CN211149052U - Confocal micro-endoscope based on spatial light modulator and digital micromirror array - Google Patents
Confocal micro-endoscope based on spatial light modulator and digital micromirror array Download PDFInfo
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- CN211149052U CN211149052U CN202020033199.9U CN202020033199U CN211149052U CN 211149052 U CN211149052 U CN 211149052U CN 202020033199 U CN202020033199 U CN 202020033199U CN 211149052 U CN211149052 U CN 211149052U
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Abstract
The utility model discloses a confocal micro-endoscope based on a spatial light modulator and a digital micromirror array, which comprises a laser, a beam expanding lens group, the spatial light modulator, a dichroic mirror, a coupling objective, an optical fiber bundle probe, a first imaging lens, the digital micromirror array and an area array photoelectric detector; the laser, the beam expanding lens group and the spatial light modulator are sequentially positioned on an incident light path of the dichroic mirror, the coupling objective lens and the optical fiber beam probe are sequentially positioned on a reflected light path of the dichroic mirror, light emitted from the optical fiber beam probe is irradiated onto human tissues and then excited to generate fluorescence, and the fluorescence reversely passes through the optical fiber beam probe and the coupling objective lens; the first imaging lens, the digital micromirror array and the area array photoelectric detector are sequentially positioned on the transmission light path of the fluorescence loop of the dichroic mirror. The scanning device aims to solve the technical problems that the scanning speed of a confocal micro-endoscope and the image acquisition speed are low and the imaging quality needs to be improved in the prior art.
Description
Technical Field
The utility model belongs to the endoscope field, more specifically relates to a confocal micro-endoscope based on spatial light modulator and digital micromirror array.
Background
The confocal endoscope can observe the morphological structure of cells in real time in a human body, greatly improves the detection rate and the detection speed of early cancers and tumors, and is the only means for acquiring cell-level resolution images in real time in the human body at present.
In the current probe type confocal endoscope in the market, a two-dimensional scanning galvanometer is generally adopted for carrying out light beam scanning, and a point detector such as a photomultiplier tube is used for carrying out signal detection. However, because the two-dimensional scanning galvanometer is a mechanical component, the scanning speed of the two-dimensional scanning galvanometer is limited by factors such as materials and precision, the current confocal endoscope system adopting the two-dimensional scanning galvanometer can only reach a frame rate of 4-10 frames per second, and the positioning precision of the mechanical component can be reduced due to the excessively high movement speed. And the mechanical parts can also reduce the precision along with the change of the temperature, so that the thermal drift is generated, and the image quality can be obviously reduced after the system is continuously operated for a period of time due to the limitation of the thermal drift, thereby influencing the final image quality.
The conventional confocal imaging system is generally provided with a detection pinhole in front of a detector, and the position and the size of the detection pinhole are difficult to change, so that the light energy utilization rate is low. There is a need for a confocal micro-endoscope that does not affect the final image quality while increasing the imaging speed, and that ensures a high light energy utilization rate.
Disclosure of Invention
To the above defect or the improvement demand of prior art, the utility model provides a confocal micro endoscope based on spatial light modulator and digital micromirror array, its aim at solve the confocal micro endoscope scanning speed among the prior art and the technical problem that the acquisition speed of image is slow, imaging quality remains to improve.
In order to achieve the above object, according to one aspect of the present invention, there is provided a confocal micro-endoscope based on a spatial light modulator and a digital micromirror array, comprising a laser, a beam expanding lens group, a spatial light modulator, a dichroic mirror, a coupling objective, an optical fiber bundle probe, a first imaging lens, a digital micromirror array, and an area array photodetector; the spatial light modulator is a spatial light modulator with pure phase modulation; the laser, the beam expanding lens group and the spatial light modulator are sequentially positioned on an incident light path of the dichroic mirror, the coupling objective lens and the optical fiber beam probe are sequentially positioned on a reflected light path of the dichroic mirror, light emitted from the optical fiber beam probe is irradiated onto human tissues and then excited to generate fluorescence, and the fluorescence reversely passes through the optical fiber beam probe and the coupling objective lens; the first imaging lens, the digital micromirror array and the area array photoelectric detector are sequentially positioned on the transmission light path of the fluorescence loop of the dichroic mirror.
Preferably, the frame rate of the area array photodetector is consistent with the frame rate of the digital micromirror array.
Preferably, the magnification ratio of the combination of the coupled objective lens and the first imaging lens is M1= d1/d0, wherein d1 is the diameter of the light-passing surface of the digital micromirror array, and d0 is the image plane field diameter; meanwhile, M1= F7/F5, F7 is a focal length of the first imaging lens, and F5 is a focal length of the coupled objective lens.
Preferably, the digital micro-mirror array further comprises a second imaging lens, and the second imaging lens is positioned between the digital micro-mirror array and the area array photodetector.
Preferably, the magnification of the second imaging lens is M2= d2/d1, where d1 is the diameter of the light-passing surface of the digital micromirror array, and d2 is the diameter of the light-passing surface of the area-array photodetector.
Preferably, the confocal micro-endoscope further comprises a reflector located between the digital micromirror array and the second imaging lens.
Preferably, the beam expanding lens group comprises a first beam expanding lens and a second beam expanding lens, and the first beam expanding lens is close to the laser; the beam expansion multiple of the beam expansion lens group = f2/f1, wherein f1 and f2 are focal lengths of the first beam expansion lens and the second beam expansion lens respectively.
Preferably, the beam expansion multiple of the beam expansion lens group = the clear area diameter of the spatial light modulator/the original spot diameter of the laser.
Generally, through the utility model discloses above technical scheme who conceives compares with prior art, can gain following beneficial effect:
the utility model provides a confocal micro-endoscope based on spatial light modulator and digital micromirror array, owing to include spatial light modulator, digital micromirror array, area array photoelectric detector simultaneously, both guaranteed the speed of acquireing of high scanning speed and image through the design, guaranteed the confocal characteristic again, avoided traditional scanning mirror "thermal drift" to the influence of image quality that shakes simultaneously, improved image quality.
And, the utility model discloses the spatial light modulator of pure phase modulation and these two different grade types of digital micromirror array have been utilized, wherein, the spatial light modulator of pure phase modulation can make and lead to light efficiency and reach about 90%, and each deflection state of spatial light modulator all corresponds with a point on the digital micromirror array, when the spatial light modulator accomplished the two-bit scanning of light beam, the state was also accomplished one "scanning" for "open" miniature speculum on the digital micromirror array (all miniature speculum mirrors are all "opened" and have been passed), consequently guaranteed high energy utilization when guaranteeing high imaging speed. Because optical signals are weak in endoscope fluorescence imaging, it is extremely important to ensure high energy utilization rate.
Drawings
Fig. 1 is a schematic structural diagram of a confocal micro-endoscope based on a spatial light modulator and a digital micromirror array according to the present invention.
Detailed Description
In order to make the objects, technical solutions and advantages of the present invention more clearly understood, the present invention is further described in detail below with reference to the accompanying drawings and embodiments. It should be understood that the specific embodiments described herein are merely illustrative of the invention and are not intended to limit the invention. Furthermore, the technical features mentioned in the embodiments of the present invention described below can be combined with each other as long as they do not conflict with each other.
As shown in fig. 1, the utility model provides a confocal micro-endoscope based on spatial light modulator and digital micromirror array, including laser 1, expand beam lens group 2, spatial light modulator 3, dichroic mirror 4, coupling objective 5, fiber bundle probe 6, first imaging lens 7, digital micromirror array 8, area array photoelectric detector 11; the laser 1, the beam expanding lens group 2 and the spatial light modulator 3 are sequentially positioned on an incident light path of the dichroic mirror 4, the coupling objective lens 5 and the optical fiber bundle probe 6 are sequentially positioned on a reflected light path of the dichroic mirror 4, light emitted from the optical fiber bundle probe 6 is irradiated onto human tissues and then excited to generate fluorescence, and the fluorescence reversely passes through the optical fiber bundle probe 6 and the coupling objective lens 5; the first imaging lens 7, the digital micromirror array 8 and the area array photodetector 11 are sequentially located on the transmission light path of the fluorescence loop of the dichroic mirror 4.
The spatial light modulator 3 is a spatial light modulator with pure phase modulation, the light transmission efficiency of the spatial light modulator can reach about 90%, and the spatial light modulator is used for realizing two-dimensional scanning of light beams and obtaining high scanning speed; the digital micromirror array 8 is a device composed of a large number of micromirrors, the micromirrors can only be spatially positioned at one of two angles, one of the two angles is defined as "on", light reflected at the angle can enter a subsequent optical path, and the other angle is "off", and light reflected at the angle cannot enter the subsequent optical path. The micro reflectors of the fluorescence at the focusing light spot of the digital micro-mirror array 8 are set to be 'on', which is equivalent to realizing the function of a small hole in the traditional confocal system, ensuring the light slicing capability, and controlling the size and the shape of the small hole through the micro reflectors set to be 'on'. For example, m × n micro mirrors are provided as small holes, i.e., rectangular shapes having an area of m × n micro mirrors.
The digital micromirror array 8 is used as a confocal small hole, filters stray light outside a focal plane, and ensures that the system has the capability of optical sectioning, so that the endoscope can directly distinguish cell structures in human tissues, the size and the shape of the small hole can be changed at will, the small holes with different sizes can be selected according to observation objects with different sizes, and support is provided for the application of the confocal endoscope in more scenes. The pixels of the photoelectric area array detector 11 correspond to the pixels of the digital micro-mirror array 8 one by one, so that high image acquisition speed is obtained. Because the utility model discloses utilize the spatial light modulator of these two different grade types of spatial light modulator and digital micromirror array, guaranteed high energy utilization, because optical signal is all very weak in endoscope fluorescence formation of image, it is extremely important to guarantee high energy utilization. The method is a novel combination of light beam scanning and signal detection, and can be applied to a confocal endoscope system.
When in work: laser emitted by the laser 1 is expanded by the beam expanding lens group 2 and then enters the spatial light modulator 3, the spatial light modulator 3 is used for deflecting light beams in a two-dimensional space, parallel light beams emitted from the spatial light modulator 3 enter the dichroic mirror 4, are reflected by the dichroic mirror 4 to enter the coupling objective 5, are coupled to the optical fiber beam probe 6 by the coupling objective 5 and then are emitted to human tissues from the far end of the optical fiber beam probe 6. The spatial light modulator 3 deflects the light beam in two dimensions continuously, so that the light focused on the human tissue through the coupling objective lens 5 also shows a continuous motion track, and the two-dimensional scanning of the incident light on the human tissue image plane is realized. The fluorescence excited by the incident light reversely passes through the fiber bundle probe 6 and the coupling objective 5, is transmitted from the dichroic mirror 4, and is imaged on the plane of the digital micromirror array 8 by the first imaging lens 7. Each object point on the image plane corresponds to an image point on the digital micromirror array 8, and light near the image point is reflected by the micro-mirrors in the digital micromirror array 8 to a subsequent light path and imaged on the pixels of the photoelectric area array detector 11.
The spatial light modulator 3 operates in synchronization with the digital micromirror array 8: the spatial light modulator 3 performs phase modulation on incident light, changes the angle of emergent light by changing the wave front of the incident light, plays a role in light beam deflection, each deflection state of the spatial light modulator 3 becomes a point on an image surface after passing through the coupling objective lens 5 and the optical fiber bundle probe 6, and the point on the image surface is conjugated with another point on the digital micro-mirror array 8 after passing through the coupling objective lens 5 and the dichroic mirror 4. The micromirror in the digital micromirror array 8 near the focal point corresponding to the deflected state of the light beam from the spatial light modulator 3 is in the "on" state, and the other micromirrors are in the "off" state. The utility model discloses just because utilized pure phase modulation's spatial light modulator (its logical light efficiency can reach about 90%) and digital micromirror array to because both synchronous working, guaranteed high energy utilization, and obtained fabulous formation of image effect.
As another example, the frame rate of the area array photodetector 11 is consistent with the frame rate of the digital micromirror array 8. The scanning speed of the spatial light modulator 3 can reach 800-1000 frames per second, the response time of the digital micromirror array is about 10-20 ns, and the frame rate of the area array photoelectric detector 11 is set to be consistent with the frame rate of the digital micromirror array 8, so that the system can reach a high overall frame rate. The improvement of the imaging effect of the high frame rate is very obvious in practical use, and firstly, the appearance of a user can be improved, so that the user can see more continuous and smooth images; second, at high frame rates, more tissue structure information is acquired in the same time, saving valuable viewing time for the user.
The coupling objective lens 5 and the first imaging lens 7 restrain the curvature radius of the lens surface and the lens thickness through optical design, and aberration is corrected, so that the imaging quality is close to the diffraction limit.
As another embodiment, the magnification of the combination of the coupling objective lens 5 and the first imaging lens 7 is designed to ensure that the size of the image surface on the digital micromirror array 8 surface after imaging is matched with the total light transmission area of the digital micromirror array 8, thereby improving the light transmission efficiency and ensuring that enough energy reaches the area array photodetector 11. Specifically, the magnification M1= d1/d0 of the combination of the coupling objective lens 5 and the first imaging lens 7, where d1 is the diameter of the light-passing surface of the digital micromirror array 8, and d0 is the image plane field diameter; where M1= F7/F5, F7 is the focal length of the first imaging lens 7, and F5 is the focal length of the coupling objective lens 5. For example, the light-passing surface of the digital micromirror array 8 has a size of 19.4mm by 12.1mm, i.e., the diameter d1=23mm of its light-passing surface; field diameter d0=0.5mm on the image plane, calculated as: m1= d1/d0= 46. In order to ensure that the imaging areas are matched, the magnification M1= the focal length F7 of the first imaging lens 7/the focal length F5 of the coupling objective lens 5, and the focal length of the coupling objective lens 5 is designed to be 5mm, and the focal length of the imaging lens 7 is designed to be 270mm, which meets the requirement.
As another embodiment, a second imaging lens 10 is further included, and the second imaging lens 10 is located between the digital micromirror array 8 and the area array photodetector 11. Since the light near the focal point is reflected by the digital micromirror array 8 as diverging light, a second imaging lens 9 is also required to image the focal point on the area array photodetector 11. Aberration is corrected by the design of the second imaging lens 9 so that the imaging quality approaches the diffraction limit.
The magnification of the second imaging lens 9 needs to match the size of the light-passing surface of the digital micromirror array 8 and the size of the photosensitive surface of the area array photodetector 11, and the passing efficiency can also be improved, specifically, the magnification M2= d2/d1 of the second imaging lens 9, where d1 is the diameter of the light-passing surface of the digital micromirror array 8, and d2 is the diameter of the light-passing surface of the area array photodetector 11. For example, the light-passing surface diameter d1=23mm of the dmd 8, and the light-passing surface diameter d2=16mm of the area array photodetector 11, which is calculated by taking 1 inch CMOS as an example: m2=16/23=0.7, it suffices to design the magnification M2 of the second imaging lens 9 to be equal to 0.7.
As another embodiment, the confocal micro-endoscope further comprises a reflector 9, the reflector 9 is located between the digital micromirror array 8 and the second imaging lens 10, because the light near the image point is deflected by an angle after being reflected by the digital micromirror array 8, the angle of the light can be changed by the reflector 9, so as to facilitate the position arrangement of the second imaging lens 10. When the optical imaging device works, light near an image point is reflected by the digital micromirror array 8 and then reflected by the total reflecting mirror 9, and is imaged on a pixel of the photoelectric area array detector 11 through the second imaging lens 10.
As another embodiment, the beam expanding lens group 2 includes a first beam expanding lens and a second beam expanding lens, and the first beam expanding lens is close to the laser 1; the beam expansion multiple = f2/f1 of the beam expanding lens group 2, wherein f1 and f2 are focal lengths of the first beam expanding lens and the second beam expanding lens, respectively. The first beam expanding lens is used for focusing incident parallel light beams, the second beam expanding lens is used for re-collimating the focused light beams into parallel light, the focal length of the second beam expanding lens is larger than that of the first beam expanding lens, so that the diameter of the emergent parallel light beams is enlarged, the focuses of the two beam expanding lenses are guaranteed to be overlapped, and the imaging quality of the two beam expanding lenses reaches the diffraction limit.
As another example, the beam expansion multiple of the beam expansion lens group 2= the clear area diameter of the spatial light modulator 3/the original spot diameter of the laser 1, and functions as: the utilization rate of the spatial light modulator 3 is improved, the spatial light modulator 3 is in a pixel type, the whole light passing surface of the spatial light modulator is divided into a plurality of sub-parts, each sub-part carries out independent modulation on light passing through the sub-part, and the more the sub-parts covered by incident light beams are, the higher the utilization rate of the spatial light modulator 3 is; and secondly, the quality of the scanned light beam is improved, and similarly, because the spatial light modulator 3 is in a pixel type, the light beam is a spatially continuous light field when being incident, and the spatially continuous light field after passing through the spatial light modulator 3 is not continuous any more but is formed by combining the pixels of the spatial light modulator 3, the more the pixels participating in forming the light beam, the higher the reduction precision of the light field is, and the smaller the aberration is.
It will be understood by those skilled in the art that the foregoing is merely a preferred embodiment of the present invention, and is not intended to limit the invention to the particular forms disclosed, but on the contrary, the intention is to cover all modifications, equivalents, and alternatives falling within the spirit and scope of the invention as defined by the appended claims.
Claims (8)
1. A confocal micro-endoscope based on a spatial light modulator and a digital micromirror array is characterized by comprising a laser (1), a beam expanding lens group (2), a spatial light modulator (3), a dichroic mirror (4), a coupling objective lens (5), an optical fiber bundle probe (6), a first imaging lens (7), a digital micromirror array (8) and an area array photoelectric detector (11); the spatial light modulator (3) is a spatial light modulator with pure phase modulation;
the laser (1), the beam expanding lens group (2) and the spatial light modulator (3) are sequentially positioned on an incident light path of the dichroic mirror (4), the coupling objective lens (5) and the optical fiber bundle probe (6) are sequentially positioned on a reflected light path of the dichroic mirror (4), light emitted from the optical fiber bundle probe (6) is irradiated onto human tissues and then excited to generate fluorescence, and the fluorescence reversely passes through the optical fiber bundle probe (6) and the coupling objective lens (5);
the first imaging lens (7), the digital micromirror array (8) and the area array photoelectric detector (11) are sequentially positioned on a transmission light path of a fluorescence loop of the dichroic mirror (4).
2. The confocal microscopy endoscope based on spatial light modulator and digital micromirror array according to claim 1, characterized in that the frame rate of the area array photodetector (11) is identical to the frame rate of the digital micromirror array (8).
3. The confocal micro-endoscope based on spatial light modulator and digital micromirror array of claim 1, characterized in that the magnification ratio M1= d1/d0 of the coupling objective lens (5) and the first imaging lens (7) combination, wherein d1 is the diameter of the light-passing surface of the digital micromirror array (8) and d0 is the image plane field-of-view diameter; meanwhile, M1= F7/F5, F7 being the focal length of the first imaging lens (7), and F5 being the focal length of the coupling objective lens (5).
4. The confocal microendoscope based on a spatial light modulator and a digital micromirror array of claim 1, further comprising a second imaging lens (10), the second imaging lens (10) being located between the digital micromirror array (8) and the area array photodetector (11).
5. The confocal micro-endoscope based on spatial light modulator and digital micromirror array of claim 4, characterized in that the magnification M2= d2/d1 of the second imaging lens (10), wherein d1 is the diameter of the light-passing surface of the digital micromirror array (8) and d2 is the diameter of the light-passing surface of the area-array photodetector (11).
6. The confocal micro-endoscope based on a spatial light modulator and a digital micromirror array of claim 1, further comprising a mirror (9), wherein the mirror (9) is located between the digital micromirror array (8) and a second imaging lens (10).
7. The confocal micro-endoscope based on the spatial light modulator and the digital micromirror array of claim 1, characterized in that the beam expanding lens group (2) comprises a first beam expanding lens and a second beam expanding lens, and the first beam expanding lens is close to the laser (1); the beam expansion multiple = f2/f1 of the beam expansion lens group (2), wherein f1 and f2 are focal lengths of the first beam expansion lens and the second beam expansion lens respectively.
8. The confocal micro-endoscope based on spatial light modulator and digital micro-mirror array according to claim 7, characterized in that the beam expansion multiple of the beam expansion lens group (2) = clear area diameter of the spatial light modulator (3)/original spot diameter of the laser (1).
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| CN112596349A (en) * | 2021-01-14 | 2021-04-02 | 之江实验室 | Two-photon parallel direct writing device and method based on multi-point array generation and independent control |
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Address after: Room 804 and Room 805, Building 1, No. 188, Fuchunjiang Road, Suzhou, Jiangsu Province, 215163 Patentee after: Jingwei Shida Medical Technology (Suzhou) Co.,Ltd. Address before: 436000, the third floor, Phoenix Avenue, special area No. 1, Wutong Lake New District, Liangzi Lake, Ezhou, Hubei Patentee before: JINGWEI SHIDA MEDICAL TECHNOLOGY (WUHAN) CO.,LTD. |
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