Endoscope data processing method and system

Abstract

The invention discloses an endoscope data processing method and system, and belongs to the field of endoscopes. The method comprises the steps that a basic pressure threshold a0 and a basic temperature threshold b0 of a user are set; collecting a pressure value a1 and a temperature value b1 through an endoscope; performing error correction on the pressure value a1 and the temperature value b1 through a compensation algorithm; according to the pressure value a1'and the temperature value b1 'after error correction, a basic pressure threshold value a0 and a basic temperature threshold value b0, a control strategy of the perfusion flow and the suction flow is generated; according to the control strategy, a PWM algorithm is adopted to generate control signals of perfusion driving and attraction driving; and the filter circuit and the isolation circuit are used for processing the control signal. In order to solve the problem that perfusion and suction flow control is not coordinated in the endoscopic surgery process in the prior art, four control strategies are generated through an error compensation algorithm and according to temperature and pressure parameters, and the stability of perfusion and suction flow control is improved.

Description

TECHNICAL FIELD

[0001] The present application relates to the field of endoscopes, more particularly, to an endoscope data processing method and system. BACKGROUND

[0002] As a precise detection device, endoscope systems need to monitor and control the pressure and temperature parameters of the working environment in real time in actual applications. The traditional endoscope system has the following technical problems in data processing:

[0003] Firstly, the existing endoscope system usually uses independent pressure and temperature sensors for data acquisition, but due to the limited accuracy of the sensors, environmental interference and other factors, the raw data collected has large errors, and there is a lack of effective error compensation mechanism, resulting in low data reliability.

[0004] Secondly, in terms of flow control, the traditional system mostly uses manual control or simple open-loop control method, and there is a lack of coordinated control mechanism between perfusion flow and suction flow. When the environmental pressure or temperature changes, the system cannot intelligently adjust the perfusion and suction flow according to the real-time data, which easily causes the pressure in the working cavity to fluctuate too much or the temperature to be out of control, affecting the stability and safety of the system.

[0005] Thirdly, the control signals in the prior art are easily affected by electromagnetic interference and noise during transmission, and lack effective signal processing and isolation measures, resulting in decreased control accuracy and delayed system response.

[0006] In addition, the traditional endoscope system usually uses a fixed control mode and cannot develop differentiated control strategies according to different pressure and temperature combinations, making it difficult to adapt to complex and variable working environments.

[0007] Therefore, there is an urgent need for an endoscope data processing method to improve the coordination of perfusion and suction flow. SUMMARY

[0008] In view of the uncoordinated control of perfusion and suction flow in the endoscopic surgery process in the prior art, the present application provides an endoscope data processing method and system, which improves the stability of perfusion and suction flow control through error compensation algorithm and four control strategies generated according to temperature and pressure parameters.

[0009] One aspect of the present application provides a method for processing endoscopic data, comprising: S1, setting a user's basic pressure threshold a0 and a basic temperature threshold b0; S2, collecting pressure value a1 and temperature value b1 through an endoscope; S3, correcting errors of the pressure value a1 and the temperature value b1 through a compensation algorithm; S4, generating a control strategy of perfusion flow and suction flow according to the error-corrected pressure value a1' and temperature value b1', and the basic pressure threshold a0 and the basic temperature threshold b0; S5, generating control signals of perfusion drive and suction drive according to the control strategy using a PWM algorithm; and S6, processing the control signals using a filter circuit and an isolation circuit.

[0010] Further, S3, correcting errors of the pressure value a1 and the temperature value b1 through a compensation algorithm, comprises: taking the pressure value a1 or the temperature value b1 as a to-be-corrected value C1; judging whether the to-be-corrected value C1 is a first collection value according to a preset first collection value X1; if yes, taking the to-be-corrected value C1 as an initial reference value, and outputting the to-be-corrected value C1 as an error-corrected value; if no, calculating a compensation value X2 according to the first collection value X1, the basic pressure threshold a0 or the basic temperature threshold b0, and the to-be-corrected value C1; calculating a final compensation value AC according to the first collection value X1, the compensation value X2, the basic pressure threshold a0 or the basic temperature threshold b0, and the to-be-corrected value C1; and correcting the to-be-corrected value C1 according to the compensation value X2 and the final compensation value AC: when the to-be-corrected value C1 is the pressure value a1, obtaining an error-corrected pressure value a1'; and when the to-be-corrected value C1 is the temperature value b1, obtaining an error-corrected temperature value b1';

[0011] In particular, in actual work, the pressure and temperature sensors of the endoscope will produce zero drift and sensitivity deviation due to environmental changes, device aging and other factors. Therefore, the present application takes the first collection value X1 as the initial reference, which fully considers the characteristics that the initial working state of the endoscope may be different each time it is used, avoids systematic errors caused by using a fixed zero point, and realizes adaptive dynamic calibration.

[0012] In addition, the present application first calculates a preliminary compensation value X2 through the first collection value X1, the basic threshold (a0 or b0) and the current collection value C1, and then calculates a final compensation value AC by comprehensively considering these parameters. This hierarchical compensation structure can more accurately capture and correct different types of error sources, including linear drift and nonlinear distortion, ensuring the accuracy of data correction.

[0013] Finally, considering the need to generate four different control strategies based on pressure and temperature data, the compensation algorithm incorporates the basic pressure threshold a0 and basic temperature threshold b0 into the compensation calculation during its design. This design makes the corrected data closer to the requirements of control decisions, improving the control accuracy and response speed of the entire system.

[0014] Furthermore, S4, based on the error-corrected pressure value a1' and temperature value b1', as well as the baseline pressure threshold a0 and baseline temperature threshold b0, a control strategy for infusion flow rate and suction flow rate is generated, including: comparing the error-corrected pressure value a1' with the baseline pressure threshold a0, and comparing the error-corrected temperature value b1' with the baseline temperature threshold b0.

[0015] Based on the comparison results, the following control strategies are generated: when a1'>a0 and b1'>b0, the first control strategy is generated; when a1'>a0 and b1'≤b0, the second control strategy is generated; when a1'≤a0 and b1'>b0, the third control strategy is generated; and when a1'≤a0 and b1'≤b0, the fourth control strategy is generated.

[0016] Specifically, in the endoscopic working environment, pressure and temperature are two key parameters that influence each other. This application couples pressure and temperature for analysis, constructing a control decision matrix based on a two-dimensional parameter space. This overcomes the limitations of traditional single-parameter control, more comprehensively reflecting the actual state within the working chamber and achieving true multi-parameter collaborative control.

[0017] In traditional systems, perfusion and suction are often controlled independently, which can easily lead to drastic fluctuations in the intracavitary environment. This approach considers perfusion and suction as a holistic system and achieves coordinated operation between the two through four strategies: enhancing suction when depressurization is needed, enhancing perfusion when cooling is needed, and minimizing intervention under normal conditions.

[0018] Furthermore, the first control strategy is to increase the suction flow rate while maintaining the preset infusion flow rate. Specifically, when both pressure and temperature exceed the limit, the suction flow rate is increased first to quickly reduce the pressure inside the cavity, while maintaining a stable infusion flow rate to avoid blurred vision due to reduced infusion, thus reflecting a balance between safety and operability.

[0019] The second control strategy is to set the infusion flow rate to equal the suction flow rate; by setting the infusion flow rate to equal the suction flow rate, the pressure can be steadily reduced through flow balance control. This equal flow rate design can maintain the circulation and renewal of the fluid in the cavity while reducing the pressure, and prevent local accumulation.

[0020] The third control strategy is to increase the infusion flow rate while setting the suction flow rate to be less than the infusion flow rate. Increasing the infusion flow rate promotes heat dissipation, while keeping the suction flow rate less than the infusion flow rate ensures that there is a net inflow to remove heat, which reflects the precise control of temperature.

[0021] The fourth control strategy is to maintain the preset basic infusion flow rate and stop the suction operation; by maintaining the basic infusion and stopping the suction, the principle of minimal intervention is adopted to reduce system energy consumption and extend the service life of the equipment.

[0022] Endoscopic systems require rapid response to environmental changes while maintaining control stability. This solution achieves rapid status determination through threshold comparison, and each strategy has a clear flow control objective, ensuring both response speed and avoiding system oscillations caused by frequent switching.

[0023] Furthermore, in step S5, according to the control strategy, a PWM algorithm is used to generate control signals for infusion drive and suction drive, including: determining the target values ​​for infusion flow rate and suction flow rate according to the control strategy; converting the target value for infusion flow rate into the target duty cycle of the infusion drive control signal, and converting the target value for suction flow rate into the target duty cycle of the suction drive control signal; adjusting the duty cycle of the infusion drive control signal and the suction drive control signal respectively according to the target duty cycle using the PWM algorithm through the MCU controller; and generating the corresponding infusion drive control signal and suction drive control signal according to the adjusted duty cycle.

[0024] Specifically, pump actuators in endoscope systems are typically driven by motors. PWM (Pulse Width Modulation) technology controls the motor speed by adjusting the duty cycle of a square wave signal, thereby precisely controlling the flow rate. Compared to traditional analog control methods, PWM offers advantages such as high control precision, fast response speed, and strong anti-interference capabilities, making it particularly suitable for applications like endoscopes that require precise control. By converting the target flow rate value into a duty cycle, a precise mapping from digital control signals to physical flow rate is achieved.

[0025] Furthermore, using the MCU controller and a PWM algorithm, the duty cycles of the infusion drive control signal and the suction drive control signal are adjusted according to the target duty cycle. This includes: when executing the first control strategy, calculating the suction flow rate amplification coefficient based on the pressure deviation value (a1'-a0) and the temperature deviation value (b1'-b0), and adjusting the duty cycle of the suction drive control signal according to the amplification coefficient, while maintaining the duty cycle of the infusion drive control signal at a preset reference value; wherein, the degree of pressure exceedance is determined by calculating (a1'-a0), the larger the deviation, the stronger the adjustment, achieving proportional fine control. The amplification coefficient is calculated based on the dual-parameter deviation to achieve adaptive enhancement of the suction flow rate, and the continuously adjustable duty cycle ensures smooth flow rate changes.

[0026] When the second control strategy is executed, the duty cycle of the infusion drive control signal is set to be equal to the duty cycle of the suction drive control signal. The precise balance between infusion and suction is achieved by setting the same duty cycle, which is difficult to achieve in analog control and demonstrates the advantages of digital control.

[0027] When the third control strategy is executed, the infusion flow rate amplification factor is calculated based on the temperature deviation value (b1'-b0), and the duty cycle of the infusion drive control signal is adjusted according to the amplification factor. Simultaneously, the duty cycle of the suction drive control signal is set to be less than that of the infusion drive control signal based on the pressure difference value (a0-a1'). The degree of temperature exceedance is determined by calculating (b1'-b0), providing a quantitative basis for adjusting the infusion flow rate. Simultaneously adjusting two PWM signals while maintaining a specific proportional relationship achieves complex coordinated control logic.

[0028] When executing the fourth control strategy, the duty cycle of the injection drive control signal is kept at a preset reference value, while the duty cycle of the attraction drive control signal is set to zero. Setting the attraction duty cycle to zero achieves true zero-power standby.

[0029] Furthermore, in step S6, a filtering circuit and an isolation circuit are used to process the control signal, including: converting the control signal into an analog signal through a DA converter; filtering the analog signal; electrically isolating the filtered signal; and outputting the electrically isolated injection drive control signal to the injection drive circuit and the electrically isolated suction drive control signal to the suction drive circuit.

[0030] Furthermore, the analog signal is filtered, including: using a π-type filter circuit to perform bandpass filtering on the analog signal. The π-type filter circuit includes a first capacitor C1, a second capacitor C2, and a resistor R; by adjusting the parameter values ​​of the first capacitor C1, the second capacitor C2, and the resistor R, the high-frequency cutoff frequency fH = 1 / (2πRC1) and the low-frequency cutoff frequency fL = 1 / (2πRC2) of the filter circuit are set to form a bandpass filter with a bandwidth BW = fH - fL; the bandpass filter is used to filter out high-frequency noise and low-frequency interference in the control signal to retain the effective frequency components of the control signal.

[0031] Another aspect of this application provides an endoscope data processing system, comprising: a parameter setting module for setting a user's baseline pressure threshold a0 and baseline temperature threshold b0; a data acquisition module connected to the endoscope for acquiring pressure values ​​a1 and temperature values ​​b1; an error correction module for correcting the pressure values ​​a1 and temperature values ​​b1 using a compensation algorithm to obtain error-corrected pressure values ​​a1' and temperature values ​​b1'; a control strategy module for generating control strategies for perfusion flow rate and suction flow rate based on the error-corrected pressure values ​​a1' and temperature values ​​b1', as well as the baseline pressure threshold a0 and baseline temperature threshold b0; a signal processing module for generating perfusion drive control signals and suction drive control signals based on the control strategies; a perfusion drive circuit for driving a perfusion pump according to the perfusion drive control signals to control the perfusion flow rate; and a suction drive circuit for driving a suction pump according to the suction drive control signals to control the suction flow rate.

[0032] Furthermore, the signal processing module includes: an MCU controller that generates control signals for injection drive and attraction drive using a PWM algorithm according to the control strategy; a DA converter that converts the control signals into analog signals; a filtering circuit that filters the analog signals to remove high-frequency signals and low-frequency interference; and an isolation circuit that electrically isolates the filtered signals to isolate the control signals from the drive circuit.

[0033] Compared to existing technologies, the advantages of this application are:

[0034] (1) An error compensation algorithm is used to correct the pressure and temperature data in real time. By setting an initial reference value and dynamically calculating the compensation value based on the first acquisition value, the measurement error caused by sensor drift and environmental factors is effectively eliminated, the data acquisition accuracy is significantly improved, and a reliable data foundation is provided for subsequent precise control.

[0035] (2) Based on the comparison results of pressure and temperature parameters with the basic threshold, four differentiated control strategies are generated, which realizes the coordinated control of infusion flow and suction flow, and avoids the problems of intracavitary pressure fluctuation and temperature runaway caused by the single control mode in the existing technology.

[0036] (3) By dynamically adjusting the duty cycle according to different control strategies through the PWM algorithm, and by combining the π-type filter circuit and the optocoupler isolation circuit to process the control signal, not only is the precise control of the injection and suction flow achieved, but also the high-frequency noise and low-frequency interference are effectively suppressed, thereby improving the anti-interference capability and control accuracy of the system. Attached Figure Description

[0037] Figure 1 This application describes the operating principle of a control signal for perfusion suction control according to an embodiment of the present application.

[0038] Figure 2 This is a diagram illustrating an analog signal filtering process according to an embodiment of this application;

[0039] Figure 3 This is a schematic diagram of an endoscope connection according to an embodiment of this application;

[0040] Figure 4 This is a schematic diagram of an endoscope lens according to an embodiment of this application.

[0041] Explanation of the labels in the diagram:

[0042] 1-Electronic endoscope, 2-Endoscope insertion part, 3-Gold finger connector, 4-Signal connection cable, 5-Endoscope handle;

[0043] 21-Head end, 22-Bent section, 51 Suction button, 52 Rotating lever, 53 Working channel, 54 Coaxial rotating device;

[0044] 210 - Image sensor, 211 - LED lighting, 212 - Water injection channel, 213 - Temperature and pressure sensor, 214 - Suction channel. Detailed Implementation

[0045] The present application will now be described in detail with reference to the accompanying drawings and specific embodiments.

[0046] Example 1

[0047] like Figure 1 As shown, pressure values ​​a1 and b1 are collected respectively. Pressure value a1 is transmitted through optocoupler isolation circuit 1 and pressure value b1 is transmitted through optocoupler isolation circuit 2. The input signals are then transmitted to the MCU control center through DA1 and DA2 respectively. The MCU control center then transmits the filtered signals to the infusion drive circuit and the suction drive circuit respectively, thereby controlling the infusion pump and the suction pump.

[0048] Specifically, step 1: Set the basic pressure threshold a0 (760 mmHg ~ 1000 mmHg) and temperature threshold b0 (27.3℃ - 1000℃);

[0049] Step 2: Collect real-time pressure values ​​a1 and temperature values ​​b1 at different locations of the electronic endoscope entering the human body;

[0050] To ensure the accuracy of real-time pressure values ​​a1 and temperature values ​​b1, algorithm compensation is required.

[0051] Determine whether this is the first time the sensor has collected data based on the first collected value X1.

[0052] The difference plus or minus value X2 is determined based on the first value X1, the basic threshold a0 or b0, and the current value C1.

[0053] The compensation value ΔC is determined based on the first numerical value X1, the difference plus or minus value X2, the basic threshold a0 or b0, and the current voltage value C1.

[0054] The current value C1 is automatically corrected based on the voltage difference plus or minus the value X2 and the compensation value ΔC to obtain the final value C1 (C1 = a1 or b1).

[0055] Step 3: Compare the pressure value a1 and temperature value b1 with the baseline thresholds a0 and b0, respectively.

[0056] When a1 > a0 and b1 > b0, it indicates that the internal pressure value exceeds the baseline pressure threshold and the temperature threshold also exceeds the baseline temperature threshold. It is necessary to increase the suction water flow rate while maintaining a certain injection water flow rate. By continuously suctioning out water, the internal pressure value is reduced, and the temperature is carried away.

[0057] When a1>a0; b1≤b0, it indicates that the internal pressure value exceeds the baseline pressure threshold, and the temperature value meets the expected set threshold, so no excessive intervention is needed. Therefore, during the operation, it is necessary to maintain a certain baseline pressure threshold, and the irrigation water flow rate needs to be equal to the aspiration water flow rate. At this time, the irrigation water flow rate can meet the needs of flushing and maintain a certain aspiration volume, so as not to cause the pressure value to be too high.

[0058] When a1≤a0; b1>b0, it indicates that the body pressure is lower than the baseline pressure threshold and the temperature is higher than the temperature threshold. It is necessary to increase the infusion water flow rate to lower the body temperature through a large water flow. At the same time, it is necessary to set the suction water flow rate < the infusion water flow rate and maintain a certain suction water flow rate to quickly lower the temperature.

[0059] When a1≤a0; b1≤b0, it indicates that the body pressure is lower than the baseline pressure threshold and the temperature is lower than the temperature threshold. In this case, it is necessary to maintain the normal perfusion water flow rate to bring the body pressure to the baseline pressure threshold. Since the temperature is lower than the temperature threshold, suction is not required in this situation.

[0060] Furthermore, the irrigation water flow rate is controlled by an intelligent pressure control drive module integrated with a matching image processor, which outputs a corresponding electrical signal to the irrigation drive circuit, thereby affecting the change in irrigation flow rate. The output of the electrical signal can be controlled by an MCU, which uses a PWM algorithm to affect the effective amplitude of the electrical signal, i.e., by changing the duty cycle.

[0061] Furthermore, the aspiration water flow rate is controlled by an intelligent pressure control drive module integrated with a matching image processor, which outputs a corresponding electrical signal to the aspiration drive circuit, thereby affecting the change in the aspiration water flow rate. The output of the electrical signal can be controlled by an MCU, which uses a PWM algorithm to affect the effective amplitude of the electrical signal, i.e., by changing the duty cycle.

[0062] To elaborate further, the electrical signals output by the MCU control center need to be converted to analog-to-digital converters (DA converters) to ensure the accuracy of the output data. Figure 2 As shown, especially for MEMS sensors with sensitivity in the range of 5-20mV, a π-type filter circuit needs to be added. This circuit consists of two capacitors and one resistor. The capacitors are mainly used to absorb high-frequency signals, while the resistor is used for signal impedance matching and also to suppress low-frequency signals. The combination of the resistor and capacitor can form a very good bandpass filter.

[0063] The bandwidth of the bandpass filter is calculated as the difference between the high-frequency cutoff frequency and the low-frequency cutoff frequency. The specific formula is: BW = fH - fL, where fH = 1 / (2πRC1) and fL = 1 / (2πRC2).

[0064] Furthermore, in order to ensure effective isolation of digital and analog signals and suppression of common-mode signals, improve differential mode rejection ratio, and more importantly, to meet the dielectric strength requirements of the electronic endoscope sensor to the matching image processor, the MOC3023M thyristor optocoupler is selected, which has a high voltage peak-to-peak value of up to 3.75KV, thus forming an optocoupler isolation circuit. Optocoupler isolation circuit 1 and optocoupler isolation circuit 2 are designed with the same chip, and are distinguished only for ease of description.

[0065] Step 4: Real-time display of the UI interface. The QT language is used to realize communication between the monitor and the matching image processor, and the current pressure and temperature value curves are displayed through the interface.

[0066] Example 2

[0067] like Figure 3 As shown, an intelligent drive system for improving the efficiency of endoscopic stone removal consists of an electronic endoscope 1, an endoscope insertion part 2, a gold finger connector 3, a signal connection line 4, and an endoscope handle 5.

[0068] The electronic endoscope 1 is electrically connected to the endoscope image processor via the plug of the signal connection cable 4. The endoscope image processor is responsible for processing the image signals acquired by the tip of the electronic endoscope 1 and displaying them on the monitor. The endoscope image processor mainly enhances the image details and color changes of human tissue parts by adjusting saturation, sharpness, and brightness, helping doctors to observe the real-time images acquired by the tip of the electronic endoscope 1 more clearly.

[0069] The handle of the electronic endoscope 1 includes an inlet connector that connects to a flushing tube, which in turn connects to an infusion pump. The flushing tube is connected to the squeezing tube of the infusion pump. The infusion pressure is adjusted by regulating the speed of the infusion pump, thereby changing the flow rate entering the inlet connector of the electronic endoscope 1. The handle of the electronic endoscope 1 includes an outlet connector that connects to a suction tube, which in turn connects to one end of a suction pump. The other end of the suction pump is connected to a waste collection bottle. The flow rate exiting the electronic endoscope 1 from the outlet connector is changed by adjusting the suction pressure of the suction pump.

[0070] An electronic endoscope 1 typically consists of a head tip 21, a curved part 22, an endoscope insertion part 2, a gold finger connector 3, a signal connection line 4, and an endoscope handle 5. The endoscope handle 5 also consists of a suction button 51, a rotation lever 52, a working channel 53, and a coaxial rotation device 54.

[0071] The tip of the electronic endoscope 1 is a crucial component for image acquisition. It integrates basic components such as the injection-molded tip, image sensor, built-in LED illumination source, and a working channel. The image sensor is the core of the endoscope's imaging process; the image sensor type is CMOS. The injection-molded tip is typically made of PC / PEEK material.

[0072] The curved section of the electronic endoscope 1 is generally achieved by a flexible snake tube, which is covered with a Pebax / Tpu outer skin. By rotating the lever 52, the internal traction wire is driven to bend the snake tube of the curved section, which can be easily inserted into the body and observed for the target area.

[0073] The insertion section of the electronic endoscope 1 is a multi-layered composite braided tubular structure, externally covered with Pebax / TPU, and internally made of 304 medical-grade stainless steel. It contains cables, a working channel, and a traction wire; the working channel is typically made of PTFE. Its main function is to insert the tip into the target tissue area of ​​the human body. The insertion tube has a certain degree of elasticity, including the tip and a bend, allowing for easy insertion into the body and observation of the target area.

[0074] The electronic endoscope 1 handle has a rotary lever to control the rotation of the curved section, and also includes a suction button 51 and a working channel 53. The suction button is pressed to initiate suction operations, and released to stop them. The endoscope handle 5 also has a working channel 53 inlet, through which diagnostic and therapeutic accessories of the electronic endoscope 1 are inserted and removed. The endoscope also has a coaxial rotating device 54, which, when rotated clockwise or counterclockwise, allows the insertion section to rotate clockwise or counterclockwise.

[0075] like Figure 4As shown, the tip of an electronic endoscope 1 typically consists of an image sensor 210, an LED illumination 211, a water injection channel 212, a temperature and pressure sensor 213, and a suction channel 214. The image sensor primarily uses the photoelectric effect to convert light signals from internal tissues into voltage signals, and then uses analog-to-digital conversion to transmit digital image data to the endoscope image processor.

[0076] The LED lighting source is mainly a white D65 standard light source (color temperature between 3000-7000K) with a color rendering index Ra>85, providing sufficient brightness for the target area to be captured by the image sensor. It usually ensures an illuminance of >1500 lux at a working distance of 10mm.

[0077] The water injection channel is made of PTFE-lined tubing and is separate from the suction channel 214. The saline solution used for external infusion pumps is injected into the working channel 53 through the working channel of the electronic endoscope 1, so as to rinse the dirt at the tip of the electronic endoscope 1 and fill the internal tissue, giving the operator a sufficient field of view while ensuring clear images.

[0078] The temperature and pressure sensors are primarily MEMS (Mechanical, Electronic, and Mechanical) sensors. For pressure measurement, changes in water pressure are transmitted to the surface of the integrated temperature and pressure sensor, causing a change in the internal pressure-sensitive resistor. This change in water pressure is then converted into a corresponding voltage signal, which is then processed by an image processing circuit to measure and output the specific numerical value of the water pressure change. Similarly, for temperature measurement, changes in water temperature are transmitted to the surface of the integrated temperature and pressure sensor, causing a change in the internal thermistor. This change in water temperature is also converted into a corresponding voltage signal, which is then processed by an image processing circuit to measure and output the specific numerical value of the water temperature change.

[0079] The suction channel and the water injection channel are independent. The insertion part of the electronic endoscope 1 has a three-lumen tube structure, which consists of two water injection channels and one suction channel. By connecting an external negative pressure source and pressing the suction button, the suction channel can drain the liquid from the tip of the electronic endoscope 1.

[0080] The foregoing illustrative description of the present application and its embodiments is not restrictive and can be implemented in other specific forms without departing from the spirit or essential characteristics of the present application. The accompanying drawings are only one embodiment of the present application, and the actual structure is not limited thereto. Therefore, if those skilled in the art are inspired by this description and design similar structures and embodiments without departing from the spirit of the present application, such designs should fall within the scope of protection of this application. Furthermore, the word "comprising" does not exclude other elements or steps, and the word "a" preceding an element does not exclude the inclusion of "a plurality" of that element. Terms such as "first," "second," etc., are used to indicate names and do not indicate any specific order.

Claims

1. A method for processing endoscopic data, characterized in that, include: S1, set the user's basic pressure threshold a0 and basic temperature threshold b0; S2, pressure value a1 and temperature value b1 are collected through an endoscope; S3, the pressure value a1 and temperature value b1 are corrected for errors through a compensation algorithm; S4. Based on the error-corrected pressure value a1' and temperature value b1', as well as the basic pressure threshold a0 and basic temperature threshold b0, a control strategy for infusion flow rate and suction flow rate is generated. S5, according to the control strategy, the PWM algorithm is used to generate control signals for injection drive and attraction drive; S6 uses a filter circuit and an isolation circuit to process the control signal.

2. The method for processing endoscopic data according to claim 1, characterized in that: S3, uses a compensation algorithm to correct errors in the pressure value a1 and temperature value b1, including: Use the pressure value a1 or temperature value b1 as the value to be corrected, C1. Based on the preset first acquisition value X1, determine whether the value to be corrected C1 is the value acquired in the first acquisition: If so, the value to be corrected, C1, will be used as the initial reference value, and the value to be corrected, C1, will be output as the value after error correction. If not, calculate the compensation value X2 based on the first collected value X1, the basic pressure threshold a0 or the basic temperature threshold b0, and the value to be corrected C1. The final compensation value ΔC is calculated based on the first collected value X1, the compensation value X2, the basic pressure threshold a0 or the basic temperature threshold b0, and the value to be corrected C1. Based on the compensation value X2 and the final compensation value ΔC, the value C1 to be corrected is corrected: When the value to be corrected C1 is the pressure value a1, the pressure value a1' after error correction is obtained; When the value to be corrected, C1, is the temperature value, b1, the temperature value after error correction is obtained.

3. The method for processing endoscopic data according to claim 1, characterized in that: S4, based on the error-corrected pressure value a1' and temperature value b1', as well as the baseline pressure threshold a0 and baseline temperature threshold b0, generates a control strategy for infusion flow rate and suction flow rate, including: Compare the error-corrected pressure value a1' with the baseline pressure threshold a0, and compare the error-corrected temperature value b1' with the baseline temperature threshold b0; Generate a control strategy based on the comparison results: When a1'>a0 and b1'>b0, the first control strategy is generated; When a1'>a0 and b1'≤b0, a second control strategy is generated; When a1'≤a0 and b1'>b0, a third control strategy is generated; When a1'≤a0 and b1'≤b0, a fourth control strategy is generated.

4. The method for processing endoscopic data according to claim 3, characterized in that: The first control strategy is to increase the suction flow while maintaining the preset infusion flow. The second control strategy is to set the infusion flow rate equal to the aspiration flow rate; The third control strategy is to increase the infusion flow rate while setting the suction flow rate to be less than the infusion flow rate; The fourth control strategy is to maintain the preset baseline infusion flow rate and stop the suction operation.

5. The method for processing endoscopic data according to claim 3, characterized in that: S5, based on the control strategy, uses a PWM algorithm to generate control signals for injection drive and attraction drive, including: Based on the control strategy, determine the target values ​​for infusion flow rate and aspiration flow rate; Convert the target value of the infusion flow rate into the target duty cycle of the infusion drive control signal, and convert the target value of the suction flow rate into the target duty cycle of the suction drive control signal; The duty cycle of the injection drive control signal and the attraction drive control signal are adjusted according to the target duty cycle by the MCU controller using the PWM algorithm. Based on the adjusted duty cycle, corresponding infusion drive control signals and suction drive control signals are generated.

6. The method for processing endoscopic data according to claim 5, characterized in that: The MCU controller uses a PWM algorithm to adjust the duty cycles of the injection drive control signal and the suction drive control signal according to the target duty cycle, including: When the first control strategy is executed, the suction flow rate increase coefficient is calculated based on the pressure deviation value (a1'-a0) and the temperature deviation value (b1'-b0). The duty cycle of the suction drive control signal is adjusted according to the increase coefficient, while the duty cycle of the injection drive control signal is maintained at the preset reference value. When the second control strategy is executed, the duty cycle of the injection drive control signal is set to be equal to the duty cycle of the attraction drive control signal; When the third control strategy is executed, the infusion flow rate increase coefficient is calculated based on the temperature deviation value (b1'-b0), and the duty cycle of the infusion drive control signal is adjusted according to the increase coefficient. At the same time, the duty cycle of the suction drive control signal is set to be less than the duty cycle of the infusion drive control signal based on the pressure difference value (a0-a1'). When the fourth control strategy is executed, the duty cycle of the infusion drive control signal is kept at the preset reference value, and the duty cycle of the attraction drive control signal is set to zero.

7. The method for processing endoscopic data according to claim 5, characterized in that: S6 employs filtering and isolation circuits to process the control signal, including: The control signal is converted into an analog signal using a DA converter; Perform filtering on the analog signal; Electrical isolation is applied to the filtered signal; The electrically isolated infusion drive control signal is output to the infusion drive circuit, and the electrically isolated suction drive control signal is output to the suction drive circuit.

8. The method for processing endoscopic data according to claim 7, characterized in that: Filtering of analog signals includes: A π-type filter circuit is used to perform bandpass filtering on the analog signal. The π-type filter circuit includes a first capacitor C1, a second capacitor C2, and a resistor R. By adjusting the parameter values ​​of the first capacitor C1, the second capacitor C2, and the resistor R, the high-frequency cutoff frequency fH = 1 / (2πRC1) and the low-frequency cutoff frequency fL = 1 / (2πRC2) of the filter circuit are set, forming a bandpass filter with bandwidth BW = fH - fL. A bandpass filter is used to remove high-frequency noise and low-frequency interference from the control signal in order to retain the effective frequency components of the control signal.

9. A system for processing endoscopic data, characterized in that, include: The parameter setting module allows users to set the basic pressure threshold a0 and the basic temperature threshold b0. The data acquisition module is connected to the endoscope and collects pressure value a1 and temperature value b1. The error correction module performs error correction on the pressure value a1 and the temperature value b1 through a compensation algorithm, and obtains the error-corrected pressure value a1' and temperature value b1'. The control strategy module generates control strategies for infusion flow rate and suction flow rate based on the error-corrected pressure value a1' and temperature value b1', as well as the basic pressure threshold a0 and basic temperature threshold b0. The signal processing module generates infusion drive control signals and suction drive control signals according to the control strategy; The infusion drive circuit drives the infusion pump according to the infusion drive control signal to control the infusion flow rate; The suction drive circuit drives the suction pump according to the suction drive control signal to control the suction flow rate.

10. The endoscopic data processing system according to claim 9, characterized in that: The signal processing module includes: The MCU controller uses a PWM algorithm to generate control signals for injection drive and attraction drive according to the control strategy; A DA converter converts control signals into analog signals; The filtering circuit filters the analog signal, removing high-frequency signals and low-frequency interference. An isolation circuit provides electrical isolation to the filtered signal, thereby isolating the control signal from the drive circuit.

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