a discrete tissue impedance signal (specifically, impedance values ​​collected periodically). , It is the sampling frequency. It is the sample number that was sampled. It is the sampling interval (for example, it can be 10ms).

[0089] Discrete-time Fourier transform is used to analyze the spectral characteristics of impedance signals. Frequency domain features of tissue electrical properties are extracted, providing a more comprehensive analysis than traditional time-domain analysis.

[0090] In this embodiment, multimodal parameters are used to adjust the power value of the ultrasonic hemostasis surgical system. Specifically, it not only combines the frequency and the rate of change of tissue impedance (i.e., the first derivative of impedance), but also introduces the second derivative parameter of impedance and impedance spectrum characteristics as key indicators for judging the vascular closure status. This allows for more precise and accurate adjustment of ultrasonic energy based on tissue status, replacing the conventional method of using tissue impedance or frequency plus time for judgment. It is not affected by the thickness of the clamped tissue or the force of gripping the tissue, and can continuously adjust the appropriate energy range during the vascular coagulation process.

[0091] In some optional embodiments, the current tissue state indicator value is used to indicate the current tissue state, which includes four types, corresponding to the four stages of blood vessel closure: the initial stage, the protein denaturation stage, the fusion stage, and the solidification stage.

[0092] In this embodiment, the vascular closure process is divided into four characteristic stages, each corresponding to different energy controls. The tissue changes in each stage are as follows:

[0093] 1. Initial stage: Tissue moisture evaporates, and impedance rises slowly. Impedance is around 100 ohms. Temperature: 30~40℃.

[0094] 2. Protein denaturation stage: Collagen fibers shrink, and impedance rises rapidly. The impedance rises to around 200 ohms at a temperature of 40-60℃.

[0095] 3. Fusion stage: Molecular reorganization occurs, and impedance reaches its peak. Impedance is maintained at 200 ohms to 250 ohms at a temperature of 70℃.

[0096] 4. Curing stage: A stable closed layer is formed, and the impedance begins to decrease. The impedance drops from 250 ohms to around 150 ohms, while the temperature rises to 80℃.

[0097] In some optional embodiments, the current tissue state indication value calculation unit is specifically used to perform a weighted summation of the first and second derivatives of the current impedance value, the impedance spectrum characteristics, and the current frequency value to obtain the current tissue state indication value.

[0098] Specifically, the current organizational status indicator value It can be calculated using the following formula:

[0099]

[0100] The above formula can be called the organizational status assessment function. Wherein, This is the current organizational status indicator value. F(t) is the impedance spectrum characteristic of the organization, F(t) is the tracking resonant frequency at the current time t, and α, β, γ, δ are weighting coefficients.

[0101] In some optional implementations, the weighting coefficients for the weighted summation of the first and second derivatives of the current impedance value, the impedance spectral characteristics, and the current frequency value are determined based on the ratio of the duration of the four stages to the total duration during the experiment.

[0102] Specifically, the weighting coefficients when performing a weighted summation of the first and second derivatives of the current impedance value, the impedance spectral characteristics, and the current frequency value. The sum can be 1, that is... During the experiment of vascular closure, the temperature of the affected tissue can be detected using an infrared thermometer, and based on the impedance of the tissue, four characteristic stages of the vascular closure process can be identified, with the duration of each stage recorded. Then calculate the weighting coefficients according to the following formulas. :

[0103] , , ,

[0104] in, .

[0105] In other optional embodiments, the weighting coefficients for the weighted summation of the first and second derivatives of the current impedance value, the impedance spectral characteristics, and the current frequency value can also be determined using a deep learning model. The process of determining these weighting coefficients using a deep learning model can be, for example:

[0106] 1. Collect vascular coagulation resonant frequency and impedance data from isolated animal tissues, with at least 200 sets of data, each set containing complete data from the start to the end of coagulation.

[0107] 2. Based on the above method for judging temperature and impedance parameters, the data corresponding to the four different stages are divided by human judgment. After cleaning and standardization, the data are divided into training / validation / test sets according to the proportion to obtain the data corresponding to the four coefficients α, β, γ, and δ.

[0108] 3. Construct an adaptation model (static model using Fully Convolutional Network (FCN), dynamic model using attention mechanism), and train it using software to obtain the learning metric contribution.

[0109] 4. Extract and normalize the model weights, and verify their performance (e.g., in R). 2 After optimization based on accuracy and clinical logic verification, the weighting coefficients α, β, γ, and δ were finally determined.

[0110] In some optional embodiments, the power adjustment module 203 includes:

[0111] The second acquisition unit is used to acquire the first and second derivatives of the current impedance value and to acquire the initial startup power value.

[0112] The target power value determination unit is used to determine the target power value based on the first and second derivatives of the current impedance value, the initial startup power value, and the current tissue status indication value.

[0113] In some optional embodiments, the target power value determination unit is specifically used to: calculate the first control parameter. The first derivative with respect to the current impedance value First product, calculate the second control parameter The second derivative with respect to the current impedance value The second product; calculate the first product. The second product And the sum of 1, as the first value. ; the first value With the initial startup power value Multiply to get the second value. ; Calculate the third control parameter Compared with the current organization status indicator value The product of these is used as the third value. ; calculate the negative third value The value of the exponential function of the exponent. ; the second value Multiply by the value of the exponential function The target power value is obtained. .

[0114] That is, the target power value The calculation formula is:

[0115]

[0116] in, The target power value, i.e., the current time. Ultrasonic hemostasis surgical systems require real-time power output. It is the initial starting power of the ultrasonic hemostasis surgical system ( The value is between 20-25W. For the current moment, , , These are the first control parameter, the second control parameter, and the third control parameter, respectively, and their values ​​range from 0 to 1.

[0117] In this embodiment, the current organization status indicator value was obtained. In other words, once the current state of the organization is known, the current moment can be calculated. Ultrasonic hemostasis surgical systems require real-time power output to achieve adaptive energy output control.

[0118] Furthermore, the energy adaptive control method for the ultrasonic hemostasis surgical system based on multi-parameter fusion analysis provided in this invention can ensure that the energy does not exceed the energy safety range corresponding to the current tissue state. Specifically, this invention focuses on the dynamic changes in tissue electrical properties (impedance, frequency) during vascular closure, and performs multi-parameter (including impedance, frequency, and frequency domain information of impedance, etc.) fusion analysis to obtain the tissue state (i.e., the vascular closure state). This can avoid tissue thermal damage caused by excessive energy and also has good adaptability to abnormal tissue states (such as calcified blood vessels).

[0119] In some optional implementations, the values ​​of the first control parameter, the second control parameter, and the third control parameter are determined by an in vitro burst pressure experiment. During the in vitro burst pressure experiment, one of the first control parameter, the second control parameter, and the third control parameter is selected as the target control parameter each time by using the controlled variable method, and the target control parameter (the value of the target control parameter varies between 0 and 1) is changed. The value corresponding to the peak burst pressure when the blood vessel clotting is completed is obtained as the value of the target control parameter.

[0120] like Figure 4 The hardware block diagram of the ultrasonic hemostasis surgical system shown illustrates its working principle: the power input is adjusted to the required DC voltage by a voltage regulator circuit, and then converted into a high-frequency sinusoidal signal by a power amplifier circuit (i.e., power amplifier circuit) and a power transformer, driving the transducer to generate high-frequency vibration. During the process of vascular closure using the ultrasonic hemostasis surgical system, the resonant frequency of the system changes in real time due to the temperature rise of the cutting head and changes in the load. To ensure maximum output efficiency, automatic frequency modulation technology is needed to keep the transducer operating at the same phase point (i.e., the resonant point). In this embodiment, the phase difference is calculated by sampling the output voltage and current signals, and the processor adjusts the digital frequency synthesizer according to the phase difference to ensure that the output frequency always tracks the resonant frequency. The following example illustrates the real-time resonant frequency tracking technology.

[0121] In some optional embodiments, the control device of the ultrasonic hemostasis surgical system further includes:

[0122] The phase difference acquisition module is used to acquire the current-voltage phase difference during the energy output process of the ultrasonic hemostasis surgery system; specifically, the current-voltage phase difference can be the current-voltage phase difference output by the energy output circuit of the ultrasonic hemostasis surgery system.

[0123] The frequency adjustment module is used to adjust the driving frequency to reduce the current-voltage phase difference. During the frequency adjustment process, the current-voltage phase difference also needs to be acquired to determine in real time whether the phase difference has decreased.

[0124] An ultrasonic hemostasis surgical system can only achieve its intended goal by outputting energy at resonance. Otherwise, it is not at the resonance point, resulting in very high impedance and minimal or almost no amplitude of the scalpel, failing to achieve the purpose of tissue cutting. Therefore, it is necessary to control and track the resonant frequency. Furthermore, the adaptive energy output control provided in the above embodiment also requires accurate resonant frequency. Therefore, this embodiment provides a technical solution for real-time resonant frequency tracking.

[0125] Specifically, such as Figure 5As shown, the phase difference between the current and voltage at the output terminal of the energy output circuit of the ultrasonic hemostasis surgical system can be calculated through the following process:

[0126] The current and voltage signals at the output of the energy output circuit are acquired using current and voltage sensors, respectively. These acquired signals are sinusoidal, and a square wave signal can be obtained through a zero-crossing comparator circuit. Finally, the processor calculates the delay N between the two square waves (e.g., N = N / V). Figure 6 As shown in the figure, combined with the current driving frequency period M, the phase difference θ = (N / M) × 360° is calculated.

[0127] In some optional embodiments, the step size for adjusting the driving frequency is determined based on the current current-voltage phase difference and the phase margin, which is determined based on the difference between the anti-resonant frequency and the resonant frequency of the ultrasonic hemostasis surgical system.

[0128] The resonant frequency and the anti-resonant frequency are the frequencies corresponding to the first detection of a current-voltage phase difference of 0° and the second detection of a current-voltage phase difference of 0° during the process of the driving frequency increasing from low to high.

[0129] Specifically, the resonant frequency and anti-resonant frequency of the ultrasonic hemostasis surgical system can be obtained by frequency sweeping (lasting 1-2 seconds). That is, as... Figure 7 As shown, after the ultrasonic hemostasis surgical system (unloaded) is started, the driving frequency is increased from low to high, and the phase difference of current and voltage is detected in real time. When the phase difference is detected for the first time to be 0°, the frequency at this time is recorded as the resonant frequency Fs; when the phase difference is detected for the second time to be 0°, the frequency at this time is recorded as the anti-resonant frequency Fp, and the phase margin W = Fp - Fs.

[0130] In this embodiment, the starting drive frequency (also called the operating frequency) of the ultrasonic hemostasis surgical system is the resonant frequency obtained by frequency sweeping as described above. For example... Figure 7 As shown, during the operation of the ultrasonic hemostasis surgical system (i.e., during energy output), the phase difference is sampled periodically, and the driving frequency is adjusted according to the change in the phase difference. When the phase difference decreases, it indicates that the driving frequency adjustment direction is correct, and the frequency should be increased or decreased. When the phase difference increases, it indicates that the driving frequency adjustment direction is incorrect, and the frequency needs to be decreased or increased in the opposite direction.

[0131] In some optional implementations, the step size is determined based on the current-voltage phase difference, the phase margin, and the difference calibration coefficient;

[0132] The difference calibration coefficient is determined based on the ratio of the difference between the first resonant frequency and the second resonant frequency to the preset duration. The first resonant frequency and the second resonant frequency are the initial resonant frequency and the end resonant frequency of the ultrasonic hemostasis surgery system before and after the preset duration of no-load output.

[0133] In this embodiment, when determining the adjustment step size S (unit: Hz) of the driving frequency of the ultrasonic hemostasis surgery system, the current phase difference, phase margin, and differential calibration coefficient are comprehensively considered. The specific formula for calculating the step size S is: S = β × phase × W × T, where β is the differential calibration coefficient, phase is the current phase difference, W is the phase margin, and T is the frequency adjustment period (unit: s). The differential calibration coefficient β is calculated based on data collected during the no-load operation of the ultrasonic hemostasis surgery system, β = Δf / Δt, where Δf is the difference between the first resonant frequency (which can be the resonant frequency obtained through frequency sweeping as described above) and the second resonant frequency, and Δt is the preset duration, which ranges from 5 to 10 seconds.

[0134] In response to the subtle differences that may occur in ultrasonic transducers due to manufacturing, processing and aging, this embodiment introduces a difference calibration coefficient to determine the adjustment step size of the driving frequency based on the current phase difference and phase margin. This allows the frequency adjustment step size to better adapt to different working states (i.e. different stages) of the ultrasonic hemostasis surgery system.

[0135] During vascular closure using an ultrasonic hemostasis system, a crucial point is accurately assessing the closure status and promptly stopping energy output to prevent further disruption of the closure or damage to the gasket. This also avoids the risk of continued energy output after tissue cutting, which could cause the blade temperature to rise excessively, affecting vascular clotting. Single impedance or frequency threshold methods are easily affected by tissue fluid, the thickness of the clamped tissue, the gripping force, and the amount of tissue grasped, resulting in a high misjudgment rate, an inability to distinguish between effective closure and tissue carbonization, and poor safety.

[0136] The following example illustrates the method for determining the completion of vascular clotting provided in this embodiment.

[0137] In some optional embodiments, the control device of the ultrasonic hemostasis surgical system further includes:

[0138] The first acquisition module is used to acquire the first and second derivatives of the current impedance value, and to acquire the current resonant frequency and the initial resonant frequency of the ultrasonic hemostasis surgery system.

[0139] The second acquisition module is used to acquire a condensation indication value based on the first and second derivatives of the current impedance value, the current resonant frequency, and the initial resonant frequency.

[0140] The stop module is used to determine that condensation is complete and stop energy output if the condensation indicator value meets the condensation completion judgment condition.

[0141] In this embodiment, during the vascular closure process, the vascular closure endpoint is comprehensively determined based on the changes in impedance (the first derivative of impedance), the second derivative of impedance, and the resonant frequency, i.e., whether the vascular closure is complete. This embodiment combines multiple factors, including the rate of change of impedance (i.e., the first derivative of impedance), the second derivative of impedance, and the current and initial resonant frequencies of the ultrasonic hemostasis system, to determine whether vascular closure is complete. This method is more accurate than related technologies that rely on a single impedance or frequency for judgment, and can minimize the risk of tissue damage.

[0142] In some optional embodiments, the second acquisition module is specifically used for:

[0143] Calculate the current resonant frequency and the initial resonant frequency The difference And calculate the absolute value of the ratio of the difference to the initial resonant frequency. ;

[0144] Calculate the absolute value of the ratio With the first threshold parameter The product of these two values ​​yields the fourth value. ;

[0145] Calculate the absolute value of the second derivative. With the second threshold parameter The product of these two values ​​yields the fifth value. ;

[0146] The absolute value of the first derivative With the fourth value The fifth value The sum of these values ​​is used as the condensation indication value.

[0147] Specifically, condensation indicator value The calculation formula is:

[0148]

[0149] in, For the current moment The resonant frequency, that is, the current resonant frequency. It is the initial resonant frequency at the start of condensation. These are the first threshold parameter and the second threshold parameter.

[0150] Specifically, the first threshold parameter and the second threshold parameter can be obtained based on actual in vitro blood vessel coagulation experiments and animal experiments, and are first selected as follows: , Starting with this, different combinations yielded coagulation indicator values ​​from the beginning to the cutting process during each vascular closure phase. The change curve, select The curve with the steepest slope corresponds to the case where the trend of change is most pronounced. The value as appropriate Value. And appropriate. The group corresponding to the value The curve of change, the latest completed closure The value is used as the condensation completion threshold ε (i.e., the first preset threshold mentioned below). Additionally... The values ​​of ε and the condensation completion threshold ε can be obtained not from a single set of experiments, but from multiple sets of experiments (>50 times). For example, each set of experiments yields a suitable value. The final result can be obtained by averaging the value and the closure threshold ε. Value and condensation completion threshold ε.

[0151] In some optional embodiments, the condensation completion judgment condition is that the condensation indication value is less than a first preset threshold ε, and the duration is greater than a second preset threshold t. min Among them, the second preset threshold t min The value range is 300-500ms.

[0152] In addition, the control device of the ultrasonic hemostasis surgical system provided in this embodiment not only stops energy output after determining that the blood vessel closure is completed and the tissue is cut, but also outputs reminder information.

[0153] Further functional descriptions of the above modules and units are the same as those in the corresponding embodiments described above, and will not be repeated here.

[0154] In this embodiment, the control device of the ultrasonic hemostasis surgical system is presented in the form of a functional unit. Here, a unit refers to an ASIC (Application Specific Integrated Circuit) circuit, a processor and memory that execute one or more software or fixed programs, and / or other devices that can provide the above functions.

[0155] According to an embodiment of the present invention, a control method embodiment for an ultrasonic hemostasis surgical system is provided. It should be noted that the steps shown in the flowchart in the accompanying drawings can be executed in a computer system such as a set of executable computer instructions. Furthermore, although a logical order is shown in the flowchart, in some cases, the steps shown or described may be executed in a different order than that shown here.

[0156] This embodiment provides a control method for an ultrasonic hemostasis surgical system, which can be used in ultrasonic hemostasis surgical systems. Figure 8 This is a flowchart of a control method for an ultrasonic hemostasis surgical system according to an embodiment of the present invention, such as... Figure 8 As shown, the process includes the following steps:

[0157] Step S801: Acquire the current parameter values ​​collected during the energy output process of the ultrasonic hemostasis surgery system. The current parameter values ​​include the current impedance value and the current frequency value.

[0158] Step S802: Determine the current organization status indication value based on the current parameter value.

[0159] Step S803: Based on the current tissue state indication value and the current impedance value, determine the current target power value and adjust the power value to the target power value.

[0160] In some optional implementations, step S802, namely determining the current organization status indication value based on the current parameter value, includes:

[0161] Step S8021: Obtain the first and second derivatives of the current impedance value, and obtain the impedance spectrum characteristics of the tissue;

[0162] Step S8022: Determine the current tissue state indication value based on the first and second derivatives of the current impedance value, the impedance spectrum characteristics, and the current frequency value.

[0163] In some optional embodiments, the current tissue state indicator value is used to indicate the current tissue state, which includes four types, corresponding to the four stages of blood vessel closure: the initial stage, the protein denaturation stage, the fusion stage, and the solidification stage.

[0164] In some optional implementations, step S8022, namely determining the current tissue state indication value based on the first and second derivatives of the current impedance value, the impedance spectrum characteristics, and the current frequency value, includes:

[0165] The current tissue state indication value is obtained by weighted summing of the first and second derivatives of the current impedance value, the impedance spectrum characteristics, and the current frequency value.

[0166] In some optional implementations, the weighting coefficients for the weighted summation of the first and second derivatives of the current impedance value, the impedance spectral characteristics, and the current frequency value are determined based on the ratio of the duration of the four stages to the total duration during the experiment.

[0167] In some optional implementations, step S803, namely determining the current target power value based on the current tissue state indication value and the current impedance value, includes:

[0168] Step S8031: Obtain the first and second derivatives of the current impedance value, and obtain the initial startup power value;

[0169] Step S8032: Determine the target power value based on the first and second derivatives of the current impedance value, the initial startup power value, and the current tissue state indication value.

[0170] In some optional implementations, step S8032, determining the target power value based on the first and second derivatives of the current impedance value, the initial startup power value, and the current tissue state indication value, includes:

[0171] Step S80321: Calculate the first product of the first control parameter and the first derivative of the current impedance value, and calculate the second product of the second control parameter and the second derivative of the current impedance value;

[0172] Step S80322: Calculate the sum of the first product, the second product, and 1, and use it as the first value;

[0173] Step S80323: Multiply the first value by the initial startup power value to obtain the second value;

[0174] Step S80324: Calculate the product of the third control parameter and the current tissue state indication value, and use it as the third value;

[0175] Step S80325: Calculate the value of the exponential function with the negative third value as the exponent;

[0176] Step S80326: Multiply the second value by the exponential function value to obtain the target power value.

[0177] In some optional implementations, the values ​​of the first control parameter, the second control parameter, and the third control parameter are determined by an in vitro burst pressure experiment. During the in vitro burst pressure experiment, one of the first control parameter, the second control parameter, and the third control parameter is selected as the target control parameter each time by using the controlled variable method. The target control parameter is then changed, and the value corresponding to the peak burst pressure when the blood vessel closure is completed is obtained as the value of the target control parameter.

[0178] In some optional embodiments, the control method for the ultrasonic hemostasis surgical system further includes:

[0179] Step S804: Obtain the current-voltage phase difference during the energy output process of the ultrasonic hemostasis surgical system;

[0180] Step S805: Adjust the driving frequency to reduce the phase difference between the current and voltage.

[0181] In some optional embodiments, the step size for adjusting the driving frequency is determined based on the current current-voltage phase difference and the phase margin, which is determined based on the difference between the anti-resonant frequency and the resonant frequency of the ultrasonic hemostasis surgical system.

[0182] The resonant frequency and the anti-resonant frequency are the frequencies corresponding to the first detection of a current-voltage phase difference of 0° and the second detection of a current-voltage phase difference of 0° during the process of the driving frequency increasing from low to high.

[0183] In some optional implementations, the step size is determined based on the current-voltage phase difference, the phase margin, and the difference calibration coefficient;

[0184] The difference calibration coefficient is determined based on the ratio of the difference between the first resonant frequency and the second resonant frequency to the preset duration. The first resonant frequency and the second resonant frequency are the initial resonant frequency and the end resonant frequency of the ultrasonic hemostasis surgery system before and after the preset duration of no-load output.

[0185] In some optional embodiments, the control method for the ultrasonic hemostasis surgical system further includes:

[0186] Step S806: Obtain the first and second derivatives of the current impedance value, and obtain the current resonant frequency and the initial resonant frequency of the ultrasonic hemostasis surgery system;

[0187] Step S807: Based on the first and second derivatives of the current impedance value, the current resonant frequency, and the initial resonant frequency, obtain the condensation indication value;

[0188] Step S808: If the condensation indicator value meets the condensation completion judgment condition, then the condensation is determined to be complete and energy output is stopped.

[0189] In some optional embodiments, step S807, obtaining the condensation indication value based on the first and second derivatives of the current impedance value, the current resonant frequency, and the initial resonant frequency, includes:

[0190] Step S8071: Calculate the difference between the current resonant frequency and the initial resonant frequency, and calculate the absolute value of the ratio of the difference to the initial resonant frequency;

[0191] Step S8072: Calculate the product of the absolute value of the ratio and the first threshold parameter to obtain the fourth value;

[0192] Step S8073: Calculate the product of the absolute value of the second derivative and the second threshold parameter to obtain the fifth value;

[0193] Step S8074: The sum of the absolute value of the first derivative and the fourth and fifth values ​​is used as the condensation indicator value.

[0194] In some optional implementations, the condensation completion judgment condition is that the condensation indication value is less than a first preset threshold and the duration is greater than a second preset threshold.

[0195] This method is implemented by the control device of the aforementioned ultrasonic hemostasis surgical system, and will not be repeated here as it has already been explained.

[0196] like Figure 9 As shown, the overall flow of the control method for the ultrasonic hemostasis surgical system provided in this embodiment of the invention can be as follows:

[0197] Step 1: Real-time tracking of resonant frequency;

[0198] Step 2: Real-time acquisition of tissue impedance values, power, frequency, and phase difference;

[0199] Step 3: Calculate the rate of change of impedance (i.e., the first derivative of impedance) and the second derivative of impedance;

[0200] Step 4: Extract the spectral characteristics of the impedance signal;

[0201] Step 5: Calculate the tissue status indicator value;

[0202] Step Six: Dynamically adjust energy output to close blood vessels;

[0203] Step 7: Use the rate of change of impedance (i.e., the first derivative of impedance), the second derivative of impedance, the current resonant frequency, and the initial resonant frequency to determine whether the condensation is complete.

[0204] This invention also provides an ultrasonic hemostasis surgical system, which has the above-described features. Figure 2 The control device of the ultrasonic hemostasis surgical system shown.

[0205] Please see Figure 10 , Figure 10 This is a schematic diagram of the structure of an ultrasonic hemostasis surgical system provided in an optional embodiment of the present invention, as shown below. Figure 10 As shown, the ultrasonic hemostasis surgical system includes one or more processors 10, a memory 20, and interfaces for connecting the various components, including high-speed interfaces and low-speed interfaces. The various components communicate with each other via different buses and can be mounted on a common motherboard or otherwise installed as needed. The processors can process instructions executed within the ultrasonic hemostasis surgical system, including instructions stored in or on memory to display graphical information of a GUI on an external input / output device (such as a display device coupled to the interface). In some alternative embodiments, multiple processors and / or multiple buses can be used with multiple memories and multiple memory modules, if desired. Figure 10 Take a processor 10 as an example.

[0206] Processor 10 may be a central processing unit, a network processor, or a combination thereof. Processor 10 may further include a hardware chip. The hardware chip may be an application-specific integrated circuit (ASIC), a programmable logic device (PLD), or a combination thereof. The programmable logic device may be a complex programmable logic device (CAMP), a field-programmable gate array (FPGA), a general-purpose array logic (GDA), or any combination thereof.

[0207] The memory 20 stores instructions executable by at least one processor 10 to cause the at least one processor 10 to perform the method shown in the above embodiments.

[0208] The memory 20 may include a program storage area and a data storage area. The program storage area may store the operating system and applications required for at least one function; the data storage area may store data created based on the use of the ultrasonic hemostasis system. Furthermore, the memory 20 may include high-speed random access memory and may also include non-transient memory, such as at least one disk storage device, flash memory device, or other non-transient solid-state storage device. In some alternative embodiments, the memory 20 may optionally include memory remotely located relative to the processor 10, which can be connected to the ultrasonic hemostasis system via a network. Examples of such networks include, but are not limited to, the Internet, intranets, local area networks, mobile communication networks, and combinations thereof.

[0209] The memory 20 may include volatile memory, such as random access memory; the memory may also include non-volatile memory, such as flash memory, hard disk or solid-state drive; the memory 20 may also include a combination of the above types of memory.

[0210] The ultrasonic hemostasis surgical system also includes an input device 30 and an output device 40. The processor 10, memory 20, input device 30, and output device 40 can be connected via a bus or other means. Figure 10 Taking the example of a connection between China and Israel via a bus.

[0211] Input device 30 can receive input digital or character information, and generate key signal inputs related to user settings and function control of the ultrasonic hemostasis surgical system, such as a touch screen, keypad, mouse, trackpad, touchpad, pointer, one or more mouse buttons, trackball, joystick, etc. Output device 40 may include display devices, auxiliary lighting devices (e.g., LEDs), and haptic feedback devices (e.g., vibration motors). The aforementioned display devices include, but are not limited to, liquid crystal displays, light-emitting diodes, displays, and plasma displays. In some alternative embodiments, the display device may be a touch screen.

[0212] The ultrasonic hemostasis surgical system also includes a communication interface for communication between the ultrasonic hemostasis surgical system and other devices or communication networks.

[0213] Of course, this ultrasonic hemostasis surgical system may also include Figure 4 The hardware circuit shown and Figure 5 The phase difference acquisition circuit shown.

[0214] This invention also provides a computer-readable storage medium. The methods described above according to embodiments of the invention can be implemented in hardware or firmware, or implemented as computer code that can be recorded on a storage medium, or implemented as computer code downloaded via a network and originally stored on a remote storage medium or a non-transitory machine-readable storage medium and then stored on a local storage medium. Thus, the methods described herein can be processed by software stored on a storage medium using a general-purpose computer, a dedicated processor, or programmable or dedicated hardware. The storage medium can be a magnetic disk, optical disk, read-only memory, random access memory, flash memory, hard disk, or solid-state drive, etc.; further, the storage medium can also include combinations of the above types of memory. It is understood that computers, processors, microprocessor controllers, or programmable hardware include storage components capable of storing or receiving software or computer code, which, when accessed and executed by the computer, processor, or hardware, implements the methods shown in the above embodiments.

[0215] A portion of this invention can be applied as a computer program product, such as computer program instructions, which, when executed by a computer, can invoke or provide the methods and / or technical solutions according to the invention through the operation of the computer. Those skilled in the art will understand that the forms in which computer program instructions exist in a computer-readable medium include, but are not limited to, source files, executable files, installation package files, etc. Correspondingly, the ways in which computer program instructions are executed by a computer include, but are not limited to: the computer directly executing the instructions, or the computer compiling the instructions and then executing the corresponding compiled program, or the computer reading and executing the instructions, or the computer reading and installing the instructions and then executing the corresponding installed program. Here, the computer-readable medium can be any available computer-readable storage medium or communication medium accessible to a computer.

[0216] Although embodiments of the invention have been described in conjunction with the accompanying drawings, those skilled in the art can make various modifications and variations without departing from the spirit and scope of the invention, and such modifications and variations all fall within the scope defined by the appended claims.

Claims

1. A control device for an ultrasonic hemostasis surgical system, characterized in that, The device includes: The current parameter value acquisition module is used to acquire the current parameter values ​​collected during the energy output process of the ultrasonic hemostasis surgery system. The current parameter values ​​include the current impedance value and the current frequency value. The current organization status indicator value determination module is used to determine the current organization status indicator value based on the current parameter value; A power adjustment module is used to determine a current target power value based on the current tissue status indication value and the current impedance value, and adjust the power value to the target power value; The current organization status indicator value determination module includes: The first acquisition unit is used to acquire the first and second derivatives of the current impedance value and to acquire the impedance spectrum characteristics of the tissue. The current tissue status indication value calculation unit is used to determine the current tissue status indication value based on the first and second derivatives of the current impedance value, the impedance spectrum characteristics, and the current frequency value; The current tissue state indicator value is used to indicate the current tissue state, which includes four types, corresponding to the four stages of blood vessel closure: the initial stage, the protein denaturation stage, the fusion stage, and the solidification stage. The current tissue state indication value calculation unit is specifically used to perform a weighted summation of the first and second derivatives of the current impedance value, the impedance spectrum characteristics, and the current frequency value to obtain the current tissue state indication value; the weighting coefficients for the weighted summation of the first and second derivatives of the current impedance value, the impedance spectrum characteristics, and the current frequency value are determined based on the ratio of the duration of the four stages to the total duration during the experiment.

2. The apparatus according to claim 1, characterized in that, The power adjustment module includes: The second acquisition unit is used to acquire the first and second derivatives of the current impedance value and to acquire the initial startup power value. The target power value determination unit is used to determine the target power value based on the first and second derivatives of the current impedance value, the initial startup power value, and the current tissue state indication value.

3. The apparatus according to claim 2, characterized in that, The target power value determination unit is specifically used for: Calculate the first product of the first control parameter and the first derivative of the current impedance value; calculate the second product of the second control parameter and the second derivative of the current impedance value. Calculate the sum of the first product, the second product, and 1, and use it as the first value; Multiply the first value by the initial startup power value to obtain the second value; Calculate the product of the third control parameter and the current tissue state indication value, and use it as the third value; Calculate the value of the exponential function with the negative third value as the exponent; The target power value is obtained by multiplying the second value by the exponential function value.

4. The apparatus according to claim 3, characterized in that, The values ​​of the first control parameter, the second control parameter, and the third control parameter are determined through an in vitro burst pressure experiment. During the in vitro burst pressure experiment, one of the first control parameter, the second control parameter, and the third control parameter is selected as the target control parameter each time by using the controlled variable method. The target control parameter is then changed, and the value corresponding to the peak burst pressure when the blood vessel clotting is completed is obtained as the value of the target control parameter.

5. The apparatus according to claim 1, characterized in that, Also includes: A phase difference acquisition module is used to acquire the current-voltage phase difference during the energy output process of the ultrasonic hemostasis surgical system; The frequency adjustment module is used to adjust the driving frequency so that the phase difference between the current and voltage is reduced.

6. The apparatus according to claim 5, characterized in that, The step size for adjusting the driving frequency is determined based on the current current-voltage phase difference and the phase margin, which is determined based on the difference between the anti-resonant frequency and the resonant frequency of the ultrasonic hemostasis surgical system. The resonant frequency and the anti-resonant frequency are the frequencies corresponding to the first detection of a current-voltage phase difference of 0° and the second detection of a current-voltage phase difference of 0° during the process of the driving frequency increasing from low to high.

7. The apparatus according to claim 6, characterized in that, The step size is determined based on the current-voltage phase difference, the phase margin, and the difference calibration coefficient; The difference calibration coefficient is determined based on the ratio of the difference between the first resonant frequency and the second resonant frequency to the preset duration. The first resonant frequency and the second resonant frequency are the initial resonant frequency and the end resonant frequency of the ultrasonic hemostasis surgery system before and after the preset duration of no-load output.

8. The apparatus according to claim 1, characterized in that, Also includes: The first acquisition module is used to acquire the first and second derivatives of the current impedance value, and to acquire the current resonant frequency and the initial resonant frequency of the ultrasonic hemostasis surgery system. The second acquisition module is used to acquire a condensation indication value based on the first and second derivatives of the current impedance value, the current resonant frequency, and the initial resonant frequency. The stop module is used to determine that condensation is complete and stop energy output if the condensation indicator value meets the condensation completion judgment condition.

9. The apparatus according to claim 8, characterized in that, The second acquisition module is specifically used for: Calculate the difference between the current resonant frequency and the initial resonant frequency, and calculate the absolute value of the ratio of the difference to the initial resonant frequency; The fourth value is obtained by multiplying the absolute value of the ratio by the first threshold parameter. The fifth value is obtained by multiplying the absolute value of the second derivative with the second threshold parameter. The sum of the absolute value of the first derivative, the fourth value, and the fifth value is used as the condensation indicator value.

10. A control method for an ultrasonic hemostasis surgical system, characterized in that, The method includes: During the energy output process of the ultrasonic hemostasis surgical system, the current parameter values ​​collected include the current impedance value and the current frequency value; Based on the current parameter values, determine the current organization status indication value; Based on the current tissue status indication value and the current impedance value, determine the current target power value and adjust the power value to the target power value; Determining the current organization status indication value based on the current parameter value includes: Obtain the first and second derivatives of the current impedance value, and obtain the impedance spectrum characteristics of the tissue; Based on the first and second derivatives of the current impedance value, the impedance spectrum characteristics, and the current frequency value, the current tissue state indication value is determined; The current tissue state indicator value is used to indicate the current tissue state, which includes four types, corresponding to the four stages of blood vessel closure: the initial stage, the protein denaturation stage, the fusion stage, and the solidification stage. The determination of the current tissue state indication value based on the first and second derivatives of the current impedance value, the impedance spectrum characteristics, and the current frequency value includes: The first and second derivatives of the current impedance value, the impedance spectrum characteristics, and the current frequency value are weighted and summed to obtain the current tissue state indication value; The weighting coefficients for the weighted summation of the first and second derivatives of the current impedance value, the impedance spectrum characteristics, and the current frequency value are determined based on the ratio of the duration of the four stages to the total duration during the experiment.

11. An ultrasonic hemostasis surgical system, characterized in that, include: The control device for the ultrasonic hemostasis surgical system according to any one of claims 1-9.

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