CN111722388A - Three-dimensional miniature endoscope - Google Patents
Three-dimensional miniature endoscope Download PDFInfo
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- CN111722388A CN111722388A CN201910712514.2A CN201910712514A CN111722388A CN 111722388 A CN111722388 A CN 111722388A CN 201910712514 A CN201910712514 A CN 201910712514A CN 111722388 A CN111722388 A CN 111722388A
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Abstract
The invention relates to the technical field of endoscopes, in particular to a three-dimensional miniature endoscope, which comprises a miniature imaging probe, wherein the miniature imaging probe comprises an objective lens which can be right opposite to an external sample, the objective lens is provided with a front aperture for collecting fluorescence photons generated by the external sample, the objective lens is connected with a photoelectric detector for collecting the fluorescence photons which can not be collected by the front aperture, and the photoelectric detector comprises an optical filter, a photoelectric sensitive unit and a driving unit which are sequentially connected with one another; meanwhile, the device also comprises a plane dichroic mirror and a vertical dichroic mirror. The invention reasonably utilizes the photoelectric detector to replace an additional optical element in the prior art, reduces the volume of the endoscope on the premise of ensuring the efficiency of collecting fluorescence photons by the endoscope, solves the problem that the volume of the endoscope is large to influence the use of the endoscope in the prior art, and simultaneously realizes the three-dimensional scanning of the endoscope by utilizing the plane dichroic mirror scanner and the vertical dichroic mirror scanner.
Description
Technical Field
The invention relates to the technical field of endoscopes, in particular to a three-dimensional miniature endoscope.
Background
With the development of science and technology, medical endoscopes have been widely used in the medical field, and are one of the important tools for human body to peep and treat organs in the human body. The structure of the endoscope is greatly improved four times in the development process of over 200 years, and the image quality of the endoscope from the primary hard tube type endoscope, the semi-curved type endoscope to the fiber endoscope and the current electronic endoscope is also in a secondary leap. At present, the endoscope can obtain a color photo or a color television image by using LED illumination, and meanwhile, the image is not a common image of a tissue organ, but a microscopic image observed under a microscope, and tiny lesions are clear and distinguishable. According to the existing clinical experience, the smaller the volume of the miniature imaging probe of the endoscope and the shorter the rigid section, the pain of the patient can be reduced to the greatest extent, so that the endoscope is always developed towards miniaturization.
The existing endoscope generally comprises an objective lens, a scanning lens, a focusing lens, a cylindrical lens, a glass slide, a collecting lens and the like, wherein the objective lens is used for converging laser light from a micro-electromechanical scanner into a living body sample so as to excite the living body sample to generate a fluorescence signal and output the fluorescence signal; the scanning lens is arranged on a light path between the micro-electromechanical scanner and the objective lens and is used for converting laser with angle change generated by two-dimensional scanning of the micro-electromechanical scanner into laser with position change; a focusing lens for focusing the laser; a lenticular lens for forming a line focus; a wave plate for changing the polarization direction of the laser light; and the collecting lens is used for collecting the nonlinear optical signal and inputting the nonlinear optical signal into the laser output optical fiber.
In nonlinear optical imaging microscopes, in particular multiphoton fluorescence microscopes, near-infrared laser pulses are focused by an objective lens and excite an isotropically emitted fluorescence signal in a sample. Biological tissue generally exhibits optical properties of strong absorption and high scattering. For epi-illumination (Epifluorescence) fluorescence detection, the same objective lens is used both to focus the excitation light and to collect the fluorescence signal. The intensity of the fluorescence signal collected by the objective lens depends on the numerical aperture of the objective lens and the front aperture of the objective lens, and the greater the numerical aperture of the objective lens and the front aperture of the objective lens, the greater the intensity of the fluorescence signal that the objective lens can collect.
Many techniques have been developed in recent years to collect fluorescence photons that cannot be collected by an objective lens, for example, a retroreflection objective lens was proposed in 2006; the emission detection technology adopting a parabolic mirror in 2007 and adopting a cylindrical mirror in 2011 is proposed, 10-time fluorescence collection efficiency enhancement is obtained through simulation, and 8.9-time fluorescence collection efficiency enhancement is obtained through experiments. In addition, by arranging 5-8 high numerical aperture optical fibers around the objective lens to collect the fluorescence that cannot be collected by the objective lens, 2-fold fluorescence collection efficiency enhancement can be obtained at the high numerical aperture objective lens and 20-fold fluorescence collection efficiency enhancement can be obtained at the low numerical aperture objective lens.
The above techniques for enhancing fluorescence collection efficiency all employ additional optical elements to collect the fluorescence photons that the objective lens cannot collect. Because the scattering angle and the discreteness of fluorescence photon are very big, the multiple reflection path of fluorescence photon is complicated after entering into extra collection light path, the loss is big, lead to extra optical element's actual collection efficiency to be limited, in order to guarantee the collection efficiency of fluorescence photon, the volume that has to be used for strengthening the extra optical element of fluorescence collection efficiency increases, this has formed serious technical obstacle towards the miniaturized development trend of endoscope, therefore how under the prerequisite of the collection fluorescence photon efficiency of assurance endoscope, can also reduce the volume of endoscope becomes the problem that awaits the opportune moment and solves.
Disclosure of Invention
In order to solve the problems, the invention provides a three-dimensional miniature endoscope which solves the problem that the endoscope is large in size and obstructs the use of the endoscope on the premise of ensuring the efficiency of the endoscope for collecting fluorescence photons.
In order to achieve the purpose, the invention adopts the technical scheme that: a three-dimensional miniature endoscope comprises a miniature imaging probe, wherein the miniature imaging probe comprises an objective lens which can be right opposite to an external sample, a front aperture used for collecting fluorescence photons generated by the external sample is formed in the objective lens, the objective lens is connected with a photoelectric detector used for collecting the fluorescence photons which can not be collected by the front aperture, the photoelectric detector comprises an optical filter, a photoelectric sensitive unit and a driving unit which are sequentially connected with each other, and the optical filter and the objective lens can be simultaneously right opposite to the external sample; the optical filter is used for filtering back-reflected and back-scattered fluorescence photons, the electric sensitive unit is used for converting the fluorescence photons passing through the optical filter into electric signals, and the driving unit is used for providing high voltage and driving signals for the photoelectric sensitive unit and is connected with an external amplifying circuit and a computer.
The principle of the invention is as follows: near infrared laser pulses are focused by an objective lens and then excite isotropically emitted fluorescence signals (namely fluorescence photons) in a sample, because the scattering angle discreteness of the fluorescence photons is very large, a front aperture arranged on the objective lens can only collect part of the fluorescence photons and the fluorescence photons can not enter the front aperture and emit the fluorescence photons to a photoelectric detector, an optical filter in the photoelectric detector is used for filtering exciting light which is reflected back and scattered back, then a photoelectric sensitive unit senses the fluorescence photons filtered by the optical filter and converts the received fluorescence light signals into electric signals, wherein a driving unit is used for providing high voltage and driving signals for the photoelectric sensitive unit to enable the photoelectric sensitive unit to convert the received fluorescence photon signals into the electric signals, meanwhile, the driving unit is connected with an external amplifying circuit and a computer and transmits the electric signals generated by the photoelectric sensitive unit to the external amplifying circuit and the computer, so that fluorescence photons not collected by the front aperture can be detected by the external circuitry and computer through the photodetector, allowing as many fluorescence photons as possible to be collected, thereby increasing the imaging clarity of the endoscope.
Because the photoelectric detector is adopted to replace the traditional extra optical element to collect fluorescence photons, and the optical filter, the photoelectric sensitive unit and the driving unit for collecting fluorescence photon signals are integrated in the photoelectric detector, the volume of the photoelectric detector is greatly reduced compared with the traditional extra optical element, so that the whole volume of the enhanced fluorescence photon collecting component is reduced, and the shielding of the enhanced fluorescence photon collecting component (the photoelectric detector in the application) on an imaging area is avoided, thereby enabling an electrophysiological experiment to have a larger operation space and realizing the accurate and smooth performance of the electrophysiological experiment; and because the volume of the photoelectric detector is reduced, the volume of the whole endoscope is further reduced while the fluorescence photon collection efficiency is ensured, the contradiction between the fluorescence photon collection efficiency and the volume in the current endoscope is well solved, and the endoscope is well improved.
The scheme has the advantages that:
1. the endoscope has small volume: compared with the prior art that an additional optical element is needed to collect the fluorescence photons which cannot be collected by the front aperture, the light path of the additional optical element is complex, the size of the additional optical element is large, the contradiction between the fluorescence photon collection efficiency and the size of the endoscope cannot be solved, and the outer diameter of a commercial endoscope in the prior art is generally 9-11 mm. Utilize the photoelectric detector to replace extra optical element in this application, change the principle that traditional extra optical element was collected to fluorescence photon, make fluorescence photon can be collected by photoelectric detector and form the signal of telecommunication, simplify the light path and make the whole volume of endoscope reduce, through the improvement of this application, the volume of endoscope can reduce to 5 x 5mm, and its fluorescence photon collection efficiency is higher, consequently, how to balance its volume and the problem of guaranteeing fluorescence photon collection efficiency of endoscope among the prior art has been solved well, make under the prerequisite that the collection fluorescence photon collection efficiency obtained the guarantee, the volume of endoscope obtains reducing.
2. The efficiency of collecting fluorescence photons is high: compared with the prior art that the additional optical element is used for collecting the fluorescence photons which are not collected by the front aperture, the light path of the additional optical element is complex, the scattering angle and the discreteness of the fluorescence photons are large, when the fluorescence photons are collected by the additional optical element, part of the fluorescence photons cannot be collected in the transmission of the additional optical element, when the fluorescence photons are collected by the photoelectric detector in the application, the fluorescence photons entering the optical filter are detected by the photoelectric sensitive unit immediately to generate an electric signal, the transmission distance of the fluorescence photons is small, the unnecessary loss of the fluorescence photons can be reduced, and therefore the collection efficiency of the fluorescence photons is improved.
Furthermore, the number of the photoelectric detectors is a plurality, and the plurality of photoelectric detectors are uniformly distributed in the circumferential direction of the front aperture.
Compared with the prior art that the additional optical element is used for collecting the fluorescence photons which cannot be collected by the front aperture, the fluorescence photons are large in scattering angle and discreteness, the collection of the fluorescence photons by the front aperture is limited, the fluorescence photons on the periphery of the front aperture in the circumferential direction cannot be collected, due to the light path propagation characteristic of the existing additional optical element, the additional optical element is required to be used for guiding the fluorescence photons, and the additional optical element cannot be distributed in the circumferential direction of the front aperture (because if the additional optical element is distributed in the circumferential direction of the front aperture, the light paths of the additional optical elements influence each other to cause the reduction of the collection efficiency of the fluorescence photons). In this scheme, because photoelectric detector's volume is less, the fluorescence photon that gets into photoelectric detector simultaneously is direct to be responded to by the sensitive unit of photoelectricity and forms the signal of telecommunication, and its light path is simple and needn't utilize optical element to carry out extra guide to the circumference in time preceding aperture can be set up a plurality of photoelectric detector, thereby makes the efficiency that the endoscope collected fluorescence photon obtain promoting, makes the imaging effect of endoscope better.
The device further comprises a plane dichroic mirror scanner, a laser unit and a control unit, wherein the plane dichroic mirror scanner is used for separating laser and a nonlinear optical signal, outputting the nonlinear optical signal and changing the incident angle of the laser to enable the laser to perform two-dimensional point scanning on the plane of the internal tissue of the external sample; and the vertical dichroic mirror scanner is used for scanning a far-end Z axis to realize three-dimensional imaging.
The planar dichroic mirror scanner is used for finishing two-dimensional scanning on the plane of the internal tissue of the external sample, meanwhile, the vertical dichroic mirror is used for finishing scanning on a far-end Z axis, and the planar dichroic mirror scanner and the vertical dichroic mirror scanner are combined, so that three-dimensional scanning on the external sample is finished.
Further, a collimating lens for collimating the laser light output from the laser input fiber and reducing chromatic aberration between the laser lights of different frequencies and outputting a laser signal is included.
The collimating lens collimates the polarized laser light into parallel light (collimation processing) and reduces chromatic aberration between the laser lights with different frequencies (achromatization processing), so that the laser light input into the plane dichroic mirror has better optical performance.
Further, the plane dichroic mirror scanner comprises a dichroic lens and a micro-electromechanical driver for driving the dichroic lens to change the angle, the dichroic lens is polarization sensitive, reflects S-polarized light and transmits p-polarized light, the dichroic lens is fixedly connected to the micro-electromechanical driver, and the plane dichroic mirror scanner is located on a back focal plane of the objective lens.
In the scheme, s-shaped linear polarized laser is output to a collimating lens from a laser input optical fiber, the s-shaped linear polarized laser is reflected and focused into a linear shape in a certain direction (X direction) on the surface of a plane dichroic mirror scanner through a cylindrical lens, the plane dichroic mirror scanner reflects the s-shaped linear polarized laser, then the focusing lens collimates the s-shaped linear polarized laser in the X direction and focuses the s-shaped linear polarized laser into a linear shape in the other direction (Y direction) vertical to the X direction, the s-shaped linear polarized laser continuously passes through a glass slide, the polarization direction of the s-shaped linear polarization rotates for 45 degrees, then the laser is focused on the surface of a vertical dichroic mirror scanner in the Y direction, the plane vertical dichroic mirror scanner reflects the laser, the reflected and diffused laser passes through the glass slide again, the polarization direction of the laser rotates for 45 degrees in the same direction again to become p-shaped linear polarized light, the p-shaped linear polarized light is focused in the X direction through the focusing lens again, and the, the planar dichroic mirror scanner transmits p-type linear polarized laser with the same wavelength, the dichroic mirror scanner is located on a back focal plane of the objective lens, a movable lens in the planar dichroic mirror scanner rotates along a rotating shaft parallel to an X axis, finally, p-type linear polarized light forms a linear focus which is located in a sample and is collimated in the X direction and focused in the Y direction through the objective lens, and the linear focus scans along the X direction, so that a two-dimensional scanning track is formed, and the laser performs two-dimensional linear scanning on a plane of an internal tissue of an external sample.
Further, the vertical dichroic mirror scanner has the same structure as the planar dichroic mirror scanner, and is located on the back focal plane of the cylindrical lens.
The structure of the vertical dichroic mirror scanner is the same as that of the planar dichroic mirror scanner, except that the vertical dichroic mirror scanner is positioned on the back focal plane of the cylindrical lens, when the dichroic mirror scanner completes one frame of two-dimensional line-scanned image, the movable dichroic mirror on the vertical dichroic mirror scanner is moved by a distance along the optical axis (Z direction), the two-dimensional line scan plane of the internal tissue of the external sample is also moved a distance along the optical axis by the principle of remote scanning (remotesScaning, see Botcherby EJ, Smith CW, Kohl MM, et al. Abstract-free-three-dimensional multiphoton imaging of neural activity at kHz rates. proceedings. the National Academy of Sciences of the United States of America.2012; 109(8):2919-2924.doi:10.1073/pnas.1111662109.) three-dimensional line scanning is achieved by scanning in the Z direction on a vertical dichroic mirror scanner.
When the endoscope is used, because the patient cannot be injected with the fluorescent dye during clinical use, only 3 label-free signal modes of two-photon excited autofluorescence, second harmonic generation and coherent anti-Stokes Raman scattering can be applied to clinic, and for the three label-free signal imaging modes, the scheme can be realized by changing the wavelength of laser in a laser incidence optical fiber and configuring a dichroic mirror scanner with different parameters; and because this scheme does not set up scanning lens and tube lens, can the whole volume of effectual reduction miniature optical probe to reach the purpose that reduces the endoscope volume. In addition, in the scheme, because the wavelengths of the laser signal input by the laser input optical fiber and the nonlinear optical signal received by the focusing lens are different (namely, the wavelengths of the laser signal and the nonlinear optical signal have a plurality of different wavelengths), the chromatic aberration effect can be achieved through the collimating lens, and the basic imaging requirement can be met.
Further, a reflecting mirror is arranged on a light path between the collimating lens and the plane dichroic mirror scanner.
The reflecting mirror is arranged on a light path between the collimating lens and the plane dichroic mirror scanner and used for adjusting the angle of the laser output by the collimating lens and reflecting the laser to the plane dichroic mirror scanner, so that the plane dichroic mirror scanner obtains the lasers with different incidence angles, and imaging is facilitated.
Furthermore, the reflector comprises a transmission surface and a reflection surface, wherein the transmission surface is provided with a transmission coating layer for enhancing the transmissivity, and the reflection surface is provided with a reflection coating layer for enhancing the reflectivity.
The transmission coating layer for enhancing the transmissivity and the reflection coating layer for enhancing the reflectivity are arranged on the reflector, so that the transmissivity and the reflectivity of the reflector can be enhanced, and the reflector has a better reflection effect.
Further, the number of the reflecting mirrors is plural.
Because the endoscope is generally small in volume, the laser input optical fiber and the laser output optical fiber are required to be reduced in installation volume as much as possible, and the positions of the laser input optical fiber and the laser output optical fiber are very close to each other, a plurality of reflecting mirrors are arranged in the endoscope and used for adjusting the light path.
Furthermore, the objective lens, the photoelectric detector, the plane dichroic mirror scanner, the vertical dichroic mirror scanner, the cylindrical lens, the collimating lens and the reflecting mirror are all provided with a shell for wrapping.
All the components are wrapped by the shell, so that the internal components of the endoscope and the external sample are separated, and the influence of the external sample on the operation of the endoscope during the detection of the endoscope is avoided.
Drawings
Fig. 1 is a schematic diagram of a three-dimensional miniature endoscope according to an embodiment of the present invention.
Fig. 2 is a schematic diagram of a three-dimensional miniature endoscope according to an embodiment of the present invention.
Fig. 3 is a schematic diagram of three-dimensional scanning of a three-dimensional miniature endoscope according to an embodiment of the present invention.
FIG. 4 is a schematic diagram of a photodetector of a three-dimensional miniature endoscope according to an embodiment of the present invention.
FIG. 5 is a diagram illustrating the cooperation of the objective lens and the photodetector of the three-dimensional miniature endoscope according to the first embodiment of the present invention.
FIG. 6 is a diagram illustrating the cooperation of the objective lens and the photodetector of the three-dimensional miniature endoscope according to the second embodiment of the present invention.
Detailed Description
The following is further detailed by way of specific embodiments:
reference numerals in the drawings of the specification include: a collimator lens 10, a cylindrical lens 12, a reflecting mirror 20, a planar dichroic mirror scanner 30, an objective lens 40, a focusing lens 50, a slide glass 60, a vertical dichroic mirror scanner 70, a collecting lens 80, a laser input fiber 90, a laser output fiber 91, a housing 100, a substrate 11, a driver 22, a photodetector 33, a filter 331, a photo-sensitive unit 332, and a driving unit 333.
Example one
One embodiment, as shown generally in fig. 1, 2 and 3, a three-dimensional miniature endoscope comprises a miniature imaging probe enclosed by a housing 100, the miniature imaging probe comprising, in order along an optical path: collimating lens 10, cylindrical lens 12, reflecting mirror 20, plane dichroic mirror scanner 30, objective lens 40, focusing lens 50, slide 60, perpendicular dichroic mirror scanner 70 and collecting lens 80, wherein objective lens 40 includes the front aperture that is used for collecting fluorescence photon, and the vertical setting of front aperture and lower extreme can just face with outside sample after passing shell 100 bottom.
The objective lens 40 is an aspheric lens, and the collimating lens 10 is used for collimating the laser light output from the laser input fiber 90, reducing chromatic aberration between the laser lights of different frequencies, and outputting a laser signal to the reflecting mirror 20. The objective lens 40 of the aspherical lens has a curvature radius varying with the central axis to improve optical quality, reduce optical elements, and reduce design cost.
The cylindrical lens 12 is used to focus the collimated laser light into a line focus in a certain direction (herein referred to as X direction) on the surface of the planar dichroic mirror scanner 30, that is, the focal position of the cylindrical lens 12 in the certain direction (X direction) is on the surface of the dichroic mirror, and the focal position of the cylindrical lens 12 in another direction (herein referred to as Y direction) orthogonal to the certain direction (X direction) is not on the surface of the dichroic mirror.
The reflecting mirror 20 includes three pieces of projecting surfaces and reflecting surfaces, and is used for translating a light path, and is made of optical glass or high molecular polymer, the transmitting surface has a transmission coating layer for enhancing transmittance, and the reflecting surface has a reflection coating layer for enhancing reflectivity, in this embodiment, the reflecting mirror 20 is placed at 45 degrees and is used for reflecting laser (laser signal) by 90 degrees to the planar dichroic mirror scanner 30.
The plane dichroic mirror scanner 30 serves to separate the laser light from the nonlinear optical signal and output the nonlinear optical signal, and also serves to change an incident angle of the laser light, and the vertical dichroic mirror scanner 70 serves to reflect the laser light and transmit the nonlinear optical signal. The plane dichroic mirror scanner 30 comprises a dichroic lens and a micro-electromechanical driver for driving the dichroic lens to rotate, the dichroic lens is physically connected to the electric driver, the dichroic lens is made of optical glass or high polymer and is used for reflecting s-type polarized laser and transmitting p-type polarized laser and nonlinear optical signals, and the plane dichroic mirror scanner 30 is positioned on a back focal plane of the objective lens 40; the structure and material of the vertical dichroic mirror scanner 70 are the same as those of the planar dichroic mirror scanner 30, and the vertical dichroic mirror scanner 70 is located at the back focal plane of the lenticular lens 12.
Referring to fig. 3 in detail, the planar dichroic mirror scanner 30 reflects s-type linearly polarized laser light, the focusing lens 50 collimates the s-type linearly polarized laser light in the X direction and focuses the s-type linearly polarized laser light in another direction (Y direction) perpendicular to the X direction, the s-type linearly polarized laser light continuously passes through the glass slide 60, the polarization direction of the s-type linearly polarized laser light rotates by 45 degrees, the laser light is focused on the surface of the vertical dichroic mirror scanner 70 in the Y direction, the vertical dichroic mirror scanner 70 reflects the laser light, the reflected and dispersed laser light passes through the glass slide 60 again, the polarization direction of the laser light rotates by 45 degrees in the same direction again to become p-type linearly polarized light, the p-type linearly polarized laser light is focused in the X direction through the focusing lens 50 again, the light beam collimated in the Y direction is projected on the surface of the planar dichroic mirror scanner 30, the planar dichroic mirror scanner 30, the plane dichroic mirror scanner 30 is located on a back focal plane of the objective lens 40, a movable lens in the plane dichroic mirror scanner 30 rotates along a rotating shaft parallel to an X axis, finally, p-type linearly polarized light passes through the objective lens 40 to form a linear focus which is located in a sample and is collimated in the X direction and focused in the Y direction, and the linear focus scans in the X direction, so that a two-dimensional scanning track is formed, and laser is enabled to perform two-dimensional line scanning on the plane of an external sample.
When the planar dichroic mirror scanner 30 completes one frame of the two-dimensional line-scanned image, the movable dichroic mirror on the vertical dichroic mirror scanner 70 is moved by a distance along the optical axis (Z direction), by the principle of far-end scanning, the two-dimensional line scanning plane of the external sample is also moved a distance along the optical axis, three-dimensional line scanning is realized by scanning in the Z direction on the vertical dichroic mirror scanner 70, nonlinear signals excited in an external sample are collected by the objective lens 40, sequentially pass through the plane dichroic mirror scanner 30 for transmitting nonlinear signal wavelength, the focusing lens 50, the glass slide 60, linearly focus on the surface of the vertical dichroic mirror scanner 70 in the Y direction, transmit the nonlinear signal wavelength through the vertical dichroic mirror scanner 70, the nonlinear signal is then linearly focused on the surface of the laser output fiber 91 in the X direction by the collecting lens 80 and finally transmitted to an external photoelectric detection device. The laser input fiber 90 is a large mode field single mode fiber, a polarization maintaining fiber or a photonic crystal fiber, and the laser output fiber 91 is a fiber bundle.
Because the linear focus formed by the linear scanning method adopted by the invention, the fluorescence collected by the objective lens 40 is also linear and moves in parallel on the end surface of the laser output optical fiber 91 along with the rotation of the plane dichroic mirror scanner 30, the detection of the moving linear fluorescence is completed by a scientific complementary metal oxide semiconductor (sCMOS) camera with a synchronizable rolling exposure shutter technology, and the position of the linear fluorescence is strictly synchronized with a certain line of photoelectric detection units currently read by a rolling shutter of the sCMOS camera, thereby realizing high-speed imaging.
In addition, in order to improve the efficiency of fluorescence photons to increase the imaging quality of the endoscope, the photodetectors 33 are uniformly arranged in the circumferential direction of the front aperture of the objective lens 40 near one end of the external sample, as shown in fig. 4, each photodetector 33 includes a filter 331, a photoelectric sensitive unit 332 and a driving unit 333, which are sequentially arranged from bottom right to top, the filter 331 is used for filtering back-reflected and back-scattered fluorescence photons, the photoelectric sensitive unit is used for converting the fluorescence photons passing through the filter 331 into an electrical signal, and the driving unit is used for providing high voltage and driving signals for the photoelectric sensitive unit, and is connected with an external amplifying circuit and a computer (not shown in the figure).
In this embodiment, as shown in FIG. 5, the photosensitive cells 332 of the photodetector 33 are formed in an annular array by a plurality of ordinary-sized avalanche diodes, the central aperture or transparent material is used for the excitation light transmitted through the microscope objective, and the plurality of ordinary-sized avalanche diodes are used for receiving the fluorescence photons that are not received by the microscope objective. The fluorescence photons which are not collected by the front aperture of the objective lens 40 can be collected by the photoelectric detector 33, and meanwhile, the collected fluorescence photon signals are converted into electric signals and then transmitted to an external amplifying circuit and a computer, so that the fluorescence photons generated by an external sample can be collected as much as possible, and the three-dimensional imaging quality of the endoscope is further improved. Compared with the use of an additional optical element, the volume of the endoscope is reasonably reduced by utilizing the photoelectric detector 33 in the scheme on the premise of ensuring that the endoscope can efficiently collect fluorescence photons, so that the volume is smaller than 5mm x 5mm and smaller than the outer diameter (9mm-11mm) of a commercial endoscope, and the endoscope in the scheme can be directly matched with the commercial endoscope for use, thereby greatly improving the practicability of the endoscope.
Example two
The difference between the second embodiment and the first embodiment is that: as shown in fig. 6, the photo-sensitive unit of the photo-detector 33 is an annular array formed by two-dimensional pixel photo-sensors, such as a CCD (charge coupled device) device, a CMOS (metal semiconductor oxide) device, an FPA (focal plane array) device, a PMT (photomultiplier tube) device, a single photon counting device, or a hybrid device based on any of the above photoelectric conversion principles, such as hamaman hybrid photo-detector (HPD), a central hole or a transparent material is used for the excitation light transmitted through the objective lens 40, and an annular array of two-dimensional pixel photo-sensors is used for receiving the fluorescence photons that cannot be received by the objective lens 40.
EXAMPLE III
The difference between the third embodiment and the first embodiment is that: the optical filter 331, the photoelectric sensitive unit 332 and the driving unit 333 are protected by a protection element, the protection element is made of a transparent insulating material, such as optical glass, and the protection element is arranged, so that on one hand, the protection element can be used for isolating an external sample from the photoelectric detector 33, and simultaneously can be used for electrical isolation, the protection element with the thickness of hundreds of microns can bear the high driving voltage of the avalanche diode, and the high voltage of the photoelectric sensitive unit 332 is prevented from causing danger to external detection personnel.
The foregoing is merely an example of the present invention and common general knowledge of known specific structures or characteristics of the embodiments is not described herein in any greater detail. It should be noted that, for those skilled in the art, without departing from the structure of the present invention, several changes and modifications can be made, which should also be regarded as the protection scope of the present invention, and these will not affect the effect of the implementation of the present invention and the practicability of the patent. The scope of the claims of the present application shall be determined by the contents of the claims, and the description of the embodiments and the like in the specification shall be used to explain the contents of the claims.
Claims (10)
1. A three-dimensional miniature endoscope comprises a miniature imaging probe, wherein the miniature imaging probe comprises an objective lens which can be right aligned with an external sample, and a front aperture for collecting fluorescence photons generated by the external sample is arranged on the objective lens, and the three-dimensional miniature endoscope is characterized in that: the objective lens is connected with a photoelectric detector used for collecting fluorescence photons which cannot be collected by the front aperture, the photoelectric detector comprises an optical filter, a photoelectric sensitive unit and a driving unit which are sequentially connected with one another, and the optical filter and the objective lens can simultaneously face an external sample; the optical filter is used for filtering back-reflected and back-scattered fluorescence photons, the photoelectric sensitive unit is used for converting the fluorescence photons passing through the optical filter into an electric signal, and the driving unit is used for providing high voltage and a driving signal for the photoelectric sensitive unit and is connected with an external amplifying circuit and a computer.
2. The three-dimensional microendoscope of claim 1, wherein: the number of the photoelectric detectors is a plurality, and the photoelectric detectors are uniformly distributed in the circumferential direction of the front aperture.
3. The three-dimensional microendoscope of claim 2, wherein: further comprising:
the plane dichroic mirror scanner is used for separating the laser and the nonlinear optical signal and outputting the nonlinear optical signal, and is also used for changing the incident angle of the laser to enable the laser to perform two-dimensional point scanning on the plane of the internal tissue of the external sample;
and the vertical dichroic mirror scanner is used for scanning a far-end Z axis to realize three-dimensional imaging.
4. A three-dimensional microendoscope as claimed in claim 3, wherein: and a collimating lens for collimating the laser light output from the laser input fiber and reducing chromatic aberration between the laser lights of different frequencies and outputting a laser signal.
5. The three-dimensional microendoscope of claim 2, wherein: the plane dichroic mirror scanner comprises a dichroic lens and a micro-electromechanical driver used for driving the dichroic lens to change an angle, the dichroic lens is polarization sensitive, reflects S-type polarized light and transmits p-type polarized light, the dichroic lens is fixedly connected to the micro-electromechanical driver, and the plane dichroic mirror scanner is located on a back focal plane of an objective lens.
6. The three-dimensional microendoscope of claim 5, wherein: the vertical dichroic mirror scanner and the plane dichroic mirror scanner are identical in structure, and the vertical dichroic mirror scanner is located on the rear focal plane of the cylindrical lens.
7. The three-dimensional microendoscope of claim 6, wherein: and a reflecting mirror is arranged on a light path between the collimating lens and the plane dichroic mirror scanner.
8. The three-dimensional microendoscope of claim 7, wherein: the reflecting mirror comprises a transmission surface and a reflection surface, wherein the transmission surface is provided with a transmission coating layer for enhancing the transmissivity, and the reflection surface is provided with a reflection coating layer for enhancing the reflectivity.
9. The three-dimensional microendoscope of claim 8, wherein: the number of the reflecting mirrors is multiple.
10. The three-dimensional microendoscope of any one of claims 1-9, wherein: the objective lens, the photoelectric detector, the plane dichroic mirror scanner, the vertical dichroic mirror scanner, the cylindrical lens, the collimating lens and the reflecting mirror are all provided with a shell for wrapping.
Applications Claiming Priority (2)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN201910210730 | 2019-03-18 | ||
| CN2019102107307 | 2019-03-18 |
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| CN113552710B (en) * | 2021-09-17 | 2022-01-18 | 清华大学 | Multi-plane microscopic imaging system based on gradient variable refractive index lens |
| CN115128788B (en) * | 2022-05-30 | 2023-11-28 | 中国人民解放军国防科技大学 | Horizontally placed microscopic device parallel to observed object |
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