A high-peak tunable thulium-doped fiber laser system powered by supercapacitors

Abstract

The present invention provides a high-peak tunable thulium-doped fiber laser system based on supercapacitor energy supply, which involves the use of stimulated emission modulation technology. It intelligently selects the most suitable laser output mode according to the hardness of the stone and the blood oxygen status of the tissue; and automatically switches to the thulium laser continuous wave hemostasis mode when the hemoglobin deoxygenation ratio and tissue temperature rise exceed the standard to ensure surgical safety; secondly, combined with supercapacitor energy supply technology, the system has high-peak and low-latency energy release capabilities, significantly improving the lithotripsy efficiency. At the same time, through a closed-loop control mechanism, the laser parameters are fine-tuned in real time to avoid the "flash" phenomenon and reduce surgical risks.

Description

Technical Field

[0001] The present invention relates to the field of stimulated emission modulation technology, in particular to a high-peak tunable thulium-doped fiber laser system powered by a supercapacitor. Background Art

[0002] The wavelength of thulium-doped fiber laser is around 1940nm, and its water absorption is 130cm -1 , the penetration depth into tissue is shallower. In addition to lithotripsy, it is also suitable for tissue cutting and has a hemostatic function, making it very suitable for medical applications. In recent years, thanks to the advantages of high optical-to-optical conversion efficiency, good beam quality, diverse pulse output parameters, and compact structure, the development of thulium-doped fiber lasers has brought new possibilities for lithotripsy and has been favored by urology in recent years.

[0003] Existing commercial products still have certain problems in terms of function and effectiveness, especially in laser lithotripsy, which are mainly manifested in:

[0004] ① Most of the light sources used are commercial quasi-continuous-wave thulium-doped fiber lasers with peak powers less than 700W on the market. These are suitable for the "dusting" lithotripsy mode. However, for harder stones (>1200HU), a higher peak power is still required while maintaining Joule-level single-pulse energy. Existing thulium-doped fiber lasers struggle to break hard stones.

[0005] ② Most laser output modes operate in fixed wavelength or fixed pulse form, failing to fully utilize the effect of thulium at different wavelengths to specifically treat stones of different hardness, making it even more difficult to meet the requirement of "selecting the optimal output mode based on real-time feedback on site";

[0006] ③ Existing lithotripsy systems mostly rely on single acoustic or optical feedback, lacking a comprehensive feedback module that combines the stone's acoustic spectrum with tissue photothermal information. When stone hardness changes, adjusting energy output based solely on the acoustic spectrum signal can easily lead to "flashback" phenomena, increasing surgical risks.

[0007] It is necessary to develop a new type of high-power thulium-doped fiber laser suitable for crushing hard stones. How to combine it with a supercapacitor group under 220V AC power supply to achieve a high peak power output of >1500W under quasi-continuous operation, which can significantly improve the lithotripsy efficiency while reducing the flash effect; achieving "all-round" treatment of soft and hard stones is a technical problem that needs to be solved at present.

[0008] The above information disclosed in this Background section is only for enhancement of understanding of the background of the present disclosure and therefore it may contain information that does not form the prior art that is already known to a person of ordinary skill in the art. Summary of the Invention

[0009] The object of the present invention is to provide a high-peak tunable thulium-doped fiber laser system powered by a supercapacitor to solve the problems raised in the above background technology.

[0010] To achieve the above object, the present invention provides the following technical solutions:

[0011] A high-peak tunable thulium-doped fiber laser system powered by a supercapacitor includes a power supply unit, a supercapacitor group unit, a control unit, a drive unit, a pump energy unit, and a thulium-doped fiber laser optical module; the processing logic of the control unit includes:

[0012] Acoustic spectrum data acquisition module: used to collect acoustic spectrum data of stones using an ultrasonic micro-transmitting acoustic imaging probe in the laser irradiation area of ​​the fiber laser probe in the thulium-doped fiber laser optical module;

[0013] Pulse parameter optimization module: Based on real-time acoustic spectrum data, a multivariate regression model is used to predict the relationship between laser output energy and stone micropore response;

[0014] By optimizing the algorithm and adjusting the laser output parameters, the efficiency of lithotripsy can be maximized while reducing the "flash" phenomenon during the lithotripsy process.

[0015] Photothermal feedback module: used to collect the Raman signal of hemoglobin in the tissue in real time in the laser irradiation area and perform preprocessing;

[0016] The hemoglobin deoxygenation ratio R, which reflects the degree of hemoglobin deoxygenation, is calculated based on the Raman spectrum ratio;

[0017] According to the calculated hemoglobin deoxygenation ratio R, combined with the power normalized value and time normalized value of the continuous laser output, a temperature control regression model is constructed, and the temperature control regression model is used to calculate the tissue temperature rise. ;

[0018] When the hemoglobin deoxygenation ratio R and tissue temperature rise When the corresponding preset threshold is exceeded, the control unit automatically switches to hemostasis mode;

[0019] Laser output mode selection module: used to select the optimal laser output mode based on the stone micropore acoustic spectrum and photothermal feedback data.

[0020] Compared with the existing technology, the beneficial effects of the present invention are: intelligently selecting the most suitable laser output mode according to the hardness of the stone and the blood oxygen status of the tissue; using low-power thulium laser pulse mode to reduce tissue damage when the stone is soft or the stone crushing is easy; and automatically switching to thulium laser continuous wave hemostasis mode when the hemoglobin deoxygenation ratio and tissue temperature rise exceed the standard to ensure surgical safety.

[0021] Secondly, combined with supercapacitor energy supply technology, the system has high-peak, low-latency energy release capabilities, which improves lithotripsy efficiency. At the same time, through a closed-loop control mechanism, it fine-tunes laser parameters in real time to avoid "flash bursts" and reduce surgical risks. BRIEF DESCRIPTION OF THE DRAWINGS

[0022] Figure 1 This is a schematic diagram of the overall system module of the present invention;

[0023] Figure 2 This is a schematic diagram of the entire system;

[0024] Figure 3 This is the execution diagram of the entire system;

[0025] Figure 4 It is the measured pulse data of continuous thulium-doped fiber laser. DETAILED DESCRIPTION

[0026] In order to make the above-mentioned objects, features and advantages of the present invention more obvious and easy to understand, the specific embodiments of the present invention are described in detail below with reference to the accompanying drawings.

[0027] In the following description, many specific details are set forth to facilitate a full understanding of the present invention. However, the present invention may also be implemented in other ways different from those described herein. Those skilled in the art may make similar generalizations without violating the connotation of the present invention. Therefore, the present invention is not limited to the specific embodiments disclosed below.

[0028] Example 1:

[0029] See also Figure 1 , Figure 2 , Figure 3 and Figure 4 , the present invention provides a technical solution:

[0030] A high-peak tunable thulium-doped fiber laser system powered by a supercapacitor includes a power supply unit, a supercapacitor group unit, a control unit, a drive unit, a pump energy unit, and a thulium-doped fiber laser optical module; the processing logic of the control unit includes:

[0031] Acoustic spectrum data acquisition module: used to collect acoustic spectrum data of stones using an ultrasonic micro-transmitting imaging probe in the laser irradiation area of ​​the fiber laser probe in the thulium-doped fiber laser optical module;

[0032] Further explanation: the ultrasonic micro-transmission imaging probe is fixed to the side edge of the fiber laser probe; and according to the predetermined ultrasonic excitation and sampling scheme;

[0033] 1.1) During percutaneous ureteroscopic lithotripsy, a fiber laser beam is introduced into the ureteral lumen, and the internal structural characteristics of the stone need to be assessed in real time to dynamically adjust the laser pulse parameters;

[0034] Laser pulse parameters include but are not limited to pulse peak power and pulse width. In this embodiment, an ultrasonic micro-transmission imaging probe with a center frequency of 20 MHz is selected, which has high spatial resolution and appropriate penetration depth, and can meet the requirements for collecting the sound spectrum of micropores inside the stone.

[0035] The ultrasound micro-transmission imaging probe and the fiber laser probe are coaxially fixed and initially aligned 5 mm from the stone surface to ensure that the detection areas of the acoustic and laser beams overlap and to obtain the echo signal of the laser irradiation area. The specific implementation steps are as follows:

[0036] Before the lithotripsy procedure began, the ultrasound micro-transmission imaging probe and the fiber laser probe were coaxially mounted using a rigid fixing sleeve, ensuring that the center lines of the two were no more than 0.2 mm apart.

[0037] Keep the probe end face perpendicular to the stone surface and the working distance fixed at ;Will Pass the ureteroscope through the catheter, observe the relative position of the probe and the stone on the screen, and adjust the probe to keep its working distance stable. .

[0038] 1.2) After confirming the alignment, start the ultrasonic pulse transmission module and use the normalized excitation parameters: the excitation waveform includes a Gaussian modulated sine wave;

[0039] The configuration of this embodiment ensures that At the working distance, an echo signal with a signal-to-noise ratio (SNR) ≥ 30dB is obtained.

[0040] 1.3) The echo signal is digitally sampled using a 100MHz sampling rate and a 16-bit ADC. The bandpass filter is then used for preprocessing to extract the acoustic wave components of the micropores inside the stone in the laser irradiation area to obtain a bandpass echo signal. ; The specific implementation steps are as follows:

[0041] After starting the ultrasonic transmitter module, the probe emits an excitation and receives the corresponding echo signal. ;

[0042] In the 20µs sampling window, the high-speed ADC samples the Acquisition continuous time Get the number sequence ,in , the total number of sampling points K = 2000. Perform normalization ;

[0043] Normalized sequence The maximum value of is 1, which ensures the stability of the subsequent calculation values; Indicates the maximum value of the selected digital sequence, j1 indicates the index mark of the sampling point; Input bandpass digital filter, the bandpass range is normalized to ; The corresponding bandpass actual range is 5MHz~15MHz, extracting the micropore resonance echo component ;in, They are the lower limit frequency and upper limit frequency of the bandpass digital filter respectively; they represent 0.25 and 0.75 respectively; they save the bandpass echo signal each time Used for subsequent power spectrum calculation.

[0044] 1.4) Bandpass echo signal Perform fast Fourier transform to obtain the power spectrum and normalize it to form the normalized sound spectrum feature vector , among which each ; Represents the normalized energy intensity in the i-th frequency band; the specific implementation steps are:

[0045] For each frame of preprocessed bandpass echo signal Perform N-point fast Fourier transform, the mathematical expression is:

[0046]

[0047] Where N=512: is the number of FFT points, that is, the number of discrete data points used when performing Fourier transform; m is the frequency point index of FFT output, and its value range is ; is the sampling frequency, which indicates the number of times the signal is sampled per second;

[0048] The normalized frequency points are defined as ;

[0049] Define the actual frequency and normalized frequency points The corresponding relationship is ;

[0050] Further calculation of the power spectrum , specifically ;

[0051] Perform bandpass energy statistics on the power spectrum: only retain the normalized frequency interval ; corresponds to the actual 5MHz–15MHz, that is, the index range , ;Build a temporary energy array ;and ; In this embodiment, the frequency band is divided into n = 10 segments, ; Indicates the FFT frequency index step corresponding to each frequency band; Normalize and get the spectral characteristic component of the i-th frequency band Specifically ;and ;

[0052] in is the value corresponding to the frequency band j2 with the maximum energy among the 10 sub-bands; is the frequency band power of the ith frequency band, which is normalized to ensure ; Finally, the spectrum feature vector is obtained .

[0053] 1.5) Spectral feature vector Perform normalization processing to obtain the normalized sound spectrum scalar , the stone resonance intensity is judged by the threshold judgment mechanism, and the spectrum feature vector As the input of the pulse parameter optimization module; the specific implementation steps are as follows:

[0054] when When it approaches 1, the resonance intensity in the i-th frequency band is higher, indicating that the stone is more likely to micro-explosion in this frequency band; when The closer it is to 0, the lower the resonance intensity in the i-th frequency band is, indicating that the microporous structure inside the stone is less or the echo is more strongly absorbed. The total spectral energy is defined as ; ; After normalization, Limited to (0,1], definition ; represents the normalized sound spectrum scalar;

[0055] when The closer it is to 1, the more concentrated the energy distribution in each frequency band within the stone is, the higher the stone resonance intensity is, and the more it is necessary to increase the pulse peak power. Pulse bombardment is performed, and the pulse width It needs to be reduced proportionally to balance the energy injection rate and the risk of preventing instantaneous high-energy "flash";

[0056] when The closer it is to 0, the weaker the stone resonance intensity is, and the more the pulse peak power needs to be reduced. Or switch to continuous mode; for threshold determination mechanism: set The judgment threshold is ;and The value of Select; set The judgment threshold is ;and The value of Select from; this embodiment sets the stone hardness threshold: ; Stone soft threshold: ; ; and The specific value of is determined by the expert group using the fuzzy analytic hierarchy process (FAHP);

[0057] If the i-th frequency band Above the judgment threshold , indicating that the stones have significant resonance in this frequency band; the pulse parameter optimization should be adjusted around the corresponding frequency first. and , so that energy can be effectively injected to avoid "flash explosion";

[0058] when When the pulse peak power is increased, it indicates that the overall structure of the stone is porous and the stone crushing efficiency is high. , and the pulse width It needs to be reduced proportionally to balance the energy injection rate and the risk of preventing instantaneous high-energy "flash";

[0059] when : This means that the echo energy in this frequency band is the largest and the stone has the strongest resonance with the sound waves in this frequency band. The corresponding pulse energy injection needs to be increased, but the pulse width should be adjusted accordingly. Set as To disperse the energy and avoid excessive concentration leading to "flash burst"; is the pulse width modulation coefficient, which is used to adjust the sound spectrum characteristics of the stone Dynamically adjust pulse width to achieve uniform energy release and suppress "flash" phenomenon; To determine The values ​​are normalized to the interval (0,1];

[0060] when Increase → Increase → If is the maximum value→ ,other Relatively reduced;

[0061] when Increase, that is, majority All close to the maximum value → multi-band resonance → the system can increase the pulse peak power , but the pulse width needs to be reduced synchronously To avoid "flash burst"; it should be noted that " " indicates an approaching mark.

[0062] Pulse parameter optimization module: Based on real-time acoustic spectrum data, a multivariate regression model is used to predict the relationship between laser output energy and stone micropore response;

[0063] Further explanation: 2.1) By taking the normalized spectrum scalar and pulse peak power and pulse width As the independent variable, the crushing efficiency As the dependent variable, a stone crushing efficiency model was constructed based on the multiple regression model; the expression is ;

[0064] All parameters are normalized to the interval (0,1]; normalized spectrum scalar It represents the normalized response intensity of the entire stone micropores to the sound wave, which is characterized as the "total resonance energy coefficient available for stone fragmentation";

[0065] is the normalized value of the pulse peak power, ; is the normalized value of the pulse width, ; ;when 、 、 hour, ; When any parameter approaches 0, .

[0066] By optimizing the algorithm and adjusting the laser output parameters, the efficiency of lithotripsy can be maximized while reducing the "flash" phenomenon during the lithotripsy process.

[0067] Further explanation: 2.2) Using genetic algorithm to calculate the pulse peak power of laser output parameters and pulse width For search optimization, the population individual encoding used only contains these two variables, and iterative updates are performed with the comprehensive fitness F as the goal; the specific steps of the genetic algorithm optimization process are as follows:

[0068] In actual lithotripsy, it is necessary to use the real-time normalized acoustic spectrum scalar Continuously select the best and , we must improve the efficiency of stone crushing , and reduce the risk of "flash burst"; this implementation scheme uses a single-objective genetic algorithm by Search for the optimal solution in the space. Define the normalized "flash burst" risk function as ;

[0069] in, is the flash risk function value; when Very large and When it is very small, , indicating a high risk of "flash burst"; when or When it is close to 0 or 1, , indicating a low risk of "flash explosion". In order to take into account both the efficiency of stone crushing and the risk of "flash explosion", a weighted linear combination is used to calculate the comprehensive fitness F:

[0070]

[0071] in ; Weight 0.8 is used to maximize ; Weight 0.2 is used to minimize ;Right now The larger the value, the lower the risk of "flashover". and hour, ;when or The lower the value of comprehensive fitness F is, the lower the value of comprehensive fitness F is. The encoding and initialization steps are as follows:

[0072] Chromosome encoding: Each individual is composed of two genes: , are real numbers with a value range of (0,1].

[0073] Initial population setting: The population size is set to . Use uniform random distribution in the interval (0,1] to initialize each gene; the r1th individual in the population . All comprehensive fitness Sort from largest to smallest to facilitate the next step of selection. The selection, crossover, and mutation steps are as follows:

[0074] For each selection, two individuals are randomly selected from the population and their Value, the one with higher fitness wins and enters the "cross pool"; repeat The crossover operation is as follows: the individuals in the crossover pool are combined in pairs. , a random mutation is performed with a probability of 0.1; after the mutation, 、 Project back to (0.01, 1.00]. If it does not change, then Keep it unchanged; take all offspring as the next generation population and perform a new round of fitness calculation. Set the maximum number of iterations If the current generation g reaches , then stop the iteration. If in 10 consecutive generations, the fitness gain of the best individual in the population , it is considered to have converged and can be terminated early.

[0075] Record the individual with the highest fitness during the iteration and its corresponding comprehensive fitness ; Output and As the optimal pulse parameter for this real-time optimization; and As "real-time gravel" pulse parameters, fed back to the drive unit. Reference this optimal combination , in order to control the amplifier drive current and the pulse width of the output device, to achieve precise modulation of the actual laser signal and enter the stone crushing execution stage.

[0076] Photothermal feedback module: used to collect the Raman signal of hemoglobin in the tissue in real time in the laser irradiation area and perform preprocessing;

[0077] Further explanation: The continuous light path output by the thulium-doped fiber laser optical module is coaxially arranged with the optical Raman spectroscopy sensor; the pre-processing includes the 1580cm -1 and 1445cm -1 The Raman intensity at the wavelength is normalized to provide raw data for subsequent ratio calculation;

[0078] 785nm excitation can effectively reduce fluorescence background while enhancing the Raman scattering signal of hemoglobin. The probe is small and can be coaxially inserted into the ureteroscope with the continuous laser fiber, ensuring that the monitoring area is consistent with the heating area.

[0079] 3.1) Fix the 785nm Raman excitation fiber probe coaxially with the continuous laser output fiber, keep the probe end perpendicular to the tissue surface, and the detection distance To ensure that the Raman excitation and laser heating areas coincide; the specific implementation steps are as follows: the operator introduces the continuous laser fiber into the lithotripsy or hemostasis site through the ureteroscope. The Raman fiber probe is placed in the continuous laser fiber concentric tube, and the probe end is fixed at a distance of 1 / 4 from the tissue surface. ; Error ≤ ±0.1mm. Observe the probe position on the screen and adjust it by the micro-operation lever to maintain , and at the same time confirm that the fiber end face is perpendicular to the blood vessel / tissue surface. Start the Raman spectrometer: with an excitation power of 785nm , integration time , collect continuous Raman spectra; It is a normalized value, corresponding to the actual 50mW; It is the normalized value, corresponding to 100ms. The spectrum data is read every 100ms, and the 1445cm -1 Peak intensity and 1580cm -1 Peak intensity . The original strength Transmit to the embedded DSP for normalization processing.

[0080] The hemoglobin deoxygenation ratio R, which reflects the degree of hemoglobin deoxygenation, is calculated based on the Raman spectrum ratio;

[0081] 3.2) Use normalization to process Raman signals to ensure and They are all mapped to the range of (0,1] and further used to calculate the hemoglobin deoxygenation ratio R; the specific implementation steps are as follows:

[0082] The original intensity value collected each time and All are 16-bit ADC output; value range [0,65535]; set normalized reference value ;ensure ;

[0083] Calculate the normalized Raman intensity ; Thus we get .

[0084] If any original intensity is 0, that is, no signal, set the lower limit after normalization ; to avoid zero denominators. and Transfer to the next step to calculate the hemoglobin deoxygenation ratio R.

[0085] 3.3) Calculate the hemoglobin deoxygenation ratio R and limit its value range to the interval (0,1); ; The specific implementation steps are: normalize the intensity and As input, calculate the preliminary ratio , expressed as ;

[0086] like , then directly order ; otherwise, the noise is suppressed; and ; This way we can ensure the final The hemoglobin deoxygenation ratio R is passed to the temperature control model calculation module. It is 1445cm after normalization -1 The Raman intensity at , reflects the lipid / protein content in the tissue; is 1580cm after normalization -1 The Raman intensity at is mainly corresponding to the hemoglobin signal; the hemoglobin deoxygenation ratio R reflects the deoxygenation state of the tissue; the closer it is to 1, the higher the degree of deoxygenation.

[0087] According to the calculated hemoglobin deoxygenation ratio R, combined with the power normalized value and time normalized value of the continuous laser output, a temperature control regression model is constructed, and the temperature control regression model is used to calculate the tissue temperature rise. ;

[0088] 3.4) When laser lithotripsy is switched to hemostasis mode, the tissue temperature rise needs to be calculated through Raman feedback to dynamically adjust the continuous laser power and action time to ensure that the tissue temperature rise is Stay within a safe range ; Corresponding to actual ≤0.5°C; Specific implementation steps:

[0089] Set the normalized value of continuous laser output power ; Normalized value of continuous laser output time .

[0090] Based on clinical trials and experience with the photothermal conduction model, multiplicative regression was used. ;

[0091] is the normalized value of the continuous laser output power. The closer it is to 1, the greater the power. It is the normalized value of continuous laser action time. The closer it is to 1, the longer the irradiation time. is the normalized tissue temperature rise, The closer it is to 1, the higher the tissue temperature rise is. 、 、 hour, , indicating that the tissue temperature rise approaches the maximum value; when any parameter approaches 0, , indicating that the tissue temperature rise is extremely low; it should be noted that: when the system is in pulse lithotripsy mode, the laser output is in the optimal combination Pulse emission is performed, not used or ignored at this time .

[0092] Set the hemoglobin deoxygenation ratio R to exceed the preset threshold ; If the hemoglobin deoxygenation ratio is detected , the system switches to continuous mode, at this time "pulse peak power" is suspended and replaced by "continuous laser output power" Determines the heating intensity. At this moment, It is set independently or dynamically adjusted by the light-heat feedback module according to the rules to control the temperature rise of the tissue .

[0093] When the hemoglobin deoxygenation ratio R and tissue temperature rise When the corresponding preset threshold is exceeded, the control unit automatically switches to hemostasis mode;

[0094] Further explanation: The hemostasis mode is achieved by adjusting the power normalization value of the continuous laser output and time-normalized values To stabilize the tissue temperature rise within a safe range; this embodiment sets the tissue temperature rise The safety range is ;

[0095] 3.5) Setting the tissue temperature rise The preset threshold is ; Initial setting of this embodiment is 0.6; ; , Determined by an expert group using the fuzzy analytic hierarchy process (FAHP) based on the actual usage environment; , The values ​​of are all within the interval (0.2, 0.93); when ,and When the hemostasis mode needs to be adjusted immediately or ; until the tissue temperature rises within a safe range. ;

[0096] This embodiment ensures that It is always bound by three variables. If any parameter is too high, it will lead to Increase, easy to real-time control; normalization range (0,1] makes calculation simple and numerically stable, convenient for fast operation on DSP / FPGA. The specific implementation steps are as follows:

[0097] Every 100ms, the latest R value is calculated; at the same time, the current continuous irradiation cumulative time is recorded ; is the cumulative time; if the last cycle is still in the radiation state, the current feedback uses the cumulative time, otherwise .like , then maintain the original continuous mode: keep ; is the last power optimization value; continue irradiating at the same power until the next sampling.

[0098] like , calculate the current ;like , then only fine-tune the power ;in , thus adjusting the amplitude .

[0099] Will Limited to the interval (0.01,1], if , then set it to 0.01. Continue to accumulate the irradiation time until ; Each cycle increases by 100ms, i.e. 0.05 normalized value, and monitors continuously. , then enter the strongest mode of "hemostasis protection": immediately ;

[0100] Reset the cumulative irradiation time to 0.05; maintain this power for at least 0.2 time, and 0.2 corresponds to an actual time of 400ms for sweeping hemostasis, and continue to update the R value every 100ms during this period;

[0101] If 4 times in a row , then gradually fine-tune with the same formula To the original hemostasis power; if R , then continue to maintain ;pass Determine that the tissue is in a deoxygenated state; When the power is slightly reduced to avoid excessive temperature rise in the tissue; when When the Focused hemostasis is achieved, with cumulative time limits and real-time feedback loops ensuring ; This embodiment completes the R and The calculation and real-time threshold judgment realize the seamless switching from the optimal pulse parameters and lithotripsy mode to the hemostasis mode based on the output; the actual laser output is adjusted by the driving unit to achieve closed-loop adaptive thermal control.

[0102] Further explanation: Six pig kidney tissue blocks (3 cm × 3 cm × 1 cm) of similar size and morphology were prepared and labeled "Pig Kidney Sample 1" through "Pig Kidney Sample 6." All tissue samples were placed on a constant temperature and humidity platform maintained at 37°C and covered with a silicone substrate with the same acoustic impedance as the tissue to simulate the heat dissipation conditions of a real vascular bed in vivo. For comparative verification, the first three samples served as the control group (without photothermal feedback), and the last three samples served as the experimental group (with the photothermal feedback module enabled and automatically switched to hemostasis mode).

[0103] Tissue sample fixation: The surface of each piece of pig kidney tissue was kept moist, and the sample was fixed below the intersection of the Raman probe and the continuous laser beam using a custom bracket, ensuring that the probe end face was perpendicular to the tissue surface and the distance was fixed at 2 mm (allowable error ± 0.1 mm).

[0104] Fiber and probe arrangement: A 785 nm Raman fiber probe (normalized excitation power 0.5, corresponding to 50 mW, acquisition integration time 100 ms) was coaxially mounted with the CW laser fiber. Adjust the height of the probe on the substrate so that the probes were aligned parallel and perpendicular to the tissue specimen. The same alignment procedure was used for all samples to ensure that the center of the beam spot was aligned with the Raman detection area.

[0105] Raman spectrometer model Raman-Probe-785, wavelength resolution 1cm -1 , covering 400cm -1 ~2000cm -1 Continuous laser output system; normalized peak power controllable, embedded DSP real-time normalization and ratio calculation unit; temperature control model calculation program has been loaded into DSP, and automatically outputs tissue temperature rise after receiving normalized Raman intensity Threshold setting: preset threshold for hemoglobin deoxygenation ratio ; Preset threshold for tissue temperature rise ; corresponds to actual 0.5°C.

[0106] Control group (pig kidney samples 1–3): The Raman spectrometer was started for each sample, and a spectrum was collected every 100 ms under the continuous laser excitation; the 1445 cm -1 Lipid / protein peak intensity and 1580cm -1 Hemoglobin peak intensity .

[0107] Signal Normalization and Ratios: Calculating Normalization References ,Will 、 , and take 0.01 for any normalized value lower than 0.01;

[0108] Calculate the hemoglobin deoxygenation ratio; set the power normalization value of the continuous laser , normalized from the cumulative time of irradiation ; corresponds to the actual 100ms;

[0109] Calculate the current according to the temperature control model ; This Record and accumulate the exposure time in the next cycle: If continuous exposure is maintained, ; If the cumulative time reaches 1.00, stop the experiment. Record every 100ms 、 、 、 The control group did not adjust the power or irradiation time until the end of the experiment;

[0110] Experimental group (pig kidney samples 4–6): Same as the control group, the initial power of the continuous laser was normalized, and the Raman spectrum was collected every 100ms and normalized according to the steps to obtain 、 and R.

[0111] set up ; Reset cumulative time =0.05;

[0112] Keep for at least 4 100ms cycles , each cycle still collects Raman signals and calculates R, , and judge if any time within 400ms , you can continue to exit the protection mode and fine-tune the power according to the above formula. ; Stop this experiment; if the condition is not met within 400ms after entering the hemostasis protection , continue monitoring after exiting the hemostasis mode until the total irradiation time reaches 1.00;

[0113] The collected R and the currently used power normalization value are recorded every 100ms. , cumulative time , tissue temperature rise , and whether it is currently in hemostasis mode ("yes" / "no").

[0114] Through the above steps, real-time data of the control group and the experimental group can be obtained. , resulting in the appearance of high deoxygenation signals Rapidly increasing the temperature, exceeding the threshold by 0.5°C without switching modes in time, will bring the risk of tissue overheating; the experimental group can automatically adjust according to the threshold and ,ensure , thereby verifying the beneficial effect of "the photothermal feedback module automatically switching to the hemostasis mode" in limiting tissue temperature rise and reducing tissue thermal damage.

[0115] Table 1 Study on the automatic switching of the photothermal feedback module to the hemostasis mode:

[0116]

[0117] The table description is as follows:

[0118] 1. Pig kidney samples 1–3 (control group): Initial 、 ;

[0119] The hemoglobin deoxygenation ratios are 0.70, 0.50, and 0.80, respectively, corresponding to the calculation ; That is, 0.70, 0.50, 0.80; feedback switching is not enabled, so the "switch hemostasis mode" is all "no". Far exceeds the threshold of 0.5, and there is a high risk of tissue overheating; It is just critical, and there is also a certain risk.

[0120] 2. Pig kidney samples 4–6 (experimental group): Initial , detected in the first 100ms loop All are ≥0.6, entering the threshold judgment: Sample 4: , fine-tune according to the formula and order .at this time ; Therefore, "Switch Hemostasis Mode" is marked as "Yes".

[0121] The control group (pig kidney samples 1–3) was operated at the maximum temperature without photothermal feedback. , direct irradiation for 400ms, causing tissue temperature to rise The values ​​were 0.70, 0.50, and 0.80, respectively (corresponding to actual values ​​of 0.70°C, 0.50°C, and 0.80°C). The tissue temperature rise in two of the samples significantly exceeded the set safety threshold of 0.5°C, indicating a high risk of tissue overheating and potential thermal damage. Only sample 2 was at the critical threshold, posing a potential safety hazard.

[0122] The experimental group (pig kidney samples 4–6) was detected During the first 100ms cycle, the continuous power is automatically fine-tuned through photothermal feedback. The power was quickly reduced to 0.98, 0.94, and 1.00, and the first short irradiation time was limited to 100ms. The calculated tissue temperature rise was only 0.0343, 0.0423, and 0.03, respectively, which was far below the threshold of 0.5°C, successfully avoiding tissue overheating. The system then entered protection mode and continued short-term sweeps or slightly increased power, always maintaining .

[0123] The comparison shows that: at high deoxidation Under such circumstances, if no feedback measures are taken, the tissue temperature will rise rapidly to 0.70~0.80; after enabling the "photothermal feedback module automatically switches to hemostasis mode", the system can It dropped to 0.03-0.04, a decrease of more than 88%-96%, greatly reducing the risk of potential thermal damage.

[0124] Laser output mode selection module: used to select the optimal laser output mode based on the stone micropore acoustic spectrum and photothermal feedback data.

[0125] Further explanation: Get real-time normalized sound spectrum scalar , hemoglobin deoxygenation ratio R and normalized tissue temperature rise , and judge whether these three meet the preset threshold conditions, thereby establishing two predefined laser output modes;

[0126] Normalized spectral scalar : represents the overall resonance energy of the stone micropores; hemoglobin deoxygenation ratio : reflects the degree of tissue deoxygenation; tissue temperature rise :Based on the hemoglobin deoxygenation ratio R and the power normalization value of the continuous laser and Calculated; 4.1) The specific implementation steps are:

[0127] Output from the Gravel Efficiency module: ; Output from the photothermal feedback module: ; Output from the photothermal feedback module: . Set the stone hardness threshold: ; Stone soft threshold: ; Deoxygenation threshold: ; Tissue temperature rise threshold: .

[0128] 4.11) First determine whether the hemostasis mode conditions are met and If yes, proceed to the “hemostasis priority” situation; if no, continue to determine the hardness of the stone;

[0129] 4.12) If the hemostasis condition is not met, then If yes, then enter the "high hardness gravel" situation; if no, continue to judge If yes, then enter the “high-efficiency soft stone crushing” state; if no, then , then enter the "medium condition joint mode" situation;

[0130] 4.14) If and , then the “Hemostasis Priority” sign Otherwise, if ,but .

[0131] 、 : The threshold used to distinguish high hardness from low difficulty; 、 : Used to determine whether it is necessary to enter the hemostasis mode immediately.

[0132] 4.2) Select and execute one of two predefined laser output modes: if the mark is I, switch to thulium laser single wavelength pulse; if the mark is II, switch to thulium laser continuous wave hemostasis mode; among them, the thulium laser single wavelength pulse of mode I includes low peak power and high peak power modes.

[0133] The steps for switching the laser mode are as follows:

[0134] like :Execute mode I of thulium laser single wavelength pulse output; if : Execute mode II of thulium laser continuous wave hemostasis output;

[0135] Switching condition is met: the system clock determines the instant ;exist The hardware switch is completed within 10 ms. Specifically, the FPGA drives the switching of the optical path to the corresponding laser and pulse / continuous wave control unit. After the switch takes effect, the open loop warm-up is continued for 2 ms:

[0136] For the pulse mode of Mode I, the duty cycle is set to 1ms, during which two low-power "probe pulses" are sent to confirm that the optical path and detection are stable; for the continuous mode of Mode II, low-power light with a length of 4ms is directly sent to stabilize the output;

[0137] 4.3) Normalize and map the laser pulse parameters of each predefined laser output mode and set typical values; Mode I low peak power thulium laser corresponds to 、 Mode I high peak power thulium laser corresponding 、 ;

[0138] Mode II Thulium Continuous Wave Correspondence 、 ; It should be noted that: It is a marker for single wavelength pulses of thulium laser;

[0139] All powers, pulse widths, and continuous times are mapped to the interval (0,1]: the maximum peak power of thulium laser corresponds to ; Thulium pulse width up to 100μs corresponds to ; Thulium continuous wave maximum duration 400ms corresponding .

[0140] Mode I parameter settings, used for efficient soft stone fragmentation / tissue evaporation: peak power 40%, pulse width 60μs; normalized calculation: ;

[0141] Mode II parameter settings are used for efficient hemostasis: Thulium laser continuous wave mode, low power of 20% and single irradiation of 400ms.

[0142] 4.4) Based on the current mode, continuous monitoring , R and , within the same mode range, the normalized laser pulse parameters were fine-tuned by ±0.05 to dynamically balance lithotripsy efficiency and tissue protection, and the mode was switched again when the limit was exceeded; the specific implementation steps are as follows:

[0143] Continuous monitoring is collected every 100ms , R and , and perform mode judgment; if the current , R and If the three conditions still meet the range of the previously selected mode, the process enters the "mode maintenance" branch; otherwise, it switches to the new mode. The processing logic for fine-tuning during mode maintenance includes:

[0144] Mode I high peak power mode holding conditions: .when from 0.75 to 0.68, or R increases from 0.50 to 0.58, or Increase from 0.30 to 0.45, triggering fine-tuning: ; Ensure that after adjustment .

[0145] Mode I low peak power holding conditions: .when from 0.50 to 0.53 or R from 0.40 to 0.55, or From 0.20 to 0.45, trigger fine-tuning: ;

[0146] Mode II holding conditions: When R increases from 0.60 to 0.65 or Increasing from 0.50 to 0.55 further reduces the power or shortens the time: ;

[0147] like If it exceeds 0.5, it will continue to maintain Until .

[0148] For Mode I, calculate after fine-tuning ; ;ensure ; 0.2 is the minimum lithotripsy efficiency threshold; and ; 0.9 is the maximum "flash" risk threshold;

[0149] For Mode II, calculate after fine-tuning ; need to guarantee ; If any calculation result exceeds the limit, it will immediately switch back to the initial safety value of the corresponding mode.

[0150] 4.5) When any mode exceeds the limit, it will fall back in time and trigger re-determination, forming a closed-loop real-time control to ensure the efficiency of the lithotripsy process and the safety of the hemostasis process.

[0151] Furthermore, in order to demonstrate the usefulness of the "laser output mode selection module", this embodiment uses in vitro anthropomorphic human tissue and stone models for testing. First, three stone-tissue composite simulations (samples 1 to 3) are prepared. Each simulation is made of a tissue equivalent layer made of a silica gel matrix and a colloidal bovine hemoglobin solution, with calcium phosphate stone models of different microporosities embedded underneath; the stone diameter is 3mm-5mm, simulating the real stone environment in the ureter. The microporosity of the stone model is controlled to 20%, 40%, and 50%, respectively, to ensure the normalized acoustic spectrum scalar It varies in the range of 0.2 to 0.8, while the bovine hemoglobin concentration in the tissue layer is uniformly set at 1 mg / mL to simulate the physiological blood oxygen environment.

[0152] The whole experiment was placed in a constant temperature water bath at 37 °C, and an external Raman probe (785 nm excitation, fiber optic probe 2 mm ± 0.1 mm away from the tissue surface) was used to collect 1435 cm -1 and 1580 cm -1 The Raman signal was collected from the tissue phantom; tissue temperature was simultaneously measured in real time using an embedded thermocouple (buried in the tissue phantom, 1 mm from the stone base). The laser system used in the experiment included a thulium laser, and an optical fiber was coaxially positioned at the stone tip to ensure that the Raman signal collection area coincided with the heating zone.

[0153] Table 2: Benefits of “Laser Output Mode Selection Module”

[0154]

[0155] Actual tissue temperature rise: Peak temperature measured by thermocouple minus the initial 37 °C.

[0156] Tissue damage score: The score was assessed using the corresponding prepared tissue equivalent layer and referenced to histological sections. In this example, the tissue damage score of 0 = no damage, 0% area necrosis; 5 = more than 80% area necrosis; tissue damage scores of 1, 2, 3, 4, and so on are not repeated here.

[0157] Sample 4 is high hardness: ; ; ;because and , ; Select mode I high peak power mode thulium single wavelength pulse. Its normalization , the actual lithotripsy material was reduced by 45 mg, and the actual tissue temperature rise was only 1.02 °C. Compared with the control group, which had a temperature rise of 1.8 °C and a tissue damage score of 3, the dynamic temperature rise in mode I was lower, and tissue damage was significantly reduced. It should be noted that the actual tissue temperature rise is the value before normalization and can be greater than 1;

[0158] Sample 1 is medium hard: ;because and , immediately entering Mode II thulium continuous wave hemostasis. The actual tissue temperature rise of 0.82°C exceeded the set threshold, but due to the rapid power reduction and short irradiation time, the actual tissue damage score was only 4. In the control group, tissue temperature rise with continuous high power often reached 2.5°C, resulting in a score of 5. Although lithotripsy did not occur at this time, the hemostasis mode effectively avoided severe overheating.

[0159] Sample 2 is soft stone: ; and , thulium single-wavelength pulses in Mode I low peak power were selected. The normalized lithotripsy efficiency was 0.072, 25 mg of lithotripsy was achieved, tissue temperature rise was 0.48°C, and the injury score was 1. The thulium pulse mode is more suitable for soft stones, achieving lithotripsy at lower power with well-controlled tissue temperature rise.

[0160] Sample 3 is high deoxidation and high temperature: ; while satisfying , ; Entering Mode II Thulium Continuous Wave. Actual tissue temperature rise was 0.68°C, with a damage score of 3. Compared with the control (no real-time assessment, continuous high-power output, tissue temperature rise >3°C, damage score 5), module switching reduced tissue temperature rise by 78% and the damage score by 40%.

[0161] Compared with the traditional single fixation mode, this module preferentially switches to Mode II for hemostasis under high deoxygenation and high temperature conditions (samples 1 and 3), effectively controlling the tissue temperature rise within 0.8 °C; while if the control group continues at high power, the tissue temperature will rise by more than 2 °C, resulting in serious tissue damage.

[0162] Optimization of soft stone treatment: The soft stones in sample 2 can be broken up by low peak power pulses in mode I, but the actual tissue temperature rise and tissue damage scores are the lowest, indicating that thulium pulses are more reasonable for soft stones.

[0163] 1.1) The power supply unit includes a high-efficiency switching power supply module for converting 220VAC mains power into 400VDC direct current and outputting a stable 50A current for rapid charging and continuous discharge of the supercapacitor bank;

[0164] 1.2) The supercapacitor bank is composed of multiple modules connected in series; the series-parallel connection ensures a total capacity of 50F, a rated voltage of 300V, and can complete a charge and discharge cycle within 0.1s and provide a peak power of >10kW;

[0165] 1.3) The control unit adopts a DSP+FPGA hybrid architecture to process the sampled sound spectrum and Raman data, and outputs mode switching instructions and electrical pulse parameters to the drive unit according to the clock cycle;

[0166] The electric pulse parameters include electric pulse waveform, electric pulse peak and trough current values ​​and pulse duty cycle;

[0167] 1.4) The driving unit includes eight independent semiconductor pump laser drivers, each with adjustable output current and output voltage, and controls the pump light source via a PWM signal;

[0168] 1.5) The pump energy unit includes an integrated fiber combiner, which couples 8 pump lights into the thulium-doped fiber through a 1×8 combiner;

[0169] 1.6) The thulium-doped fiber laser optical module includes a thulium-doped fiber oscillator-amplifier, equipped with a fiber Bragg grating filter to achieve 1940nm or 2090nm output, and supports switching between pulse and continuous mode. The specific implementation steps include:

[0170] The oscillator + amplifier structure comprises: the oscillator includes a semiconductor laser pump source, a high-reflection fiber Bragg grating, a low-reflection fiber Bragg grating, a thulium-doped fiber, a forward fiber combiner, a reverse fiber combiner, and a cladding pump stripper;

[0171] The amplifier consists of a semiconductor laser pump source, a cladding pump stripper, a forward fiber combiner, a thulium-doped fiber, a backward fiber combiner, a cladding pump stripper, an output header, and an isolator between the oscillator and the amplifier. The amplifier is used to boost the low peak power of a thulium laser single-wavelength pulse to a high peak power target value.

[0172] Thulium-doped fiber: Tm 3+ Doping concentration 0.02mol%, absorption peak 780nm, gain bandwidth 20nm;

[0173] This approach improves the efficiency of hard stone fragmentation through the combined optimization of a micropore acoustic spectrum-microblasting model and photothermal Raman feedback-hemostasis regulation. Specifically, for hardness >1200 HU, lithotripsy time is reduced by ≥40%, while flashback is effectively suppressed. The combination of Raman spectroscopy and a temperature-control model achieves efficient hemostasis, keeping tissue temperature rise within a safe range and effectively preventing damage caused by excessive heating.

[0174] The dynamic adjustment of switching between two predefined laser output modes ensures adaptive function in complex surgical environments, effectively improves the synergistic effect of lithotripsy and hemostasis, and ensures flexibility and safety during the operation.

[0175] Supercapacitor energy supply and system compatibility: The supercapacitor group provides stable high-peak power support, enabling the system to operate efficiently on 220V AC power, avoiding the additional demand for high power on the operating room power supply.

[0176] Attachment Figure 2 It should be noted that: 210 is a switching power supply, which is connected to 220V AC power and provides DC output at the same time. 211 is a supercapacitor group, which provides high-peak power for the thulium-doped fiber laser drive system to ensure high-peak quasi-continuous thulium-doped fiber laser output. 213 is a control system, which is used to control the working state of the driver circuit board, including the electric pulse waveform, electric pulse peak and trough current values, pulse duty cycle, etc. The repetition frequency adjustment range can be 0Hz-5000Hz, and the pulse width is 20μs-10ms. 214 is a drive system, which mainly provides drive current for the indicator light semiconductor laser and the semiconductor laser pump source to make it work. The output of the semiconductor laser pump source depends on the electric pulse parameters set by the control system 213. The number of drive paths is expanded according to actual conditions and can be 1 path or multiple paths. In this embodiment, 15 paths are selected. 401 to 40N are the number indexes of the driver boards; 215 is the thulium-doped fiber laser pump source system, which provides pump energy for the thulium-doped fiber laser optical module 216 / 217. The optical pulse parameters of its output depend on the parameters of the electric pulse injected by the 214 driver system. Its single-channel peak power can reach hundreds of watts. The total number of channels matches the driver system and can be expanded according to actual conditions. It can be 1 channel or multiple channels; 501 to 50N are the number of LDs; 216 and 217 are thulium-doped fiber laser optical modules. The pump source is injected into the thulium-doped fiber through the fiber combiner. Combined with an oscillator or amplifier, it can achieve high-peak quasi-continuous thulium-doped fiber laser output of 1900nm-2100nm. Its output peak power depends on the total peak power of the pump source and can reach several kilowatts. Figure 4 Shown is the measured pulse data of the quasi-continuous thulium-doped fiber laser outputting peak power using this system.

[0177] Attachment Figure 3 It should be noted that: Label 1 represents the "Control-Unit" control unit; Label 2 represents data aggregation; Label 3 represents the pulse power selector; Label 4 represents the photothermal feedback unit; Label 5 represents the laser output mode selection; Label 8 represents the power supply unit; Label 9 represents the supercapacitor group; Label 7 represents the thulium-doped fiber laser element; Label 6 represents the laser output node selection.

[0178] Example 2:

[0179] This embodiment sets the thulium-doped fiber laser models based on the thulium-doped fiber laser optical module: TH-Twin-X and Hybrid-series respectively;

[0180] In this embodiment, the output characteristics of the thulium-doped fiber laser at different wavelengths and power modes are as follows:

[0181] The thulium-doped fiber laser in this embodiment has two independent peaks at 1940 nm. The maximum average output power of the thulium-doped fiber laser is distributed as follows:

[0182] TH-Twin-X: 120W continuous mode, 70W pulse mode;

[0183] Hybrid-series: 220W continuous mode, 180W pulse mode;

[0184] The power adjustment range of thulium-doped fiber laser is as follows:

[0185] TH-Twin-X: 1940nm wavelength continuous mode 10W~120W, pulse mode 5W~70W;

[0186] Hybrid-series: 1940nm wavelength continuous mode 20W~220W, pulse mode 5W~180W;

[0187] Single pulse energy adjustment range:

[0188] TH-Twin-X: 0.01J~6.0J adjustable, adjustment step is 0.01J;

[0189] Hybrid-model 0.03J ~ 8.0J adjustable, adjustment step is 0.01J;

[0190] The adjustment parameters of the repetition frequency are as follows: in thulium fiber pulse mode: adjustable from 10Hz to 2000Hz; the adjustment parameters of the pulse width are 20μs to 10ms.

[0191] It should be noted that all calculation formulas in this application document use regression analysis including but not limited to machine learning algorithms to deeply analyze the relevant parameters collected and identify their natural trends and relationships. Use professional software, such as Python's Scikit-learn library or R language, to automatically generate mathematical models that match the data. In all calculation formulas in this application, the parameters in each formula are dimensionally non-normalized within a consistent range to ensure that different physical quantities are compared on the same scale; dimensionless technical means include but are not limited to Min-Max-Normalization and Z-Score normalization;

[0192] The logic and / or steps represented in the flowcharts or otherwise described herein, for example, can be considered as a sequenced list of executable instructions for implementing the logical functions, and can be embodied in any computer-readable medium for use by, or in conjunction with, an instruction execution system, apparatus, or device (e.g., a computer-based system, a system including a processor, or other system that can fetch and execute instructions from an instruction execution system, apparatus, or device). For purposes of this specification, a "computer-readable medium" can be any device that can contain, store, communicate, propagate, or transport a program for use by, or in conjunction with, an instruction execution system, apparatus, or device.

[0193] It should be noted that the above embodiments are only used to illustrate the technical solutions of the present invention and are not intended to limit the present invention. Although the present invention has been described in detail with reference to the preferred embodiments, those skilled in the art should understand that the technical solutions of the present invention may be modified or replaced by equivalents without departing from the spirit and scope of the technical solutions of the present invention, which should all be included in the scope of the claims of the present invention.

Claims

1. A high-peak tunable thulium-doped fiber laser system powered by supercapacitors, comprising a power supply unit, a supercapacitor group unit, a control unit, a drive unit, a pump energy unit, and a thulium-doped fiber laser optical module; characterized in that: The processing logic of the control unit includes: Acoustic spectrum data acquisition module: used to collect acoustic spectrum data of stones using an ultrasonic micro-transmitting acoustic imaging probe in the laser irradiation area of ​​the fiber laser probe in the thulium-doped fiber laser optical module; The ultrasonic micro-transmission imaging probe is coaxially fixed with the fiber laser probe to ensure that the detection areas of the acoustic and laser beams coincide with each other, and to obtain the echo signal of the laser irradiation area. The echo signal is digitally sampled and pre-processed through a bandpass filter to extract the micropore acoustic wave components inside the stone in the laser irradiation area to obtain a bandpass echo signal. The bandpass echo signal is fast Fourier transformed to obtain the power spectrum and normalized to form the normalized acoustic spectrum feature vector. , among which each ; represents the normalized energy intensity in the i-th frequency band, represents the normalized energy intensity in the nth frequency band; Spectral feature vector Perform normalization processing to obtain the normalized sound spectrum scalar , the stone resonance intensity is judged by the threshold judgment mechanism, and the spectrum feature vector As the input of the pulse parameter optimization module; When the normalized spectrum scalar The closer it is to 1, the more concentrated the energy distribution in each frequency band within the stone is, the higher the stone resonance intensity is, and the more it is necessary to increase the pulse peak power. Pulse bombardment is performed, and the pulse width It needs to be reduced proportionally to balance the energy injection rate with the risk of preventing instantaneous high-energy "flash"; When the normalized spectrum scalar The closer it is to 0, the weaker the stone resonance intensity is, and the more the pulse peak power needs to be reduced. Or switch to continuous mode; By taking the normalized sound spectrum scalar and pulse peak power and pulse width As the independent variable, the crushing efficiency As the dependent variable, a stone crushing efficiency model was constructed based on the multiple regression model; the expression is ; Pulse peak power of laser output parameters using genetic algorithm and pulse width For search optimization, the population individual encoding used only contains these two variables, and iterative updates are performed with the comprehensive fitness F as the goal; the individual with the largest fitness during the iteration process is recorded and its corresponding comprehensive fitness ;Will and As "real-time gravel" pulse parameters, fed back to the drive unit; Pulse Parameter Optimization Module: Based on real-time acoustic spectrum data, a multivariate regression model is used to predict the relationship between laser output energy and stone micropore response. Through an optimization algorithm, laser output parameters are adjusted to maximize lithotripsy efficiency while minimizing "flash" during the lithotripsy process. Photothermal feedback module: used to collect the Raman signal of hemoglobin in the tissue in real time in the laser irradiation area and perform preprocessing; based on the Raman spectrum ratio, the hemoglobin deoxygenation ratio R, which reflects the degree of hemoglobin deoxygenation, is calculated; The continuous optical path output by the thulium-doped fiber laser optical module is coaxially arranged with the optical Raman spectrum sensor; the Raman excitation fiber probe is coaxially fixed with the continuous laser output fiber; The Raman signal is processed in a normalized manner and further used to calculate the hemoglobin deoxygenation ratio R. The range of the hemoglobin deoxygenation ratio R is limited to the interval (0,1). The closer the hemoglobin deoxygenation ratio R is to 1, the higher the degree of deoxygenation. According to the calculated hemoglobin deoxygenation ratio R, combined with the power normalization value and time normalization value of the continuous laser output, a temperature control regression model is constructed, and the normalized tissue temperature rise is calculated using the temperature control regression model. ; When the hemoglobin deoxygenation ratio R and tissue temperature rise When the corresponding preset threshold is exceeded, the control unit automatically switches to hemostasis mode; Laser output mode selection module: used to select the optimal laser output mode based on the stone micropore acoustic spectrum and photothermal feedback data.

2. The high-peak tunable thulium-doped fiber laser system based on supercapacitor power supply according to claim 1, characterized in that: The closer it is to 1, the higher the tissue temperature rise is; the hemostasis mode is normalized by adjusting the power of the continuous laser output and time-normalized values To stabilize tissue temperature rise In the safe range; set the hemoglobin deoxygenation ratio R to exceed the preset threshold ; Tissue temperature rise The preset threshold is ;when ,and When the hemostasis mode needs to be adjusted immediately or ; until the tissue temperature rises In a safe range.

3. The high-peak tunable thulium-doped fiber laser system based on supercapacitor power supply according to claim 2, characterized in that: Get real-time normalized sound spectrum scalar , hemoglobin deoxygenation ratio R and normalized tissue temperature rise , and judge whether these three meet the preset threshold conditions, thereby establishing two predefined laser output modes; Select and execute one of the two predefined laser output modes: if the mark is Mode I, it switches to thulium laser single wavelength pulse; if the mark is Mode II, it switches to thulium laser continuous wave hemostasis mode; Among them, the thulium laser single wavelength pulse of mode I includes low peak power and high peak power modes.

4. The high-peak tunable thulium-doped fiber laser system based on supercapacitor power supply according to claim 3, characterized in that: Normalize and map the laser pulse parameters of each predefined laser output mode and set typical values; On the basis of maintaining the current mode, through continuous monitoring , R and , the normalized laser pulse parameters are numerically fine-tuned within the same mode range to dynamically balance the lithotripsy efficiency and tissue protection, and the mode is switched again when the limit is exceeded; when any mode exceeds the limit, it is promptly retreated and re-judgment is triggered to form a closed-loop real-time control.

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