Endoscope imaging system and control method thereof

Abstract

The invention relates to the technical field of endoscope imaging, in particular to an endoscope imaging system and a control method thereof. According to the scheme, firstly, a light source module sends out first visible light and / or second visible light according to a control instruction, and the target tissue generates reflected light after being irradiated by the first visible light and the second visible light by controlling the brightness proportion of the first visible light and the second visible light irradiated to the target tissue; receiving the reflected light through an image sensor of the camera module, and generating a three-color response signal according to the reflected light; and finally, processing the three-color response signal through an image processing module to obtain a corresponding image, and outputting the image. By the adoption of the scheme, the problem that the target tissue image identification degree in current endoscope imaging is low is effectively solved.

Description

Technical Field

[0001] The present invention relates to the technical field of endoscope imaging, and in particular to an endoscope imaging system and a control method thereof. Background Art

[0002] Endoscopes can enter the patient's body without or with minimal invasion, and can accurately diagnose or treat by viewing endoscopic images. Therefore, endoscopes are increasingly used in the medical field. The main function of an endoscope light source is to provide illumination for endoscopic imaging, so the endoscope light source is crucial to the endoscope. After entering the human body, the endoscope directly or indirectly illuminates the human tissue through the light source or its supporting optical system, and receives the reflected light from the human tissue through the endoscope camera assembly for imaging.

[0003] There are many kinds of endoscope light sources at present, such as xenon lamps or white light LED light sources that directly provide white light illumination. Endoscopes using such light sources only perform white light imaging of the human body and have a single function, resulting in low recognition of target tissues in the imaging image. Summary of the invention

[0004] An endoscopic imaging system and a control method thereof provided by the present invention effectively solve the problem that the existing endoscopic imaging system has a low recognition degree of target tissue in the imaging image due to the single lighting function.

[0005] According to the first aspect, an embodiment provides an endoscope imaging system, including a light source module, a camera module and an image processing module;

[0006] The light source module comprises a first light source and a second light source, wherein the first light source is used to emit a first visible light, and the second light source is used to emit a second visible light having a discontinuous spectral characteristic;

[0007] The camera module includes an image sensor having three color response channels of red, green and blue, and the image sensor is used to receive reflected light formed after the target tissue is irradiated by the visible light emitted by the light source module, so as to obtain a three-color response signal corresponding to the reflected light;

[0008] The image processing module is used to control the brightness ratio of the first visible light and the second visible light, and is also used to process the three-color response signal to obtain a corresponding image and output it.

[0009] In a feasible implementation, the light source module is located at the leading end of the endoscope body.

[0010] In an achievable embodiment, the spectrum of the second visible light includes a first characteristic peak and a second characteristic peak;

[0011] The wavelength range of the first characteristic peak is 400nm-440nm, and the wavelength range of the second characteristic peak is 520nm-570nm; and the half-peak width of the first characteristic peak is less than 40nm, and the half-peak width of the second characteristic peak is less than 80nm.

[0012] In an achievable implementation, the spectrum of the second visible light further includes a third characteristic peak;

[0013] The wavelength range of the third characteristic peak is 600nm-700nm; and the half-peak width of the third characteristic peak is less than 120nm.

[0014] In one feasible implementation, the waveforms of the first visible light and the second visible light are complementary within a wavelength range of 380 nm-780 nm.

[0015] In an achievable implementation, the first light source is a white light LED light source having a continuous spectrum characteristic, and the wavelength range of the first visible light is 380nm-780nm; or,

[0016] The first light source is an LED light source with discontinuous spectrum characteristics. The first visible light emitted by the LED light source with discontinuous spectrum characteristics is a special spectrum light wave composed of a mixture of blue light waves, cyan light waves and orange light waves.

[0017] In an achievable implementation, the first light source is an LED light source having a discontinuous spectrum characteristic, and the spectrum of the special spectrum light wave includes a fourth characteristic peak, a fifth characteristic peak, and a sixth characteristic peak;

[0018] The wavelength range of the fourth characteristic peak is 400nm-480nm, the wavelength range of the fifth characteristic peak is 450nm-510nm, and the wavelength range of the sixth characteristic peak is 580nm-630nm; and,

[0019] The half-width of the fourth characteristic peak is less than 30 nm, and the half-widths of the fifth characteristic peak and the sixth characteristic peak are both greater than 40 nm.

[0020] In an achievable implementation, the image processing module processes the three-color response signal to obtain a corresponding image, including: matching a corresponding image processing mechanism according to a brightness ratio of the first visible light and the second visible light to perform image processing on the three-color response signal to obtain a corresponding image.

[0021] In an achievable implementation manner, after performing image processing on the three-color response signal to obtain a corresponding image, the method further includes:

[0022] The images corresponding to the three-color response signals are processed respectively according to a preset conversion function to obtain and output corresponding monochrome display signals.

[0023] In an achievable embodiment, the device further includes a display module, wherein the display module includes three-color display channels; the three-color display channels are used to form corresponding monochrome images according to corresponding monochrome display signals;

[0024] The display module is used to display one of the three monochrome images; or to display a combination of multiple of the three monochrome images.

[0025] In an achievable implementation, the second light source is an LED light source composed of a purple semiconductor light emitting chip and a green phosphor;

[0026] The emission peak wavelength of the purple semiconductor light-emitting chip is within the wavelength range of 400nm-440nm, and the half-peak width is less than 30nm; the emission peak wavelength of the green phosphor is within the wavelength range of 520nm-550nm, and the half-peak width is less than 70nm.

[0027] In an achievable implementation, the second light source is a white light LED light source composed of the purple semiconductor light emitting chip, green phosphor and red phosphor;

[0028] The emission peak wavelength of the purple semiconductor light-emitting chip is within the wavelength range of 400nm-440nm, and the half-peak width is less than 30nm; the emission peak wavelength of the green phosphor is within the wavelength range of 520nm-550nm, and the half-peak width is less than 70nm; the emission peak wavelength of the red phosphor is within the wavelength range of 600nm-680nm, and the half-peak width is less than 110nm.

[0029] In an achievable implementation, the brightness ratio of the first visible light and the second visible light includes, but is not limited to, 0:1, 1:0, 1:1 or 0.5:1.

[0030] According to a second aspect, an embodiment provides a method for controlling an endoscopic imaging system, using the above-mentioned endoscopic imaging system, the method comprising:

[0031] Controlling the brightness ratio of the first light source and the second light source;

[0032] Acquire the three-color response signals collected by the camera module;

[0033] The three-color response signal is processed according to the brightness ratio of the first visible light and the second visible light to obtain and output a corresponding image.

[0034] According to an endoscopic imaging system / control method of the above embodiment, first, the light source module emits the first visible light and / or the second visible light according to the control instruction, and by controlling the brightness ratio of the first visible light and the second visible light irradiated to the target tissue, the target tissue generates reflected light after being irradiated by the first visible light and the second visible light; then, the image sensor of the camera module receives the reflected light, and generates a three-color response signal according to the reflected light; finally, the three-color response signal is processed by the image processing module to obtain the corresponding image and output it. By adopting the above scheme of the present application, the problem of low recognition of the target tissue image in the current endoscopic imaging is effectively solved. BRIEF DESCRIPTION OF THE DRAWINGS

[0035] Figure 1 A schematic diagram of the structure of the endoscope imaging system provided in this embodiment;

[0036] Figure 2 An imaging principle diagram of the endoscopic imaging system provided in this embodiment;

[0037] Figure 3 is a graph showing the relationship between the second visible light spectrum, the hemoglobin spectrum absorption coefficient and the image sensor RGB response spectrum of the present embodiment;

[0038] Figure 4 is a curve diagram showing the relationship between the first visible light spectrum and the RGB response spectrum of the image sensor of this embodiment;

[0039] Figure 5 A graph showing the relationship between the first visible light and the second visible light spectrum of the non-continuous spectral characteristic of the present embodiment and the RGB response spectrum of the image sensor;

[0040] Figure 6 A graph showing the relationship between the 1:1 combined illumination light, the first visible light and the second visible light spectrum with non-continuous spectral characteristics, and the RGB response spectrum of the image sensor in this embodiment;

[0041] Figure 7 is a graph showing the relationship between the first visible light + second visible light spectrum, the hemoglobin spectrum absorption coefficient and the image sensor RGB response spectrum of the present embodiment;

[0042] Figure 8 A graph showing the relationship between the 0.5:1 combined illumination light, the first visible light and the second visible light spectrum with non-continuous spectral characteristics, and the RGB response spectrum of the image sensor in this embodiment;

[0043] Fig. 9 This is a flow chart of a control method for an endoscopic imaging system provided in this embodiment.

[0044] Reference numerals: 10, light source module; 11, first light source; 12, second light source; 20, camera module; 21, image sensor; 30, image processing module; 40, display module. DETAILED DESCRIPTION

[0045] The present invention is further described in detail below by specific embodiments in conjunction with the accompanying drawings. Wherein similar elements in different embodiments adopt associated similar element numbers. In the following embodiments, many detailed descriptions are for making the present application better understood. However, those skilled in the art can easily recognize that some features can be omitted in different situations, or can be replaced by other elements, materials, methods. In some cases, some operations related to the present application are not shown or described in the specification, this is to avoid the core part of the present application being overwhelmed by too much description, and for those skilled in the art, it is not necessary to describe these related operations in detail, and they can fully understand the related operations according to the description in the specification and the general technical knowledge in the art.

[0046] In addition, the features, operations or characteristics described in the specification can be combined in any appropriate manner to form various implementations. At the same time, the steps or actions in the method description can also be interchanged or adjusted in a manner that is obvious to those skilled in the art. Therefore, the various sequences in the specification and the drawings are only for the purpose of clearly describing a certain embodiment and are not meant to be a required sequence, unless otherwise specified that a certain sequence must be followed.

[0047] The serial numbers of the components in this document, such as "first", "second", etc., are only used to distinguish the objects described and do not have any order or technical meaning. The "connection" and "coupling" mentioned in this application, unless otherwise specified, include direct and indirect connections (couplings).

[0048] As we all know, in order to perceive colors, conventional color imaging sensors use a filter system based on the principle of tristimulus values ​​in front of the sensor's photosensitive area to distinguish different colors to achieve color imaging. Therefore, conventional image sensors using an RGB filter system have a higher response in the 380nm-520nm band for the blue response channel; a higher response in the 460nm-610nm band for the green response channel; and a higher response in the 580nm-800nm ​​band for the red response channel. It can be seen that the blue response channel and the green response channel of conventional image sensors have more response overlap in the 470nm-520nm band, and the green response channel and the red response channel have more response overlap in the 580nm-610nm band.

[0049] Human tissues, especially vascular tissues and blood, contain a large amount of hemoglobin, which has a special absorption spectrum for light of different wavelengths. Hemoglobin Hb has strong absorption peaks near 440nm and 555nm, and oxygenated hemoglobin HbO2 has strong absorption peaks near 415nm, 540nm and 575nm, while its absorption coefficient is very small in the band greater than 600nm. That is to say, when light in the 380nm-450nm band is irradiated on hemoglobin, it will be strongly absorbed, and when light in the 520nm-600nm band is irradiated on hemoglobin, it will be partially absorbed, and when light in the band greater than 600nm is irradiated on hemoglobin, it will be strongly reflected due to low absorption. At the same time, human tissue is a scattering material for light. According to the laws of physics, light with a shorter wavelength is more strongly scattered in human tissue and has a shorter transmission distance in human tissue; while light with a longer wavelength is less scattered in human tissue and has a longer transmission distance in human tissue. Therefore, in the field of tissue imaging, the spectral absorption characteristics of hemoglobin and the scattering characteristics of human tissue can be used to perform special imaging of vascular tissue at different depths in the human body. However, when using conventional color imaging sensors to image vascular tissue, it is not easy to identify vascular tissue because the response bands of the blue response channel and the green response channel overlap with the absorption peak of hemoglobin / oxyhemoglobin.

[0050] Therefore, the present application proposes an endoscopic imaging system and a control method thereof. The endoscopic imaging system of the present application uses a color image sensor with red, green and blue color response channels for imaging. The light source part is composed of two white light LED light sources with different emission spectra. The brightness ratio of the two light sources is controlled by image processing to form different illumination lights for imaging to improve the recognition of vascular tissue in human tissue. The specific scheme is detailed in the following embodiments.

[0051] refer to Figure 1 and Figure 2In this embodiment, an endoscope imaging system is provided, comprising a light source module 10, a camera module 20 and an image processing module 30. In addition, a display module 40 is also included. The light source module 10 is located at the tip of the endoscope body. Specifically, the light source module 10 comprises a first light source 11 and a second light source 12. The first light source 11 is used to emit a first visible light, and the second light source 12 is used to emit a second visible light with a discontinuous spectral characteristic. The camera module 20 comprises an image sensor 21 having a red, green and blue three-color response channel. The image sensor 21 is used to receive the reflected light formed after the target tissue is irradiated by the visible light emitted by the light source module 10, so as to obtain a three-color response signal corresponding to the reflected light. The image processing module 30 is used to control the brightness ratio of the first visible light and the second visible light, and is also used to process the three-color response signal to obtain a corresponding image and output it to the display module 40. The display module 40 comprises a three-color display channel. The three-color display channel is used to form a corresponding monochrome image according to a corresponding monochrome display signal. The display module 40 is used to display one of the three monochrome images; or, to display a combination of multiple of the three monochrome images.

[0052] In operation, the endoscope imaging system of this embodiment controls the working states of the first light source 11 and the second light source 12 in the light source module 10 through the image processing module 30 to generate different illumination spectra. Specifically, the brightness ratio of the first visible light and the second visible light emitted by the light source module 10 is controlled to generate illumination spectra with different wavelength proportions. Then, different image processing mechanisms are used in combination with different imaging purposes to achieve different imaging effects.

[0053] In practical applications, the light source is integrated into the endoscope body or the front end of the body or the outside of the body. Specifically, the light source module 10 of the endoscope can be set at the handle position of the endoscope body or the outside of the body, and the light waves emitted by the light source module 10 are transmitted to the head end through the optical fiber. Alternatively, the light source module 10 is set at the front end of the endoscope body. In practical applications, it is preferred to miniaturize the light source module 10 and set it at the front end of the endoscope body, because at this time the illumination light emitted by the light source module 10 does not need to be transmitted through the optical fiber but can be directly irradiated to the target tissue position, so that the light energy loss is minimized; considering that the endoscope body is often bent in the human body during use, therefore, the present application makes the system simpler and more reliable by abandoning the optical fiber, and there will be no problem of illumination light intensity attenuation caused by the breakage of the optical fiber after long-term use; at the same time, there are no light transmission elements such as optical fibers and light energy coupling devices, and the manufacturing cost of the endoscope is lower.

[0054] Furthermore, the image processing module 30 processes the three-color response signal to obtain a corresponding image, including: matching a corresponding image processing mechanism according to a brightness ratio of the first visible light and the second visible light to perform image processing on the three-color response signal to obtain a corresponding image.

[0055] When the endoscope imaging system is working, the image processing module 30 can control the brightness ratio of the first light source 11 and the second light source 12 according to the doctor's control instruction to output illumination light with different wavelength ratios to irradiate the target tissue. The illumination light reflected by the target tissue is responded to by the blue response channel, green response channel, and red response channel of the color image sensor 21 of the camera module 20 respectively and generates a blue response signal B, a green response signal G, and a red response signal R; then, after the response signal of the image sensor 21 is transmitted to the image processing module 30, the image processing module 30 performs a specific gain, attenuation, inversion, and other preset mixing operations on the grayscale image generated by the blue response signal B, the grayscale image generated by the green signal G, and the grayscale image generated by the red response signal R to obtain a new blue channel output grayscale image fb (B, G, R), a new green channel output grayscale image fg (B, G, R), and a new red channel output grayscale image fr (B, G, R). The above-mentioned new grayscale images are respectively output to the display channels corresponding to the display unit, and finally a color composite image is displayed on the display. Specifically, since the three response channels of red, green and blue all output grayscale images, the blue channel responds to the information returned by the blue wavelength to form a grayscale image, the green channel responds to the green wavelength to form a grayscale image, and the red channel responds to the red wavelength to form a grayscale image. After specific calculations, three new grayscale images are obtained. Finally, the three new grayscale images are output to the three display channels of the display unit 40 respectively. After the blue display channel receives the grayscale image, the blue color rendering unit of the display module 40 displays the new blue grayscale image information. Similarly, the last three colors are superimposed in the human eye to form a color image.

[0056] Specifically, if it is necessary to enhance imaging and distinguish vascular tissue at different depths in human tissue, after receiving the instruction, the image processing module 30 controls the second light source 12 in the light source module 10 to light up at 100% brightness to generate a second visible light, and the brightness of the first light source 11 is set to 0% brightness, that is, the first light source 11 is turned off, and the second light source 12 is lit to generate a second visible light.

[0057] In some embodiments, the second visible light comprises a first characteristic peak and a second characteristic peak; the wavelength range of the first characteristic peak is 400nm-440nm, and the wavelength range of the second characteristic peak is 520nm-570nm; and the half-width of the first characteristic peak is less than 40nm, and the half-width of the second characteristic peak is less than 80nm.

[0058] Among them, the second light source 12 is an LED light source composed of a purple semiconductor light-emitting chip and a green phosphor; the emission peak wavelength of the purple semiconductor light-emitting chip is in the wavelength range of 400nm-440nm, and the half-peak width is less than 30nm; the emission peak wavelength of the green phosphor is in the wavelength range of 520nm-550nm, and the half-peak width is less than 70nm.

[0059] It can be seen that the second visible light emitted by the second light source 12 in this embodiment includes a purple light wave with a first characteristic peak and a green light wave with a second characteristic peak. Specifically, when the purple light wavelength with a first characteristic peak in the second visible light is irradiated on the target tissue, considering that the purple light wavelength is short and the scattering is strong in the target tissue, the penetration depth of purple light or blue light is small and it cannot reach the deep layer of the tissue. The purple light can only illuminate the surface of the tissue, and the image output by the blue channel of the image sensor 21 only reflects the structural information of the surface of the tissue. Therefore, the grayscale image of the blue channel is a surface tissue image. During imaging, part of it is reflected by the epidermis and mucosa in the target tissue, and part of it is strongly absorbed by the blood oxygen protein in the blood vessels in the human body. Therefore, the purple light reflected by the blood vessels is weaker than the reflected light of the mucosa. Therefore, the grayscale image of the epidermis and mucosa in the output of the blue channel of the endoscope image sensor 21 is high, while the grayscale of the blood vessels is weak. Therefore, the grayscale image output by the blue channel is only the grayscale image of the surface tissue, and the grayscale of the image of the blood vessels in the surface tissue will be lower than the grayscale of other surface tissues such as the mucosa. Therefore, the interference of other deep tissues, especially the interference of middle and deep blood vessels, can be excluded in the image of the blue channel of the endoscope, and the superficial blood vessels can be more clearly distinguished in the surface of the tissue.

[0060] In the target tissue with strong scattering, the penetration depth of light with a long wavelength is deeper. When the green light with the second characteristic peak in the second visible light is irradiated on the target tissue, due to the deep penetration depth of the green light, part of it is reflected by the epidermal mucosa and middle tissue in the target tissue, and part of it is absorbed by the blood oxygen protein in the blood vessels of the surface tissue and middle tissue in the human body. Therefore, in the grayscale image output by the green channel of the image sensor 21, the grayscale of the non-vascular tissue in the target tissue is high, while the grayscale of the surface blood vessels and the middle blood vessels is weak. The green light corresponding to the second characteristic peak has a deeper penetration depth than the purple light corresponding to the first characteristic peak with a shorter wavelength, so the green light can reach deeper in the tissue, and then the image output by the green channel of the image sensor 21 mainly contains the structural information of the surface and middle layers of the tissue.

[0061] Since the purple light wave corresponding to the first characteristic peak in the second visible light has a high response only in the blue response channel of the endoscope image sensor 21, and the green light wave corresponding to the second characteristic peak has a high response only in the green response channel of the endoscope image sensor 21. Therefore, the purple light wave and the green light wave will not affect the contrast of the grayscale image of other color response channels, or the purple light wave and the green light wave have little effect on the contrast of the grayscale image of other color response channels. The grayscale image B output by the blue response channel of the image sensor 21 mainly contains the surface structure information of the target tissue, especially the information of the surface blood vessels, in which the grayscale of the blood vessels is relatively low and the grayscale of the non-vascular tissue is relatively high; the grayscale image G output by the green response channel mainly contains the surface and middle structure information of the target tissue, especially the information of the surface and middle blood vessels, in which the grayscale of the blood vessels is relatively low and the grayscale of the non-vascular tissue is relatively high.

[0062] In some embodiments, the spectrum of the second visible light further includes a third characteristic peak, wherein the wavelength range of the third characteristic peak is 600nm-700nm; and the half-peak width of the third characteristic peak is less than 120nm.

[0063] Among them, the second light source 12 is an LED light source composed of a purple semiconductor light-emitting chip, green phosphor and red phosphor; the emission peak wavelength of the purple semiconductor light-emitting chip is in the wavelength range of 400nm-440nm, and the half-peak width is less than 30nm; the emission peak wavelength of the green phosphor is in the wavelength range of 520nm-550nm, and the half-peak width is less than 70nm; the emission peak wavelength of the red phosphor is in the wavelength range of 600nm-680nm, and the half-peak width is less than 110nm.

[0064] It can be known that the second visible light emitted by the second light source 12 in this embodiment includes a purple light wave with a first characteristic peak, a green light wave with a second characteristic peak, and a red light wave with a third characteristic peak.

[0065] Red light with a longer wavelength has a deeper penetration depth than purple light (or blue light) and green light with a shorter wavelength, so red light can reach deeper into the tissue. Specifically, when the red light wave corresponding to the third characteristic peak in the second visible light is irradiated on the target tissue, the red light is transmitted more strongly and more, and penetrates deeper into the tissue because the tissue has low scattering of red light. The hemoglobin in the blood vessels of the target tissue has low absorption of red light and strong reflection. Therefore, when the blood vessels in the tissue are irradiated with red light, they will reflect red light, and the reflected red light will be transmitted out of the tissue. In the red channel output image of the image sensor 21 during imaging, since the blood vessels in the tissue reflect red light, the image grayscale values ​​of the blood vessels in the surface, middle and deep tissues are higher, and the image grayscale values ​​of non-vascular tissues are low.

[0066] Since the purple light corresponding to the first characteristic peak in the second visible light has a high response only in the blue response channel of the endoscope image sensor 21, the green light corresponding to the second characteristic peak has a high response only in the green response channel of the endoscope image sensor 21, and the red light wave corresponding to the third characteristic peak has a high response only in the red response channel of the endoscope image sensor 21. Therefore, the purple light wave, the green light wave, and the red light wave will not affect the contrast of the grayscale image of other color response channels, or the purple light wave, the green light wave, and the red light wave have little effect on the contrast of the grayscale image of other color response channels. The grayscale image B output by the blue response channel of the image sensor 21 mainly contains the surface structure information of the target tissue, especially the information of the surface blood vessels, wherein the grayscale of the blood vessels is relatively low, and the grayscale of the non-vascular tissue is relatively high; the grayscale image G output by the green response channel mainly contains the surface and middle structure information of the target tissue, especially the information of the surface and middle blood vessels, wherein the grayscale of the blood vessels is relatively low, and the grayscale of the non-vascular tissue is relatively high; the grayscale image R output by the red response channel contains the surface, middle and deep structure information of the target tissue, especially the information of the surface, middle and deep structure blood vessels in the tissue, wherein the grayscale of the blood vessels is relatively high, and the grayscale of the non-vascular tissue is relatively the lowest.

[0067] The spectrum of the second light source 12 of this embodiment has three characteristic peaks (the first characteristic peak, the second characteristic peak and the third characteristic peak), such as Figure 3 As shown, the peak wavelength of the first characteristic peak is within the wavelength range of 400nm-440nm, the half-peak width is less than 40nm, the first characteristic peak is within the response band of the blue response channel of the image sensor 21 and overlaps or partially overlaps with the absorption peak of the 400nm-440nm band of the hemoglobin; the peak wavelength of the second characteristic peak is within the wavelength range of 520nm-570nm, the half-peak width is less than 80nm, the second characteristic peak is within the response band of the green response channel of the image sensor 21 and overlaps or partially overlaps with the absorption peak of the 540nm-570nm band of the hemoglobin; the peak wavelength of the third characteristic peak is within the wavelength range of 600nm-700nm, the half-peak width is less than 120nm, the third characteristic peak is within the response band of the red response channel of the image sensor 21 and within the band range with a small absorption coefficient of the hemoglobin. In addition, the first characteristic peak, the second characteristic peak, and the third characteristic peak overlap less between the blue, green, and red three-color response channels of the image sensor 21. The relative energies of the first characteristic peak, the second characteristic peak and the third characteristic peak in the spectrum may be the same or different, and may be the same, such as Figure 3The relative energy ratio shown in is 1:1:1; it can also be different, for example, the first characteristic peak is the highest, the second characteristic peak is the second highest, and the third characteristic peak is the lowest; or, for example, the first characteristic peak is the highest, the second characteristic peak is the lowest, and the third characteristic peak is the second highest. Preferably, the energy of the first characteristic peak is the highest, and the energy of the first characteristic peak is 2 to 5 times that of the second characteristic peak.

[0068] In addition, when the second light source 12 is an LED light source composed of a purple semiconductor light-emitting chip and green phosphor, the green phosphor is specifically covered on the purple semiconductor light-emitting chip. Specifically, when the white light LED light source is working, the emitted light is a special spectrum light wave composed of a mixture of purple light waves emitted by the purple semiconductor light-emitting chip and green light waves emitted by the green phosphor after being excited. Therefore, this light source composed of a light-emitting chip and exciting the phosphor to emit light has a compact structure and a small light source size, which is very suitable for being placed at the tip of an endoscope.

[0069] When the second light source 12 is a white light LED composed of a purple semiconductor light-emitting chip, green phosphor and red phosphor, specifically, the green phosphor and red phosphor are covered on the purple semiconductor light-emitting chip. Specifically, when the white light LED light source is working, the emitted light is a special spectrum light wave composed of a mixture of purple light waves emitted by the purple semiconductor light-emitting chip, green light waves emitted by the green phosphor after being excited, and red light waves emitted by the red phosphor after being excited. The light source of this kind, which is composed of a light-emitting chip and excites the phosphor to emit light, has a compact structure and a small light source size, and is very suitable for being placed at the tip of an endoscope. In addition, the purple, green, red and other lights have been evenly mixed in the phosphor layer inside the light source. Therefore, when the tip is close to the tissue to magnify and image the tissue structure, there will be no uneven spatial distribution of the color of the illumination light when the light source is illuminated at a close distance. In the specific implementation, the purple semiconductor light-emitting chip emits purple light with a peak wavelength in the range of 400nm-440nm and a half-peak width of less than 30nm; the green light phosphor emits green light with a peak wavelength in the range of 520nm-550nm and a half-peak width of less than 70nm; the red light phosphor emits red light with a peak wavelength in the range of 600nm-680nm and a half-peak width of less than 110nm. Due to the limitations of the peak position and half-peak width of purple light, green light and red light, the spectrum of this special spectrum light wave (i.e., white light LED light source) is discontinuous or has typical peaks and troughs in the visible light range of 380nm-780nm. At this time, the first characteristic peak overlaps or partially overlaps with the strong absorption peak of blood oxygen protein in the 400nm-440nm band, the second characteristic peak overlaps or partially overlaps with another lower absorption peak of blood oxygen protein in the 520nm-570nm band, and the third characteristic peak is in the band with a lower coefficient of blood oxygen protein. The light emitted by the second light source 12 overlaps with the strong absorption peak, the lower absorption peak, and the lower absorption coefficient band of hemoglobin. At the same time, the first characteristic peak of the second light source 12 is at a position where the blue channel of the image sensor 21 responds more, the second characteristic peak is at a position where the green channel of the image sensor 21 responds more, and the third characteristic peak is at a position where the red channel of the image sensor 21 responds more. Among them, the green light phosphor can be aluminate green powder, phosphate green powder, halogen oxide green powder, nitrogen oxide green powder or silicate green powder phosphor, or it can also be nitride green powder phosphor, etc.; the red light phosphor can be nitride red powder phosphor, sulfide red powder phosphor or fluoride red powder phosphor, etc.

[0070] In some embodiments, the first light source 11 is a white light LED light source with continuous spectrum characteristics, and the wavelength range of the first visible light is 380nm-780nm; or, the first light source 11 is an LED light source with discontinuous spectrum characteristics, and the first visible light emitted by the LED light source with discontinuous spectrum characteristics is a special spectrum light wave composed of a mixture of blue light waves, cyan light waves and orange light waves.

[0071] Specifically, when the first light source 11 is an LED light source with continuous spectrum characteristics, the LED light source with continuous spectrum characteristics is a white light LED light source in the usual sense, and the wavelength emitted by the light source has a certain proportion of energy output in the 380nm-780nm band, and has a better color rendering. Preferably, the first light source 11 has a higher energy proportion in the 440nm-480nm blue band, and at this time, the waveforms of the first visible light and the second visible light in the wavelength range of 380nm-780nm are complementary. When the endoscope imaging system is working, if a normal white light image is required, the image processing module 30 controls the first light source 11 in the light source module 10 to light up at 100% brightness to generate the first visible light, and the brightness of the second light source 12 is set to 0% brightness, that is, the second light source 12 is turned off. Under the illumination of the first visible light, the camera module 20 collects the reflected light of the target tissue for imaging, and the image processing module 30 processes the collected image to output a white light image with high color reproduction of the target tissue under normal white light. The relationship between the spectrum of the first visible light of the ordinary white light LED light source of this solution and the RGB response spectrum of the image sensor 21 is as follows: Figure 4 shown.

[0072] When the first light source 11 is an LED light source with discontinuous spectrum characteristics, the first light source 11 can be a white light LED composed of a purple or blue semiconductor light emitting chip, a cyan phosphor and an orange phosphor. When the LED light source is working, the emitted light is a special spectrum light wave composed of a narrow-band purple or blue light wave emitted by the purple or blue semiconductor light emitting chip, a cyan light wave emitted by the cyan phosphor after being excited, and an orange light wave emitted by the orange phosphor after being excited.

[0073] In some embodiments, the first light source 11 is an LED light source with discontinuous spectral characteristics, and the spectrum of the special spectral light wave includes a fourth characteristic peak, a fifth characteristic peak and a sixth characteristic peak; the wavelength range of the fourth characteristic peak is 400nm-480nm, the wavelength range of the fifth characteristic peak is 450nm-510nm, and the wavelength range of the sixth characteristic peak is 580nm-630nm; and the half-peak width of the fourth characteristic peak is less than 30nm, and the half-peak widths of the fifth characteristic peak and the sixth characteristic peak are both greater than 40nm.

[0074] Specifically, when the first light source 11 is an LED light source with a discontinuous spectrum characteristic, the spectrum of the first light source 11 has three characteristic peaks, namely, the fourth characteristic peak, the fifth characteristic peak and the sixth characteristic peak; wherein, the peak wavelength of the fourth characteristic peak is within the wavelength range of 400nm-480nm, and the half-peak width is less than 30nm; the peak wavelength of the fifth characteristic peak is within the wavelength range of 450nm-510nm, and the half-peak width is greater than 40nm; the peak wavelength of the sixth characteristic peak is within the wavelength range of 580nm-630nm, and the half-peak width is greater than 40nm. It can be seen that the fifth characteristic peak overlaps more between the blue and green response channels of the image sensor 21; the sixth characteristic peak overlaps more between the green and red response channels of the image sensor 21.

[0075] In actual applications, in the first light source 11 with discontinuous spectrum characteristics, the purple or blue semiconductor light-emitting chip emits purple or blue light with a peak wavelength in the range of 400nm-480nm and a half-width less than 30nm; the cyan-green phosphor emits cyan light with a peak wavelength in the range of 450nm-510nm and a half-width greater than 40nm; the orange phosphor emits orange light with a peak wavelength in the range of 580nm-630nm and a half-width greater than 40nm. Due to the peak position limitations of purple or blue light, cyan light and orange light, the spectrum of this special spectrum LED light source has typical and obvious peaks and troughs in the visible light range of 380nm-780nm, and has the characteristics of a discontinuous spectrum light source. Among them, the cyan phosphor can be a phosphate cyan phosphor, a halophosphate blue phosphor, etc., and the orange phosphor can be a silicate orange phosphor, etc. Figure 5 It includes a spectral curve of the first visible light of the first light source 11 composed of a purple semiconductor chip, a halophosphate blue powder phosphor and a silicate orange powder phosphor, and a spectral curve of the second visible light of the second light source 12 composed of a purple semiconductor chip, a nitride green powder phosphor peak and a nitride red powder phosphor.

[0076] In some embodiments, the first visible light and the second visible light have complementary waveforms within a wavelength range of 380 nm-780 nm.

[0077] Specifically, when it is known that the first light source 11 is an LED light source with discontinuous spectrum characteristics, the peak wavelength of the first characteristic peak of the spectrum of the second light source 12 with discontinuous spectrum characteristics is within the wavelength range of 400nm-440nm, and the half-peak width is less than 40nm; the peak wavelength of the second characteristic peak is within the wavelength range of 520nm-570nm, and the half-peak width is less than 80nm; the peak wavelength of the third characteristic peak is within the wavelength range of 600nm-700nm, and the half-peak width is less than 120nm. It can be obtained that the waveforms of the first light source 11 and the second light source 12 are complementary within the wavelength range of 380nm-780nm.

[0078] In addition, when the first light source 11 is an LED light source with a discontinuous spectrum characteristic, and the endoscope imaging system needs to perform white light imaging, the first light source 11 and the second light source 12 are simultaneously lit. Since the wavelengths of the first light source 11 and the second light source 12 are complementary, the combined illumination light that is simultaneously lit is a continuous, spectrally uniform white illumination light in the wavelength range of 380nm-780nm. In a specific implementation, the brightness ratio of the first light source 11 and the second light source 12 can be controlled, for example Figure 6 To have Figure 5 The white illumination light obtained by combining the first light source 11 and the second light source 12 in the spectrum shown is in a brightness ratio of 1:1, and has good color rendering properties. The color temperature of the illumination light is about 5000K and the color rendering index is 96.

[0079] Furthermore, after performing image processing on the three-color response signals to obtain corresponding images, the method further includes: processing the images corresponding to the three-color response signals respectively according to a preset conversion function to obtain corresponding monochrome display signals and output them.

[0080] After performing image processing on the three-color response signals, the image processing module 30 also generates a blue display signal fb (B, G, R), a green display signal fg (B, G, R), and a red display signal fr (B, G, R); after the blue display signal is input into the blue display channel of the image display module 40, the green display signal is input into the green display channel of the image display module 40, and the red display signal is input into the red display channel of the image display module 40, the display displays a color composite image.

[0081] In some embodiments, the endoscopic imaging system also includes a display module 40, which includes three-color display channels; the three-color display channels are used to form corresponding monochrome images according to corresponding monochrome display signals; the display module 40 is used to display one of the three monochrome images; or, to display a combination of multiple of the three monochrome images.

[0082] When the intensity of the vascular tissue is differentiated as described above, the second light source 12 is lit at 100% brightness to generate the second visible light, and the brightness of the first light source 11 is set to 0%, that is, the first light source 11 is turned off as an example for explanation:

[0083] Specifically, under the illumination of the second visible light, a new grayscale image is obtained and the enhanced display effect is achieved by performing specific preset mixed operations such as gain, attenuation, inversion, and synthesis on the blue response channel output grayscale image B corresponding to the surface vascular structure of the target tissue, the green response channel output grayscale image G corresponding to the middle vascular structure, and the red response channel output grayscale image R corresponding to the deep vascular structure, and then the grayscale images after the operation are output to the blue display channel, green display channel, and red display channel of the display module 40, respectively.

[0084] In clinical use, if it is necessary to emphasize or display the vascular structure information in the surface tissue of the human body, the second visible light can be used alone for illumination imaging, and the illumination light wave of the first characteristic peak in the second visible light is mainly imaged by the blue response channel response in the image sensor 21. The grayscale image B of the blue response channel in the image sensor 21 can be directly or after transformation output to the red, green and blue display channels of the display module 40. That is, the red display channel DR of the display module 40 is fr(B), the green display channel DG of the display module 40 is fg(B), and the blue display channel DB of the display module 40 is fb(B), and fr, fg, and fb are specific conversion functions. For example, the grayscale image B of the blue response channel can be directly given to the green and blue display channels, and the grayscale image B of the blue response channel can be given to the red display channel after grayscale inversion, that is, DG=B, DB=B, DR=255-B. In the grayscale image B of the blue response channel, the grayscale of the blood vessels is relatively low, and the grayscale of the non-vascular tissue is relatively high. At this time, the surface blood vessels in the display screen have less blue components, less green components, and more red components, and appear brown. The non-vascular tissue has more blue components, more green components, and less red components, and appears cyan. The color contrast between the blood vessels and non-vascular tissues is increased, which is conducive to the display of blood vessels.

[0085] If it is necessary to emphasize or display the vascular structure information in the surface tissue and the middle tissue of the human body at the same time, the second visible light can be used alone for illumination imaging. At this time, the second visible light includes the first characteristic peak and the second characteristic peak. The illumination light wave of the first characteristic peak in the second visible light is mainly imaged by the blue response channel in the image sensor 21, and the illumination light wave of the second characteristic peak is mainly imaged by the green response channel in the image sensor 21. The grayscale image B of the blue response channel and the grayscale image G of the green response channel of the image sensor 21 can be directly or after transformation output to the red, green and blue display channels of the display module 40. That is, the red display channel DR of the display module 40 is fr (B, G), the green display channel DG of the display module 40 is fg (B, G), and the blue display channel DB of the display module 40 is fb (B, G). For example, the grayscale image B of the blue response channel can be directly given to the green and blue display channels, and the grayscale image G of the green response channel can be given to the red display channel, that is, DG = B, DB = B, DR = G. At this time, the grayscale image B of the blue response channel has a relatively low grayscale of blood vessels, while the grayscale of non-vascular tissue is relatively high; the grayscale image G output by the green response channel has a relatively low grayscale of surface and middle-layer blood vessels, while the grayscale of non-vascular tissue is relatively high; at this time, the blood vessels in the surface tissue in the display screen have less blue components, less green components, and more red components, and the surface blood vessels in the display screen appear brown; the blood vessels in the middle tissue have more blue components, more green components, and less red components, and the middle-layer blood vessels in the display screen appear cyan; the non-vascular tissue has more blue components, more green components, and more red components, and the non-vascular tissue in the display screen appears white or pinkish white. The color contrast between the surface and middle-layer blood vessels and non-vascular tissue is increased, which is conducive to the display of blood vessels.

[0086] Some pathological characteristics of human tissue are mostly reflected in the changes in tissue morphology at the lesion location, especially the abnormal proliferation of surface and middle layer tissues, in which case the morphology and quantity of surface and middle layer vascular tissues will change significantly. In some implementations, when the second visible light only contains the first characteristic peak and the second characteristic peak but not the third characteristic peak, the interference of the third characteristic peak light wave energy on the blue and green channels of the image sensor is avoided, which is beneficial to improve the contrast and signal-to-noise ratio of the grayscale images output by the blue and green channels, and is beneficial to better observe the surface and middle layer vascular tissues.

[0087] If it is necessary to emphasize or display the vascular structure information in the deep tissue of the human body at the same time, the second visible light can be used alone for illumination imaging. At this time, the second visible light includes the first characteristic peak, the second characteristic peak and the third characteristic peak. The illumination light wave of the first characteristic peak in the second visible light is mainly imaged by the blue response channel in the image sensor 21, the illumination light wave of the second characteristic peak is mainly imaged by the green response channel in the image sensor 21, and the illumination light wave of the third characteristic peak is mainly imaged by the red response channel in the image sensor 21. The grayscale image R of the red response channel and the grayscale image G of the green response channel of the image sensor 21 can be transformed and output to the red, green and blue display channels of the display module 40. That is, the red display channel DR of the display module 40 is fr(R, G), the green display channel DG of the display module 40 is fg(R, G), and the blue display channel DB of the display module 40 is fb(R, G). For example, when the second visible light is illuminated for imaging, the grayscale of the surface and middle layer blood vessels in the grayscale image G output by the green response channel of the image sensor 21 is relatively low, and the grayscale of the non-vascular tissue is relatively high; in the red channel output image R, the grayscale value of the image of the blood vessels in the surface, middle and deep layers of the tissue is the highest, and the grayscale value of the image of the non-vascular tissue is the lowest. At this time, the red channel output image R is first inverted, and the grayscale value of the image of the blood vessels in the surface, middle and deep layers of the tissue is the lowest, and the grayscale value of the image of the non-vascular tissue is the highest. Then, the inverted grayscale image R is subtracted from the grayscale image G, and the grayscale image f(R, G) after the operation contains only the deep blood vessel structure information with lower grayscale and the non-vascular tissue with higher grayscale. Then, the grayscale image f(R, G) is output to the blue display channel and the green display channel of the display module 40 respectively, and then the grayscale image f(R, G) is inverted and then output to the red display channel of the display module 40. Finally, the deep vascular tissue in the display image has less blue component, less green component, and more red component, and the deep blood vessels appear brown in the display image; the non-vascular tissue has more blue component, more green component, and less red component, and appears cyan; and the grayscale information of the shallow and middle blood vessels is subtracted by calculation, so that it is not presented or is rarely presented. Against the cyan background of the non-vascular tissue, the brown deep blood vessels are conducive to the display of the blood vessels.

[0088] In some embodiments, the brightness ratio of the first visible light and the second visible light includes, but is not limited to, 0:1, 1:0, 1:1 or 0.5:1. The brightness ratio of the two can also be adjusted according to the user's preference. If the user wants the display unit to output an image closer to the natural and real tissue color, the brightness of the two (the first visible light and the second visible light) is adjusted to make the output light closer to the continuous wavelength natural light with high color rendering; if the user wants the display unit to output an image with a greater color contrast and easier to distinguish vascular tissue, the brightness of the two is adjusted to make the output light have a special light with higher peak and trough contrast.

[0089] The light source module 10 of this embodiment can have continuous white light illumination with multiple characteristic peaks. Specifically, for example, when the first light source 11 is an LED light source with continuous spectrum characteristics, the first visible light and the second visible light are turned on at the same time to enhance blood vessels under white light imaging. The image captured by the camera module 20 is close to a normal white light image, but the display of blood vessels is enhanced at the same time. Under this illumination, the grayscale of the shallow blood vessels in the blue response channel of the image sensor 21 is lower than the grayscale of the non-vascular tissue, and the contrast is greater than when only the first visible light is used for illumination; the grayscale of the shallow and middle blood vessels in the green response channel is lower than the grayscale of the non-vascular tissue, and the contrast is greater than when only the first visible light is used for illumination; the grayscale of the shallow, middle and deep blood vessels in the red response channel is higher than the grayscale of the non-vascular tissue, and the contrast is greater than when only the first visible light is used for illumination; after the three response channels are fused into a color image, the shallow, middle and deep blood vessels will be redder and easier to observe than when only the first visible light is used for illumination. When the first light source 11 with continuous spectrum characteristics is turned on at 100% brightness and the second light source 12 is turned on at 60% brightness, the relationship between the first visible light and the second visible light, the hemoglobin spectral absorption coefficient and the image sensor red, green and blue response spectral coefficients is as follows: Figure 7 shown.

[0090] For another example, when the first light source 11 is an LED light source with a discontinuous spectrum feature, the brightness of the second light source 12 can be increased and the brightness of the first light source 11 can be reduced to enhance blood vessels under white light imaging. For example, when the brightness ratio of the first light source 11 and the second light source 12 having the spectrum described in the above paragraph is 0.5:1, the combined white illumination light has good color rendering, with a color temperature of about 4800K and a color rendering index of 86, which can meet the needs of white light imaging, and has obvious peak wavelengths at the blood vessel absorption peak wavelengths of 420nm and 540nm. The combined illumination light spectrum is as follows: Figure 8 shown.

[0091] The first light source 11 and the second light source 12 have different brightness ratios, and different imaging effects can be obtained by matching different image processing and image display methods. The first light source 11 has a high brightness ratio, and the image is closer to a normal white light image, and the image color reproduction is good; the second light source 12 has a high brightness ratio, and the contrast between the vascular tissue and other tissues in the image is large, and the blood vessels are easier to identify. The image processing module 30 can control the brightness ratio of the first light source 11 and the second light source 12 according to the user's selection. The image processing module 30 can analyze the collected image and automatically adjust the brightness ratio of the first light source 11 and the second light source 12 according to the analysis results. For example, when the user wants to observe a white light image and wants to have a blood vessel enhancement function, the image processing module 30 can analyze the spatial frequency, color ratio and other characteristics of the image in real time; considering that the blood vessels in the tissue, especially the capillaries, are particularly small, they belong to the high-frequency part in the image, while the detailed structures of other tissues such as the cortex and mucosa are not obvious and belong to the low-frequency part in the image; therefore, when the brightness contrast between the high-frequency features and the low-frequency features in the image spatial frequency is low, it means that the vascular tissue is not obvious in the image. At this time, the image processing module 30 can automatically increase the brightness ratio of the second light source 12, and again determine whether the brightness contrast between the high-frequency features and the low-frequency features reaches the threshold.

[0092] refer to Fig. 9 This embodiment provides a control method for an endoscopic imaging system, which adopts the endoscopic imaging system of the above embodiment. The control method specifically includes the following steps:

[0093] Step 100: Control the brightness ratio of the first light source 11 and the second light source 12;

[0094] Step 200: Acquire the three-color response signals collected by the camera module 20;

[0095] Step 300: Process the three-color response signal according to the brightness ratio of the first visible light and the second visible light to obtain and output a corresponding image.

[0096] In actual application, when the endoscopic imaging system is working, after receiving the control instruction of the doctor, the image processing module 30 controls the working state of the first light source 11 and the second light source 12 to generate illumination spectra with different brightness ratios to irradiate the target tissue, and the target tissue reflects the illumination light and is acquired by the camera module 20. After collecting the reflected light, the camera module 20 responds and generates three-color response signals (blue response signal B, green response signal G and red response signal R) through the three-color response channels (blue response channel, green response channel, and red response channel) of the image sensor 21; then, the image processing module 30 performs specific gain, attenuation, inversion and other preset mixed operations on the three-color response signals to obtain the corresponding grayscale image and output it. In addition, the principle of selecting the brightness ratio of the first light source 11 and the second light source 12 of the light source module 10 in the endoscopic imaging system, the principle of displaying the image processed by the image processing module 30, and the specific process of the image sensor 21 in the camera module 20 collecting the spectrum reflected by the target tissue have been described in detail in the above-mentioned embodiment of the endoscopic imaging system, and this embodiment will not be repeated in detail here.

[0097] The above specific examples are used to illustrate the present invention, which is only used to help understand the present invention and is not intended to limit the present invention. For those skilled in the art, according to the concept of the present invention, some simple deductions, modifications or substitutions can be made.

Claims

1. An endoscopic imaging system, characterized in that: It includes a light source module, a camera module and an image processing module; The light source module comprises a first light source and a second light source, wherein the first light source is used to emit a first visible light, and the second light source is used to emit a second visible light having a discontinuous spectral characteristic; The camera module includes an image sensor having three color response channels of red, green and blue, and the image sensor is used to receive reflected light formed after the target tissue is irradiated by the visible light emitted by the light source module, so as to obtain a three-color response signal corresponding to the reflected light; The image processing module is used to control the brightness ratio of the first visible light and the second visible light, and is also used to process the three-color response signal to obtain a corresponding image and output it.

2. The endoscopic imaging system according to claim 1, characterized in that: The light source module is located at the leading end of the endoscope body.

3. The endoscopic imaging system according to claim 1, characterized in that: The spectrum of the second visible light includes a first characteristic peak and a second characteristic peak; The wavelength range of the first characteristic peak is 400nm-440nm, and the wavelength range of the second characteristic peak is 520nm-570nm; and the half-peak width of the first characteristic peak is less than 40nm, and the half-peak width of the second characteristic peak is less than 80nm.

4. The endoscopic imaging system according to claim 3, characterized in that: The spectrum of the second visible light also includes a third characteristic peak; The wavelength range of the third characteristic peak is 600nm-700nm; and the half-peak width of the third characteristic peak is less than 120nm.

5. The endoscopic imaging system according to claim 1, characterized in that: The waveforms of the first visible light and the second visible light within the wavelength range of 380nm-780nm are complementary.

6. The endoscopic imaging system according to claim 5, characterized in that: The first light source is a white light LED light source with continuous spectrum characteristics, and the wavelength range of the first visible light is 380nm-780nm; or, The first light source is an LED light source with discontinuous spectrum characteristics. The first visible light emitted by the LED light source with discontinuous spectrum characteristics is a special spectrum light wave composed of a mixture of blue light waves, cyan light waves and orange light waves.

7. The endoscopic imaging system according to claim 6, characterized in that: The first light source is an LED light source with a discontinuous spectrum characteristic, and the spectrum of the special spectrum light wave includes a fourth characteristic peak, a fifth characteristic peak and a sixth characteristic peak; The wavelength range of the fourth characteristic peak is 400nm-480nm, the wavelength range of the fifth characteristic peak is 450nm-510nm, and the wavelength range of the sixth characteristic peak is 580nm-630nm; and, The half-width of the fourth characteristic peak is less than 30 nm, and the half-widths of the fifth characteristic peak and the sixth characteristic peak are both greater than 40 nm.

8. The endoscopic imaging system according to claim 1, wherein: The image processing module processes the three-color response signal to obtain a corresponding image, including: matching a corresponding image processing mechanism according to a brightness ratio of the first visible light and the second visible light to perform image processing on the three-color response signal to obtain a corresponding image.

9. The endoscopic imaging system according to claim 7, characterized in that: After performing image processing on the three-color response signals to obtain corresponding images, the method further includes: The images corresponding to the three-color response signals are processed respectively according to a preset conversion function to obtain and output corresponding monochrome display signals.

10. The endoscopic imaging system according to claim 3, characterized in that: The second light source is an LED light source composed of a purple semiconductor light emitting chip and a green phosphor; The emission peak wavelength of the purple semiconductor light-emitting chip is within the wavelength range of 400nm-440nm, and the half-peak width is less than 30nm; the emission peak wavelength of the green phosphor is within the wavelength range of 520nm-550nm, and the half-peak width is less than 70nm.

11. The endoscopic imaging system according to claim 4, characterized in that: The second light source is an LED light source composed of a purple semiconductor light emitting chip, green phosphor and red phosphor; The emission peak wavelength of the purple semiconductor light-emitting chip is within the wavelength range of 400nm-440nm, and the half-peak width is less than 30nm; the emission peak wavelength of the green phosphor is within the wavelength range of 520nm-550nm, and the half-peak width is less than 70nm; the emission peak wavelength of the red phosphor is within the wavelength range of 600nm-680nm, and the half-peak width is less than 110nm.

12. A control method for an endoscope imaging system, characterized in that: Using the endoscopic imaging system according to any one of claims 1 to 11, the method comprises: Controlling the brightness ratio of the first light source and the second light source; Acquire the three-color response signals collected by the camera module; The three-color response signal is processed according to the brightness ratio of the first visible light and the second visible light to obtain and output a corresponding image.

Images