Endoscope light source device and endoscope system

Abstract

The utility model provides an endoscope light source device and an endoscope system. The endoscope light source device comprises a plurality of light sources, a light combining assembly and a converging assembly. The plurality of light sources are used for emitting a plurality of light beams with different wavebands; the light combining assembly is arranged on light emitting paths of the light sources and used for combining the light beams. The converging assembly is arranged on a light emitting path of the light combining assembly and used for converging the combined light beams on an optical axis behind the converging assembly, and the endoscope light source device is provided with a preset converging surface which is located behind the converging assembly and is perpendicular to the optical axis; and each light beam has illumination distribution with the similarity greater than or equal to 80% on the preset convergence surface. In this way, the light beams emitted by the light sources can form light spots which are roughly the same in illuminance distribution trend and the same in size in the preset light passing area of the preset convergence face, and therefore the color distribution of the convergence light spots formed by the light beams emitted by the light sources on the preset convergence face can be more uniform.

Description

Technical Field

[0001] The utility model relates to the technical field of endoscopes, and particularly to an endoscope light source device and an endoscope system. Background Art

[0002] As a non-invasive imaging method, endoscopic imaging can effectively extend the human line of sight and is widely used in imaging diagnosis and image-guided treatment in multiple fields such as the digestive tract, cardiovascular and cerebrovascular systems, urinary system, and respiratory system, greatly improving the inspection accuracy of diseases.

[0003] The endoscope used in endoscopic imaging is usually connected with an endoscope light source device. Multiple light sources in the endoscope light source device can emit multiple beams of different wavelength bands. The multiple beams of different wavelength bands are converged by a light combining component and then converged by a converging lens onto the receiving surface of the light guiding part of the endoscope and introduced into the endoscope.

[0004] However, there is a problem that the illumination light formed after the multiple beams of different wavelength bands emitted by the multiple light sources are converged has an uneven color distribution. Summary of the Utility Model

[0005] In order to at least partially solve the problems existing in the prior art, according to one aspect of the present utility model, an endoscope light source device is provided. The endoscope light source device includes multiple light sources, a light combining component, and a converging component. The multiple light sources are used for emitting multiple beams of different wavelength bands; the light combining component is arranged on the light output optical path of the multiple light sources and is used for combining the multiple beams; and the converging component is arranged on the light output optical path of the light combining component and is used for respectively converging the combined multiple beams on the optical axis behind the converging component, wherein: the endoscope light source device has a predetermined converging surface located behind the converging component and perpendicular to the optical axis, and each beam has an illuminance distribution with a similarity greater than or equal to 80% on the predetermined converging surface.

[0006] For the endoscope light source device provided by the present utility model, the similarity of the illuminance distributions of the respective beams emitted by the multiple light sources on the predetermined converging surface is greater than or equal to 80%, which can make the respective beams emitted by the multiple light sources form light spots with substantially the same illuminance distribution trend and the same size within a predetermined light passing area on the predetermined converging surface. Thus, the color distribution of the converging light spots formed by the respective beams emitted by the multiple light sources on the predetermined converging surface can be more uniform. Such an endoscope light source device is applied to an endoscope system, and the converging light spots with a more uniform color distribution are introduced into the endoscope, and the diagnosis and treatment effect can be better.

[0007] Exemplarily, multiple light beams respectively have maximum optical power at their respective convergence points, and each of the multiple light beams has a defined optical power within a predetermined light-transmitting area on a predetermined convergence plane; then, each light beam has an illuminance distribution with a similarity greater than or equal to 80% on the predetermined convergence plane, including: the ratio of the defined optical power of each light beam to its maximum optical power is equal.

[0008] Exemplarily, the predetermined convergence plane passes through the convergence point of one of the multiple light beams.

[0009] Exemplarily, each of the multiple light sources includes a light-emitting element and a collimating lens disposed on the light-emitting optical path of the light-emitting element. Among them, each light-emitting element has the same light-emitting area, each collimating lens has the same optical characteristics, and the relative positions of each light-emitting element and its corresponding collimating lens on their respective optical paths are set such that each light beam has an illuminance distribution with a similarity greater than or equal to 80% on the predetermined convergence plane.

[0010] Exemplarily, the distance from each light-emitting element along its respective optical path to the converging assembly is equal, and the position of each collimating lens on its respective optical path is set such that each light beam has an illuminance distribution with a similarity greater than or equal to 80% on the predetermined convergence plane.

[0011] Exemplarily, the multiple light sources include a first light source, a second light source, and a third light source. The first light source and the second light source are relatively arranged on both sides of the optical axis of the converging assembly. The combining optical assembly includes a first combining optical element disposed on the optical axis of the converging assembly. The first combining optical element includes a first combining portion and a second combining portion. The first combining portion is used to reflect the first light beam emitted by the first light source to the converging assembly and transmit the second light beam emitted by the second light source. The second combining portion is used to reflect the second light beam to the converging assembly and transmit the first light beam, where:

[0012] The third light source is disposed on the side of the optical axis of the converging assembly. The combining optical assembly further includes a second combining optical element disposed on the optical axis of the converging assembly. The second combining optical element is closer to the converging assembly than the first combining optical element. The second combining optical element is used to reflect the third light beam emitted by the third light source and transmit the second light beam and the first light beam;

[0013] Or, the third light source is disposed on the optical axis of the converging assembly, the third light source is farther from the first combining optical element than the first combining optical element, and the first combining optical element is further used to transmit the third light beam emitted by the third light source.

[0014] Exemplarily, the first combining portion includes a first filter, the second combining portion includes a second filter, and the first filter and the second filter are arranged crosswise; or

[0015] The first light combining element is a light combining prism, and a first filter film and a second filter film are cross-deposited in the light combining prism. The first filter film is configured as a first light combining portion, and the second filter film is configured as a second light combining portion.

[0016] Exemplarily, the plurality of light sources further includes a fourth light source. The third light source is disposed on the side of the optical axis of the converging assembly, and the fourth light source is disposed on the optical axis of the converging assembly and is farther from the converging assembly than the first light combining element. The first light combining element and the second light combining element are further configured to transmit a fourth light beam emitted by the fourth light source.

[0017] Exemplarily, the plurality of light sources further includes a fifth light source. The fifth light source is located on the same side of the optical axis of the converging assembly as the third light source. The second light combining element is further configured to reflect a fifth light beam emitted by the fifth light source. The light combining assembly further includes a third light combining element disposed on the side of the optical axis of the converging assembly. The third light combining element is configured to reflect one of the third light beam and the fifth light beam to the second light combining element and transmit the other of the third light beam and the fifth light beam to the second light combining element.

[0018] Exemplarily, the wavelengths of the first light beam, the fourth light beam, and the second light beam increase or decrease in sequence; the wavelengths of the first light beam, the fourth light beam, and the second light beam are all greater than or all less than the wavelengths of the third light beam and the fifth light beam.

[0019] According to another aspect of the present invention, an endoscope system is provided. The endoscope system includes an endoscope and any one of the endoscope light source devices as described above. The receiving surface of the light guiding portion of the endoscope is located on a predetermined converging surface.

[0020] A series of simplified concepts are introduced in the summary of the invention, which will be further described in detail in the detailed description section. The summary of the invention does not mean to attempt to define the key features and essential technical features of the claimed technical solution, nor does it mean to attempt to determine the protection scope of the claimed technical solution.

[0021] The advantages and features of the present invention will be described in detail below with reference to the accompanying drawings. BRIEF DESCRIPTION OF THE DRAWINGS

[0022] The following drawings of the present invention are used as a part of the present invention to understand the present invention. The embodiments and descriptions thereof shown in the drawings are used to explain the principles of the present invention. In the drawings,

[0023] Figure 1 is a schematic diagram of an endoscope system according to an exemplary embodiment of the present invention;

[0024] Figure 2 is a schematic diagram of an endoscope light source device according to an exemplary embodiment of the present invention;

[0025] Figure 3 Schematic diagram of an endoscope light source device according to an exemplary embodiment of the present utility model;

[0026] Figure 4 Schematic diagram of an endoscope light source device according to an exemplary embodiment of the present utility model;

[0027] Figure 5 Schematic diagram of an endoscope light source device according to an exemplary embodiment of the present utility model;

[0028] Figure 6 Schematic diagram of an annular workpiece according to an exemplary embodiment of the present utility model;

[0029] Figure 7A Schematic diagram of illumination light generated by an endoscope light source device for comparison with the endoscope light source device provided by the present utility model;

[0030] Figure 7B Schematic diagram of illumination light generated by an endoscope light source device according to an exemplary embodiment of the present utility model; and

[0031] Figure 8 Flowchart of a calibration method according to an exemplary embodiment of the present utility model.

[0032] Wherein, the above-mentioned drawings include the following reference numerals:

[0033] 10, endoscope light source device; 111, first light source; 1111, first light beam; 1112, first light-emitting element; 1113, first collimating lens; 112, second light source; 1121, second light beam; 1122, second light-emitting element; 1123, second collimating lens; 113, third light source; 1131, third light beam; 1132, third light-emitting element; 1133, third collimating lens; 114, fourth light source; 1141, fourth light beam; 1142, fourth light-emitting element; 1143, fourth collimating lens; 115, fifth light source; 1151, fifth light beam; 1152, fifth light-emitting element; 1153, fifth collimating lens; 121, first light combining element; 1211, first light combining part; 1212, second light combining part; 122, second light combining element; 123, third light combining element; 130, converging assembly; 140, optical axis; 150, predetermined converging surface; 20, endoscope; 30, host; 40, display; 50, object to be examined; 70, annular workpiece; 71, predetermined light passing hole. Detailed implementation manners

[0034] In the following description, numerous details are provided to enable a thorough understanding of the present utility model. However, those skilled in the art can understand that the following description only exemplarily shows the preferred embodiments of the present utility model, and the present utility model can be implemented without one or more such details. In addition, to avoid confusion with the present utility model, some technical features well known in the art are not described in detail.

[0035] According to one aspect of the present utility model, an endoscope light source device is provided. The endoscope light source device can be applied to various devices or systems, including but not limited to endoscope systems. Therefore, according to another aspect of the present utility model, an endoscope system is provided. The endoscope system can include an endoscope and any of the endoscope light source devices to be introduced below. Refer to Figure 1 , the endoscope system can include an endoscope light source device 10, an endoscope 20, a host 30, and a display 40. Referring to Figure 2 , the endoscope 20 can include a light guide portion 21. The endoscope light source device 10 can have a predetermined converging surface 150, and the predetermined converging surface 150 can be located on the receiving surface of the light guide portion 21 of the endoscope 20. The light beam emitted by the endoscope light source device 10 can reach one end of the endoscope 20 close to the object to be examined 50 through the light guide portion 21 to illuminate the object to be examined 50. Thus, the endoscope 20 can collect the image information of the object to be examined 50, and the corresponding generated image signal can be transmitted to the host 30. The host 30 can process the image signal and finally transmit it to the display 40 for display.

[0036] The endoscope light source device 10 can include a plurality of light sources, a light combining component, and a converging component 130. Among them, the plurality of light sources can include two or more light sources.

[0037] The plurality of light sources can be used to emit a plurality of light beams in different wavelength bands. The light source generally can include a light emitting element. The plurality of light emitting elements included in the plurality of light sources can be various forms of light emitting elements. The plurality of light emitting elements can be the same form of light emitting elements with each other, or different forms of light emitting elements. Preferably, the plurality of light emitting elements corresponding to the plurality of light sources can all be in the form of LEDs. The angle of the light emitted by an LED is 180°, and it is necessary to collimate the light emitted by the LED. Therefore, when the light emitting element is an LED, the light source generally can also include a collimating lens. Taking Figure 2 as an example, the first light source 111 can include a first light emitting element 1112 and a first collimating lens 1113, and the first collimating lens 1113 can collimate the light emitted by the first light emitting element 1112. It should be noted that as Figure 2In the illustrated schematic diagram, the first collimating lens 1113 includes only one lens, but the present application does not limit the specific structure of the collimating lens. That is to say, the collimating lens may include multiple lenses, and under the combined action of the multiple lenses, the light emitted by the light-emitting element is collimated. The multiple light-emitting elements included in the multiple light sources may respectively emit multiple light beams of different wavelength bands. Light beams of different wavelength bands usually have different colors. For example Figure 2 In the illustrated embodiment, the first light-emitting element 1112 may emit blue light with a wavelength range of 430 nm to 500 nm, and the second light-emitting element 1122 may emit light with a wavelength range of

[0038] 500 nm to 580 nm of green light, and the third light-emitting element 1132 may emit red light with a wavelength range of 610 nm to 650 nm. At this time, it can be considered that the first light source 111, the second light source 112, and the third light source 113 respectively emit blue light, green light, and red light.

[0039] The light combining component may be disposed on the light output optical paths of the multiple light sources for combining the multiple light beams. The light combining component may cause the multiple light beams to form a combined light beam through reflection, refraction, and / or transmission. The light combining component may include multiple light combining elements, and the light combining elements may be in various forms such as dichroic mirrors, filter plates, and light combining prisms. As Figure 2 shown, the light combining component may include a first light combining element 121. The first light combining element 121 may combine the first light beam 1111 emitted by the first light source 111, the second light beam 1121 emitted by the second light source 112, and the third light beam 1131 emitted by the third light source 113. For example, the first light combining element 121 may include a first light combining portion 1211 and a second light combining portion 1212 disposed crosswise, and both the first light combining portion 1211 and the second light combining portion 1212 may be filter plates.

[0040] The converging component 130 may be disposed on the light output optical path of the light combining component. The converging component 130 may be used to respectively converge the multiple combined light beams on the optical axis 140 behind the converging component 130 (i.e., in the direction away from the light source along the optical path), and the multiple light beams may respectively have the maximum optical power at their respective converging points. The combined light beam formed by the multiple light beams passing through the light combining component may be converged by the converging component 130. The converging component 130 may be a converging lens or other various forms. When only any one light source is turned on, a optical power meter may be disposed on the optical axis 140 behind the converging component. By moving the optical power meter, the optical power values at different positions on the optical axis 140 can be measured. The maximum optical power value is the maximum optical power of the light beam emitted by the light source after being converged by the converging component 130 on the optical axis 140. The position where the optical power meter measures the maximum optical power is the converging point of the light beam emitted by the light source on the optical axis 140, that is, the focal point of the light beam on the optical axis 140.

[0041] The endoscopic light source device 10 may have a predetermined converging surface 150 located behind the converging assembly 130 and perpendicular to the optical axis 140. The predetermined converging surface 150 may intersect the optical axis 140 at the converging point of any one of the plurality of light beams on the optical axis 140. It can be understood that the predetermined converging surface 150 can be set at any position according to actual needs. For example, the endoscopic light source device 10 may include a calibration light source, and the predetermined converging surface 150 intersects the optical axis 140 at the converging point of the light beam emitted by the calibration light source on the optical axis 140, wherein the calibration light source is only used to determine the position of the predetermined converging surface 150 during optical path debugging and does not participate in the synthesis of the illumination light. The calibration light source can be selected according to actual needs, so that the predetermined converging surface 150 can be perpendicular to the optical axis 140 and can intersect the optical axis 140 at any suitable position.

[0042] Each of the plurality of light sources may have a defined optical power within a predetermined light-transmitting area on the predetermined converging surface 150. When only any one light source is turned on, a power meter with a defined aperture may be set at the position where the predetermined converging surface 150 intersects the optical axis 140. The power meter with a defined aperture can only measure the optical power within the predetermined light-transmitting area. For example, a ring-shaped workpiece for defining the predetermined light-transmitting area may be added to a common power meter. As Figure 6 shown, a predetermined light-transmitting hole 71 may be provided on the ring-shaped workpiece 70, and the light-transmitting area of the predetermined light-transmitting hole 71 is equal to the predetermined light-transmitting area. By adding such a ring-shaped workpiece 70 to the power meter, a power meter with a defined aperture can be obtained, and the power meter with a defined aperture can only measure the optical power under the predetermined light-transmitting area. The endoscopic light source device 10 may be connected to the light guide portion of the endoscope 20, and the illumination light emitted by the endoscopic light source device 10 may reach the light receiving surface of the light guide portion. The predetermined light-transmitting area may be determined with reference to the area of the light receiving surface. Therefore, the illumination light received by the power meter with a defined aperture can simulate the illumination light received on the light receiving surface of the light guide portion.

[0043] Of course, obtaining the maximum optical power and the defined optical power of each light source in the manner mentioned above is only an example. It can be understood that the methods for obtaining the maximum optical power and the defined optical power of each light source can also be in various other forms, which will not be elaborated here.

[0044] To make the color of the illumination light emitted by the endoscope light source device 10 more uniform, in the conventional solution, it is possible to make the multiple collimated light beams emitted by multiple light sources have the same beam diameter when incident on the converging component 130, so that the light spots respectively formed by the multiple light beams emitted by the multiple light sources at the focal position have the same size. To achieve the same beam diameter when each light beam is incident on the converging component 130, multiple light-emitting elements in the multiple light sources can respectively have the same light-emitting surface size and be collimated by collimating lenses with the same optical characteristics, so that the collimated light beams emitted by each light source have the same beam diameter. Further, in practical applications, although the collimating lens can collimate the light beam emitted by the light-emitting element, in fact, there is usually still a certain divergence angle in the collimated light beam, which results in different beam diameters of the collimated light beam at positions with different optical paths. Based on this, multiple light sources can also be arranged to have the same distance from the converging component 130 along the optical path. Specifically, multiple light-emitting elements in the multiple light sources can be respectively arranged to have the same distance from the converging component 130 along the optical path, that is, the optical paths of the multiple light beams emitted by the multiple light-emitting elements to the converging component 130 are the same. Multiple light beams with the same optical path are respectively incident on the converging component 130 and, after being converged respectively, the sizes of the formed light spots can be more closely approximated. In this way, the color of the illumination light formed by the superposition of multiple light spots can be more uniform.

[0045] However, in practical applications, the inventors of the present application found that: even if multiple light-emitting elements in multiple light sources are respectively arranged to have the same distance from the converging component 130 along the optical path, the sizes of the light spots respectively formed by the multiple light beams emitted by the multiple light-emitting elements on the predetermined converging surface 150 are still different, as Figure 7A shown, and there is still a problem of uneven color in the converging light spot finally formed on the predetermined converging surface 150, and the color of the formed illumination light is also uneven.

[0046] After careful research by the inventors, it is found that the main reason why it is still difficult to obtain a mixed illumination light with uniform color in the conventional solution is that: the focal positions formed after the converging component 130 converges light beams of various colors are different, which will cause the sizes of the light spots respectively formed by the multiple light beams emitted by the multiple light-emitting elements on the predetermined converging surface 150 to be still different, and there is still a problem of uneven color in the converging light spot formed on the predetermined converging surface 150. In addition, in practical applications, it is inevitable that there are processing or assembly errors, so there is still a deviation between the beam diameter of each light beam when incident on the converging component 130 and the ideal state.

[0047] In summary, making the light-emitting elements in multiple light sources have the same light-emitting surface size, making the optical characteristics of the collimating lenses in multiple light sources the same, and setting multiple light sources to have the same distance from the converging component 130 along the optical path, it is possible to expect to obtain a converging light spot with more uniform color in an ideal situation. However, due to the influence of various error factors in reality, the color of the actually obtained converging light spot is still not uniform enough.

[0048] To solve this problem, the inventor conducted in-depth research, multiple simulations and tests, and found that: to make the color distribution of the converging light spots formed by the light beams emitted by multiple light sources on the predetermined converging surface 150 more uniform, it is necessary that the light spots of the light beams emitted by each light source on the predetermined converging surface 150 have the same size and have a substantially the same illuminance distribution trend. Among them, the same light spot size indicates that the light beams of various colors are superimposed within the same size range. The same illuminance distribution trend means that when the light beams of various colors are superimposed, the areas with high illuminance are superimposed on each other, and a part of the formed converging light spot will have high illuminance, and the areas with low illuminance are superimposed on each other, and a part of the formed converging light spot will have low illuminance. In this way, the illuminance distribution of the converging light spot can be substantially the same as that of monochromatic light, and the color distribution of such a converging light spot will be relatively uniform. That is, when the optical path in the endoscopic light source device is designed such that the illuminance distributions of the respective light beams on the predetermined converging surface 150 have a similarity greater than or equal to 80%, it means that after the respective light beams are converged by the converging component 130, they are all focused on the predetermined converging surface 150 and have substantially the same light spot size. Thus, a mixed illumination light with uniform color can be obtained.

[0049] Specifically, when designing or debugging the optical path, to make the respective light beams emitted by multiple light sources have the same illuminance distribution trend on the predetermined converging surface 150, the illuminance distribution of each light beam on the predetermined converging surface 150 can be obtained first using an optical measuring instrument, and the divergence angle of each light beam incident on the converging component 130 can be adjusted with reference to the similarity of the illuminance distributions of the respective light beams so that the illuminance distributions of the respective light beams on the predetermined converging surface 150 are the same.

[0050] In addition, the inventor found that to make the light spots of the light beams emitted by each light source have the same size and have a substantially the same illuminance distribution trend on the predetermined converging surface 150, the ratio of the defined optical power to the maximum optical power of the respective light beams emitted by multiple light sources can be made equal.

[0051] Specifically, since integrating the illuminance distribution curve of each light beam within a predetermined light-transmitting area gives the optical power value of that light beam within the predetermined light-transmitting area, if the ratios of the limited optical power to the maximum optical power of each light beam within the predetermined light-transmitting area are all equal, it can be considered that each light beam has the same optical power distribution on the predetermined convergence plane 150. Furthermore, it can be considered that each light beam has a similar illuminance distribution on the predetermined convergence plane 150. For the light spot B1 formed by the light beam emitted by the light source A1 on the predetermined convergence plane 150, integrating the part of the illuminance distribution curve of the light spot B1 corresponding to the predetermined light-transmitting area gives the limited optical power C1 of the light spot B1, and integrating the complete illuminance distribution curve of the light spot B1 gives the maximum optical power C2 of the light spot B1. For the light spot B2 formed by the light beam emitted by the light source A2 on the predetermined convergence plane 150, integrating the part of the illuminance distribution curve of the light spot B2 corresponding to the predetermined light-transmitting area gives the limited optical power C3 of the light spot B2, and integrating the complete illuminance distribution curve of the light spot B2 gives the maximum optical power C4 of the light spot B2. If C1 / C2 is equal to C3 / C4, it indicates that the optical power distributions of the light spot B1 and the light spot B2 on the predetermined convergence plane 150 are the same, and thus it can be considered that the illuminance distribution trends of the light spot B1 and the light spot B2 on the predetermined convergence plane 150 are the same. That is to say, if the ratios of the limited optical power to the maximum optical power of each light beam within the predetermined light-transmitting area are all equal, it can be considered that each light beam has a similar illuminance distribution within the predetermined light-transmitting area.

[0052] In this way, by making the ratios of the limited optical power to the maximum optical power of each light beam emitted by multiple light sources equal, it is possible to make each light beam emitted by multiple light sources have a similar illuminance distribution within the predetermined light-transmitting area on the predetermined convergence plane 150. This can also achieve a more uniform color distribution of the converging light spots formed by the light beams emitted by multiple light sources on the predetermined convergence plane 150.

[0053] In the endoscopic light source device 10 provided in the present application, each light beam emitted by multiple light sources can have an illuminance distribution with a similarity greater than or equal to 80% on the predetermined convergence plane 150. When the similarity of the illuminance distributions of each light beam emitted by multiple light sources on the predetermined convergence plane 150 is greater than or equal to 80%, it can be considered that the illuminance distributions are substantially the same.

[0054] It can be understood that in the endoscope light source device 10 provided by the present application, before the similarity of the illuminance distributions of the respective light beams emitted by multiple light sources on the predetermined convergence surface 150 is greater than or equal to 80%, the multiple light sources can be respectively set to have the same distance from the optical path to the converging lens 130 in advance. After such pre-assembly is completed, only fine-tuning of each light source is required to achieve that the similarity of the illuminance distributions of the respective light beams emitted by the multiple light sources on the predetermined convergence surface 150 is greater than or equal to 80%. In this way, the optical path debugging efficiency of the overall device can be higher. The fine-tuning of each light source can be to adjust the position of the collimating lens in each light source, or to adjust the optical characteristics of the collimating lens in the light source, or to adjust the position of the light-emitting element in each light source. Since the light-emitting elements in each light source are usually fixedly connected to heat dissipation structures, drive circuits, etc., the position of the light-emitting element is not easy to adjust, and adjusting the position of the collimating lens is much simpler. By adjusting the position of the collimating lens to make the similarity of the illuminance distributions of the respective light beams emitted by the multiple light sources on the predetermined convergence surface 150 greater than or equal to 80%, the optical path debugging efficiency can be higher.

[0055] In the endoscope light source device 10 provided by the present utility model, the similarity of the illuminance distributions of the respective light beams emitted by multiple light sources on the predetermined convergence surface 150 is greater than or equal to 80%, which can enable the respective light beams emitted by the multiple light sources to form light spots with substantially the same illuminance distribution trend and the same size within the predetermined light-transmitting area on the predetermined convergence surface 150. Thus, the color distribution of the converging light spots formed by the respective light beams emitted by the multiple light sources on the predetermined convergence surface 150 can be more uniform. When such an endoscope light source device 10 is applied to an endoscope system, the converging light spots with a more uniform color distribution are introduced into the endoscope 20, and the diagnosis and treatment effect can be better.

[0056] In an embodiment of the present utility model, multiple light beams may respectively have maximum optical powers at their respective convergence points, and each of the multiple light beams may have a defined optical power within a predetermined light-transmitting area on a predetermined convergence plane. Then, each light beam has an illuminance distribution with a similarity greater than or equal to 80% on the predetermined convergence plane, including: the ratios of the defined optical powers of the respective light beams to their maximum optical powers are equal. As described above, to make the spot sizes of the light beams emitted by each light source the same and have a substantially similar illuminance distribution trend on the predetermined convergence plane 150, the ratios of the defined optical powers of the respective light beams emitted by multiple light sources to their maximum optical powers can be made equal. When determining that each light beam has an illuminance distribution with a similarity greater than or equal to 80% on the predetermined convergence plane by making the ratios of the defined optical powers of the respective light beams emitted by multiple light sources to their maximum optical powers equal, the maximum optical power value of each light beam at its respective convergence point can be measured using an optical power meter, and the defined optical power within the predetermined light-transmitting area of each light beam at the predetermined convergence plane 150 can be measured by means of installing an annular workpiece. In this way, the ratios of the defined optical powers to the maximum optical powers of the respective light beams can be obtained respectively, and the overall optical path debugging operation process can be simpler.

[0057] In an embodiment of the present utility model, the predetermined convergence plane 150 may pass through the convergence point of one of the multiple light beams. As Figure 2 shown, the endoscopic light source device 10 may use the convergence point of the first light beam 1111 emitted by the first light source 111 on the optical axis 140 as the intersection point of the predetermined convergence plane 150 and the optical axis 140. When determining the position of the predetermined convergence plane 150, an optical power meter may be set on the optical axis 140, only the first light source 111 is turned on, and the point where the maximum optical power is measured using the optical power meter is the convergence point of the first light beam 1111 emitted by the first light source 111 on the optical axis 140. In this way, it is not necessary to set a calibration light source. Here, taking the convergence point of the first light beam 1111 emitted by the first light source 111 on the optical axis 140 as the intersection point of the predetermined convergence plane 150 and the optical axis 140 is only an example, and it may also be the convergence point of any other light source on the optical axis 140 as the intersection point of the predetermined convergence plane 150 and the optical axis 140. Such an endoscopic light source device 10 is more convenient during calibration because it is not necessary to set a calibration light source. Taking the convergence point of any one of the multiple light sources as the intersection point of the predetermined convergence plane 150 and the optical axis 140, the position of the predetermined convergence plane 150 can be more clearly defined, and the cost is lower, the structure is simpler, and it is easier to implement.

[0058] In an embodiment of the present utility model, each of the multiple light sources may include a light-emitting element and a collimating lens provided on the light-emitting optical path of the light-emitting element. As Figure 2As shown, the first light source 111 may include a first light-emitting element 1112 and a first collimating lens 1113, the second light source 112 may include a second light-emitting element 1122 and a second collimating lens 1123, and the third light source 113 may include a third light-emitting element 1132 and a third collimating lens 1133. Among them, each light-emitting element may have the same light-emitting area, each collimating lens may have the same optical characteristics, and the relative positions of each light-emitting element and its corresponding collimating lens on their respective optical paths may be set such that the illuminance distributions of the respective light beams on a predetermined convergence plane have a similarity greater than or equal to 80%. The meaning that each light-emitting element may have the same light-emitting area is that the light-emitting areas of each of the multiple light sources are equal, or the difference in the light-emitting areas is within a predetermined range. The predetermined range mentioned here may be a relatively small numerical range, for example, it may be an acceptable error range. The light-emitting areas of the respective light-emitting surfaces are equal, and the collimating lenses have the same optical characteristics, which can enable the respective light beams to have substantially the same beam diameter and divergence angle after exiting from the collimating lenses; since the emitted light beams are collimated light beams, when the respective light beams are incident on the converging assembly, they also have substantially the same beam diameter and divergence angle. Thus, after being converged by the converging assembly, converging spots with substantially the same size can be obtained. Further, by adjusting the relative positions between the light-emitting elements and the collimating lenses, the divergence angles of the corresponding light beams incident on the converging assembly can be finely adjusted, and then the positions of their converging focal points can be adjusted so that the converging points of the respective light beams are all located on the predetermined convergence plane. It can be seen that the endoscope light source device with the characteristics of this optical path is convenient for optical path debugging. Optionally, when the light-emitting areas of the respective light-emitting elements are different, collimating lenses with different optical characteristics may also be used as long as it can be ensured that the light beams emitted by the respective collimating lenses have substantially the same beam diameter and divergence angle.

[0059] Exemplarily, the distance from each light-emitting element to the converging component 130 along its respective optical path can be equal, and the position of each collimating lens on its respective optical path can be set such that the illuminance distribution of each light beam on a predetermined converging surface has a similarity greater than or equal to 80%. Since in practical applications, ideal collimation cannot be achieved, and even the collimated light beam still has a certain divergence angle, therefore, the equal distance from each light-emitting element to the converging component 130 along its respective optical path can make each light beam still have an approximate beam diameter when incident on the converging component 130. Thus, after being converged by the converging component 130, converging spots with approximate sizes can be obtained. On this basis, by only slightly adjusting the setting position of the collimating lens, each light beam can be converged on the predetermined converging surface, and the sizes of the converging spots are approximately the same. In addition, since the light-emitting elements in each light source are usually fixedly connected to a heat dissipation structure, a driving circuit, etc., the position of the light-emitting elements is not easy to adjust, while adjusting the position of the collimating lens is relatively much simpler. By adjusting the position of the collimating lens to make the similarity of the illuminance distribution of each light beam emitted by multiple light sources on the predetermined converging surface 150 greater than or equal to 80%, the optical path debugging efficiency can be higher.

[0060] Exemplarily, referring to Figure 2 , the first light source 111 and the second light source 112 can be on the side of the optical axis 140 of the converging component 130. The first light source 111 and the second light source 112 can be arranged on the same side of the optical axis 140 or on the opposite sides of the optical axis 140. As Figure 2 shown, the first light source 111 and the second light source 112 are arranged on the opposite sides of the optical axis 140.

[0061] In an embodiment of the present invention, referring to Figure 2, the first light source 111 and the second light source 112 can be oppositely arranged on both sides of the optical axis 140 of the converging component 130. When the first light source 111 and the second light source 112 are oppositely arranged on both sides of the optical axis 140, it can be simpler and more convenient to set the multiple light sources to have the same spacing along their respective optical paths from the converging component 130, and this can further shorten the size of the endoscope light source device 10 in the extending direction of the optical axis 140. The light combining component can include a first light combining element 121 arranged on the optical axis 140 of the converging component 130. The first light combining element 121 can be used to reflect the first light beam 1111 emitted by the first light source 111 to the converging component 130 and transmit the second light beam 1121 emitted by the second light source 112, and can also be used to reflect the second light beam 1121 to the converging component 130 and transmit the first light beam 1111. The first light combining element 121 can include a first light combining part 1211 and a second light combining part 1212. Among them, the first light combining part 1211 can be used to reflect the first light beam 1111 emitted by the first light source 111 to the converging component 130 and transmit the second light beam 1121 emitted by the second light source 112, and the second light combining part 1212 can be used to reflect the second light beam 1121 to the converging component 130 and transmit the first light beam 1111.

[0062] In an embodiment of the present utility model, referring to Figure 3 , the third light source 113 can be arranged on the optical axis 140 of the converging component 130. The third light source 113 can be farther away from the converging component 130 relative to the first light combining element 121. The first light combining element 121 can also be used to transmit the third light beam 1131 emitted by the third light source 113. Generally, the endoscope light source device 10 can form white light as the illumination light. To form white light, the first light emitting element 1112 can emit blue light with a wavelength range of 430 nm to 500 nm, and the second light emitting element 1122 can emit light with a wavelength range of

[0063] The green light with a wavelength range of 500 nm to 580 nm and the red light with a wavelength range of 610 nm to 650 nm emitted by the third light-emitting element 1132. At this time, the first light beam 1111 is blue light, the second light beam 1121 is green light, and the third light beam 1131 is red light. The blue light, green light, and red light can be combined to form white light. The first light-combining part 1211 can be a filter. The first light-combining part 1211 in the form of a filter can reflect the blue light with a wavelength range of 430 nm to 500 nm, so that the first light-combining part 1211 can reflect the first light beam 1111; and the first light-combining part 1211 in the form of a filter can transmit the green light with a wavelength range of 500 nm to 580 nm and the red light with a wavelength range of 610 nm to 650 nm, so that the first light-combining part 1211 can transmit the second light beam 1121 and the third light beam 1131. The second light-combining part 1212 can be a filter. The second light-combining part 1212 in the form of a filter can reflect the green light with a wavelength range of 500 nm to 580 nm, so that the second light-combining part 1212 can reflect the second light beam 1121; and the second light-combining part 1212 in the form of a filter can transmit the blue light with a wavelength range of 430 nm to 500 nm and the red light with a wavelength range of 610 nm to 650 nm, so that the second light-combining part 1212 can transmit the first light beam 1111 and the third light beam 1131. Such a first light-combining part 1211 and a second light-combining part 1212 can be arranged crosswise. A part of the first light beam 1111 emitted by the first light-emitting element 1112 can first be reflected by the first light-combining part 1211 and then transmitted through the second light-combining part 1212 to reach the converging component 130, and another part can first be transmitted through the second light-combining part 1212 and then be reflected by the first light-combining part 1211 to reach the converging component 130. The same is true for the second light beam 1121 emitted by the second light-emitting element 1122, which will not be elaborated here. A part of the third light beam 1131 emitted by the third light-emitting element 1132 can first be transmitted through the first light-combining part 1211 and then transmitted through the second light-combining part 1212 to reach the converging component 130, and another part can first be transmitted through the second light-combining part 1212 and then transmitted through the first light-combining part 1211 to reach the converging component 130. Such an endoscope light source device 10 can have a smaller size in the direction perpendicular to the optical axis 140, can meet the needs of more occasions, and has a wider application range.

[0064] In an embodiment of the present invention, refer to Figure 3, multiple light sources may include a first light source 111, a second light source 112, and a third light source 113. The first light source 111 and the second light source 112 may be disposed on the sides of the optical axis 140 of the converging component 130. The light combining component may include a first light combining element 121 disposed on the optical axis 140 of the converging component 130. The first light combining element 121 may include a first light combining portion 1211 and a second light combining portion 1212. The first light combining portion 1211 may be configured to reflect the first light beam 1111 emitted by the first light source 111 to the converging component 130 and transmit the second light beam 1121 emitted by the second light source 112. The second light combining portion 1212 may be configured to reflect the second light beam 1121 to the converging component 130 and transmit the first light beam 1111. The third light source 113 may be disposed on the sides of the optical axis 140 of the converging component 130. The light combining component may further include a second light combining element 122 disposed on the optical axis 140 of the converging component 130. The second light combining element 122 may be closer to the converging component 130 than the first light combining element 121. The second light combining element 122 may be configured to reflect the third light beam 1131 emitted by the third light source 113 and transmit the second light beam 1121 and the first light beam 1111. The first light combining portion 1211 may be a filter. The first light combining portion 1211 in the form of a filter may reflect blue light with a wavelength range of 430 nm to 500 nm, so that the first light combining portion 1211 can reflect the first light beam 1111; and the first light combining portion 1211 in the form of a filter may transmit green light with a wavelength range of 500 nm to 580 nm, so that the first light combining portion 1211 can transmit the second light beam 1121. The second light combining portion 1212 may be a filter. The second light combining portion 1212 in the form of a filter may reflect green light with a wavelength range of 500 nm to 580 nm, so that the second light combining portion 1212 can reflect the second light beam 1121; and the second light combining portion 1212 in the form of a filter may transmit blue light with a wavelength range of 430 nm to 500 nm, so that the second light combining portion 1212 can transmit the first light beam 1111. The second light combining element 122 may be a filter. The second light combining element 122 in the form of a filter may reflect red light with a wavelength range of 610 nm to 650 nm, so that the second light combining element 122 can reflect the third light beam 1131; and the second light combining element 122 in the form of a filter may transmit blue light with a wavelength range of 430 nm to 500 nm and transmit green light with a wavelength range of 500 nm to 580 nm, so that the second light combining element 122 can transmit the first light beam 1111 and transmit the second light beam 1121. Such first light combining portion 1211 and second light combining portion 1212 may be cross - arranged.The first light beam 1111 emitted by the first light-emitting element 1112 can be such that a part of it is first reflected by the first light-combining part 1211 and then transmitted through the second light-combining part 1212, and then transmitted through the second light-combining element 122 to reach the converging assembly 130; another part is first transmitted through the second light-combining part 1212 and then reflected by the first light-combining part 1211, and then transmitted through the second light-combining element 122 to reach the converging assembly 130. The same applies to the second light beam 1121 emitted by the second light-emitting element 1122, which will not be elaborated here. The third light beam 1131 emitted by the third light-emitting element 1132 directly reaches the converging assembly 130 after being reflected by the second light-combining element 122. Such an endoscope light source device 10 can have a smaller size in the extending direction of the optical axis 140, can be applicable to the needs of more occasions, and thus has a wider range of applications.

[0065] The first light source 111, the second light source 112, and the third light source 113 mentioned above are only for distinction and are not subject to any limitations. Exemplarily, the first light source 111, the second light source 112, and the third light source 113 are a red-wavelength light source, a green-wavelength light source, and a blue-wavelength light source respectively. Similarly, there is no special limitation on which color light source among the red-wavelength light source, the green-wavelength light source, and the blue-wavelength light source the first light source 111, the second light source 112, and the third light source 113 are respectively. It only requires that the first light source 111, the second light source 112, and the third light source 113 emit light beams of different wavelengths, and the emitted light beams are one of the red-wavelength light, the green-wavelength light, and the blue-wavelength light. When the first light source 111, the second light source 112, and the third light source 113 are a red-wavelength light source, a green-wavelength light source, and a blue-wavelength light source respectively, the endoscope light source device 10 can synthesize white light at the predetermined converging surface 150, and the lighting effect is better when using white light as the illumination light.

[0066] In an embodiment of the present invention, referring to Figure 4 , the plurality of light sources may further include a fourth light source 114. The third light source 113 can be arranged on the side of the optical axis 140 of the converging assembly 130, and the fourth light source 114 can be arranged on the optical axis 140 of the converging assembly 130 and be farther away from the converging assembly 130 relative to the first light-combining element 121. The first light-combining element 121 and the second light-combining element 122 can also be used to transmit the fourth light beam emitted by the fourth light source 114. The fourth light source 114 is only different from the first light source 111, the second light source 112, and the third light source 113 mentioned above in the wavelength of the emitted light beam, and the others can be set with reference to the above-mentioned first light source 111, second light source 112, and third light source 113. In such an endoscope light source device 10, the number of light sources participating in the synthesis of the illumination light is more, and the light beams of different wavelengths emitted by different light sources can enable the synthesized illumination light to achieve more functions, can be applicable to the needs of more occasions, and thus has a wider range of applications.

[0067] In one embodiment of the present utility model, refer to Figure 4 , the plurality of light sources may further include a fifth light source 115. The fifth light source 115 and the third light source 113 may be located on the same side of the optical axis 140 of the converging component 130. The second light combining element 122 may further be configured to reflect the fifth light beam 1151 emitted by the fifth light source 115. The light combining assembly may further include a third light combining element 123 located on the side of the optical axis 140 of the converging component 130. The third light combining element 123 may be configured to reflect one of the third light beam 1131 and the fifth light beam 1151 to the second light combining element 122 and transmit the other of the third light beam 1131 and the fifth light beam 1151 to the second light combining element 122. In such an endoscope light source device 10, the number of light sources participating in the synthesis of the illumination light is larger. The light beams of different wavelengths emitted by different light sources can enable the synthesized illumination light to achieve more functions, can meet the needs of more occasions, and thus have a wider application range.

[0068] Exemplarily, the first light combining portion 1211 may include a first filter, and the second light combining portion 1212 may include a second filter. The first filter and the second filter may be arranged in a cross pattern. The manner of arranging the first filter and the second filter in a cross pattern can be arbitrary. For example, the first filter can be cut into two pieces and adhesively connected to the second filter respectively to complete the cross arrangement of the first filter and the second filter; alternatively, the second filter can be cut into two pieces and adhesively connected to the first filter respectively to complete the cross arrangement of the first filter and the second filter. Such a structure of the first light combining element 121 is simpler, more convenient to manufacture, and easier to implement.

[0069] Exemplarily, refer to Figure 5 , the first light combining element 121 may be a light combining prism. A first filter film and a second filter film may be cross-deposited in the light combining prism. The two cross surfaces of the light combining prism may be respectively deposited with the first filter film and the second filter film. The first filter film may be configured as the first light combining portion 1211, and the second filter film may be configured as the second light combining portion 1212. The first filter film and the second filter film may respectively perform the functions of the above-mentioned first filter and second filter. The size of the intersection of the light combining prism is smaller, which can avoid the problem that effective reflection and transmission cannot be performed at the intersection when the first filter and the second filter are arranged in a cross pattern. Thus, the arrangement of the light combining prism can improve the utilization rate of the light beam.

[0070] Exemplarily, the wavelengths of the first light beam 1111, the fourth light beam 1141, and the second light beam 1121 can increase or decrease in sequence. When the third light source 113 is disposed on the side of the optical axis 140, the fourth light source 114 can be farther away from the converging assembly 130 relative to the first light combining element 121 and the second light combining element 122, and the first light combining element 121 and the second light combining element 122 can also be used to transmit the fourth light beam 1141 emitted by the fourth light source 114. In addition to meeting their own optical property requirements, the first light combining element 121 and the second light combining element 122 are also required to be able to transmit the fourth light beam 1141 emitted by the fourth light source 114. Taking the wavelengths of the first light beam 1111, the fourth light beam 1141, and the second light beam 1121 decreasing in sequence as an example, such a first light source 111, a fourth light source 114, and a second light source 112 can be arranged around the first light combining element 121 in sequence, and the film stack design and fabrication of such a first light combining element 121 can be simpler. The case where the wavelengths of the first light beam 1111, the fourth light beam 1141, and the second light beam 1121 increase in sequence is similar and will not be elaborated here. Moreover, when the first light source 111 and the second light source 112 respectively emit light beams of different wavelengths, and the emitted light beams are one of red wavelength light and green wavelength light, the light beam emitted by the fourth light source 114 can be amber light, and the amber light can have a wavelength range of 580 nm to 610 nm. In the illumination light generated by such an endoscope light source device 10, since amber light is added, and the amber light can highlight the bleeding points on the tissue, such illumination light can assist in more clearly observing the bleeding points. When such an endoscope light source device 10 is applied to an endoscope system, the illumination light with amber light is introduced into the endoscope 20. When the endoscope 20 participates in the diagnosis and treatment, the bleeding points can be quickly found and hemostasis can be performed to prevent excessive bleeding.

[0071] Exemplarily, the wavelengths of the first light beam 1111, the fourth light beam 1141, and the second light beam 1121 can be all greater than or all less than the wavelengths of the third light beam 1131 and the fifth light beam 1151.

[0072] Take the case where the wavelengths of the first light beam 1111, the fourth light beam 1141, and the second light beam 1121 are all greater than the wavelengths of the third light beam 1131 and the fifth light beam 1151. Since the wavelengths of the third light beam 1131 and the fifth light beam 1151 are both relatively small, the fifth light source 115 can be arranged on the same side of the optical axis 140 as the third light source 113. The third light source 113 and the fifth light source 115 can form a certain angle, and a simple film system design can be used between them to ensure that the light beams emitted by both can be incident on the converging component 130. Here, the simple film system design can be, for example, reflecting short wavelengths and transmitting long wavelengths. For example, the fifth light source 115 and the third light source 113 are located on the same side of the optical axis 140 of the converging component 130, and the second light combining element 122 is also used to reflect the fifth light beam 1151 emitted by the fifth light source 115. The third light combining element 123 can be used to reflect one of the third light beam 1131 and the fifth light beam 1151 to the second light combining element 122 and transmit the other of the third light beam 1131 and the fifth light beam 1151 to the second light combining element 122. When the first light source 111, the second light source 112, and the third light source 113 emit light beams of different wavelengths, and the emitted light beams are one of red wavelength light, green wavelength light, and blue wavelength light, the light beam emitted by the fifth light source 115 can be ultraviolet light, and the ultraviolet light can have a wavelength range of 350 nm to 430 nm. Since the wavelength of the fifth light beam 1151 is the smallest, the third light combining element 123 can be a simple film system design that transmits short wavelengths and reflects long wavelengths, so that the fifth light beam 1151 can pass through the third light combining element 123, while the third light beam 1131 can be reflected by the third light combining element 123. As Figure 4 shown, the third light combining element 123 can be used to reflect the third light beam 1131 to the second light combining element 122, and the third light combining element 123 can be used to transmit the fifth light beam 1151 to the second light combining element 122; the third light beam 1131 can reach the converging component 130 after being reflected by the third light combining element 123 and then reflected by the second light combining element 122, and the fifth light beam 1151 can reach the converging component 130 after being transmitted by the third light combining element 123 and then reflected by the second light combining element 122. In such an endoscope light source device 10, such a design can make the internal structure more compact on the premise of ensuring that the distances of each light source along its optical path to the converging component 130 are approximately equal.

[0073] Exemplarily, the third light source 113 can be a blue light source. The blue wavelength light emitted by the blue light source can have a wavelength range of 430 nm to 500 nm. When the fifth light source 115 and the third light source 113 are located on the same side of the optical axis 140, since the ultraviolet wavelength light emitted by the fifth light source 115 can have a wavelength range of 350 nm to 430 nm, the wavelength ranges of the light beams emitted by the third light source 113 and the fifth light source 115 are similar, which is convenient for the production and processing of the third light combining element 123.

[0074] When the light beam emitted by the fifth light source 115 is ultraviolet light, due to the addition of ultraviolet light, and ultraviolet light can assist in more clearly highlighting the superficial blood vessels on the tissue, helping the doctor to find the diseased tissue. When such an endoscope light source device 10 is applied to an endoscope system, the illumination light with ultraviolet light is introduced into the endoscope 20, and the diagnostic and therapeutic effect can be better.

[0075] Exemplarily, the second light combining element 122 can be a filter. The light combining element in the form of a filter has a simpler structure and is also easier to produce and process.

[0076] Similarly, the third light combining element 123 can be a filter. The light combining element in the form of a filter has a simpler structure and is also easier to produce and process.

[0077] The calibration method of the endoscope light source device 10 provided by the present utility model may include:

[0078] Step S10: Set a plurality of light sources at positions having equal predetermined distances along their respective optical paths to the converging component;

[0079] Step S20: Set the calibration light source at a position where the distance along its optical path to the converging component is equal to the predetermined distance, measure the optical power of the light beam emitted by the calibration light source on the optical axis behind the converging component, and set the plane where the maximum optical power M is obtained as the predetermined converging plane;

[0080] Step S30: Measure the maximum optical power Ni of the light beam emitted by the light source to be debugged among the plurality of light sources on the optical axis behind the converging component respectively;

[0081] Step S40: Place an annular workpiece having a predetermined light-transmitting area at the predetermined converging plane, and measure the defined optical power m of the calibration light source within the predetermined light-transmitting area; and

[0082] Step S50: For each light source to be debugged, adjust the divergence angle of the light beam emitted by the light source to be debugged incident on the converging component, so that the defined optical power ni of the light beam emitted by the light source to be debugged within the predetermined light-transmitting area is ni = Ni × m / M, where i represents the i-th light source to be debugged.

[0083] Exemplarily, each of the plurality of light sources includes a light-emitting element and a collimating lens. Adjusting the divergence angle of the light beam emitted by the light source to be debugged incident on the converging component includes: adjusting the relative position between the light-emitting element and the collimating lens of the light source to be debugged.

[0084] Exemplarily, the calibration light source is one of the plurality of light sources, and the light source to be debugged is the light source other than the calibration light source among the plurality of light sources.

[0085] Exemplarily, the steps of measuring the optical powers of the calibration light source and the light source to be debugged using an optical power meter and placing an annular workpiece with a predetermined light-transmitting area at a predetermined convergence plane include: setting the optical power meter at the predetermined convergence plane and installing the annular workpiece at the head end of the optical power meter.

[0086] Exemplarily, step S30 may be executed before installing the annular workpiece 70 at the head end of the optical power meter.

[0087] When calibrating the endoscopic light source device, first, multiple light sources may be respectively set at positions having equal predetermined distances along their respective optical paths to the converging component 130. At this time, the distances between the multiple light sources and the converging component 130 along the optical paths are equal. Then, the calibration light source is set at a position where the distance along its optical path to the converging component is equal to the predetermined distance, the optical power of the light beam emitted by the calibration light source on the rear optical axis of the converging component is measured, and the plane where the maximum optical power M is obtained is set as the predetermined convergence plane. Among them, the calibration light source may be a light source independent of the multiple light sources, or the calibration light source may also be one of the multiple light sources. At this time, the distance from the calibration light source to the converging component 130 along the combined optical path is equal to the predetermined distance, that is, the distances between the calibration light source and other light sources and the converging component 130 along the optical paths are equal.

[0088] Subsequently, there are two methods to continue the calibration.

[0089] In the first method, after measuring the maximum optical power M of the calibration light source on the predetermined convergence plane 150, the maximum optical powers Ni of the light beams emitted by the light sources to be debugged among the multiple light sources on the rear optical axis of the converging component can be measured respectively. An annular workpiece 70 with a predetermined light-transmitting area may be placed at the predetermined convergence plane 150. Refer to Figure 6 , the annular workpiece 70 may be an annular part with a predetermined light-transmitting hole 71, and the predetermined light-transmitting area is the area of the predetermined light-transmitting hole 71. The annular workpiece 70 may be installed at the head end of the optical power meter, so that the light-receiving range of the optical power meter can be limited within the predetermined light-transmitting area, and thus the limited optical power m of the calibration light source under the predetermined light-transmitting area can be measured. Finally, for each light source to be debugged, the divergence angle of the light beam emitted by the light source to be debugged incident on the converging component is adjusted so that the limited optical power ni of the light beam emitted by the light source to be debugged within the predetermined light-transmitting area is equal to Ni×m / M, where i represents the i-th light source to be debugged. Among them, adjusting the divergence angle of the light beam emitted by the light source to be debugged incident on the converging component may include: adjusting the relative position between the light-emitting element of the light source to be debugged and the collimating lens.

[0090] In the second method, after measuring the maximum optical power M of the calibration light source on the predetermined converging surface 150, a ring-shaped workpiece with a predetermined light-transmitting area can be placed at the predetermined converging surface, and the limited optical power m of the calibration light source within the predetermined light-transmitting area can be measured. After measuring the limited optical power m of the calibration light source under the predetermined light-transmitting area, the ring-shaped workpiece can be removed, and the maximum optical power Ni of the light beam emitted by the light source to be debugged among multiple light sources can be measured respectively on the rear optical axis of the converging component. Finally, for each light source to be debugged, the divergence angle of the light beam emitted by the light source to be debugged incident on the converging component is adjusted so that the limited optical power ni of the light beam emitted by the light source to be debugged within the predetermined light-transmitting area is ni = Ni × m / M, where i represents the i-th light source to be debugged. Among them, adjusting the divergence angle of the light beam emitted by the light source to be debugged incident on the converging component may include: adjusting the relative position between the light-emitting element of the light source to be debugged and the collimating lens.

[0091] In the description of the present invention, it should be understood that the orientation or positional relationship indicated by orientation words such as "front", "rear", "upper", "lower", "left", "right", "lateral", "vertical", "perpendicular", "horizontal" and "top", "bottom", etc. is usually based on the orientation or positional relationship shown in the drawings. It is only for the convenience of describing the present invention and simplifying the description. Without contrary description, these orientation words do not indicate and imply that the device or element referred to must have a specific orientation or be constructed and operated in a specific orientation. Therefore, it cannot be understood as a limitation to the protection scope of the present invention; the orientation words "inside" and "outside" refer to the inside and outside relative to the contour of each component itself.

[0092] For the convenience of description, regional relative terms such as "above...", "over...", "on the upper surface of...", "above-mentioned", etc. can be used here to describe the regional positional relationship between one or more components or features shown in the drawings and other components or features. It should be understood that the regional relative terms not only include the orientation of the components described in the drawings, but also different orientations during use or operation. For example, if the components in the drawings are inverted as a whole, the components "above other components or features" or "over other components or features" will include the situation where the components are "below other components or structures" or "under other components or structures". Thus, the exemplary term "above..." can include both "above..." and "below...". In addition, these components or features can also be positioned at other different angles (such as rotating 90 degrees or other angles), and this article is intended to include all these situations.

[0093] It should be noted that the terms used herein are only for describing specific embodiments and are not intended to limit the exemplary embodiments according to the present utility model. As used herein, unless the context clearly indicates otherwise, the singular forms are also intended to include the plural forms. In addition, it should be understood that when the terms "comprise" and / or "include" are used in this specification, they specify the presence of features, steps, operations, components, assemblies, and / or combinations thereof.

[0094] It should be noted that the terms "first", "second", etc. in the specification, claims and above-mentioned drawings of the present utility model are used to distinguish similar objects and are not necessarily used to describe a specific order or sequence. It should be understood that the data used in this way can be interchanged under appropriate circumstances so that the embodiments of the present utility model described herein can be implemented in an order other than those illustrated or described herein.

[0095] The present utility model has been illustrated by the above embodiments. However, it should be understood that the above embodiments are only for the purpose of exemplification and illustration, and are not intended to limit the present utility model within the scope of the described embodiments. In addition, those skilled in the art can understand that the present utility model is not limited to the above embodiments, and more variations and modifications can be made according to the teachings of the present utility model, and these variations and modifications all fall within the scope of protection required by the present utility model. The scope of protection of the present utility model is defined by the appended claims and their equivalent scope.

Claims

1. An endoscope light source device, characterized in that: include: A plurality of light sources for emitting a plurality of light beams in different wavelength bands; A light combining component, arranged on the light output paths of the multiple light sources, for combining the multiple light beams; as well as A converging component is arranged on the light output path of the light combining component, and is used to converge the multiple combined light beams onto the optical axis behind the converging component, wherein: The endoscope light source device has a predetermined converging surface located behind the converging component and perpendicular to the optical axis, and each light beam has an illumination distribution with a similarity greater than or equal to 80% on the predetermined converging surface.

2. The endoscope light source device according to claim 1, characterized in that: The multiple light beams have maximum optical power at their respective convergence points, and each of the multiple light beams has limited optical power within a predetermined light-transmitting area on the predetermined convergence surface; Then, each of the light beams has an illumination distribution with a similarity greater than or equal to 80% on the predetermined converging surface, including: The ratio of the limited optical power of each light beam to its maximum optical power is equal.

3. The endoscope light source device according to claim 2, characterized in that: The predetermined converging surface passes through a converging point of one of the plurality of light beams.

4. The endoscope light source device according to claim 1, characterized in that: Each of the plurality of light sources comprises a light emitting element and a collimating lens arranged on a light emitting path of the light emitting element, wherein each of the light emitting elements has the same light emitting area, each of the collimating lenses has the same optical characteristics, and, The relative positions of each light emitting element and its corresponding collimating lens on their respective optical paths are arranged so that each light beam has an illumination distribution with a similarity greater than or equal to 80% on the predetermined converging surface.

5. The endoscope light source device according to claim 4, characterized in that: The distance from each light emitting element to the converging component along its own optical path is equal, and the position of each collimating lens on its own optical path is set so that each light beam has an illumination distribution with a similarity greater than or equal to 80% on the predetermined converging surface.

6. The endoscope light source device according to claim 5, characterized in that: The plurality of light sources include a first light source, a second light source and a third light source, The first light source and the second light source are arranged opposite to each other on both sides of the optical axis of the converging component. The light combining component includes a first light combining element arranged on the optical axis of the converging component. The first light combining element includes a first light combining portion and a second light combining portion. The first light combining portion is used to reflect a first light beam emitted by the first light source to the converging component and transmit a second light beam emitted by the second light source. The second light combining portion is used to reflect the second light beam to the converging component and transmit the first light beam. in: The third light source is arranged on the side of the optical axis of the converging component, and the light combining component further comprises a second light combining element arranged on the optical axis of the converging component, the second light combining element is closer to the converging component than the first light combining element, and the second light combining element is used to reflect the third light beam emitted by the third light source and transmit the second light beam and the first light beam; Alternatively, the third light source is disposed on the optical axis of the converging component, the third light source is farther away from the converging component than the first light combining element, and the first light combining element is further used for transmitting a third light beam emitted by the third light source.

7. The endoscope light source device according to claim 6, characterized in that: The first light combining unit includes a first filter, the second light combining unit includes a second filter, and the first filter and the second filter are cross-arranged; or The first light combining element is a light combining prism. A first light filter film and a second light filter film are cross-plated in the light combining prism. The first light filter film is configured as the first light combining portion, and the second light filter film is configured as the second light combining portion.

8. The endoscope light source device according to claim 6, characterized in that: The multiple light sources also include a fourth light source. The third light source is arranged on the side of the optical axis of the converging component. The fourth light source is arranged on the optical axis of the converging component and is farther away from the converging component relative to the first light combining element. The first light combining element and the second light combining element are also used to transmit a fourth light beam emitted by the fourth light source.

9. The endoscope light source device according to claim 8, characterized in that: The multiple light sources also include a fifth light source, and the fifth light source and the third light source are located on the same side of the optical axis of the converging component. The second light combining element is also used to reflect a fifth light beam emitted by the fifth light source. The light combining component also includes a third light combining element located on the side of the optical axis of the converging component, and the third light combining element is used to reflect one of the third light beam and the fifth light beam to the second light combining element and transmit the other of the third light beam and the fifth light beam to the second light combining element.

10. The endoscope light source device according to claim 9, characterized in that: The wavelengths of the first light beam, the fourth light beam and the second light beam increase or decrease successively; The wavelengths of the first light beam, the fourth light beam, and the second light beam are all greater than or smaller than the wavelengths of the third light beam and the fifth light beam.

11. An endoscope system, characterized in that: The invention comprises an endoscope and an endoscope light source device as claimed in any one of claims 1 to 10, wherein the receiving surface of the light guide portion of the endoscope is located on the predetermined converging surface.

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