Laser flicker suppression method and system for endoscope diagnosis

Abstract

The invention provides a laser flicker suppression method and system for endoscope diagnosis, and belongs to the technical field of endoscope image processing. A pulse synchronization signal PluseSYNC of laser equipment is led out, a certain delay time is added to serve as a frame synchronization signal of CMOS exposure, and the CMOS immediately starts data acquisition of a new frame when receiving the frame synchronization signal. By adjusting the exposure time of the CMOS and staggering the exposure time of the CMOS from the flicker time of the laser pulse, the possibility that the flicker of the laser pulse is collected and exposed by the CMOS is avoided from a signal source, so that a local overexposure image caused by the laser pulse is not generated in an image, and the clearness and completeness of the imaging content are ensured.

Description

Technical Field

[0001] The present invention relates to the technical field of endoscope image processing, and in particular to a method and system for an endoscope system to solve the problem of light flickering affecting image effects during laser treatment. Background Art

[0002] During holmium laser lithotripsy with endoscopes such as ureteroscopes, the holmium laser device will emit pulsed lasers, which will generate plasma when irradiating stones for lithotripsy. Its de-excitation process will emit strong visible light flashes, which usually last for hundreds of microseconds. The exposure time of commonly used imaging sensors (CMOS) is several milliseconds, which is much shorter than the exposure time of a frame of image. CMOS often uses a rolling shutter design, which results in only some lines in a frame of image receiving exposure to laser flashes when flashes occur, so that the output image presents a partially overexposed image with obvious dividing lines, which seriously affects the image effect of the video.

[0003] Because the wavelength of light emitted by holmium laser is widely distributed in the visible light band, it cannot be filtered out by optical solutions such as filtering, and its light flicker is an unavoidable phenomenon in laser surgery. The current mainstream solution is to use image algorithms to identify overexposed areas and then suppress them through image processing or use previous data frames for compensation. However, due to the uncertainty of the position and intensity of the overexposed areas, and the fact that the data of the overexposed areas is overexposed, the effective information of the image has been lost. The image processing algorithm alone can only alleviate the visual problem caused by image flicker, but it cannot make up for the lost image information. Summary of the invention

[0004] In view of the shortcomings of the prior art, the present invention provides a method and system for suppressing laser flicker for endoscopic diagnosis. The present invention adjusts the exposure timing of CMOS to avoid the possibility of laser pulse flicker being captured and exposed by CMOS from the signal source, fundamentally solving the problem of local over-exposed images caused by laser flicker, and eliminates image flicker without losing any image information.

[0005] In order to achieve the above technical objectives, the present invention adopts the following technical solutions:

[0006] A method for suppressing laser flicker for endoscopic diagnosis comprises the following steps:

[0007] S1: pre-processing the exposure time of CMOS according to the laser pulse configuration of the laser device;

[0008] S2: Lead out the pulse synchronization signal Pluse_SYNC of the laser device;

[0009] S3: Add a delay time to the pulse synchronization signal Pluse_SYNC to convert it into a delayed pulse synchronization signal Delay_Pluse_SYNC;

[0010] S4: convert the delayed pulse synchronization signal Delay_Pluse_SYNC into a frame synchronization signal Frame_SYNC for CMOS exposure, and send it to the CMOS;

[0011] S5: CMOS starts a new frame and begins exposure immediately after receiving the frame synchronization signal.

[0012] Preferably, in step S3, the delay time is required to be no less than the flash duration of the laser pulse emitted by the laser device, and the calculation formula of the delay time T2 is: T2=T0+τ, wherein T0 is the flash duration of the laser pulse emitted by the laser device, and τ is the system delay of the transmission link.

[0013] Preferably, in step S1, the exposure time of the CMOS is preprocessed, specifically:

[0014] S11: If the exposure time of the CMOS is less than the time interval between two laser pulses emitted by the laser device, there is no need to adjust the exposure time of the CMOS;

[0015] S12: If the exposure time of the CMOS is greater than the time interval between two laser pulses emitted by the laser device, the exposure time of the CMOS needs to be adjusted, and the calculation formula for limiting the upper limit value T1 of the exposure time of the CMOS is: T1=1 / F1, where the pulse frequency of the laser device is F1.

[0016] Preferably, for step S12, after adjusting the exposure time of the CMOS, compensation is performed by increasing the CMOS gain, and the calculation formula for the ratio G / G0 of the new gain G and the original gain G0 is: G / G0=k*T4 / T3, wherein T3 is the exposure time of the CMOS after adjustment, T4 is the original exposure time of the CMOS, and k is an adjustment coefficient, which can be adjusted according to the actual image effect.

[0017] Preferably, step S4 specifically includes: performing logic level conversion on the delayed pulse synchronization signal Delay_Pluse_SYNC to convert it into a signal that meets the CMOS reception requirement, and then sending it to the CMOS as the frame synchronization signal Frame_SYNC for CMOS exposure.

[0018] The present invention also provides a laser flicker suppression system for endoscopic diagnosis, using the laser flicker suppression method for endoscopic diagnosis as described above, the system includes a laser device, an endoscope, an endoscope image processor, a medical monitor and a medical cold light source;

[0019] Laser equipment is used to emit laser pulses for surgical treatment;

[0020] The endoscope is used to enter the human body to collect real-time images. At the same time, the laser pulses emitted by the laser device are introduced into the lesions inside the human body through the instrument channel of the endoscope via optical fiber.

[0021] The endoscope image processor is used to collect the endoscope image from the endoscope, and send it to the medical monitor after image processing;

[0022] The medical monitor is used to display the images transmitted by the endoscope image processor in real time;

[0023] Medical cold light sources are used to provide lighting for endoscopes.

[0024] Preferably, the endoscope comprises a CMOS, an independent delay device, and a processor;

[0025] The pulse synchronization signal Pluse_SYNC of the laser device is connected to the input end of the delay device, and is processed by the delay device to become a delayed pulse synchronization signal Delay_Pluse_SYNC, and then converted into a frame synchronization signal Frame_SYNC connected to the frame synchronization signal or field synchronization signal of the CMOS as the start signal of the frame exposure of the CMOS;

[0026] The processor is connected to the CMOS to realize the configuration and operation of the CMOS, and the processor is connected to the delay device to configure the delay time of the delay device.

[0027] Preferably, the processor may use one of FPGA, single-chip microcomputer and ARM.

[0028] Preferably, the endoscope comprises a CMOS, a processor having a delay function;

[0029] The pulse synchronization signal Pluse_SYNC of the laser device is connected to the processor, and is first delayed by the processor to become the pulse synchronization signal Delay_Pluse_SYNC, and then becomes the frame synchronization signal Frame_SYNC, which is connected to the frame synchronization signal or field synchronization signal of the CMOS as the start signal of the frame exposure of the CMOS;

[0030] The processor is connected to the CMOS to realize the configuration and operation of the CMOS.

[0031] Preferably, the processor can use one of FPGA, single-chip microcomputer, ARM, and delay chip with delay function.

[0032] Compared with the prior art, the beneficial effects of the present invention are:

[0033] 1) The present invention leads out the pulse synchronization signal Pluse_SYNC of the laser device, and adds a certain delay time as the frame synchronization signal of CMOS exposure. After receiving the frame synchronization signal, CMOS immediately starts a new frame and starts exposure, so that the exposure time of CMOS and the time of laser pulse flickering can be controlled to be staggered. Compared with the traditional method of optimizing the overexposed area through image algorithm, the present invention avoids the possibility of flickering pulses being detected by CMOS from the signal source, and there will be no flickering image caused by laser pulses in the generated image, which fundamentally solves the problem of local overexposure of the image caused by laser flickering, and eliminates the image flickering without losing any image information, and the imaging content is clear and complete.

[0034] 2) In addition, for some extreme cases, the present invention also provides a method for compensating for the change in image brightness caused by the lack of exposure time by increasing the CMOS gain, making the method more stable and reliable in practical applications.

[0035] 3) The present invention is not limited to laser equipment. This solution can be used to solve the interference of pulse flickering light that can provide synchronization signals. For example, liquid electrolithotomy equipment in medical treatment uses high voltage generated by high-voltage radio frequency pulses to break up stones. Its high-voltage radio frequency will produce electric sparks during the discharge process, which can also be solved by this solution. The present invention has a wide range of practical applications. BRIEF DESCRIPTION OF THE DRAWINGS

[0036] Figure 1 A method flow chart of a laser flicker suppression method for endoscopic diagnosis according to an embodiment of the present invention;

[0037] Figure 2 A flowchart of a laser flicker suppression method for endoscopic diagnosis according to an embodiment of the present invention;

[0038] Figure 3 A signal timing diagram of a laser flicker suppression method for endoscopic diagnosis according to an embodiment of the present invention;

[0039] Figure 4 A schematic block diagram of the structure of a laser flicker suppression system for endoscopic diagnosis according to an embodiment of the present invention;

[0040] Figure 5 This is a pulse synchronization signal link diagram of a laser flicker suppression system for endoscopic diagnosis according to Embodiment 3 of the present invention;

[0041] Figure 6 This is a pulse synchronization signal link diagram of a laser flicker suppression system for endoscopic diagnosis according to Embodiment 4 of the present invention;

[0042] Figure 7This is the original imaging effect picture without any processing;

[0043] Figure 8 This is an imaging effect diagram after applying a laser flicker suppression method or system for endoscopic diagnosis according to an embodiment of the present invention. DETAILED DESCRIPTION

[0044] The following will be combined with the attached embodiment of the present invention Figure 1 ~Attached Figure 8 , the technical solutions in the embodiments of the present invention are clearly and completely described. Obviously, the described embodiments are only part of the embodiments of the present invention, not all of them. Based on the embodiments of the present invention, all other embodiments obtained by ordinary technicians in this field without creative work are within the scope of protection of the present invention.

[0045] In the description of the present invention, it should be understood that the terms "coaxial", "bottom", "one end", "top", "middle", "the other end", "upper", "one side", "top", "inside", "front", "center", "both ends" and the like indicate positions or positional relationships based on the attached Figures 1 to 7 The orientation or positional relationship shown is only for the convenience of describing the present invention and simplifying the description, and does not indicate or imply that the device or element referred to must have a specific orientation, be constructed and operate in a specific orientation, and therefore should not be understood as a limitation on the present invention.

[0046] In the present invention, unless otherwise clearly stipulated and limited, the terms such as "installation", "setting", "connection", "fixation" and "screw-on" should be understood in a broad sense. For example, it can be a fixed connection, a detachable connection, or an integral one; it can be a mechanical connection or an electrical connection; it can be a direct connection or an indirect connection through an intermediate medium; it can be the internal connection of two elements or the interaction relationship between two elements. Unless otherwise clearly defined, ordinary technicians in this field can understand the specific meanings of the above terms in the present invention according to the specific circumstances.

[0047] Example 1

[0048] Combination Figure 1 As shown, an embodiment of the present invention provides a method for suppressing laser flicker for endoscopic diagnosis, comprising the following steps:

[0049] S1: pre-processing the exposure time of CMOS according to the laser pulse configuration of the laser device;

[0050] S2: Lead out the pulse synchronization signal Pluse_SYNC of the laser device;

[0051] S3: Add a delay time to the pulse synchronization signal Pluse_SYNC to convert it into a delayed pulse synchronization signal Delay_Pluse_SYNC;

[0052] S4: convert the delayed pulse synchronization signal Delay_Pluse_SYNC into a frame synchronization signal Frame_SYNC for CMOS exposure, and send it to the CMOS;

[0053] S5: CMOS starts a new frame and begins exposure immediately after receiving the frame synchronization signal.

[0054] The present invention can control the staggered exposure time of CMOS and the time of laser pulse flickering. Compared with the traditional method of optimizing the overexposed area through image algorithm, the present invention avoids the possibility of flicker pulses being detected by CMOS from the signal source, and there will be no flickering image caused by laser pulses in the generated image, which fundamentally solves the problem of local overexposure of the image caused by laser flickering, and eliminates image flickering without losing any image information, and the imaging content is clear and complete.

[0055] Before and after using the method of the present invention Figure 7 , Figure 8 As shown, after using the method of the present invention, the generated image will not have a partially overexposed image, and the image display content is clear and complete without losing any image information.

[0056] Example 2

[0057] Combination Figure 1 to Figure 3 As shown, an embodiment of the present invention provides a method for suppressing laser flicker for endoscopic diagnosis, comprising the following steps:

[0058] S1: pre-processing the exposure time of CMOS according to the laser pulse configuration of the laser device;

[0059] S2: Lead out the pulse synchronization signal Pluse_SYNC of the laser device;

[0060] S3: Add a delay time to the pulse synchronization signal Pluse_SYNC to convert it into a delayed pulse synchronization signal Delay_Pluse_SYNC;

[0061] S4: convert the delayed pulse synchronization signal Delay_Pluse_SYNC into a frame synchronization signal Frame_SYNC for CMOS exposure, and send it to the CMOS;

[0062] S5: CMOS starts a new frame and begins exposure immediately after receiving the frame synchronization signal.

[0063] Among them, CMOS is an image sensor, which is mainly used to receive light reflected from the human body, convert light signals into electrical signals through the photoelectric effect, and the electrical signals generated by each pixel unit constitute the original image information, which is transmitted to the endoscope image processor to generate a digital image. It contains many pixel units, each of which is equipped with a photodiode and a corresponding transistor circuit. The pulse synchronization signal of the laser device is an electrical signal used to control the timing of the laser pulse output.

[0064] Among them, the transmission and connection of signals between different devices described in this method are all commonly used signal transmission methods in the field and will not be repeated here.

[0065] Laser equipment can set the energy and frequency of the laser. First, according to the characteristics and related configurations of the laser equipment, input the pulse frequency F1 of the laser equipment and the flash duration T0 of the laser pulse emitted by the laser equipment. The duration of visible light excited by laser pulses is generally fixed, and there are not many types of medical lasers. You can first obtain a list of durations corresponding to different laser types and energies through experiments, and set the laser pulse flash duration T0 according to the measurement results.

[0066] In this embodiment, in step S3, the delay time is required to be no less than the flashing duration of the laser pulse emitted by the laser device, and the calculation formula of the delay time T2 is: T2=T0+τ, wherein T0 is the flashing duration of the laser pulse emitted by the laser device, and τ is the system delay of the transmission link.

[0067] According to the conventional configuration of laser pulses of laser equipment, the laser pulse frequency of laser equipment is generally 1 to 60 Hz, which generally does not exceed the frame rate of 60 FPS of CMOS used in conventional endoscopes. In general, the exposure time of CMOS is less than the time interval between two laser pulses emitted by the laser equipment, and each frame of the image will not be affected by the laser pulse light flicker more than once. Therefore, in this case, there is no need to adjust the exposure time of CMOS.

[0068] In the specific implementation process of this embodiment, because different devices may use different level standards, conversion may be required to achieve device compatibility to prevent damage to the device due to level mismatch. Therefore, in step S4, the delayed pulse synchronization signal Delay_Pluse_SYNC needs to be converted into a signal that meets the CMOS reception requirements. Specifically, the conversion can be performed through a level conversion chip or an inverter. The converted signal is used as the frame synchronization signal Frame_SYNC of CMOS exposure and sent to the CMOS.

[0069] In the process of executing the embodiment of the present invention, the signal changes as follows: Figure 3As shown, the starting point of the laser pulse flashing is a, and its duration is ab. The pulse synchronization signal Pluse_SYNC is synchronized with the laser pulse. The delayed pulse synchronization signal Delay_Pluse_SYNC after the pulse synchronization signal Pluse_SYNC is delayed starts at the end point b of the laser pulse. After conversion, Delay_Pluse_SYNC is sent to CMOS as a frame synchronization signal Frame_SYNC. After receiving the frame synchronization signal Frame_SYNC, CMOS immediately starts a new frame and starts exposure. Its exposure time is completely staggered in time with the laser pulse.

[0070] Because the duration of the pulsed flickering light excited by the laser device is relatively stable, generally in the hundreds of microseconds. The present invention leads out the pulse synchronization signal Pluse_SYNC of the laser device, and by adding a certain delay time as the frame synchronization signal of the CMOS exposure, the CMOS immediately starts a new frame and starts exposure after receiving the frame synchronization signal, so that the exposure time of the CMOS and the time of the laser pulse flickering can be controlled to be staggered. Compared with the traditional method of optimizing the overexposed area through image algorithms, the present invention avoids the possibility of the flickering pulse being detected by the CMOS from the signal source, and the generated image will not produce an overexposed area, which fundamentally solves the problem of local overexposure of the image caused by laser flickering, and eliminates image flickering without losing any image information.

[0071] Before and after using the method of the present invention Figure 7 , Figure 8 As shown, after using the method of the present invention, the generated image will not have a partially overexposed image, and the image display content is clear and complete without losing any image information.

[0072] Example 3

[0073] Different from Example 1, this example illustrates that in some extreme cases, the exposure time of the CMOS may be greater than the time interval between two laser pulses emitted by the laser device, resulting in multiple laser pulse flashing exposures in one frame of image.

[0074] At this time, when the exposure time of the CMOS is greater than the time interval between two laser pulses emitted by the laser device, it is necessary to increase the exposure time of the CMOS for preprocessing, that is, adjust the exposure time of the CMOS, and set the exposure time of the CMOS not to exceed its upper limit value T1. The calculation formula for the upper limit value T1 of the exposure time of the CMOS is: T1=1 / F1, where the pulse frequency of the laser device is F1.

[0075] In this embodiment, because the exposure time of the CMOS may be reduced due to adjustment, after the exposure time of the CMOS is adjusted, the CMOS gain needs to be increased for compensation, and the calculation formula of the ratio G / G0 of the new gain G and the original gain G0 is: G / G0=k*T4 / T3, wherein T3 is the exposure time of the CMOS after adjustment, T4 is the original exposure time of the CMOS, and k is the adjustment coefficient, which can be adjusted according to the actual image effect.

[0076] The overall workflow of the method in this embodiment is shown in the attached Figure 2 According to the pulse frequency F1 of the input laser device and the flashing duration T0 of the laser pulse emitted by the laser device, when the exposure time of the CMOS is greater than the time interval between two laser pulses emitted by the laser device, it is necessary to pre-set the exposure time of the CMOS so that it cannot exceed its upper limit T1 and increase the gain control G of the CMOS; then the pulse synchronization signal Pluse_SYNC of the laser device is connected, and after being delayed by a delay device for T2 time, it is finally converted into a frame synchronization signal Frame_SYNC, which is connected to the frame synchronization signal or field synchronization signal of the CMOS as the start signal of the frame exposure of the CMOS.

[0077] The method of the present invention can compensate for the change in image brightness caused by the lack of exposure time by increasing the CMOS gain. In addition to the above-mentioned method of compensating for the reduction in exposure time by the CMOS gain control method, in this embodiment, the compensation image can also be achieved by other methods, such as using an image algorithm in an image processor to increase the brightness of the image, such as a brightness enhancement algorithm, an image digital gain, an image contrast, and an image gamma algorithm.

[0078] Example 4

[0079] Combination Figure 4 and Figure 5 As shown, an embodiment of the present invention further provides a laser flicker suppression system for endoscopic diagnosis, which uses a laser flicker suppression method for endoscopic diagnosis as described above, including a laser device, an endoscope, an endoscope image processor, a medical monitor, and a medical cold light source;

[0080] Laser equipment is used to emit laser pulses for surgical treatment;

[0081] The endoscope is used to enter the human body to collect real-time images. At the same time, the laser pulses emitted by the laser device are introduced into the lesions inside the human body through the instrument channel of the endoscope via optical fiber.

[0082] The endoscope image processor is used to collect the endoscope image from the endoscope, and send it to the medical monitor after image processing;

[0083] The medical monitor is used to display the images transmitted by the endoscope image processor in real time;

[0084] Medical cold light sources are used to provide lighting for endoscopes.

[0085] In this embodiment, the endoscope includes a CMOS, an independent delay device, and a processor; the pulse synchronization signal Pluse_SYNC of the laser device is connected to the input end of the delay device, processed by the delay device to become a delayed pulse synchronization signal Delay_Pluse_SYNC, and then converted into a frame synchronization signal Frame_SYNC, which is connected to the frame synchronization signal or field synchronization signal of the CMOS as the start signal of the frame exposure of the CMOS.

[0086] The processor is connected to the CMOS to realize the relevant configuration and operation of the CMOS, and the processor is connected to the delay device to configure the delay time of the delay device.

[0087] In this embodiment, the delay time processing of the pulse synchronization signal Pluse_SYNC is performed by a separate delay device, wherein the processor can use one of FPGA, single-chip microcomputer and ARM.

[0088] Before and after using the system of the present invention Figure 7 , Figure 8 As shown, after using the system of the present invention, the generated image will not have a partially overexposed image, and the image display content is clear and complete without losing any image information.

[0089] Example 5

[0090] Combination Figure 4 and Figure 6 As shown, different from Example 3, in this embodiment, the endoscope includes a CMOS and a processor with a delay function; the pulse synchronization signal Pluse_SYNC of the laser device is connected to the processor, first delayed by the processor, and becomes a pulse synchronization signal Delay_Pluse_SYNC, and then becomes a frame synchronization signal Frame_SYNC, which is connected to the frame synchronization signal or field synchronization signal of the CMOS as the start signal of the frame exposure of the CMOS. The processor is connected to the CMOS to realize the configuration and operation of the CMOS.

[0091] In this embodiment, the delay time processing of the pulse synchronization signal Pluse_SYNC can be performed by a processor with a delay function, and can be specifically implemented by an FPGA, a single-chip microcomputer, an ARM, a delay chip, etc. with a delay function.

[0092] Before and after using the system of the present invention Figure 7 , Figure 8As shown, after using the system of the present invention, the generated image will not have a partially overexposed image, and the image display content is clear and complete without losing any image information.

[0093] The present invention is not limited to laser equipment. This solution can be used to solve any situation where pulse flickering light interference can provide a synchronization signal. For example, liquid electrolithotomy equipment used in medical treatment uses high voltage generated by high-voltage radio frequency pulses to break up stones. Its high-voltage radio frequency will produce electric sparks during the discharge process, which can also be solved by this solution.

[0094] The above description is only an embodiment of the present invention and is not intended to limit the present invention. Any modification, equivalent replacement and improvement made within the application scope of the present invention shall be included in the protection scope of the present invention.

Claims

1. A method for suppressing laser flicker for endoscopic diagnosis, characterized in that: The following steps are involved: S1: pre-processing the exposure time of CMOS according to the laser pulse configuration of the laser device; S2: Lead out the pulse synchronization signal Pluse_SYNC of the laser device; S3: Add a delay time to the pulse synchronization signal Pluse_SYNC to convert it into a delayed pulse synchronization signal Delay_Pluse_SYNC; S4: convert the delayed pulse synchronization signal Delay_Pluse_SYNC into a frame synchronization signal Frame_SYNC for CMOS exposure, and send it to the CMOS; S5: CMOS starts a new frame and begins exposure immediately after receiving the frame synchronization signal.

2. A method for suppressing laser flicker for endoscopic diagnosis according to claim 1, characterized in that: In step S3, the delay time is required to be no less than the flash duration of the laser pulse emitted by the laser device. The calculation formula of the delay time T2 is: T2=T0+τ, where T0 is the flash duration of the laser pulse emitted by the laser device, and τ is the system delay of the transmission link.

3. The laser flicker suppression method for endoscopic diagnosis according to claim 1, characterized in that: In step S1, the exposure time of the CMOS is preprocessed, specifically: S11: If the exposure time of the CMOS is less than the time interval between two laser pulses emitted by the laser device, there is no need to adjust the exposure time of the CMOS; S12: If the exposure time of the CMOS is greater than the time interval between two laser pulses emitted by the laser device, the exposure time of the CMOS needs to be adjusted, and the calculation formula for limiting the upper limit value T1 of the exposure time of the CMOS is: T1=1 / F1, where the pulse frequency of the laser device is F1.

4. The laser flicker suppression method for endoscopic diagnosis according to claim 3, characterized in that: For step S12, after adjusting the exposure time of the CMOS, compensation is performed by increasing the CMOS gain, and the calculation formula for the ratio G / G0 of the new gain G and the original gain G0 is: G / G0=k*T4 / T3, wherein T3 is the exposure time of the CMOS after adjustment, T4 is the original exposure time of the CMOS, and k is the adjustment coefficient, which is adjusted according to the actual image effect.

5. The laser flicker suppression method for endoscopic diagnosis according to claim 1, characterized in that: Step S4 specifically includes: performing logic level conversion on the delayed pulse synchronization signal Delay_Pluse_SYNC to convert it into a signal that meets the CMOS reception requirement, and then sending it to the CMOS as the frame synchronization signal Frame_SYNC for CMOS exposure.

6. A laser flicker suppression system for endoscopic diagnosis, characterized in that: A laser flicker suppression method for endoscopic diagnosis using any one of claims 1 to 5, comprising a laser device, an endoscope, an endoscope image processor, a medical monitor, and a medical cold light source; Laser equipment is used to emit laser pulses for surgical treatment; The endoscope is used to enter the human body to collect real-time images. At the same time, the laser pulses emitted by the laser device are introduced into the lesions inside the human body through the instrument channel of the endoscope via optical fiber. The endoscope image processor is used to receive the endoscope image collected by the endoscope, and send it to the medical monitor after image processing; The medical monitor is used to display the images transmitted by the endoscope image processor in real time; Medical cold light sources are used to provide lighting for endoscopes.

7. A laser flicker suppression system for endoscopic diagnosis according to claim 6, characterized in that: The endoscope includes CMOS, independent delay device, and processor; The pulse synchronization signal Pluse_SYNC of the laser device is connected to the input end of the delay device, and is processed by the delay device to become a delayed pulse synchronization signal Delay_Pluse_SYNC, and then converted into a frame synchronization signal Frame_SYNC connected to the frame synchronization signal or field synchronization signal of the CMOS as the start signal of the frame exposure of the CMOS; The processor is connected to the CMOS to realize the configuration and operation of the CMOS, and the processor is connected to the delay device to configure the delay time of the delay device.

8. The laser flicker suppression system for endoscopic diagnosis according to claim 7, characterized in that: The processor uses one of FPGA, single-chip microcomputer and ARM.

9. The laser flicker suppression system for endoscopic diagnosis according to claim 6, characterized in that: The endoscope includes a CMOS,processor with a delay function; The pulse synchronization signal Pluse_SYNC of the laser device is connected to the processor, and is first delayed by the processor to become the pulse synchronization signal Delay_Pluse_SYNC, and then becomes the frame synchronization signal Frame_SYNC, which is connected to the frame synchronization signal or field synchronization signal of the CMOS as the start signal of the frame exposure of the CMOS; The processor is connected to the CMOS to realize the configuration and operation of the CMOS.

10. The laser flicker suppression system for endoscopic diagnosis according to claim 9, characterized in that: The processor uses one of FPGA, single-chip microcomputer, ARM and delay chip with delay function.

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