WO2018094695A1

WO2018094695A1 - Endoscope system and control method therefor

Info

Publication number: WO2018094695A1
Application number: PCT/CN2016/107300
Authority: WO
Inventors: 李勇; 樊睿; 熊思思
Original assignee: 深圳迈瑞生物医疗电子股份有限公司
Priority date: 2016-11-25
Filing date: 2016-11-25
Publication date: 2018-05-31
Also published as: CN108601504A

Abstract

An endoscope system (100) using a semiconductor light source to perform illumination and using a grayscale sensor (113) to perform image collection. The semiconductor light source can overcome the disadvantages of an xenon lamp that the service life of the xenon lamp is short, the luminous flux of the xenon lamp cannot be regulated and the observatory light intensity for special light is weak. The grayscale sensor (113) can overcome the disadvantages of a color sensor that the resolution of the color sensor is low, the color sensor is easy to reach a limit and is easy to cause resolution reduction and energy loss. A light source device (2) formed by the semiconductor light source has the feature for regulating light energy, and can operate with the grayscale sensor (113) to compensate a response difference for light of different colors, and the cooperation between the semiconductor light source and the grayscale sensor (113) can improve image quality.

Description

Technical field

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

[0002]

BACKGROUND

[0004] In the medical field, endoscope-based diagnostics are increasingly used in the field of minimally invasive surgery. The inside of the living body can be observed by means of a medical endoscope. The endoscope is configured as a light source device that supplies illumination light to the endoscope, an insertion portion that can be inserted into the living body for observation of the tissue, and an image processor that processes the output image. In the observation of the living tissue using the endoscope, in addition to ordinary light observation using visible light (normal light) illumination, special light observation capable of observing an increase in blood vessels should be provided.

[0005] For neoplastic lesions, past conventional white light diagnosis was analyzed by contrasting differences between diseased and normal tissues. In recent years, special light imaging has been applied in tumor diagnosis. In the narrow-band imaging (NBl), the narrow-band blue or narrow-band green light that is strongly absorbed by the blood illuminates the tissue, which improves the contrast of the capillaries. In a normal tissue in which a living tissue is cancerous or the like, the state of the blood vessel is different from that of the normal tissue, and the blood vessel emphasis observation is considered to have applicability in the diagnosis of early cancer discovery. Therefore, how to configure the endoscope device to enable the endoscope device to achieve normal image observation and special light observation, and achieve good image acquisition is a technical problem that technicians in the field have been trying to solve.

[0006]

SUMMARY OF THE INVENTION

According to a first aspect of the present invention, an endoscope system capable of outputting a color image is provided, the system comprising a light source device, an insertion portion, and an imaging control portion. The light source device includes a semiconductor light source unit for distributing a plurality of monochromatic lights of different wavelength ranges. The front end of the insertion portion is provided with a gradation sensor for image acquisition, and the gradation sensor collects image signals under a plurality of monochromatic lights. The imaging control unit generates a plurality of monochrome images correspondingly based on the image signals acquired by the gradation sensors, and combines the monochrome images into a color image. According to a second aspect of the present invention, there is provided a control method of an endoscope system including a light source device, an insertion portion, and an imaging control portion, the light source device including a semiconductor light source, and the insertion portion including the image Grayscale sensor acquired. The control method of the endoscope system includes: a semiconductor light source alternately providing first monochromatic light and second monochromatic light having different wavelength ranges, the first monochromatic light and the second monochromatic light guiding insertion portion; the gradation sensor is Image acquisition is performed under the first monochromatic light and the second monochromatic light, respectively, and the first image signal and the second image signal are alternately generated; and the imaging control unit generates the first single according to the first image signal and the second image signal respectively The color image and the second monochrome image combine the first monochrome image and the second monochrome image into a color image.

[0010] According to a third aspect of the invention, an endoscope system comprising a normal light viewing mode and a special light viewing mode is provided. The system includes:

[0011] a light source control portion for controlling the first semiconductor light source portion to operate in the normal light observation mode, and controlling the second semiconductor light source to operate in the special light mode;

[0012] the first semiconductor light source portion is configured to provide a plurality of broadband light beams of different wavelength ranges;

[0013] the second semiconductor light source for providing narrowband light;

[0014] an endoscope including an insertion portion insertable into a living body, the front end of the insertion portion being provided with a gradation sensor for image acquisition;

[0015] an imaging control unit that generates a monochrome image according to an image signal acquired by the grayscale sensor in the special light observation mode, and generates a color image according to the image signal acquired by the grayscale sensor in the ordinary light observation mode

[0016]

BRIEF DESCRIPTION OF THE DRAWINGS

1 is a schematic view of an endoscope system according to a first embodiment of the present invention;

2 is a schematic structural view of the spectroscopic wheel of FIG. 1;

3 is a spectral response graph of a gray scale sensor; [0020] FIG.

4 is a schematic view of an endoscope system according to a second embodiment of the present invention;

[0022] FIG. 5a is a first configuration diagram of the inconsistent spectral response of the compensated gradation sensor in the present invention;

[0023] FIG. 5b is a second configuration diagram of the inconsistent spectral response of the compensated gradation sensor in the present invention;

6 is a flow chart of a method of controlling an endoscope system of the present invention. [0025]

DETAILED DESCRIPTION

[0027] The present invention will be further described in detail below in conjunction with the drawings and specific embodiments. It is to be understood that the description of the specific embodiments is intended to be illustrative of the invention, and no limitation of the invention. The term "proximal" and "distal" as used in the present invention refers to the near-end layout of the endoscope system relative to the operator during use, and also has no limiting meaning.

[0028] The present invention provides an endoscope system which, from the perspective of a light source device and an image collector, enables an endoscope system to output higher image quality, have higher image collection efficiency, and more Suitable for special light imaging in narrowband light. The light source device utilizes the illumination advantages of the semiconductor light source with adjustable light flux, and can compensate the response characteristics of the grayscale sensor of the system to different monochromatic lights, and improve the overall quality of the output image. The gradation sensor used can reduce energy loss, improve color resolution, and easily collect color components under various color lights, and the gradation sensor can cooperate with the illuminating design of the semiconductor light source unit under multiple monochromatic light beams. Exposure separately to improve the utilization of light energy.

[0029] The present invention may provide an endoscope system including an endoscope, a light source device, a host, and a display; in other optional configurations, the endoscope system may further include a device carrying function The trolley, the pneumoperitone machine that forms the pneumoperitoneum in a minimally invasive environment, the cleaning equipment for cleaning the endoscope, and the like. The endoscope system can introduce light of the light source device through an endoscope to a portion to be observed, such as a living body, and an acquisition device of the endoscope performs image acquisition, and the host generates an image of the to-be-observed portion according to the collected signal, and the image finally Can be displayed by the display.

[0030] The light-emitting component of the light source device is a semiconductor light source that provides wide-band light or narrow-band light (also referred to as narrow-band light). The wide-band light corresponds to ordinary light illumination, so that the light source device can be used for ordinary light observation, and the wide band can refer to a wavelength bandwidth of several tens of nanometers, but is not limited thereto; the narrow-band light corresponds to special light illumination, so that the light source device can be used for special For light observation, a narrow band generally refers to a wavelength band of a few nanometers, but is not limited thereto. The semiconductor light source has a long service life of about 20,000 hours, which avoids the need to replace the light source unit during the use of the endoscope system. The luminous flux of the semiconductor light source can be adjusted so that the unit can provide a plurality of monochromatic lights, which can output different luminous fluxes according to system requirements, especially in response to the response characteristics of the endoscope acquisition device.

[0031] The light source device may include a first semiconductor light source portion for providing general light illumination, the first semiconductor The light source portion may include a first semiconductor light source and a beam splitter, and the light generated by the first semiconductor light source obtains a plurality of wide-band light through the optical splitter, and each of the wide-band light has a different wavelength range, so that the first semiconductor light source portion is illuminated, The speculum system is capable of color imaging. In the specific embodiments below, the first semiconductor light source may generate excitation light to further excite the fluorescent material to produce monochromatic light; or may be a plurality of light emitting units that directly generate monochromatic light of different wavelength ranges. The spectroscope can be a fluorescent color wheel partially or entirely provided with different fluorescent materials. The fluorescent material can be coated on the surface of the fluorescent color wheel or embedded inside the fluorescent color wheel. The optical splitter can also be an optical component that can perform different optical propagations of light in different wavelength ranges.

[0032] The endoscope of the system includes an insertion portion and a camera portion, and the insertion portion is a part of the scope body that can be inserted into the living body by an operator. The insertion portion has on the one hand an introduction portion for directing light generated by the light source device to the portion to be observed (and the light exiting optical system 114), and on the other hand, an object side optical system and an image pickup device for image acquisition. The lead-in portion can be a light guiding fiber, and the light source device is therefore equipped with an optical system design for focusing the light to focus the generated light into the fiber. The image acquisition device is a grayscale sensor. After receiving the light reflected from the portion to be observed, the grayscale sensor generates an image signal in the form of an electrical signal by photoelectric conversion. The image signal is then transmitted to the host to form a captured image. The gradation sensor has a higher resolution, and the response range of different monochromatic lights is dynamically adjustable, and the image saturation phenomenon can be avoided as much as possible. All the pixels of the gradation sensor can respond under a single light illumination. High energy efficiency. The combination of the gray scale sensor and the semiconductor light source unit in the endoscope system can cooperate to improve the light energy utilization rate and output image quality of the endoscope system as a whole.

[0033] The host of the system may include an imaging control unit, a system control unit, an image processor, etc., and the above components may be integrated or may be discrete components in the host. The imaging control section controls the frame rate of the gradation sensor and the exposure time, and can receive an image signal output by the gradation sensor, thereby generating an image. The light source device of the system emits monochromatic light, and the imaging control unit receives the image signal and outputs a monochrome image correspondingly, and then combines the respective monochrome images into a color image. The imaging control unit transmits the color image to the system control unit, and then the image processor performs post-processing on the formed color image, such as image detail enhancement, image denoising, etc., and finally displays the processed image on the display. In some embodiments, the imaging control unit may also generate a corresponding monochrome image based on the image signal acquired under the illumination of the monochromatic light, and then output the display. [0034] The above endoscope system uses a semiconductor light source for illumination, and adopts a grayscale sensor for image acquisition, which can overcome the shortcomings of short life of the light source, unadjustable luminous flux, and special light and light, and can overcome the low resolution of the image sensor. The disadvantages of easy saturation, special light observation resolution and energy loss, the synergy between the two enables the endoscope system to efficiently obtain high quality images.

1 shows an endoscope system 100 of a first embodiment of the present invention. The endoscope system 100 includes an endoscope 1, a light source device 2, a main unit 3, and a display 4; wherein the light source device 2 can utilize the semiconductor light source unit 21 to provide a plurality of monochromatic lights of different wavelength ranges for illumination; The endoscope 1 may include a gradation sensor 113 disposed at the front end of the insertion portion 11 thereof for image acquisition; the host computer 3 may include an imaging control portion 31 for controlling the exposure period of the gradation sensor 113 under each monochromatic light And used to generate images. The endoscope system 100 can introduce the monochromatic light generated by the light source device 2 into the to-be-observed portion through the endoscope 1, and the gradation sensor 113 of the endoscope 1 performs image collection under the illumination of the monochromatic light. The image signal is generated, and the imaging control unit 31 of the host computer 3 divides the acquired image signals by the gradation sensor 113 to generate corresponding monochrome light images, and then combines the monochromatic light images into a color image reflecting the portion to be observed. The endoscope system 100 can overcome the shortcomings of short-lived light source and non-adjustable light flux at the light source end, and overcome the disadvantages of low resolution, easy saturation, high energy loss, and use of a semiconductor light source. The system constructed by unit 2 1 and gradation sensor 113 has higher light energy utilization, more flexible system adjustment and better image quality.

[0036] The light source device 2 can perform ordinary light illumination based on wide-band light. The semiconductor light source unit 21 of the light source device 2 can separately provide a plurality of wide-band monochromatic lights of different wavelength ranges for the ordinary light observation mode, and the endoscope system 100 generates a color image under ordinary light illumination. For example, a plurality of monochromatic lights of different wavelength ranges can be perceived as different colors of light; for example, a plurality of monochromatic lights of different wavelength ranges can be red, green, blue, yellow, and the like. The semiconductor light source unit 21 is subsequently described as providing light of different colors, which is only a specific example. In the case of ordinary light illumination using monochromatic light, the gradation sensor 113 can utilize all of its pixel points to make a full pixel point response to monochromatic light of different colors, with high resolution and energy utilization, thereby improving image quality. .

[0037] The light source device 2 can perform special light illumination based on narrow-band light. On the basis of the semiconductor light source unit 21, the light source device 2 may further include a narrow-band light source 22 for generating narrow-band light for a special light observation mode, and the endoscope system 100 generates a monochrome having a blood vessel enhancement effect under special light illumination. image. Narrowband light source 22 For a laser, an LED light source or a laser LED, for example, the narrow-band light source 22 may be a laser emitting a narrow-band blue laser having a peak wavelength of at least one value of blue light in the range of 390 nm to 460 nm. The narrow-band light source 22 and the semiconductor light source unit 21 operate in a distributed manner to provide narrow-band light and ordinary light. The endoscope system 200 equipped with the light source device 2 can perform ordinary light observation or special light observation. In the case of special light illumination using narrow-band light, the grayscale sensor 113 can also utilize all of its pixels to make a full-pixel point response to narrow-band light, with high resolution and energy utilization, further improving the image quality under special light observation.

[0038] The light source device 2 may further include a light source control section 23 and a dichroic mirror 24. The light source control section 23 controls the narrow-band light source 22 and the semiconductor light source unit 21 to operate under the control of the host computer 3; that is, the narrow-band light source 22 is turned on, and the semiconductor light source unit 21 is turned off, and vice versa. The dichroic mirror 24 is disposed on a plurality of monochromatic light and narrow-band light transmission optical paths, and the optical paths of the plurality of monochromatic lights and the narrow-band optical paths are merged into the same optical path via the dichroic mirror 24. For example, as shown in Fig. 1, a plurality of monochromatic lights can be transmitted through the dichroic mirror 24, and the narrowband light can be reflected by the dichroic mirror 24 such that the optical paths of the two are combined into the same optical path; and vice versa. On the optical path behind the dichroic mirror 24, the narrow-band light and the plurality of monochromatic lights are distributed in the direction of the endoscope 1 along the same optical path synthesized.

[0039] In some examples, the light source device 2 may further include a coupling mirror 25 disposed between the dichroic mirror 24 and the light source introduction port of the endoscope 1. The coupling mirror 25 allows the light transmitted from the dichroic mirror 24 to be focused, thereby being better introduced into the endoscope 1 to minimize light loss and improve the overall illumination quality of the system. The optical path synthesis of the dichroic mirror 24 and the focusing action of the coupling mirror 25 both better introduce light into the endoscope 1 (e.g., within the light guiding fiber). At the same time, the use of the dichroic mirror 24 makes the overall structure of the light source device 2 more compact and the light propagation path shorter.

[0040] The imaging control unit 31 controls the exposure time of the gradation sensor 113 according to the light emission of the respective ray ray by the light source device 2, and causes the gradation sensor 113 to emit light under the illumination of each ray and the ray of each ray. Same or in the same proportion. The gradation sensor 113 can provide each ray 吋 in the light source device, synchronize the exposure under each ray, and separately collect the corresponding image signals.

[0041] For example, as shown in FIG. 1, the semiconductor light source unit 21 of the light source device 2 may include a first semiconductor light source 211 and a first splitter wheel 212. The first semiconductor light source 211 may be a laser that emits a blue laser having a wavelength in the range of 400 nm to 480 nm, which is the excitation light of the semiconductor light source unit 21. The first dichroic wheel 212 includes at least two (ie, a plurality of) spectroscopic regions, and some or all of the spectroscopic regions are coated with phosphors, The light splitting region provides a plurality of monochromatic lights of different wavelength ranges under the irradiation of the excitation light, wherein the spectroscopic region coated with the phosphor is excited to emit a monochromatic light whose wavelength is converted, and is not coated with the phosphor The splitting region is illuminated by the excitation light, and directly transmits the excitation light to emit excitation light whose wavelength is not converted. Wherein, the plurality of splitting lights of the first dichroic wheel 212 are arranged on the optical path of the excitation light, and the splitting area of the first dichroic wheel 212 currently located on the optical path provides monochromatic light of a corresponding wavelength range. The first dichroic wheel 212 can be a single rotating wheel as shown in FIG. 1. The plurality of dichroic zones are a plurality of zones divided on the wheel, the single rotating wheel is rotated, and the plurality of zones are rotated to the light of the excitation light. On the road, it is illuminated by the excitation light in turn. The first dichroic wheel 2 12 may also be a wheel set including a plurality of rotating wheels, and the plurality of dichroic zones are respectively located on the plurality of rotating wheels. During the rotation of the plurality of rotating wheels, the plurality of regions are bifurcated to the excitation light. The light path is sequentially illuminated by the excitation light.

Referring to FIGS. 1 and 2, the first beam splitter 212 may be a single fluorescent color wheel having three light splitting regions 212a, 212b. 212c defined thereon. The fluorescent color wheel is rotated after the light source device 2 is powered on, so that the three light splitting regions 212a, 212b. 212c are alternately located on the optical path of the excitation light, thereby providing a single corresponding to the three light splitting regions 21 2a, 212b. 212c, respectively. Shade. The spectroscopic region 212a is coated with a red phosphor, and the blue laser light emitted from the first semiconductor light source 211 is irradiated to the red phosphor on the spectroscopic region 212a, and then converted into monochromatic light in the form of red fluorescence. The spectroscopic region 212b is coated with a green phosphor, and the blue laser light emitted from the first semiconductor light source 211 is irradiated to the green phosphor on the spectroscopic region 212b, and then converted into monochromatic light in the form of green fluorescence. The spectroscopic region 212c is not coated with phosphor, and the blue laser light emitted from the first semiconductor light source 211 is irradiated onto the region 212c without wavelength conversion, and is still emitted by the blue laser light after transmission. In the example of Figure 1-2, the fluorescent color wheel rotates to provide three kinds of monochromatic light of red (R), green (G) and blue (B), and the gray sensor 113 is illuminated in RGB. Next, respectively receiving red, green, and blue light reflected from the to-be-observed portion to generate a corresponding image signal, and the imaging controller 31 can respectively obtain a red light image, a green light image, and a blue light image, and then the R GB three-color image. Synthesized into a pair of color images. It can be understood that the three spectroscopic regions are only specific examples of the plurality of spectroscopic regions, and the fluorescent color wheel can also be divided into two, four, five or more spectroscopic regions. The above-mentioned definitions of "red" and "green" for the phosphor mean that the phosphor emits red light and green light under the excitation light, and is not used to limit the color of the phosphor itself. Red phosphors and green phosphors can be called red phosphors and green phosphors, respectively.

[0043] In some embodiments, the light source device 2 may further include a second splitter wheel 213, and the second splitter wheel 213 may also be For a single rotating wheel or a wheel set including a plurality of rotating wheels, the second beam splitting wheel 213 may also include at least two beams of light of a plurality of monochromatic lights of different wavelength ranges generated by excitation light from the first semiconductor light source 211. Area. For the sake of distinction, the light splitting area of the first light splitting wheel 212 may be referred to as a first light splitting area, and the light splitting area of the second light splitting wheel 213 may be referred to as a second light splitting area.

[0044] For example, the first dichroic wheel 212 and the second dichroic wheel 213 have the same spectroscopic area configuration (number, phosphor type, area size, etc.), and the second dichroic wheel 213 is used as a spare part of the first dichroic wheel 212, When the first dichroic wheel 212 is aged or has failed, the second dichroic wheel 213 is activated to ensure proper operation of the endoscope system 100.

[0045] For example, the first splitter wheel 212 and the second splitter wheel 213 have different splitting zone configurations, such as number, phosphor type, and/or area size, such that after excitation light illumination, the two splitter wheels can provide different Monochrome light output, which ultimately changes the imaged image. In this case, the endoscope system 100 can have a first working mode and a second working mode under normal light observation. The first dichroic wheel 212 only accesses the optical path of the excitation light in the first working mode, and the second dichroic wheel 213 only In the second working mode, the optical path of the excitation light is connected; the two form a bifurcation working mode in different working modes. In the first working mode and the second working mode, the light source device provides different combinations of monochromatic light illumination, so that the color images finally obtained in the two working modes have different color rendering effects. The splitter wheel can be configured according to different needs to form different splitting zones to achieve corresponding lighting effects under different imaging requirements.

[0046] For example, the first beam splitter has three light splitting regions, respectively providing blue light, red light, and green light, and the light exits of the three color lights are the same, and the second light splitting wheel has four light splitting regions, respectively providing blue light. , red light, green light and yellow light, and the red light exits longer than the light of other colors, the yellow light is a monochromatic light provided by the second splitter wheel, and the wavelength range is different from the three provided by the first splitter wheel. Monochromatic light. Thereafter, the first dichroic wheel provides three primary color imaging in the first working mode, and the second dichroic wheel further provides a color image integrating the yellow light image in the second working mode, and finally changes the color rendering effect of the obtained color image. .

[0047] In addition, although the gradation sensor 113 can perform full pixel point response for monochromatic light of different wavelength ranges, the gradation sensor 113 has different response rates to different monochromatic lights. As shown in FIG. 3, FIG. 3 is a spectral response curve of the gamma sensor 113, particularly a gamma sensor or a CMOS sensor, for red, green, and blue light. The gamma sensor 113 has a stronger response to green light and a weaker response to red and blue light. . In this embodiment of the invention, the color image is a red light image, a green light image, and a blue light image obtained by separately collecting red, green, and blue light from the grayscale sensor 113; when the gray light sensor outputs a red light image, The green light image and the blue light image have the same amplitude, and the final synthesized color image has the best quality. In view of the inconsistent response of the gradation sensor 113 to the RGB three-color light, increasing the energy of the blue and red light received by the gradation sensor 113 and/or reducing the energy of the green light, the gamma sensor 113 can be compensated for the inconsistency in response to the RGB three-color light. . Therefore, according to the inconsistency of the response of the gradation sensor 113 to different monochromatic lights, the present invention proposes to provide a plurality of monochromatic lights of different energies by the semiconductor light source, so that the plurality of monochromatic lights received by the gradation sensor 113 have Different energies, this energy difference can compensate for the difference in response of the grayscale sensor 113 to different monochromatic lights.

[0048] For example, the plurality of light splitting regions of the first light splitting wheel 212 may have different size distribution regions, so that the excitation light respectively illuminates the plurality of light splitting regions with different lengths, so that the plurality of light splitting regions of different wavelength ranges are separated. Differently, in the case where the first semiconductor light source 211 has a constant luminous flux, the plurality of spectral divisions provide a plurality of monochromatic lights of different energy sizes. The plurality of monochromatic light exit pupils of different wavelength ranges are different, and the exposure time of the gray scale sensor 1 13 responding to the plurality of monochromatic lights is also adjusted correspondingly. Wherein, the distribution area of the spectroscopic area corresponding to the weaker light response of the gray scale sensor may be increased, and/or the distribution area of the spectroscopic area corresponding to the light having a stronger response of the gray scale sensor may be reduced, thereby increasing the gray scale sensor The received response to the energy of the weaker light, and/or the energy of the responsive gray light received by the grayscale sensor, compensates for the difference in response of the grayscale sensor 113 to different monochromatic light. This compensation method can be as shown in Figure 5b.

Specifically, in combination with the RGB partitioning mode of FIG. 2, the area of the spectroscopic area 212b (i.e., the green light area) can be reduced, and the areas of the spectroscopic areas 212a and 212c (i.e., the red light area and the blue light area) can be increased. When the endoscope system 10 0 is operated, the exposure time of the gradation sensor 113 is synchronously adjusted, so that the exposure period of the gradation sensor 113 to the spectroscopic area 212b is shortened, and the exposure periods of the spectroscopic areas 212a and 212c are lengthened. In this configuration, the green light energy received by the gray scale sensor 113 is reduced, and the red and blue light energies are increased, which compensates for the inconsistency of the gray scale sensor 113 for strong response to green light and weak response to red light and blue light.

[0050] The above-mentioned distribution area may refer to the total area of the sector-shaped area occupied by each splitting section on the spectroscopic wheel, or may refer to the angle value occupied by the spectroscopic area on the spectroscopic wheel, or may refer to the phosphor irradiated by the excitation light. The coated area on the splitter wheel, etc. For a single color zone, the angle refers to the direction of travel of the excitation light in the beam splitting zone, relative to the center of rotation of the first beam splitter 212. Different distributions of the above plurality of spectroscopic regions The area can be determined as follows: Pre-calculating the corresponding exposure time required for the gray level sensor to receive different monochromatic light whose energy meets a certain ratio, and calculating the respective angular sizes of the different monochromatic lights on the splitting wheel according to the exposure time/ area size. The endoscope system adopts the spectroscopic rim designed by the structure, and can be illuminated by the semiconductor light source unit at a desired ratio of the pupils according to the relationship between the angle size/area size and the exposure pupil, and the gradation sensor is used in the Exposure is performed separately under the desired inter-turn ratio, and different monochromatic lights of the energy ratio are received, which compensates to some extent the inconsistency of the gray-scale sensor response to different monochromatic lights.

[0051] The closer the amplitudes of the respective monochrome images are, the better the quality of the synthesized color images is. In some examples, the respective distribution regions of the plurality of spectroscopic regions are designed according to the correspondence between the exposure pupils and the size of the distribution regions: a plurality of monochromatic lights of different energies provided by the semiconductor light source unit 21, in the pair of grayscale sensors 113 Under different responses of a plurality of monochromatic lights, the amplitude of the image signals acquired by the gradation sensor 113 under each monochromatic light is the same, and the resulting monochromatic image has the same amplitude. In some examples, the size of the distribution area of the plurality of light splitting regions is adjusted such that the amplitude of the image signals acquired by the grayscale sensors in each monochromatic light is similar or conforms to a specific ratio, thereby improving the amplitude difference of each monochrome image to a certain extent, thereby improving Image Quality.

For example, the endoscope system 100 of the present invention can adjust the luminous flux of the emitted excitation light by the first semiconductor light source 211 to illuminate different splitting regions 第一 of the first dichroic wheel 212 to provide illumination under excitation light. The luminous flux of the different monochromatic lights satisfies the desired ratio, thereby compensating for the difference in response of the gamma sensor 113 to different monochromatic lights. The light source control unit 23 is configured to control the first semiconductor light source 211 to split the excitation light of different luminous fluxes for different light splitting regions of the first light splitting wheel 212, so that the plurality of light splitting regions are illuminated by the excitation light of different luminous fluxes. Multiple monochromatic lights of different luminous flux sizes are provided. Wherein, the light flux of the first semiconductor light source 211 corresponding to the light splitting region corresponding to the light having a weak response of the illumination gradation sensor may be increased, and/or the light splitting region corresponding to the light having a stronger response of the illumination gradation sensor may be reduced. The luminous flux of the semiconductor light source 211, such that the energy of the weaker light received by the grayscale sensor is increased, and/or the energy of the stronger light received by the grayscale sensor is reduced, so that the grayscale sensor 113 receives different orders. The difference in energy of the chromatic light can compensate for the difference in response of the gradation sensor 113 to different monochromatic lights. As shown in the sequence diagram of the luminous flux of the first semiconductor light source 2 11 in Fig. 5a, the first semiconductor light source 211 has different luminous fluxes at different turns.

[0053] The different luminous fluxes for illuminating different spectroscopic regions may be determined as follows: under the condition that the distribution regions of different spectroscopic regions have the same size (ie, under the same conditions of exposure of the gradation sensor under each monochromatic light), Calculating the luminous flux of each monochromatic light required for the grayscale sensor to receive a certain proportion of different monochromatic light, and then calculating the illumination to different spectroscopic regions to provide the desired monochromatic pupil excitation light according to the excitation efficiency of the different phosphors. The luminous flux size. The endoscope system prestores the calculated information of the luminous flux size, and establishes a correspondence relationship between each monochromatic light (or a spectroscopic region providing each monochromatic light) and the luminous flux size; during operation, the semiconductor light source unit can be issued The desired amount of excitation light of the luminous flux illuminates the corresponding spectroscopic region, thereby changing the luminous flux of the plurality of monochromatic lights, so that the gradation sensor receives the different monochromatic light in proportion to the energy, and compensates the gradation sensor to a certain extent. Inconsistency in monochromatic light response.

[0054] Specifically, in combination with the RGB partitioning mode of FIG. 2, the red, green, and blue light-splitting areas on the fluorescent color wheel have the same size distribution area (the same time between illuminations), and the semiconductor light source unit 21 has corresponding The same red, green, and blue light are shining. Thereby, the light flux of the red light splitting region and the blue light splitting region is increased by the first semiconductor light source 211, and/or the light flux of the green light splitting region of the first semiconductor light source 211 is reduced, so that the red light and green emitted by the semiconductor light source unit 21 are caused. Light and blue light will have different luminous flux sizes, and in the case of the same illumination, the gray light sensor 113 receives a total of different amounts of red, green, and blue light energy. The fluorescent color wheel rotates to cause the first semiconductor light source 211 to sequentially illuminate the red splitting region, the green splitting region and the blue splitting region 吋, and the first semiconductor light source 211 synchronously outputs the adjusted excitation light corresponding to the luminous flux, and the fluorescent color wheel sequentially provides the luminous flux adjusted red. Light, green, blue, and grayscale sensors 113 are simultaneously exposed to the image, resulting in an image with improved image quality.

[0055] Further, as shown in FIG. 1, the light source device of the endoscope system further includes a detecting device 27, which can detect the spectroscopic region on the optical path of the excitation light, thereby determining that it is the first dichroic wheel 212. Which of the splitting regions is located on the optical path of the excitation light, and an indication signal indicating the detected spectroscopic region is generated based on the detection result. The system control unit 32 of the host computer 3 receives the instruction signal from the detecting device 27, and determines the magnitude of the luminous flux to be output by the first semiconductor light source 211 based on the instruction signal, and outputs the information of the luminous flux magnitude to the light source control unit 23, and the light source control unit. 23 controls the first semiconductor light source 211 to output excitation light of a magnitude of the luminous flux. On the other hand, the system control unit 32 determines the color of the monochromatic light to be output by the first semiconductor light source 211 based on the instruction signal, and notifies the imaging control unit 31 of the color information, and the imaging control unit 31 controls the synchronization of the gradation sensor 113 accordingly. The exposure is exposed during the day, and a monochrome image of the corresponding color is obtained.

[0056] In some examples, the detecting device includes a photodetector and a marker disposed on the spectroscopic wheel. The photodetector determines which spectroscopic region is currently detected based on the reflected light received from the marker. Photodetection The detector can be an infrared photodetector. The photodetector may include a photoelectric pair tube formed by the light emitting portion and the light receiving portion. After the light emitted from the light emitting portion to the marker is reflected, the reflected light is received by the light receiving portion to determine the intensity of the light. The mark body on the splitter wheel may include a first mark body having a high reflectance and a low absorptivity, and the generated reflected light is strong, and the photodetector correspondingly generates a high level signal. The mark body on the splitter wheel may include a second mark body having a low reflectance and a high absorptance, and the generated reflected light is weak, and the photodetector correspondingly generates a low level signal. According to the intensity of the reflected light, the photodetector can determine which combination of markers or markers are currently detected, thereby determining which detected based on the correspondence between the pre-established marker (or combination of markers) and the spectroscopic region. A splitting zone, according to which an indication signal corresponding to the splitting zone is generated.

[0057] For example, the manner in which the marker arrays are combined is used to distinguish different light splitting regions. The endoscope system 100 can thus be provided with an arrangement 1 : a first marker and a second marker, an arrangement 2: a second marker and a first marker; and an arrangement 3: a second marker and a second marker. In this arrangement, the photodetector will receive the combination of strong & weak, weak & strong and weak & weak reflected light, thereby distinguishing the splitting regions corresponding to each combination.

[0058] Each of the marker bodies may be disposed on the wheel body of the spectroscopic wheel, in particular at a junction between two of the beam splitting regions. Each of the markers may also be disposed on the rotating shaft of the spectroscopic wheel, and the setting position preferably corresponds to the boundary between the two of the spectroscopic regions. In order to prevent the marking body from being broken or broken by the excitation light, the position of the marking body on the wheel body does not fall into the optical path of the excitation light.

[0059] In some examples, the endoscope system 100 has a preset luminous flux emission sequence of the first semiconductor light source 211.

(RGB order) and the rotation order of the first dichroic wheel 212, the emission length of the excitation light of each luminous flux is the same as the emission pupil corresponding to the spectroscopic area on the first dichroic wheel 212, for example, the luminous flux sequence shown in Fig. 5a The preset exposure time of each of the monochromatic lights by the gradation sensor 113 is also the same as the output pupil corresponding to the spectroscopic area on the first dichroic wheel 212. The detecting means does not need to actually detect the respective splitting regions located on the path of the excitation light, but only the marker capable of indicating the red spectroscopic region 212a can be provided, thereby detecting only the red spectroscopic region. The detecting device outputs an indication signal 吋 indicating that the red spectroscopic region 212a will be illuminated, and then the first semiconductor light source 211 can emit light in accordance with a preset luminous flux, and sequentially illuminate the red spectroscopic region 212a, the green spectroscopic region 212b, and the blue spectroscopic region 212c. The gradation sensor is exposed separately according to each preset exposure time.

[0060] For another example, the endoscope system can control the luminous flux of the excitation light that illuminates different splitting regions, and can also use the splitter wheels with different sizes of the distribution regions of the splitting regions, and the two can jointly adjust the difference emitted by the semiconductor light source unit. The energy of monochromatic light. The above design idea of the distribution area of the spectroscopic area of the first spectroscopic wheel 212 The design idea of the luminous flux of the first semiconductor light source 211 that illuminates the first dichroic wheel 212 is equally applicable to the second dichroic wheel 213.

[0061] The semiconductor light source unit 21 can separately emit monochromatic light of different wavelength ranges for illumination, wherein the luminous flux of the monochromatic light in different wavelength ranges can be adjusted to ensure that the energy of the monochromatic light in different wavelength ranges meets the desired ratio. In order to compensate the inconsistency of the gray-scale sensor for the monochromatic light of different wavelengths, and improve the image quality of the synthesized color image; or the illumination time of the monochromatic light of different wavelength ranges can be preset to satisfy the desired ratio, thereby compensating for the gray The sensitivity of the sensor to the monochromatic light in different wavelength ranges improves the image quality of the synthesized color image.

The above-described semiconductor light source unit 21 can generate monochromatic light of different wavelength ranges by wavelength conversion. The illuminating light is irradiated to a specific spectroscopic area on the spectroscopic wheel, that is, a specific monochromatic illumination light is generated by corresponding wavelength conversion, and light of other unnecessary wavelength ranges is not generated, energy waste is not caused, and system heating can be improved and reduced.

[0063] FIG. 4 illustrates an endoscope system 200 in accordance with another embodiment of the present invention. The endoscope system 200 includes an endoscope 1 , a light source device 2 , a main body 3 , and a display 4 , wherein the endoscope system 200 can introduce light generated by the light source device 2 through the endoscope 1 to a portion to be observed, the endoscope The gradation sensor 113 of 1 performs image acquisition under light illumination to generate an image signal, and the imaging control unit 31 of the host 3 uses the image signal acquired by the gradation sensor 113 to generate an image reflecting the portion to be observed.

[0064] The light source device 2 can perform ordinary light illumination based on wide-band light, and can also perform special light illumination based on narrow-band light. The light source device 2 may include a semiconductor light source unit 28 that provides a plurality of wide-band monochromatic light of different wavelength ranges for ordinary light illumination, and may also include a narrow-band light source 22 for generating narrow-band light for special light illumination. Regardless of the use of wide-band light for ordinary light illumination or narrow-band light for special light illumination, the grayscale sensor 113 can utilize all of its pixels to make a full pixel point response for different light, with high resolution and energy utilization. Improve image quality.

[0065] In the endoscope system 200, the semiconductor light source unit 28 includes a plurality of semiconductor light sources respectively generating a plurality of different wavelength ranges of monochromatic light, such as a second semiconductor light source and a third semiconductor light source, wherein the second semiconductor light source is used The first monochromatic light is generated in a first wavelength range, and the third semiconductor light source is used to generate a second monochromatic light in the second wavelength range, the first monochromatic light and the second monochromatic light having different wavelength ranges. The second semiconductor light source and the third semiconductor light source are bifurcated, thereby causing the semiconductor light source unit 28 to emit different wavelengths A range of monochromatic lights.

[0066] Referring specifically to FIG. 4, the semiconductor light source unit 28 may be a three-color semiconductor light source unit, wherein the plurality of semiconductor light sources include a red LED, a green LED, and a blue LED, and the three LEDs are sequentially lit, and the red light and the green light are distributed respectively. The light and blue light, the grayscale sensor 113 sequentially acquires the red light image signal, the green light image signal and the blue light image signal in synchronization, and the imaging controller 31 respectively generates a red light image, a green light image and a blue light image, and synthesizes these monochrome images. Get a color image.

[0067] The light source device 2 may further include a light source control section 23 and an X-type dichroic mirror 26. The light source control section 23 controls the second semiconductor light source and the third semiconductor light source inside the semiconductor light source unit 28 to perform branching operation to thereby generate monochromatic light. The X-type dichroic mirror 26 is disposed on the optical paths of the first monochromatic light and the second monochromatic light, wherein the first monochromatic light is transmitted through the X-type dichroic mirror 26, and the second monochromatic light is transmitted through the X-shaped dichroic After being reflected by the color mirror 26, it is branched in the direction of the insertion portion of the endoscope 1 along the same optical path. The X-type dichroic mirror 26 allows for a more rational spatial layout of the plurality of semiconductor light sources, and also allows the emitted light to be more easily focused to the introduction interface of the endoscope 1.

The light source control unit 23 also controls the narrow-band light source 22 and the semiconductor light source unit 28 to operate under the control of the host computer 3; that is, the narrow-band light source 22 is turned on, and the semiconductor light source unit 28 is turned off, and vice versa. The light source device 2 may further include a dichroic mirror 24 disposed on a plurality of monochromatic light and narrow-band light transmission optical paths, and a plurality of monochromatic light paths and narrow-band light paths passing through the dichroic mirror After 24, it is synthesized into the same optical path. As shown in Fig. 4, a plurality of monochromatic lights can be transmitted through the dichroic mirror 24, and the narrowband light can be reflected by the dichroic mirror 24 so that the optical paths of the two are combined into the same optical path. On the optical path behind the dichroic mirror 24, the narrowband light and the plurality of monochromatic lights are distributed along the same optical path synthesized in the direction of the endoscope 1.

[0069] In some examples, the light source device 2 may further include a coupling mirror 25 disposed between the dichroic mirror 24 and the light source introduction port of the endoscope 1. The coupling mirror 25 allows the light transmitted from the dichroic mirror 24 to be focused, thereby being better introduced into the endoscope 1 to minimize light loss and improve the overall illumination quality of the system. The optical path synthesis of the dichroic mirror 24 and the X-type dichroic mirror 26, as well as the focusing action of the coupling mirror 25, can better introduce light into the endoscope 1 (e.g., within the light guiding fiber).

[0070] To compensate for the responsiveness of the gamma sensor to different monochromatic lights, the endoscope system 200 of this embodiment can control the luminous flux of each semiconductor light source, and/or control the luminous flux of each semiconductor light source, respectively. The monochromatic light that is irradiated to different wavelength ranges of the object to be observed has a desired ratio of energy, so that the energy of the different monochromatic light received by the gradation sensor satisfies a desired ratio. [0071] Specifically, the light source control unit 23 can distinguish the illuminating length of the second semiconductor light source from the illuminating length of the third semiconductor light source, thereby adjusting the light exit pupil of the different monochromatic light, so that the light output of each monochromatic light 吋Meet the expected ratio. As described above, the exposure time of the gradation sensor 113 coincides with the exit pupil of each monochromatic light, so that the luminous fluxes of the second semiconductor light source and the third semiconductor light source are not changed, the first monochromatic light and the second monochrome The energy of the light will satisfy the desired ratio, and the energy received by the gradation sensor 113 for each monochromatic light also satisfies the desired ratio, thereby compensating for the difference in response of the gradation sensor 113 to the first monochromatic light and the second monochromatic light.

[0072] Specifically, the light source control unit 23 can control the luminous fluxes of the second semiconductor light source and the third semiconductor light source such that the luminous flux satisfies a desired ratio, so that the monochromatic light energy received by the gradation sensor 113 also satisfies a desired ratio to compensate The difference in response of the grayscale sensor 113 to different monochromatic lights. For example, when the gradation sensor responds to the first monochromatic light more strongly than the response to the second monochromatic light, the light source control portion 23 increases the luminous flux of the second monochromatic light, and/or lowers the first monochromatic light. The luminous flux is such that the energy of the second monochromatic light received by the gradation sensor is greater than the energy of the first monochromatic light, thereby compensating for the difference in response of the gradation sensor to the two.

[0073] The semiconductor light source of each of the above endoscope systems may be a laser light source, an LED light source or a laser diode; and a laser diode or a laser light source is preferably used for the endoscope system. The gradation sensor of each of the above endoscope systems may be a CCD sensor or a CMOS sensor.

[0074] Each of the above endoscope systems employs a gradation sensor with higher image resolution and energy utilization due to its full pixel point response. Especially compared to color sensors, the image resolution of grayscale sensors is four times that of color sensors. Especially under special light illumination, the illumination light is narrow-band blue light. The gray-scale sensor can receive narrow-band blue light with all pixel points, high resolution and no energy waste, which can improve the image quality under narrow-band illumination. Each of the above endoscope systems uses a semiconductor light source with a gray scale sensor, and can flexibly adjust the light source output according to the response characteristics of the gray scale sensor, and the two are combined to further improve the image quality. Each of the above endoscope systems uses a gray scale sensor to overcome the problem of stray light interference from the color sensor. The gray scale sensor of the present invention collects image signals under different monochromatic light, and the interference of the invalid spectral stray light has been avoided from the illumination. However, color filter filters have limited filtering power, and there is always no ineffective stray light that is not completely filtered out.

[0075] In the above endoscope system, in order to avoid the coloring phenomenon, the luminous flux of the semiconductor light source can be improved as a whole, the exposure time of the gradation sensor can be reduced, and the object to be observed in the movement can be reduced on the image collected by the bifurcation. Misplacement and inability to coincide. 6, the present invention further provides a control method of an endoscope system, the endoscope system may include a light source device, an insertion portion, and an imaging control portion, the light source device includes a semiconductor light source, and the insertion portion includes an image Grayscale sensor acquired. The control method includes: a semiconductor light source alternately providing first monochromatic light and second monochromatic light having different wavelength ranges, the first monochromatic light and the second monochromatic light being directed to the insertion portion; the gradation sensor is in the first single Image capturing is performed separately under the chromatic light and the second monochromatic light, and the first image signal and the second image signal are alternately generated; and the imaging control unit respectively generates the first monochrome image according to the first image signal and the second image signal The second monochrome image combines the first monochrome image and the second monochrome image into a color image. Based on the control method, the endoscope system can utilize a semiconductor light source with a grayscale sensor to obtain a color image based on the bifurcation acquisition under different color lights.

[0077] wherein, in order to overcome the difference in response of the gradation sensor to different monochromatic lights, for example, the response to the first monochromatic light is stronger than the second monochromatic light, the control method includes first using the semiconductor light source to alternately provide different energies. Monochromatic light and second monochromatic light. In this case, the first monochromatic light and the second monochromatic light received by the gradation sensor are different in energy, for example, the energy of the first monochromatic light is smaller than the energy of the second monochromatic light, based on which the gradation sensor can be compensated The difference in response between a monochromatic light and a second monochromatic light causes the image signals produced by the grayscale sensor to be similar, identical, or at a desired ratio under different monochromatic light, thereby resulting in a higher quality or desired quality of the resulting image. .

[0078] The energy of the monochromatic light can be represented by the luminous flux cumulative value within a certain time interval. Based on this, in order to obtain luminous flux of different energies, the luminous flux of the monochromatic light or the monochromatic light can be adjusted. In some examples, the control method includes pre-setting an illumination period required to generate a single color image, and then setting a first monochromatic light during a first period of illumination, and a second between illuminations The second monochromatic light is provided during the period, and the first period and the second period have different lengths. Thus, the first monochromatic light and the second monochromatic light will illuminate different lengths to obtain first monochromatic light and second monochromatic light of different energies. In some examples, the control method includes adjusting the luminous flux of the first monochromatic light and/or the second monochromatic light such that the first monochromatic light and the second monochromatic light have different luminous fluxes, thereby obtaining a first monochromatic color of different energies. Light and second monochromatic light.

[0079] The imaging control unit controls the gradation sensor to perform the synchronous exposure according to the illuminating design of each monochromatic light in the light source device, that is, controls the exposure time length of the gradation sensor. For example, the first monochromatic light and the second monochromatic light have different illuminating lengths, and the gradation sensor performs the same adjustment on the exposure period of the first monochromatic light and the second monochromatic light. For example, the first monochromatic light and the second monochromatic light have different luminous fluxes and the luminous lengths are the same, 灰度, gray scale The sensor has the same exposure length to the first monochromatic light and the second monochromatic light. The imaging control unit controls the exposure of the gradation sensor to enable the gradation sensor to correspondingly and efficiently collect the monochromatic light of different wavelength ranges.

[0080] The control method of the endoscope system of FIG. 6 can not only generate a color image, but also the light source device can adjust the energy of each emitted monochromatic light in accordance with the response characteristic of the gradation sensor, thereby improving the quality of the color image; The gradation sensor also cooperates with the illuminating design of the light source device to synchronize exposure and improve the utilization of light energy.

[0081] The light source control part of the present invention may adopt a control circuit design controlled by the system control part, and may also adopt other hardware design, software, firmware or a combination thereof. The imaging control part of the present invention may adopt hardware, software, firmware, Or a combination thereof is implemented in an endoscope system, thereby enabling the endoscope system to generate a color image, a special image with enhanced blood vessel effect, obtain a high quality image, etc., according to various embodiments of the present invention, using hardware such as an MCU And other general purpose processors.

The invention has been described above by way of specific examples, but the invention is not limited to these specific embodiments. It will be apparent to those skilled in the art that various modifications, equivalents, changes and the like may be made to the present invention. These changes should be included in the scope of the present invention as long as they do not depart from the spirit of the backup. Here, the "one embodiment" or "another embodiment" and the like described above may represent the same embodiment, and may also represent different embodiments.

technical problem

Problem solution

Advantageous effects of the invention

Claims

Claim

An endoscope system, comprising:

a light source device comprising a semiconductor light source unit for distributing a plurality of monochromatic lights of different wavelength ranges;

An insertion portion, the front end of which is provided with a grayscale sensor for image acquisition, and the grayscale sensor collects image signals under a plurality of monochromatic lights;

The imaging control unit generates a plurality of monochrome images correspondingly based on the image signals acquired by the gradation sensors, and combines the monochrome images into a color image.

The endoscope system according to claim 1, wherein said semiconductor light source unit comprises:

a first semiconductor light source that generates excitation light;

a first beam splitting wheel comprising at least two first beam splitting regions, wherein the at least two first beam splitting regions can provide a plurality of monochromatic lights of different wavelength ranges under excitation light illumination;

Wherein, the at least two first splitting lights of the first light splitting wheel are located on the optical path of the excitation light, and the first light splitting wheel located on the optical path provides the monochromatic light of the corresponding wavelength range.

The endoscope system according to claim 2, wherein one of the at least two first light splitting regions is provided with a phosphor, and the phosphor is excited by the excitation light to emit a single wavelength range Color light; or a plurality of the at least two first light splitting regions are coated with different phosphors, and the phosphors are excited by the excitation light to emit monochromatic light of a corresponding wavelength range.

The endoscope system according to claim 2, wherein at least two of the first beam splitting regions of the first beam splitting wheel have differently distributed regions.

The endoscope system according to claim 2, further comprising detection means for detecting a first spectroscopic region on an optical path of the excitation light, thereby generating a representation indicating the detected The indication signal of the first beam splitting zone.

The endoscope system according to claim 5, wherein the semiconductor light source unit further includes a light source control unit, and the light source control unit is configured to generate the light source control unit according to the detection device. The indication signal controls the first semiconductor light source to emit excitation light of different luminous fluxes. The endoscope system according to claim 5, wherein said detecting means comprises a photodetector, and a marker body disposed on the first spectroscopic wheel; said photodetector being received according to said tag body Reflecting the light, determining a first beam splitting region on the optical path of the excitation light.

The endoscope system according to claim 2, wherein the semiconductor light source unit further comprises a second splitter wheel, the second splitter wheel comprising at least two second splitting zones, the at least two second The light splitting region may generate a plurality of monochromatic lights of different wavelength ranges under excitation light, wherein a wavelength range of one or more of the plurality of monochromatic lights generated by the second splitter wheel is different from the first splitter wheel Providing a wavelength range of the plurality of monochromatic lights; the endoscope system includes a first working mode and a second working mode, wherein the first dichroic wheel accesses the optical path of the excitation light in the first working mode, The second splitter wheel accesses the optical path of the excitation light in the second working mode.

a second semiconductor light source for generating a first monochromatic light of a first wavelength range;

a third semiconductor light source for generating a second monochromatic light of a second wavelength range;

a light source control unit, configured to control the second semiconductor light source and the third semiconductor light source to emit light;

a first dichroic mirror disposed on the optical path of the first monochromatic light and the second monochromatic light; the first monochromatic light is transmitted through the first dichroic mirror, and the second monochromatic light is passed through The first dichroic mirror reflects, and the first monochromatic light and the second monochromatic light are respectively transmitted along the same optical path in the direction of the insertion portion after being transmitted and reflected.

The endoscope system according to claim 9, wherein the light source control portion is further configured to control a light emission length of the second semiconductor light source and the third semiconductor light source, wherein the light source control portion causes the The illuminating length of the second semiconductor light source is different from the illuminating length of the third semiconductor light source.

The endoscope system according to claim 9, wherein the light source control unit further The first monochromatic light and the second monochromatic light for controlling the second semiconductor light source and the third semiconductor light source to emit different luminous fluxes.

[Claim 12] The endoscope system according to any one of claims 1 to 11, wherein the light source device further comprises:

a narrowband light source for generating narrowband light, wherein the narrowband light source and the semiconductor light source unit are separately illuminated;

a second dichroic mirror, wherein the optical path of the narrowband light and the optical path of the plurality of monochromatic lights are combined into the same optical path by the second dichroic mirror, and the narrowband light and the plurality of monochromatic light branches along the same The optical path is transmitted in the direction of the insertion portion.

The endoscope system according to any one of claims 1 to 11, wherein the imaging control unit controls the gradation according to each of the plurality of monochromatic lights. The sensor divides the exposure time of the image signal under the plurality of monochromatic lights.

[Claim 14] The endoscope system according to any one of claims 2 to 11, wherein the first, second, and third semiconductor light sources are laser light sources, LED light sources, or laser diodes; and Or the gradation sensor is a CCD sensor or a CMOS sensor.

[Claim 15] A method of controlling an endoscope system, wherein the endoscope system includes a light source device, an insertion portion, and an imaging control portion, the light source device includes a semiconductor light source, and the insertion portion includes The gamma sensor for image acquisition, the control method comprising: the semiconductor light source alternately providing first monochromatic light and second monochromatic light having different wavelength ranges, the first monochromatic light and the second monochromatic light Guiding the insertion portion;

The gradation sensor performs image acquisition under the first monochromatic light and the second monochromatic light, respectively, and alternately generates the first image signal and the second image signal;

The imaging control unit respectively generates a first monochrome image and a second monochrome image according to the first image signal and the second image signal, and combines the first monochrome image and the second monochrome image into a color image .

[Claim 16] The control method of the endoscope system according to claim 15, wherein the alternately providing the first monochromatic light and the second monochromatic light by the semiconductor light source comprises: the semiconductor light sources alternately providing different The first monochromatic light and the second monochromatic light of energy. The control method of the endoscope system according to claim 16, wherein the first and second monochromatic lights of the semiconductor light source alternately providing different energies comprise: setting illumination for generating a single color image Daytime, and

Providing a first monochromatic light during a first period of the illumination, and providing a second monochromatic light during a second period of the illumination, the first period and the second period having Different lengths. The control method of the endoscope system according to claim 16, wherein the first and second monochromatic lights of the semiconductor light source alternately providing different energies comprise: adjusting the first monochromatic light and / or the luminous flux of the second monochromatic light, the luminous flux of the first monochromatic light is distinguished from the luminous flux of the second monochromatic light.

An endoscope system comprising a normal light observation mode and a special light observation mode, characterized in that:

a light source control unit configured to control the first semiconductor light source unit to operate in a normal light observation mode, and to control the second semiconductor light source to operate in a special light mode;

The first semiconductor light source portion is configured to provide a plurality of wide-band light of different wavelength ranges for the second semiconductor light source for providing narrow-band light;

The endoscope includes an insertion portion insertable into the interior of the living body, the front end of the insertion portion being provided with a gradation sensor for image acquisition;

The imaging control unit generates a monochrome image based on the image signal acquired by the gradation sensor in the special light observation mode, and generates a color image based on the image signal acquired by the gradation sensor in the normal light observation mode.

The endoscope system according to claim 19, wherein the first semiconductor light source portion includes a first semiconductor light source and a beam splitter, and light generated by the first semiconductor light source obtains different wavelength ranges via the spectroscope Multiple wide band lights.

The endoscope system according to claim 20, wherein the first semiconductor light source comprises a plurality of light emitting units for distributing a plurality of wide-band light of different wavelength ranges, the first optical splitter being first a dichroic mirror, wherein the optical paths of the broadband light provided by the plurality of light emitting units are combined into the same optical path by the first dichroic mirror. The endoscope system according to claim 20, wherein said first semiconductor light source is for providing excitation light, said beam splitter is a beam splitter having a plurality of light splitting regions, and said plurality of splitting lights are rotated to be located The plurality of broadband light beams of the different wavelength ranges are provided on the optical path of the excitation light and under illumination of the excitation light.

The endoscope system according to claim 22, wherein the plurality of spectroscopic regions have different distribution angles on the spectroscopic wheel.

The endoscope system according to claim 22, wherein the luminous flux of the excitation light is adjustable, and different light splitting regions of the plurality of light splitting regions are located on the optical path of the excitation light, the excitation light having different Luminous flux.

The endoscope system according to any one of claims 22 to 24, further comprising detection means for detecting a spectroscopic region located on an optical path of the excitation light, thereby generating a representation An indication signal of the detected splitting zone;

The imaging control unit controls the gradation sensor to divide the exposure time for image acquisition under the plurality of wide-band light signals according to the indication signal; and the light source control unit adjusts the luminous flux of the excitation light according to the indication signal.

The endoscope system according to claim 20, further comprising a second dichroic mirror disposed on the optical path of the wide band light and the narrow band light; the optical path of the wide band light and the narrow band light The second dichroic mirror is synthesized into the same optical path.

The endoscope system according to any one of claims 20 to 26, wherein the first semiconductor light source portion comprises a laser light source, an LED light source or a laser diode, and the second semiconductor light source is a laser light source, an LED light source or a laser diode.