CN110623634A - Line scanning miniature optical probe - Google Patents
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- CN110623634A CN110623634A CN201810653765.3A CN201810653765A CN110623634A CN 110623634 A CN110623634 A CN 110623634A CN 201810653765 A CN201810653765 A CN 201810653765A CN 110623634 A CN110623634 A CN 110623634A
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Classifications
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/0033—Features or image-related aspects of imaging apparatus classified in A61B5/00, e.g. for MRI, optical tomography or impedance tomography apparatus; arrangements of imaging apparatus in a room
- A61B5/004—Features or image-related aspects of imaging apparatus classified in A61B5/00, e.g. for MRI, optical tomography or impedance tomography apparatus; arrangements of imaging apparatus in a room adapted for image acquisition of a particular organ or body part
- A61B5/0042—Features or image-related aspects of imaging apparatus classified in A61B5/00, e.g. for MRI, optical tomography or impedance tomography apparatus; arrangements of imaging apparatus in a room adapted for image acquisition of a particular organ or body part for the brain
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/0059—Measuring for diagnostic purposes; Identification of persons using light, e.g. diagnosis by transillumination, diascopy, fluorescence
- A61B5/0062—Arrangements for scanning
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/0059—Measuring for diagnostic purposes; Identification of persons using light, e.g. diagnosis by transillumination, diascopy, fluorescence
- A61B5/0071—Measuring for diagnostic purposes; Identification of persons using light, e.g. diagnosis by transillumination, diascopy, fluorescence by measuring fluorescence emission
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- G—PHYSICS
- G02—OPTICS
- G02B—OPTICAL ELEMENTS, SYSTEMS OR APPARATUS
- G02B26/00—Optical devices or arrangements for the control of light using movable or deformable optical elements
- G02B26/08—Optical devices or arrangements for the control of light using movable or deformable optical elements for controlling the direction of light
- G02B26/10—Scanning systems
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- G—PHYSICS
- G02—OPTICS
- G02B—OPTICAL ELEMENTS, SYSTEMS OR APPARATUS
- G02B27/00—Optical systems or apparatus not provided for by any of the groups G02B1/00 - G02B26/00, G02B30/00
- G02B27/09—Beam shaping, e.g. changing the cross-sectional area, not otherwise provided for
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Abstract
The invention relates to the technical field of optical imaging, and provides a line scanning micro optical probe aiming at the technical problems of low imaging speed and the like of the existing micro probe, which comprises: a collimating lens for collimating the laser light output from the laser input fiber, reducing chromatic aberration between the laser lights of different frequencies, and outputting a laser signal; a lenticular lens for forming a line focus; the 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 line scanning on the plane of the internal tissue of the living body sample; an objective lens for converging the laser light from the dichroic mirror scanner into the interior of the living body sample to excite the living body sample to generate a nonlinear optical signal and for outputting the nonlinear optical signal; and the collecting lens is used for collecting the nonlinear optical signal.
Description
Technical Field
The invention relates to the technical field of optical imaging, in particular to a line scanning micro optical probe.
Background
For high resolution neuroscience research on experimental animals, multiphoton microscopy is commonly employed as a technique for noninvasive optical brain imaging. Generally, when a desktop multiphoton microscope is used, the head of a living specimen (an animal to be studied) needs to be fixed all the time, and the living specimen is under physical restraint and emotional stress (fear, unknown) all the time during an experiment, and the behavior of the living specimen in the case of free movement cannot be effectively studied.
In order to solve the above problems, chinese patent publication No. CN107049247A discloses a miniature two-photon microscopic imaging apparatus and method, and a living body sample behavior imaging system, wherein the miniature two-photon microscopic imaging apparatus includes: a femtosecond pulse laser for generating laser with a wavelength of 920 nm; the femtosecond pulse laser modulator is used for receiving the laser output by the femtosecond pulse laser, pre-chirping pulse broadening of the compensation laser to a preset value and outputting the pulse broadening; a microprobe, the microprobe comprising: a scanning imaging part for receiving laser output by the femtosecond pulse laser modulator, wherein the laser scans tissues inside a living body sample to excite the living body sample to generate a fluorescence signal; and a laser output optical fiber for receiving and outputting the fluorescence signal output by the scanning imaging part. The miniature two-photon microscopic imaging device can stably observe the activities of dendrites and dendrite spines of freely moving animals in natural physiological environment.
In the specific use process of the above scheme, the total weight of the micro probe and the fixed support is about 2.15g (described in paragraph 0035 of the above document), the micro probe comprises a micro electromechanical scanner (MEMS), an objective lens, a scanning lens, a collimator, a dichroic mirror and a collecting lens (see paragraph 0071 and fig. 1 of the above document for details), and the imaging principle is that the micro electromechanical scanner (MEMS) is used for two-dimensionally scanning the plane of the internal tissue of the living body sample by the laser (with wavelength of 920 nm) by rotating to change the incident angle of the laser. The objective lens is used for converging laser from the micro-electromechanical scanner to the interior of the living body sample so as to excite the living body sample to generate the fluorescence signal and outputting the fluorescence signal. The scanning lens is arranged on an optical path between the micro-electromechanical scanner and the objective lens and is used for converting laser light with angle change generated by two-dimensional scanning of the micro-electromechanical scanner into laser light with position change. The collimator is arranged between the laser input fiber and the micro-electromechanical scanner and is used for collimating the laser light output from the laser input fiber and reducing chromatic aberration between the laser lights with different frequencies so as to match the image of the objective lens together with the scanning lens. The dichroic mirror is provided between the scanning lens and the objective lens, and is used for separating the laser light and the fluorescent signal and outputting the fluorescent signal.
In the scheme, the imaging speed of the miniature probe is low (only 40Hz), and the miniature probe can only be used for two-dimensional scanning imaging, so that the structure of the miniature probe still has an optimizable space, the weight of the miniature probe can be continuously optimized, the volume of the miniature probe can be continuously optimized, and experimental errors caused by abnormal behaviors of a living body sample due to the fact that the living body sample is not suitable for the weight of the miniature probe in the research process are reduced.
In addition, the above-described microprobe has a problem that it cannot be used in combination with a commercial endoscope. The main reasons are that the bending diameter (20mm-40mm) of the commercial endoscope cannot be satisfied, and the defect of detecting a no-mark signal cannot be satisfied. Particularly, since the objective lens of the miniature probe needs to be provided with the tube lens and the scanning lens, the volume cannot be further reduced (cannot be reduced to 5mm × 5mm), and since the miniature probe mainly aims at detecting a living sample injected with fluorescent dye, when the miniature probe is used in a commercial endoscope, the miniature probe cannot clinically inject the fluorescent dye into a patient, so that the miniature probe cannot be applied to clinics.
Disclosure of Invention
The invention provides a line scanning micro optical probe, aiming at the technical problems that the existing micro probe has too low imaging speed, too heavy weight and too large volume and cannot be applied to clinic.
The basic scheme provided by the invention is as follows: a line scanning micro-optic probe comprising:
the collecting lens is used for collecting the nonlinear optical signals and imaging the nonlinear optical signals on the surface of the laser output optical fiber, and the laser output optical fiber is an imaging optical fiber bundle;
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. The laser input fiber is a large mode field single mode fiber or a polarization maintaining fiber or a photonic crystal fiber;
a cylindrical lens for focusing the collimated laser light into a line focus in a certain direction (herein referred to as X direction) on a surface of the dichroic mirror scanner, that is, a focus position in a certain direction (X direction) of the cylindrical lens is on the surface of the dichroic mirror, and a focus position in another direction (herein referred to as Y direction) of the cylindrical lens orthogonal to the certain direction (X direction) is not on the surface of the dichroic mirror;
the 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 line scanning on the plane of the internal tissue of the living body sample;
and an objective lens for converging the laser light from the dichroic mirror scanner into the interior of the living body sample to excite the living body sample to generate a nonlinear optical signal and for outputting the nonlinear optical signal.
The working principle and the advantages of the invention are as follows: in this scheme, laser light is output from a laser input fiber to a collimating lens, the collimating lens collimates the received laser light into parallel light (collimation processing), and reduces chromatic aberration between the laser light of different frequencies (achromatization processing), and then a cylindrical lens focuses the collimated laser light into a line shape in a certain direction (X direction) on the surface of a dichroic mirror scanner. The dichroic mirror scanner reflects the received laser to the objective lens, the dichroic mirror scanner is located on a back focal plane of the objective lens, the objective lens collimates the laser which is scattered in the X direction and reflected by the dichroic mirror scanner, meanwhile, the basically collimated laser in the Y direction is focused, a linear focus parallel to the Y direction is formed at the focus, the dichroic mirror in the dichroic mirror scanner rotates along a rotating shaft parallel to the Y direction, the linear focus is made to scan along the X direction, a two-dimensional scanning track is formed, and the purpose of enabling the laser to perform two-dimensional line scanning on the plane of the internal tissue of the living body sample is achieved.
After the living body sample generates the nonlinear optical signal, the objective lens is also used for collecting the nonlinear optical signal and outputting the nonlinear optical signal to the dichroic mirror scanner, the nonlinear optical signal is transmitted by the dichroic mirror scanner and then output to the collecting lens, and the collecting lens can effectively collect the nonlinear optical signal, output the nonlinear optical signal to the laser output optical fiber and finally transmit the nonlinear optical signal to external photoelectric detection equipment.
In the aspect of imaging the brain of the moving animal, the scanning lens and the lens barrel lens are not arranged in the scheme, and the dichroic mirror scanner and the micro electro mechanical scanner in the prior art are replaced by the dichroic mirror scanner and the cylindrical lens, so that the imaging speed is greatly improved, the internal structure is optimized, and the self weight is reduced on the premise of meeting the imaging quality. On the premise that the weight of the miniature optical probe is reduced, when data of a living body sample is acquired, particularly in the aspect of brain imaging of a moving animal, the miniature optical probe is more conveniently worn on the head of the animal, the influence of the weight on the movement of the animal is reduced, and detection errors are avoided.
In the aspect of combining with a commercial endoscope, because a patient cannot be injected with a fluorescent dye in clinical use, only 3 label-free signal modes of two-photon excitation autofluorescence, second harmonic generation and coherent anti-Stokes Raman scattering can be applied to the clinic. Specifically, two-photon excitation of autofluorescence TPEAF, i.e., 2 excitation photons are incident, fluorescence photons of a cell endogenous fluorophore are emitted, second harmonic generation SHG, i.e., one excitation photon is incident, a photon with a wavelength of 1/2 is emitted, coherent anti-stokes raman scattering CARS, i.e., 3 photons with 2 wavelengths are incident, and a photon with a wavelength satisfying 2 incident wavelength specific raman shift is emitted. The 3 imaging modes without the mark signals can be realized by changing the wavelength of laser in the laser incident optical fiber and configuring dichroic mirror scanners with different parameters. And because the scheme is not provided with the scanning lens and the tube lens, the whole volume of the miniature optical probe can be effectively reduced, so that the aim of combining with a commercial endoscope for use in clinic is fulfilled. 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 collecting lens are different, namely, the wavelengths have a plurality of different wavelengths, the chromatic aberration effect can be achieved through the collimating lens, so that the basic imaging requirement can be met.
Now that practical applications drive technological development, engineers think of some variants, and even if there are no specific application requirements, but would be considered to be of no use at all and would not continue to develop. Engineers in the existing MEMS two-dimensional scanner are all the origins of electronic engineering (micromachining process) or mechanical engineering (structural design), and they have good technical capabilities in the structural design and process implementation of the MEMS two-dimensional scanner, especially some engineers who are transferred from the computer chip manufacturing industry, and they have made great impetus for the implementation and progress of the MEMS two-dimensional scanner technology.
There is no need or power for engineers who do MEMS two-dimensional scanners to change the structure of existing MEMS two-dimensional scanners. An improved direction for engineers in MEMS two-dimensional scanners is now to increase the scanning speed. For engineers and most researchers, if the problem of reducing the weight and volume of the micro-optical probe is encountered, since the weight and volume of the MEMS two-dimensional scanner are affected by the chip manufacturing process and the material of the reflective mirror, it is very difficult to further reduce the weight and volume of the MEMS two-dimensional scanner, which is basically equivalent to reaching the technical bottleneck, and for engineers, the weight and volume of the micro-optical probe is equivalent to the technical bottleneck (cannot be improved based on the original design).
According to the micro optical probe, the dichroic mirror scanner and the cylindrical lens are adopted to replace a dichroic mirror and a micro electro mechanical scanner in the prior art, and the scanning lens and the tube lens are omitted, so that the purposes of greatly improving the imaging speed, optimizing the internal structure and reducing the self weight are achieved on the premise of meeting the imaging quality. The requirements of small volume and light weight of the miniature optical probe are met when the brain of the moving animal is imaged. In addition, the collimating lens and the objective lens have the achromatic function in the scheme, and the endoscope can be combined with the existing commercial endoscope without injecting fluorescent dye to a patient.
The laser beam source further comprises a reflecting mirror, wherein the reflecting mirror is arranged on a light path between the collimating lens and the dichroic mirror scanner and is used for adjusting the angle of the laser output by the collimating lens and reflecting the laser to the dichroic mirror scanner.
The design of adding the speculum can conveniently adjust the incident angle of the laser of inputing on the dichroic mirror scanner, the formation of image of being convenient for.
Furthermore, the reflector is used for turning the light path, the material is optical glass or high molecular polymer, the reflector comprises a transmission surface and a reflection surface, the transmission surface is provided with an optical coating film for enhancing the transmissivity, and the reflection surface is provided with an optical coating film for enhancing the reflectivity.
By the design, a better reflection effect can be achieved.
Further, the dichroic mirror scanner includes a dichroic mirror and an annular micro-electromechanical driver that does not affect transmission of the nonlinear optical signal, the dichroic mirror is covered on the annular micro-electromechanical driver, and the micro-electromechanical driver can drive the dichroic mirror to change an angle, or a movable mirror is manufactured by a process integration method using a material relatively transparent to visible light and near infrared light, such as silicon dioxide, and optical coating processing is performed on the movable mirror to form the dichroic mirror.
The existing micro-electromechanical scanner (MEMS) includes a plurality of mirrors and a plurality of MEMS actuators, wherein the MEMS actuators can respectively actuate the mirrors to change angles. In this scheme, the mirror plate is replaced by a dichroic mirror plate, and in this scheme the mems driver does not affect the transmission of the nonlinear optical signal. Its dichroic lens has played the effect of dichroic mirror among the prior art promptly, has also reached the effect that lets micro-electromechanical driver change the laser reflection angle, but also can reach and reduce component quantity for whole miniature optical probe volume is littleer, weight is lighter. By the assembling mode, the dichroic mirror scanner can be obtained at low cost.
Furthermore, the back surface of the wafer of the dichroic mirror scanner is hollowed by etching technology with transmission holes for transmitting the nonlinear optical signal, and the transmission holes are positioned on the back surface of the dichroic mirror.
Above-mentioned design, the comparatively ripe product of acquisition that can be quick.
The optical fiber comprises a large mode field single mode fiber, a polarization maintaining fiber and a photonic crystal fiber.
The design can meet the purpose that when the scheme is matched with a commercial endoscope for use, lasers with different wavelengths need to be input. The scheme and the commercial endoscope can be matched for use more conveniently.
Further, the device also comprises a laser output optical fiber which is an optical fiber bundle.
The design can facilitate the collection of nonlinear optical signals and meet the imaging requirement.
The device further comprises a shell, the shell is a sealing structure made of high molecular polymer materials, and the collecting lens, the cylindrical lens, the lens collimating lens, the dichroic mirror scanner, the objective lens and the reflecting mirror are all arranged in the shell.
Such a design enables other elements to be tightly packed, waterproof, provide a biocompatible surface, and do not cause any damage to the living sample (or human body).
Drawings
FIG. 1 is a schematic diagram of an embodiment of a micro-optical probe of the present invention;
FIG. 2 is a schematic view of the structure of FIG. 1;
FIG. 3 is a schematic view showing the state in which the apparatus of FIG. 1 is mounted on a mouse;
fig. 4 is a schematic structural diagram of a dichroic mirror scanner;
FIG. 5 is a view from another perspective of FIG. 4;
FIG. 6 is a front cross-sectional view of a dichroic mirror scanner produced by etching;
FIG. 7 is a schematic view of the present invention in use with a commercial endoscope;
FIG. 8 is a schematic diagram of a two-dimensional line scan according to the present invention.
FIG. 9 is a schematic view of the principle of fluorescence detection according to the present invention
Detailed Description
The following is further detailed by the specific embodiments:
reference numerals in the drawings of the specification include: collimating lens 10, cylindrical lens 12, reflecting mirror 20, dichroic mirror scanner 30, objective lens 40, collecting lens 50, laser input fiber 60, laser output fiber 61, housing 70, substrate 11, driver 22, dichroic mirror 33.
The embodiment is basically as shown in the attached figures 1 and 2: the miniature optical probe comprises the following components in sequence according to a light path: the laser scanning device comprises a collimating lens 10, a cylindrical lens 12, a reflecting mirror 20, a dichroic mirror scanner 30, an objective lens 40 and a collecting lens 50, wherein the objective lens 40 is an aspheric lens, and the collimating lens 10 is used for collimating laser light output from a laser input fiber 60, reducing chromatic aberration among laser light 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 lenticular 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 dichroic mirror scanner 30, that is, the focal position of the lenticular lens 12 in a certain direction (X direction) is on the surface of the dichroic mirror, and the focal position of the lenticular 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 is used to adjust the angle of the laser light output from the lenticular lens 12 and reflect the laser light to the dichroic mirror scanner 30. In other embodiments, the reflecting mirror 20 may be a plurality of pieces for translating the optical path, and is made of optical glass or high molecular polymer, and has an optical coating film for enhancing the transmittance on the transmission surface and an optical coating film for enhancing the reflectance on the reflection surface;
the dichroic mirror scanner 30 is configured to separate the laser light from the nonlinear optical signal and output the nonlinear optical signal, and is further configured to change an incident angle of the laser light to allow the laser light to perform one-dimensional scanning on a plane of the internal tissue of the living body sample, that is, the cylindrical lens 12 focuses the collimated laser light into a line shape in a certain direction (X direction) on the surface of the dichroic mirror scanner 30. The dichroic mirror scanner 30 reflects the received laser light to the objective lens 40, the dichroic mirror scanner 30 is located at a back focal plane of the objective lens 40, the objective lens 40 collimates the laser light scattered in the X direction reflected by the dichroic mirror scanner 30 while focusing the substantially collimated laser light in the Y direction and forming a line focus parallel to the Y direction at the focal point, the dichroic mirror in the dichroic mirror scanner 30 rotates along a rotation axis parallel to the Y direction to scan the line focus in the X direction, thereby converging a two-dimensional laser scanning image into the interior of the living body sample to excite the living body sample to generate a nonlinear optical signal, the objective lens 40 then receives and inputs the nonlinear optical signal to the dichroic mirror scanner 30, the nonlinear optical signal is transmitted from the dichroic mirror scanner 30 to the collecting lens 50, the collecting lens 50 is used to efficiently collect the nonlinear optical signal, wherein, the laser input fiber 60 is a large mode field single mode fiber or a polarization maintaining fiber or a photonic crystal fiber, the laser output fiber is a fiber bundle, and the two-dimensional line scanning schematic diagram is shown in detail in fig. 8;
in addition, because the linear focus is formed by the linear scanning mode adopted by the invention, the fluorescence collected by the objective lens is also linear and moves in parallel on the end surface of the laser output optical fiber along with the rotation of the dichroic mirror scanner, the detection of the moving linear fluorescence is completed by a scientific complementary metal oxide semiconductor camera with a synchronizable rolling exposure shutter technology, the position of the linear fluorescence is strictly synchronous with a certain row of photoelectric detection units currently read by a rolling shutter of the sCMOS camera, so that high-speed imaging is realized, and the schematic diagram of the fluorescence detection principle is shown in detail in FIG. 9;
the specific dichroic mirror scanner 30 comprises a dichroic mirror 33 and a micro-electromechanical driver 22 which does not affect the transmission of the nonlinear optical signal, the dichroic mirror 33 covers the micro-electromechanical driver 22, and the micro-electromechanical control surface can drive the dichroic mirror 33 to change the angle;
the device further comprises a shell 70, the shell 70 is a sealing structure made of high molecular polymer materials, and the collecting lens 50, the cylindrical lens 12, the collimating lens 10, the dichroic mirror scanner 30, the objective lens 40 and the reflecting mirror 20 are all installed in the shell 70.
When in specific use: the collimating lens 10 of the present embodiment uses an achromatic collimating lens 10, which is model #65-286, Edmund Optics inc, Barrington, NJ, USA; diameter: 2mm, equivalent focal length: 3mm, special near infrared light, can collimate output laser and reduce chromatic aberration between different frequency components of femtosecond laser, thus being beneficial to improving transmission efficiency (up to 50% from laser source to sample), beam focusing and excitation efficiency. Of course, the design wavelength may be achromatic, and any 2 wavelengths between 700nm and 1600nm, which may be 817nm and 1064nm, but are not limited to these two wavelengths, and the material is optical glass or high molecular polymer, and the surface has an optical coating film with enhanced transmittance for laser collimation.
The objective lens 40, the diameter of the movable dichroic mirror in the dichroic mirror scanner 30 is 1mm, and the package size is 4.5 × 4.5mm2The first resonant frequency is 400Hz, the maximum optical scanning angle is +/-15 degrees, the size of the support frame is 512x512, and the maximum field of view is 400x400um2The adopted Japanese Bingson ORCA-FLASH 4.0CMOS camera can reach 512x512@400 fps. Specifically, the mirror plate 20 on the existing microelectromechanical scanner is replaced with a dichroic mirror 33. In yet another embodiment, the objective lens 40 is an achromatic design with any 2 wavelengths between 700nm and 1600nm, typically 817nm and 1064nm, but not limited to these two wavelengths, and is made of optical glass or polymer, and has an optical coating with enhanced transmittance on its surface, and the structure can be a conventional refractive lens, a gradient index lens or a gradient index lens with a curved profile, for focusing the incident laser light in the external sample, exciting the nonlinear optical signal, and collecting the nonlinear optical signal in an epi-detection manner.
In yet another embodiment, collection lens 50 is of achromatic design, designed at any 2 wavelengths between 350nm and 700nm, typically 408nm and 633nm, but not limited to these two wavelengths, and is made of optical glass or a high molecular polymer with an optical coating of enhanced transmittance on its surface for focusing and coupling the received nonlinear optical signal into the collection fiber.
The specific laser input fiber 60 is a large mode field single mode fiber or a polarization maintaining fiber or a photonic crystal fiber, the design wavelength is any wavelength between 700nm and 1600nm, and the material is optical glass, quartz, plastic or high molecular polymer and is used for transmitting laser generated by an external excitation light source.
The dichroic mirror scanner 30 is of a uniaxial structure, the lens is a dichroic mirror 33, and the dichroic mirror 33 is made of optical glass or high molecular polymer and is used for reflecting laser with the wavelength of 700nm-1600nm and transmitting nonlinear optical signals with the wavelength of 350nm-700 nm.
The objective lens 40 is an achromatic design, and is designed to have any 2 wavelengths between 700nm and 1600nm, typically 817nm and 1064nm, but not limited to these two wavelengths, and is made of optical glass or high molecular polymer, and has an optical coating with a surface with enhanced transmittance, and the structure may be a conventional refractive lens, a gradient index lens or a gradient index lens with a curved surface profile, and is used for focusing incident laser on the surface of a living body sample (or human body) to excite a nonlinear optical signal.
The mirror 20 is placed at 45 degrees for reflecting the laser light (laser signal) 90 degrees to the dichroic mirror scanner 30.
In this embodiment, the volume of the final housing 70 (i.e., the entire miniature optical probe) is less than 5mm, less than the outer diameter (9mm-11mm) of a commercial endoscope, and can be used in direct cooperation with a commercial endoscope. And the combined use is convenient, and in addition, the view of the commercial endoscope is shielded very little. In addition, in this embodiment, the collecting lens 50 feeds back the nonlinear optical signal to an external photoelectric imaging device, which is composed of a plurality of photomultiplier tube detectors, a plurality of dichroic mirrors, a plurality of optical filters, and a plurality of collecting lenses, and is configured to receive the nonlinear optical signal transmitted by the collecting optical fiber and complete photoelectric conversion for processing by a computer. When the endoscope is used with a commercial endoscope, since the laser input fiber 60 and the laser output fiber 61 need to be installed in a reduced size as much as possible, and the positions of the laser input fiber 60 and the laser output fiber 61 on the micro optical probe are very close to each other, a plurality of reflectors 20 (as shown in fig. 7) are provided in the present embodiment for adjusting the optical path, so as to facilitate the use with the commercial endoscope.
For specific use, the present invention can be mounted on the top of the head of a mouse (as shown in FIG. 3). In other embodiments, the composition can be also applied to the top of the head of other animals, such as marmoset, rabbit, etc.
In this embodiment, a dichroic mirror scanner 30 (as shown in fig. 4 and 5) is further disclosed, which includes a substrate 11, a driver 22, and a mirror surface, where the driver 22 is fixed on the substrate 11, the driver 22 is configured to change an angle of the mirror surface according to an instruction, the mirror surface includes a plurality of dichroic mirrors 33, the dichroic mirrors 33 include ultrathin sheets, the ultrathin sheets are coated with dichroic films, the dichroic mirrors 33 are configured to reflect laser light and allow nonlinear optical signals to pass through, the driver 22 includes a plurality of mirror bodies through which the nonlinear optical signals can pass, the dichroic mirrors 33 are respectively fixed on the mirror bodies, the mirror bodies are ring-shaped, the dichroic mirrors 33 are fixed on surfaces of the mirror bodies, the substrate 11 is made of a high polymer, and the mirror surfaces are in a shape of a circular disk.
When in specific use: of course, in other embodiments, it is also possible to select an existing micro-electromechanical scanner (MEMS), replace the mirror 20 side with the dichroic mirror 33, and etch out the back side of the substrate 11 at the position corresponding to the dichroic mirror 33 by deep reactive ion etching (as shown in fig. 6). The driver 22 of the conventional two-dimensional scanning device is usually driven by electrostatic, and the present embodiment adopts the design of the conventional driver 22 in the design of the driver 22, and specifically, the mems cap surface micromachining process soi mems ps can be adopted. This technology is the prior art, and is not described herein again, and in this application, the following differences are emphasized.
First, in the present embodiment, the mirror surface is selected as the dichroic mirror 33, and the surface of the reflecting mirror 20 formed by the second layer of polysilicon, the second layer of phosphosilicate glass, and the third layer of polysilicon in the soi mems process is replaced by an ultrathin sheet coated with a dichroic film, that is, the reflecting mirror 20 is selected in the prior art, which is the dichroic mirror 33 selected in the present embodiment. Second, regarding the transmittance of the substrate 11, in practical use, the nonlinear optical signal is required to be transmitted completely from the two-dimensional scanner, so that the selection of the substrate 11 is particularly important, the back of the dichroic mirror 33 is a hollow structure, and the back of the substrate 11 is hollow by a deep reactive ion etching technology, and an annular mirror body is arranged, so that the effect of facilitating the transmission of the nonlinear optical signal is achieved.
Specifically, in the hollow design of the substrate 11, the substrate 11 that has been hollow may be selected as a supporting structure of the driver 22, the driver 22 is selected from an annular driver 22, and torsion beams are disposed at two ends of the driver 22, so that the effect of facilitating transmission of the nonlinear optical signal may also be achieved.
The foregoing is merely an example of the present invention, and common general knowledge in the field of known specific structures and characteristics is not described herein in any greater extent than that known in the art at the filing date or prior to the priority date of the application, so that those skilled in the art can now appreciate that all of the above-described techniques in this field and have the ability to apply routine experimentation before this date can be combined with one or more of the present teachings to complete and implement the present invention, and that certain typical known structures or known methods do not pose any impediments to the implementation of the present invention by those skilled in the art. 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 line scanning micro-optic probe comprising:
a collimating lens for collimating the laser light output from the laser input fiber, reducing chromatic aberration between the laser lights of different frequencies, and outputting a laser signal;
it is characterized by also comprising:
a lenticular lens for forming a line focus;
the 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 line scanning on the plane of the internal tissue of the living body sample;
an objective lens for converging the laser light from the dichroic mirror scanner into the interior of the living body sample to excite the living body sample to generate a nonlinear optical signal and for outputting the nonlinear optical signal;
and the collecting lens is used for collecting the nonlinear optical signal and focusing the nonlinear optical signal on the end face of the laser output optical fiber.
2. The line scanning micro optical probe of claim 1, wherein: the laser beam splitter further comprises a reflecting mirror, wherein the reflecting mirror is arranged on a light path between the collimating lens and the dichroic mirror scanner and used for adjusting the angle of the laser output by the collimating lens and reflecting the laser to the dichroic mirror scanner.
3. The line scanning micro optical probe of claim 2, wherein: the reflector is used for turning the light path, the material is optical glass or high molecular polymer, the reflector comprises a transmission surface and a reflection surface, the transmission surface is provided with an optical coating film for enhancing the transmissivity, and the reflection surface is provided with an optical coating film for enhancing the reflectivity.
4. The line scanning micro optical probe of claim 1, wherein: the dichroic mirror scanner comprises a dichroic mirror and an annular micro-electromechanical driver which does not affect the transmission of nonlinear optical signals, the dichroic mirror is covered on the annular micro-electromechanical driver, the micro-electromechanical driver can drive the dichroic mirror to change the angle, or a movable mirror is manufactured by a process integration method by using a material which is relatively transparent to visible light and near infrared light, such as silicon dioxide, and optical coating processing is carried out on the movable mirror to form the dichroic mirror.
5. The line scanning micro optical probe of claim 4, wherein: the back of the wafer of the dichroic mirror scanner is hollowed by etching technology with transmission holes for transmission of the nonlinear optical signal, which are located on the back of the dichroic mirror.
6. The line scanning micro optical probe of claim 4, wherein: the dichroic mirror scanner is located at the back focal plane of the objective lens.
7. The line scanning micro optical probe of claim 4, wherein: the dichroic mirror scanner reflects laser light having a wavelength of 700nm to 1600nm and transmits nonlinear optical signals having a wavelength of 350nm to 700 nm.
8. The line scanning micro optical probe of any one of claims 1-7, wherein: the fiber laser also comprises a laser input fiber, wherein the laser input fiber is a large mode field single-mode fiber or a polarization maintaining fiber or a photonic crystal fiber.
9. The line scanning micro optical probe of any one of claims 1-7, wherein: the laser device also comprises a laser output optical fiber which is an optical fiber bundle.
10. The line scanning micro optical probe of any one of claims 1-7, wherein: the device also comprises a shell, the shell is a sealing structure made of high molecular polymer materials, and the collecting lens, the cylindrical lens, the collimating lens, the dichroic mirror scanner, the objective lens and the reflector are all arranged in the shell.
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| CN201810653765.3A CN110623634A (en) | 2018-06-22 | 2018-06-22 | Line scanning miniature optical probe |
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| CN201810653765.3A CN110623634A (en) | 2018-06-22 | 2018-06-22 | Line scanning miniature optical probe |
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| US20050187441A1 (en) * | 2004-01-19 | 2005-08-25 | Kenji Kawasaki | Laser-scanning examination apparatus |
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| CN104568872A (en) * | 2014-12-17 | 2015-04-29 | 深圳先进技术研究院 | Fluorescent micro-spectrum imaging system with optical sectioning strength |
| CN107991769A (en) * | 2018-01-12 | 2018-05-04 | 凝辉(天津)科技有限责任公司 | Two-dimensional scan device |
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| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US20050187441A1 (en) * | 2004-01-19 | 2005-08-25 | Kenji Kawasaki | Laser-scanning examination apparatus |
| CN104458696A (en) * | 2014-12-02 | 2015-03-25 | 天津大学 | Digital micro-mirror element based micro curing raman spectrometer |
| CN104568872A (en) * | 2014-12-17 | 2015-04-29 | 深圳先进技术研究院 | Fluorescent micro-spectrum imaging system with optical sectioning strength |
| CN107991769A (en) * | 2018-01-12 | 2018-05-04 | 凝辉(天津)科技有限责任公司 | Two-dimensional scan device |
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