Endoscopic imaging system and control method therefor

Abstract

The present invention relates to the technical field of endoscopic imaging, and in particular to an endoscopic imaging system and a control method therefor. In the solution of the present application, first, a light source module emits first visible light and / or second visible light on the basis of a control instruction, and an image processing module controls a brightness ratio of the first visible light to the second visible light when irradiating a target tissue, so that the target tissue generates reflected light after irradiated by the first visible light and the second visible light; then, an image sensor of a camera module receives the reflected light, and generates a three-color response signal on the basis of the reflected light; and finally, the image processing module processes the three-color response signal to obtain a corresponding image and output the corresponding image. The described solution of the present application effectively solves the problem of low recognition of target tissue images in existing endoscopic imaging.

Description

An endoscopic imaging system and its control method Technical Field

[0001] This invention relates to the field of endoscopic imaging technology, and more specifically to an endoscopic imaging system and its control method. Background Technology

[0002] Endoscopes can enter a patient's body non-invasively or minimally invasively, allowing for precise diagnosis and treatment by viewing endoscopic images. Therefore, the application of endoscopes in the medical field is becoming increasingly widespread. The main function of the endoscopic light source is to provide illumination for endoscopic imaging; therefore, the endoscopic light source is crucial to the endoscope. After the endoscope enters the human body, it directly or indirectly illuminates the human tissue through the light source or its associated optical system. The endoscopic camera module receives the reflected light from the human tissue to form an image.

[0003] There are many types of light sources for endoscopes, such as xenon lamps or white LED light sources that provide direct white light illumination. Endoscopes using these light sources only perform white light imaging of the human body, which is a single function and results in low recognition of target tissues in the imaging images. Summary of the Invention

[0004] The present invention provides an endoscopic imaging system and its control method, which effectively solves the problem that the target tissue in the imaging image is poorly identified due to the single illumination function of the existing endoscopic imaging system.

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

[0006] The light source module includes a first light source and a second light source. 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 with discontinuous spectral characteristics.

[0007] The camera module includes an image sensor with red, green and blue three-color response channels. The image sensor is used to receive the reflected light formed after the target tissue is irradiated by visible light emitted by the light source module, thereby obtaining the 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 signals to obtain the corresponding image and output it.

[0009] In one feasible implementation, the light source module is located at the tip of the endoscope body.

[0010] In one feasible implementation, 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; furthermore, the half-width at half maximum (WHM) of the first characteristic peak is less than 40nm, and the half-width at half maximum (WHM) of the second characteristic peak is less than 80nm.

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

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

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

[0015] In one feasible implementation, the first light source is a white LED light source with continuous spectrum characteristics, 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 spectral characteristics. The first visible light emitted by the LED light source with discontinuous spectral characteristics is a special spectral light wave composed of a mixture of blue light waves, cyan light waves, and orange light waves.

[0017] In one feasible implementation, the first light source 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.

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

[0019] The full width at half maximum (FWHM) of the fourth characteristic peak is less than 30 nm, while the FWHMs of the fifth and sixth characteristic peaks are both greater than 40 nm.

[0020] In one feasible 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 the brightness ratio of the first visible light and the second visible light to process the three-color response signal to obtain a corresponding image.

[0021] In one feasible implementation, after performing image processing on the three-color response signals to obtain the corresponding image, the method further includes:

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

[0023] In one feasible implementation, the system further includes a display module, which includes a three-color display channel; the three-color display channel is used to form a corresponding monochrome image based on a corresponding monochrome display signal.

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

[0025] In one feasible implementation, the second light source is an LED light source composed of a violet semiconductor light-emitting chip and a green phosphor.

[0026] The emission peak wavelength of the violet semiconductor light-emitting chip is in the wavelength range of 400nm-440nm and the half-width at half-maximum (WHM) is less than 30nm; the emission peak wavelength of the green phosphor is in the wavelength range of 520nm-550nm and the WHM is less than 70nm.

[0027] In one feasible implementation, the second light source is composed of the violet semiconductor light-emitting chip, green phosphor and red phosphor to form a white LED light source;

[0028] The emission peak wavelength of the violet semiconductor light-emitting chip is in the wavelength range of 400nm-440nm and the half-width at half-maximum (WHM) is less than 30nm; the emission peak wavelength of the green phosphor is in the wavelength range of 520nm-550nm and the WHM is less than 70nm; the emission peak wavelength of the red phosphor is in the wavelength range of 600nm-680nm and the WHM is less than 110nm.

[0029] In one feasible 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, one embodiment provides a control method for an endoscopic imaging system, employing the aforementioned endoscopic imaging system, the method comprising:

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

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

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

[0034] According to the above embodiment of an endoscopic imaging system / control method, firstly, the light source module emits first visible light and / or second visible light according to a control command. By controlling the brightness ratio of the first and second visible light illuminating the target tissue, the target tissue generates reflected light after being irradiated by the first and second visible light. Then, the image sensor of the camera module receives the reflected light and generates a three-color response signal based on the reflected light. Finally, the image processing module processes the three-color response signal to obtain and output the corresponding image. By adopting the above solution of this application, the problem of low image recognition of target tissue in current endoscopic imaging is effectively solved. Attached Figure Description

[0035] Figure 1 is a schematic diagram of the endoscopic imaging system provided in this embodiment;

[0036] Figure 2 is a schematic diagram of the imaging principle 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 blood oxygen protein spectrum absorption coefficient and the RGB response spectrum of the image sensor in this embodiment.

[0038] Figure 4 is a graph showing the relationship between the first visible light spectrum and the RGB response spectrum of the image sensor in this embodiment.

[0039] Figure 5 is a graph showing the relationship between the first and second visible light spectra of the discontinuous spectral characteristics of this embodiment and the RGB response spectrum of the image sensor.

[0040] Figure 6 is a graph showing the relationship between the first and second visible light spectra with discontinuous spectral characteristics of the 1:1 combined illumination light in this embodiment and the RGB response spectrum of the image sensor.

[0041] Figure 7 is a graph showing the relationship between the first visible light + second visible light spectrum, the absorption coefficient of the blood oxygen protein spectrum, and the RGB response spectrum of the image sensor in this embodiment.

[0042] Figure 8 is a graph showing the relationship between the first and second visible light spectra with discontinuous spectral characteristics of the 0.5:1 combined illumination light in this embodiment and the RGB response spectrum of the image sensor.

[0043] Figure 9 is a flowchart of the control method of the 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 Implementation

[0045] The present invention will now be described in further detail with reference to specific embodiments and accompanying drawings. Similar elements in different embodiments are referred to by associated similar element reference numerals. In the following embodiments, many details are described to facilitate a better understanding of this application. However, those skilled in the art will readily recognize that some features may be omitted in different situations, or may be replaced by other elements, materials, or methods. In some cases, certain operations related to this application are not shown or described in the specification. This is to avoid obscuring the core parts of this application with excessive description. For those skilled in the art, detailed description of these related operations is not necessary; they can fully understand the related operations based on the description in the specification and general technical knowledge in the art.

[0046] Furthermore, the features, operations, or characteristics described in the specification can be combined in any suitable manner to form various embodiments. At the same time, the steps or actions in the method description can be rearranged or adjusted in a manner obvious to those skilled in the art. Therefore, the various orders in the specification and drawings are only for the clear description of a particular embodiment and do not imply a necessary order, unless otherwise stated that a particular order must be followed.

[0047] The serial numbers assigned to components in this document, such as "first" and "second," are used only to distinguish the described objects and have no sequential or technical meaning. The terms "connection" and "linkage" used in this application, unless otherwise specified, include both direct and indirect connections (linkages).

[0048] As is well known, conventional color imaging sensors employ a filter system based on the tristimulus principle in front of the sensor's photosensitive area to separate different colors and achieve color imaging. Therefore, conventional image sensors using an RGB filter system exhibit high response in the blue channel (380nm-520nm), high response in the green channel (460nm-610nm), and high response in the red channel (580nm-800nm). It can be seen that the blue and green response channels of conventional image sensors have significant overlap in the 470nm-520nm band, and the green and red response channels have significant overlap in the 580nm-610nm band.

[0049] Human tissues, especially vascular tissues and blood, contain a large amount of hemoglobin. Hemoglobin has a specific absorption spectrum for different wavelengths of light. Hemoglobin (Hb) has strong absorption peaks near 440nm and 555nm, while oxyhemoglobin (HbO2) has strong absorption peaks near 415nm, 540nm, and 575nm. Its absorption coefficient is very small in wavelengths above 600nm. This means that light in the 380nm-450nm wavelength range is strongly absorbed by hemoglobin, light in the 520nm-600nm wavelength range is partially absorbed, and light above 600nm is strongly reflected due to low absorption. Furthermore, human tissue is a scattering material for light. According to the laws of physics, shorter wavelengths of light are scattered more strongly within human tissue and travel shorter distances; conversely, longer wavelengths of light are scattered less strongly and travel longer distances. 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, the response bands of the blue and green response channels coincide with the absorption peaks of hemoglobin / oxyhemoglobin, making it difficult to identify vascular tissue.

[0050] Therefore, this application proposes an endoscopic imaging system and its control method. The endoscopic imaging system of this application uses a color image sensor with red, green, and blue color response channels for imaging. The light source consists of two white LEDs with different emission spectra. By controlling the brightness ratio of the two light sources through image processing, different illumination lights are formed for imaging to improve the recognition of blood vessels in human tissue. For details, please refer to the following embodiments.

[0051] Referring to Figures 1 and 2, an endoscopic imaging system provided in this embodiment includes a light source module 10, a camera module 20, and an image processing module 30. It also includes a display module 40. The light source module 10 is located at the tip of the endoscope body. Specifically, the light source module 10 includes a first light source 11 and a second light source 12. The first light source 11 emits first visible light, and the second light source 12 emits second visible light with discontinuous spectral characteristics. The camera module 20 includes an image sensor 21 with red, green, and blue three-color response channels. The image sensor 21 receives reflected light formed after the target tissue is irradiated by the visible light emitted by the light source module 10, thereby obtaining the three-color response signal corresponding to the reflected light. The image processing module 30 controls the brightness ratio of the first and second visible light, and also processes the three-color response signal to obtain a corresponding image and outputs it to the display module 40. The display module 40 includes a three-color display channel; the three-color display channel is used to form a corresponding monochrome image based on the 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 this embodiment, the endoscopic imaging system controls the operating states of the first light source 11 and the second light source 12 in the light source module 10 via 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 simultaneously employed to achieve different imaging effects for different imaging purposes.

[0053] In practical applications, the light source is integrated into the endoscope body, its tip, or the exterior of the endoscope. Specifically, the light source module 10 can be located at the handle of the endoscope body or on the exterior of the endoscope body, and the light waves emitted by the light source module 10 can be transmitted to the tip via optical fibers. Alternatively, the light source module 10 can be located at the tip of the endoscope body. In practical applications, it is preferable to miniaturize the light source module 10 and place it at the tip of the endoscope body, because in this case, the illumination light emitted by the light source module 10 does not need to be transmitted through optical fibers and can directly irradiate the target tissue, minimizing light energy loss. Considering that the endoscope body is frequently bent inside the human body during use, this application omits the optical fiber to make the system simpler and more reliable, avoiding the problem of illumination intensity attenuation caused by optical fiber breakage after long-term use. At the same time, without optical fibers, optical coupling devices, and other light transmission elements, the manufacturing cost of the endoscope is lower.

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

[0055] When the endoscopic 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 instructions 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 imaging module 20, respectively, and generates a blue response signal B, a green response signal G, and a red response signal R. Then, the response signals of the image sensor 21 are transmitted to the image processing module 30. The image processing module 30 performs specific preset mixing operations such as gain, attenuation, and inversion on the grayscale images generated by the blue response signal B, the green signal G, and 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 output to the corresponding display channels of the display unit, and finally the color composite image is displayed on the monitor. Specifically, since the red, green, and blue response channels 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 receiving the grayscale image, the blue display channel displays the new blue grayscale image information in the blue color display unit of the display module 40. Similarly, the three colors are superimposed in the human eye to form a color image.

[0056] Specifically, if it is necessary to enhance imaging and differentiate blood vessels 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 be lit at 100% brightness to generate 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, and the second light source 12 is lit to generate second visible light.

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

[0058] The second light source 12 is composed of a violet semiconductor light-emitting chip and a green phosphor LED light source; the emission peak wavelength of the violet 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 is understood that the second visible light emitted by the second light source 12 in this embodiment includes a violet light wave with a first characteristic peak and a green light wave with a second characteristic peak. Specifically, when the violet light wavelength with the first characteristic peak in the second visible light irradiates the target tissue, considering that the violet light wavelength is short and scatters strongly in the target tissue, and that the penetration depth of violet or blue light is small and cannot reach the deep tissue layers, the violet light can only illuminate the surface of the tissue. The image output by the blue channel of the image sensor 21 only reflects the structural information of the surface tissue. Therefore, the grayscale image of the blue channel is a surface tissue image. During imaging, part of the light is reflected by the epidermis and mucous membrane in the target tissue, and part is strongly absorbed by the blood oxygen proteins in the blood vessels. As a result, the violet light reflected by the blood vessels is weaker than the light reflected by the mucous membrane. Therefore, in the grayscale image output by the blue channel of the endoscopic image sensor 21, the grayscale of the epidermis and mucous membrane 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. The grayscale of the blood vessels in the surface tissue will be lower than that of other surface tissues such as mucosa. Thus, the interference of other deep tissues, especially the interference of middle and deep blood vessels, can be eliminated in the blue channel image of the endoscope, and the superficial blood vessels can be distinguished more clearly in the tissue surface.

[0060] Within target tissues with strong scattering, longer wavelength light penetrates deeper. When green light, which has a second characteristic peak in the second visible light spectrum, illuminates the target tissue, due to its greater penetration depth, part of it is reflected by the epidermis, mucous membranes, and middle layers of the target tissue, while the rest is absorbed by oxygen-producing proteins in the blood vessels of the superficial and middle layers of the human body. Therefore, in the grayscale image output by the green channel of image sensor 21, the grayscale of non-vascular tissues in the target tissue is high, while the grayscale of superficial and middle blood vessels is low. The green light corresponding to the second characteristic peak penetrates deeper than the violet light corresponding to the shorter wavelength first characteristic peak, thus green light can reach deeper into the tissue. Consequently, the image output by the green channel of image sensor 21 mainly contains structural information of the superficial and middle layers of the tissue.

[0061] Since the violet 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, the violet and green light waves do not affect the contrast of the grayscale images of other color response channels, or the violet and green light waves have a small impact on the contrast of the grayscale images of other color response channels. The grayscale image B output by the blue response channel of the image sensor 21 mainly contains information on the surface structure of the target tissue, especially the information on the surface blood vessels, where the grayscale of blood vessels is relatively low and the grayscale of non-vascular tissues is relatively high; the grayscale image G output by the green response channel mainly contains information on the surface and middle structure of the target tissue, especially the information on the surface and middle blood vessels, where the grayscale of blood vessels is relatively low and the grayscale of non-vascular tissues 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 600 nm-700 nm; and the full width at half maximum (FWHM) of the third characteristic peak is less than 120 nm.

[0063] The second light source 12 is composed of a violet semiconductor light-emitting chip, a green phosphor, and a red phosphor, forming an LED light source. The emission peak wavelength of the violet semiconductor light-emitting chip is in the wavelength range of 400nm-440nm, and the half-width at half-maximum (WHM) is less than 30nm. The emission peak wavelength of the green phosphor is in the wavelength range of 520nm-550nm, and the WHM is less than 70nm. The emission peak wavelength of the red phosphor is in the wavelength range of 600nm-680nm, and the WHM is less than 110nm.

[0064] It is 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 its longer wavelength, penetrates deeper than shorter wavelengths of violet (or blue) and green light. Therefore, red light can reach deeper into tissues. Specifically, when the red light wave corresponding to the third characteristic peak of the second visible light spectrum illuminates the target tissue, the tissue scatters red light less, resulting in stronger and greater red light transmission and deeper penetration. Meanwhile, hemoglobin in the blood vessels of the target tissue absorbs red light less and reflects it more strongly. Therefore, when blood vessels in the tissue are illuminated by red light, they reflect the red light, which is then transmitted back through the tissue. During imaging, in the red channel output image of the image sensor 21, because blood vessels in the tissue reflect red light, the image grayscale values ​​of blood vessels in the superficial, middle, and deep tissues are higher, while the image grayscale values ​​of non-vascular tissues are lower.

[0066] Because the violet 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, the violet, green, and red light waves do not affect the contrast of the grayscale image in other color response channels, or the violet, green, and red light waves have a small impact on the contrast of the grayscale image in other color response channels. The grayscale image B output by the blue response channel of image sensor 21 mainly contains information on the surface structure of the target tissue, especially the information on the surface blood vessels, where the grayscale of blood vessels is relatively low and the grayscale of non-vascular tissue is relatively high; the grayscale image G output by the green response channel mainly contains information on the surface and middle structure of the target tissue, especially the information on the surface and middle blood vessels, where the grayscale of blood vessels is relatively low and the grayscale of non-vascular tissue is relatively high; the grayscale image R output by the red response channel contains information on the surface, middle and deep structure of the target tissue, especially the information on the surface, middle and deep blood vessels in the tissue, where the grayscale of blood vessels is relatively high and the grayscale of non-vascular tissue is relatively low.

[0067] The three characteristic peaks (first characteristic peak, second characteristic peak, and third characteristic peak) of the spectrum of the second light source 12 in this embodiment are shown in Figure 3. The peak wavelength of the first characteristic peak is located in the wavelength range of 400nm-440nm and the half-width at half-maximum (WHM) 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 blood oxygen protein in the 400nm-440nm band. The peak wavelength of the second characteristic peak is located in the wavelength range of 520nm-570nm and the WHM 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 blood oxygen protein in the 540nm-570nm band. The peak wavelength of the third characteristic peak is located in the wavelength range of 600nm-700nm and the WHM is less than 120nm. The third characteristic peak is within the response band of the red response channel of the image sensor 21 and is within the band where the absorption coefficient of the blood oxygen protein is small. Furthermore, the first, second, and third characteristic peaks have minimal overlap among the blue, green, and red response channels of the image sensor 21. The relative energies of the first, second, and third characteristic peaks in the spectrum can be the same or different. They can be the same, i.e., a relative energy ratio of 1:1:1 as shown in Figure 3; or they can 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 first characteristic peak has the highest energy, and its energy is 2 to 5 times that of the second characteristic peak.

[0068] Furthermore, when the second light source 12 is an LED light source composed of a violet semiconductor light-emitting chip and a green phosphor, specifically, the green phosphor is coated on the violet semiconductor light-emitting chip. Specifically, when this white LED light source is working, the emitted light is a special spectral light wave composed of a mixture of violet light waves emitted by the violet semiconductor light-emitting chip and green light waves emitted after the green phosphor is excited. Therefore, this type of light source, consisting of a single light-emitting chip and excited phosphor, has a compact structure and can be made small, making it very suitable for placement at the tip of an endoscope.

[0069] When the second light source 12 is a white LED composed of a violet semiconductor light-emitting chip, green phosphor, and red phosphor, specifically, green and red phosphors are coated on the violet semiconductor light-emitting chip. Specifically, when this white LED light source is working, the emitted light is a special spectral light wave composed of a mixture of violet light waves emitted by the violet semiconductor light-emitting chip, green light waves emitted by the excited green phosphor, and red light waves emitted by the excited red phosphor. This type of light source, consisting of a single light-emitting chip and excited phosphors, has a compact structure and can be made small, making it very suitable for placement at the tip of an endoscope. Furthermore, the violet, green, and red lights are uniformly mixed in the phosphor layer inside the light source; therefore, when the tip is close to the tissue for magnified imaging of the tissue structure, there will be no uneven color spatial distribution of the illumination light during close-range illumination. In practical implementation, the violet semiconductor light-emitting chip emits violet light with a peak wavelength range of 400nm-440nm and a half-width at half-maximum (HWHM) of less than 30nm; the green phosphor emits green light with a peak wavelength range of 520nm-550nm and a HWHM of less than 70nm; and the red phosphor emits red light with a peak wavelength range of 600nm-680nm and a HWHM of less than 110nm. Due to the limitations of the peak positions and HWHM of violet, green, and red light, the spectrum of this special spectral light wave (i.e., the white LED light source) is discontinuous or exhibits typical peaks and troughs in the visible light range of 380nm-780nm. At this time, the first characteristic peak in the 400nm-440nm band coincides with or partially coincides with the strong absorption peak of hemoglobin; the second characteristic peak in the 520nm-570nm band coincides with or partially coincides with another lower absorption peak of hemoglobin; and the third characteristic peak is in the band where the coefficient of hemoglobin is relatively low. The light emitted by the second light source 12 overlaps with the strong absorption peak, lower absorption peak, and lower absorption coefficient band of the blood oxygen protein. Simultaneously, the first characteristic peak of the second light source 12 is located at a position with a high response in the blue channel of the image sensor 21, the second characteristic peak is located at a position with a high response in the green channel of the image sensor 21, and the third characteristic peak is located at a position with a high response in the red channel of the image sensor 21. The green phosphor can be aluminate green phosphor, phosphate green phosphor, halide green phosphor, nitride green phosphor, or silicate green phosphor, or it can also be nitride green phosphor, etc.; the red phosphor can be nitride red phosphor, sulfide red phosphor, or fluoride red phosphor, etc.

[0070] In some embodiments, the first light source 11 is a white LED light source with continuous spectral 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 spectral characteristics, and the first visible light emitted by the LED light source with discontinuous spectral characteristics is a special spectral light wave composed of a mixture of blue light wave, cyan light wave and orange light wave.

[0071] Specifically, when the first light source 11 is an LED light source with continuous spectrum characteristics, which is a white LED light source in the general sense, the light source emits energy with a certain proportion of each wavelength in the 380nm-780nm wavelength range, exhibiting good color rendering. Preferably, the first light source 11 has a high energy proportion in the 440nm-480nm blue wavelength range. In this case, the waveforms of the first visible light and the second visible light in the 380nm-780nm wavelength range are complementary. When the endoscopic imaging system is working and requires a normal white light image, the image processing module 30 controls the first light source 11 in the light source module 10 to be lit at 100% brightness to generate the first visible light, and sets the brightness of the second light source 12 to 0%, i.e., turns off the second light source 12. Under the illumination of the first visible light, the camera module 20 collects the reflected light from the target tissue for imaging, and the image processing module 30 processes the collected image and outputs a white light image with high color reproduction of the target tissue under normal white light conditions. Figure 4 shows the relationship between the spectrum of the first visible light from a common white LED light source using this scheme and the RGB response spectrum of the image sensor 21.

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

[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 400 nm-480 nm, the wavelength range of the fifth characteristic peak is 450 nm-510 nm, and the wavelength range of the sixth characteristic peak is 580 nm-630 nm; and the full width at half maximum (FWHM) of the fourth characteristic peak is less than 30 nm, while the FWHMs of the fifth and sixth characteristic peaks are both greater than 40 nm.

[0074] Specifically, when the first light source 11 is an LED light source with discontinuous spectral characteristics, 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. Among them, the peak wavelength of the fourth characteristic peak is located in the wavelength range of 400nm-480nm, and the half-width at half-maximum (WHM) is less than 30nm; the peak wavelength of the fifth characteristic peak is located in the wavelength range of 450nm-510nm, and the WHM is greater than 40nm; the peak wavelength of the sixth characteristic peak is located in the wavelength range of 580nm-630nm, and the WHM is greater than 40nm. It can be seen that the fifth characteristic peak overlaps significantly between the blue and green response channels of the image sensor 21; the sixth characteristic peak overlaps significantly between the green and red response channels of the image sensor 21.

[0075] In practical applications, the first light source 11, which possesses discontinuous spectral characteristics, comprises a violet or blue light-emitting semiconductor chip that emits violet or blue light with a peak wavelength in the range of 400nm-480nm and a half-width at half-maximum (HWHM) of less than 30nm; a cyan-green phosphor that emits cyan light with a peak wavelength in the range of 450nm-510nm and a HWHM greater than 40nm; and an orange phosphor that emits orange light with a peak wavelength in the range of 580nm-630nm and a HWHM greater than 40nm. Due to the peak positions of violet or blue light, cyan light, and orange light, the spectrum of this special spectral LED light source exhibits typical and distinct peaks and troughs in the visible light range of 380nm-780nm, thus possessing the characteristics of a discontinuous spectral light source. The cyan phosphor can be phosphate cyan phosphor, halophosphate blue phosphor, etc., and the orange phosphor can be silicate orange phosphor, etc. Figure 5 shows the spectrum of the first visible light source 11, which is composed of a violet semiconductor chip, halophosphate blue phosphor, and silicate orange phosphor, and the spectrum of the second visible light source 12, which is composed of a violet semiconductor chip, nitride green phosphor, and nitride red phosphor.

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

[0077] Specifically, given that the first light source 11 is an LED light source with discontinuous spectral characteristics, the second light source 12, which also has discontinuous spectral characteristics, has a first characteristic peak with a peak wavelength in the range of 400nm-440nm and a half-width at half-maximum (WHM) of less than 40nm; a second characteristic peak with a peak wavelength in the range of 520nm-570nm and a WHM of less than 80nm; and a third characteristic peak with a peak wavelength in the range of 600nm-700nm and a WHM of less than 120nm. Therefore, it can be concluded that the waveforms of the first light source 11 and the second light source 12 are complementary in the wavelength range of 380nm-780nm.

[0078] Furthermore, when the first light source 11 is an LED light source with discontinuous spectral characteristics, and the endoscopic imaging system requires white light imaging, the first light source 11 and the second light source 12 are lit simultaneously. Since the wavelengths of the first light source 11 and the second light source 12 are complementary, the combined illumination light lit simultaneously is a continuous, spectrally uniform white illumination light within the wavelength range of 380nm-780nm. In specific implementations, the brightness ratio of the first light source 11 and the second light source 12 can be controlled. For example, Figure 6 shows the combined white illumination light with the brightness ratio of the first light source 11 and the second light source 12, which has the spectrum shown in Figure 5, at a ratio of 1:1. This illumination light has good color rendering properties, with a color temperature of approximately 5000K and a color rendering index of 96.

[0079] Furthermore, after processing the three-color response signals to obtain the corresponding images, the process also includes: processing the images corresponding to the three-color response signals according to preset conversion functions to obtain the corresponding monochrome display signals and output them.

[0080] After processing the three-color response signals, the image processing module 30 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). 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 then shows the color composite image.

[0081] In some embodiments, the endoscopic imaging system further includes a display module 40, which includes a three-color display channel; the three-color display channel is used to form a corresponding monochrome image according to the 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.

[0082] Taking the intensity differentiation of vascular tissue as described above, the second light source 12 is lit at 100% brightness to generate the second visible light, while the brightness of the first light source 11 is set to 0%, i.e., the first light source 11 is turned off, as an example:

[0083] Specifically, under the illumination of the second visible light, a new grayscale image is obtained by performing specific preset mixing operations such as gain, attenuation, inversion, and synthesis on the grayscale image B output by the blue response channel corresponding to the surface blood vessel structure of the target tissue, the grayscale image G output by the green response channel corresponding to the middle blood vessel structure, and the grayscale image R output by the red response channel corresponding to the deep blood vessel structure, thereby enhancing the display. Then, the processed grayscale images are output to the blue display channel, green display channel, and red display channel of the display module 40, respectively.

[0084] In clinical applications, when it is necessary to emphasize or display vascular structure information in the surface tissues of the human body, a second visible light can be used alone for illumination imaging. The illumination 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 grayscale image B of the blue response channel in the image sensor 21 can be directly or after transformation and output to the red, green, and blue display channels of the display module 40. That is, the red display channel DR=fr(B), the green display channel DG=fg(B), and the blue display channel DB=fb(B) of the display module 40, where fr, fg, and fb are specific transformation functions. For example, the grayscale image B of the blue response channel can be directly fed to the green and blue display channels, and the grayscale image B of the blue response channel can be inverted and then fed to the red display channel, i.e., DG=B, DB=B, DR=255-B. In the grayscale image B of the blue response channel, the grayscale of blood vessels is relatively low, and the grayscale of non-vascular tissues is relatively high. At this time, the surface blood vessels in the displayed image have less blue component, less green component, and more red component, appearing as brown. Non-vascular tissues contain more blue, more green, and less red, appearing as cyan. The increased color contrast between vascular and non-vascular tissues is beneficial for visualizing blood vessels.

[0085] If it is necessary to simultaneously emphasize or display vascular structure information in the superficial and middle layers of human tissue, second visible light can be used for illumination imaging alone. In this case, the second visible light includes a first characteristic peak and a second characteristic peak. The illumination wave of the first characteristic peak in the second visible light is mainly imaged by the blue response channel in image sensor 21, and the illumination wave of the second characteristic peak is mainly imaged by the green response channel in image sensor 21. The grayscale image B of the blue response channel and the grayscale image G of the green response channel of image sensor 21 can be directly or after transformation and output to the red-green-blue display channels of display module 40. That is, the red display channel DR of display module 40 is DR=fr(B, G), the green display channel DG=fg(B, G), and the blue display channel DB=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, i.e., DG=B, DB=B, DR=G. At this point, in the grayscale image B of the blue response channel, the grayscale of blood vessels is relatively low, while the grayscale of non-vascular tissue is relatively high. In the grayscale image G output by the green response channel, the grayscale of superficial and middle-layer blood vessels is relatively low, while the grayscale of non-vascular tissue is relatively high. Therefore, in the displayed image, the blood vessels in the superficial tissue have fewer blue and green components and more red components, appearing brown. The blood vessels in the middle tissue have more blue, more green, and less red components, appearing cyan. The non-vascular tissue has more blue, more green, and more red components, appearing white or pinkish-white. The increased color contrast between the superficial and middle-layer blood vessels and non-vascular tissue is beneficial for displaying blood vessels.

[0086] Many pathological features of human tissues are manifested in changes in tissue morphology at the lesion site, particularly abnormal proliferation in the superficial and middle layers of tissue. In such cases, the morphology and quantity of blood vessels in the superficial and middle layers will change significantly. In some implementations, when the second visible light only contains the first and second characteristic peaks and not the third characteristic peak, the interference of the third characteristic peak's light wave energy on the blue and green channels of the image sensor is avoided. This is beneficial for improving the contrast and signal-to-noise ratio of the grayscale images output from the blue and green channels, and facilitates better observation of blood vessels in the superficial and middle layers.

[0087] If it is necessary to simultaneously emphasize or display vascular structure information in deep human tissues, second visible light can be used alone for illumination imaging. In this case, the second visible light includes a first characteristic peak, a second characteristic peak, and a 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 image sensor 21, the illumination light wave of the second characteristic peak is mainly imaged by the green response channel in image sensor 21, and the illumination light wave of the third characteristic peak is mainly imaged by the red response channel in image sensor 21. The grayscale image R of the red response channel and the grayscale image G of the green response channel of image sensor 21 can be transformed and output to the red, green, and blue display channels of display module 40. That is, the red display channel DR of display module 40 is DR = fr(R, G), the green display channel DG of display module 40 is DG = fg(R, G), and the blue display channel DB of display module 40 is DB = fb(R, G). For example, during second visible light illumination imaging, the grayscale image G output by the green response channel of image sensor 21 shows relatively low grayscale values ​​for superficial and intermediate blood vessels, and relatively high grayscale values ​​for non-vascular tissues. In the red channel output image R, the grayscale values ​​for blood vessels are highest in the superficial, intermediate, and deep tissues, while the grayscale values ​​for non-vascular tissues are lowest. At this point, the red channel output image R is first inverted, resulting in the lowest grayscale values ​​for blood vessels and the highest grayscale values ​​for non-vascular tissues in the superficial, intermediate, and deep tissues. Then, the inverted grayscale image R is subtracted from the grayscale image G, resulting in a grayscale image f(R, G) containing only information about the lower-grayscale deep blood vessel structures and the higher-grayscale non-vascular tissues. Subsequently, the grayscale image f(R, G) is output to the blue and green display channels of display module 40, and then inverted again before being output to the red display channel of display module 40. Ultimately, in the displayed image, deep blood vessels have fewer blue and green components and more red components, so they appear brown; non-vascular tissues have more blue and green components and less red components, so they appear cyan; while the grayscale information of shallow and medium-layer blood vessels is subtracted, so they are not displayed or are displayed very little. Against the cyan background of non-vascular tissues, the brown deep blood vessels are beneficial for the display of 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 can also be adjusted according to user preference. If the user wants the output image of the display unit to be closer to natural, realistic tissue colors, the brightness of both (the first visible light and the second visible light) can be adjusted to make the output light closer to high color rendering continuous wavelength natural light. If the user wants the output image of the display unit to have greater color contrast and be easier to distinguish vascular tissue, the brightness of both can be adjusted to give the output light a special light with higher peak and trough contrast.

[0089] In this embodiment, the light source module 10 can provide continuous white light illumination with multiple characteristic peaks. Specifically, for example, when the first light source 11 is an LED light source with continuous spectral characteristics, both the first and second visible light are simultaneously activated to enhance blood vessels under white light imaging. The image acquired 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 superficial blood vessels in the blue response channel of the image sensor 21 is lower than that of non-vascular tissue, resulting in greater contrast compared to illumination with only the first visible light; the grayscale of superficial and middle blood vessels in the green response channel is lower than that of non-vascular tissue, resulting in greater contrast compared to illumination with only the first visible light; the grayscale of superficial, middle, and deep blood vessels in the red response channel is higher than that of non-vascular tissue, resulting in greater contrast compared to illumination with only the first visible light; after the three response channels are fused into a color image, the superficial, middle, and deep blood vessels will appear redder and easier to observe compared to illumination with only the first visible light. When the first light source 11 with continuous spectral characteristics is lit at 100% brightness and the second light source 12 is lit at 60% brightness, the relationship between the absorption coefficients of the first and second visible light, the blood oxygen protein spectrum, and the red-green-blue response spectral coefficients of the image sensor is shown in Figure 7.

[0090] For example, when the first light source 11 is an LED light source with discontinuous spectral characteristics, the brightness of the second light source 12 can be increased and the brightness of the first light source 11 can be decreased 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 with the spectrum described above is 0.5:1, the combined white illumination light has good color rendering properties, with a color temperature of approximately 4800K and a color rendering index of 86, which can meet the needs of white light imaging. Furthermore, it has obvious peak wavelengths at the blood vessel absorption peak wavelengths of 420nm and 540nm. The spectrum of the combined illumination light is shown in Figure 8.

[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 higher brightness ratio, resulting in an image closer to a normal white light image with good color reproduction; the second light source 12 has a higher brightness ratio, leading to greater contrast between blood vessels and other tissues in the image, making blood vessels 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 user selection. The image processing module 30 can analyze the acquired images and automatically adjust the brightness ratio of the first light source 11 and the second light source 12 based on the analysis results. For example, when a 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 features of the image in real time. Considering that blood vessels, especially capillaries, are very small in tissues, they belong to the high frequency part in the image, while the detailed structures of other tissues such as the skin and mucous membrane are not obvious and belong to the low frequency part in the image. Therefore, when the brightness contrast between high frequency features and low frequency features in the spatial frequency of the image is low, it means that the blood vessel 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 judge again whether the brightness contrast between high frequency features and low frequency features reaches the threshold.

[0092] Referring to Figure 9, this embodiment provides a control method for an endoscopic imaging system. Using 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 signal collected by the camera module 20;

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

[0096] In practical applications, when the endoscopic imaging system is in operation, after receiving the doctor's control command, 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. The target tissue reflects this illumination light, which is then captured by the camera module 20. After acquiring the reflected light, the camera module 20 responds through the three-color response channels (blue response channel, green response channel, and red response channel) of the image sensor 21 and generates three-color response signals (blue response signal B, green response signal G, and red response signal R). Then, the image processing module 30 performs specific preset mixing operations such as gain, attenuation, and inversion 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 acquiring the spectrum reflected by the target tissue have been described in detail in the above embodiments of the endoscopic imaging system, and will not be repeated here.

[0097] While the principles herein have been illustrated in various embodiments, numerous modifications to the structure, arrangement, proportions, elements, materials, and components, particularly suited to specific environmental and operational requirements, may be used without departing from the principles and scope of this disclosure. These modifications and other alterations or alterations will be included within the scope of this document.

[0098] The foregoing specific descriptions have been described with reference to various embodiments. However, those skilled in the art will recognize that various modifications and changes can be made without departing from the scope of this disclosure. Therefore, considerations for this disclosure are to be illustrative rather than restrictive, and all such modifications are to be included within its scope. Similarly, advantages, other advantages, and solutions to problems with respect to various embodiments have been described above. However, benefits, advantages, solutions to problems, and any elements that produce these, or make them more explicit, should not be construed as critical, essential, or necessary. The term “comprising” and any other variations thereof as used herein are non-exclusive inclusion, meaning that a process, method, article, or apparatus that includes a list of elements includes not only those elements but also other elements not expressly listed or not part of the process, method, system, article, or apparatus. Furthermore, the term “coupled” and any other variations thereof as used herein refer to physical connections, electrical connections, magnetic connections, optical connections, communication connections, functional connections, and / or any other connections.

[0099] Those skilled in the art will recognize that many changes can be made to the details of the above embodiments without departing from the basic principles of the invention. Therefore, the scope of the invention should be determined according to the following claims.

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 includes a first light source and a second light source. 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 with discontinuous spectral characteristics. The camera module includes an image sensor with red, green and blue three-color response channels. The image sensor is used to receive the reflected light formed after the target tissue is irradiated by visible light emitted by the light source module, thereby obtaining the 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 signals to obtain the corresponding image and output it.

2. The endoscopic imaging system as described in claim 1, characterized in that, The light source module is located at the tip of the endoscope body.

3. The endoscopic imaging system as described in 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; furthermore, the half-width at half maximum (WHM) of the first characteristic peak is less than 40nm, and the half-width at half maximum (WHM) of the second characteristic peak is less than 80nm.

4. The endoscopic imaging system as described in 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 600 nm-700 nm; and the full width at half maximum (FWHM) of the third characteristic peak is less than 120 nm.

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

6. The endoscopic imaging system as described in claim 5, characterized in that, The first light source is a white 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 spectral characteristics. The first visible light emitted by the LED light source with discontinuous spectral characteristics is a special spectral light wave composed of a mixture of blue light waves, cyan light waves, and orange light waves.

7. The endoscopic imaging system as described in claim 6, characterized in that, The first light source 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 400 nm-480 nm, the wavelength range of the fifth characteristic peak is 450 nm-510 nm, and the wavelength range of the sixth characteristic peak is 580 nm-630 nm; and, The full width at half maximum (FWHM) of the fourth characteristic peak is less than 30 nm, while the FWHMs of the fifth and sixth characteristic peaks are both greater than 40 nm.

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

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

10. The endoscopic imaging system as described in claim 3, characterized in that, The second light source is an LED light source composed of a violet semiconductor light-emitting chip and a green phosphor; The emission peak wavelength of the violet semiconductor light-emitting chip is in the wavelength range of 400nm-440nm and the half-width at half-maximum (WHM) is less than 30nm; the emission peak wavelength of the green phosphor is in the wavelength range of 520nm-550nm and the WHM is less than 70nm.

11. The endoscopic imaging system as described in claim 4, characterized in that, The second light source is composed of a violet semiconductor light-emitting chip, a green phosphor, and a red phosphor, forming an LED light source; The emission peak wavelength of the violet semiconductor light-emitting chip is in the wavelength range of 400nm-440nm and the half-width at half-maximum (WHM) is less than 30nm; the emission peak wavelength of the green phosphor is in the wavelength range of 520nm-550nm and the WHM is less than 70nm; the emission peak wavelength of the red phosphor is in the wavelength range of 600nm-680nm and the WHM is less than 110nm.

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

Images