TWI692342B - Rapid tissue molecule spectral imaging device - Google Patents

Abstract

The invention provides a rapid tissue molecule spectral imaging device. The device comprises a light emitting unit, a steering unit, a scanning unit and a detection unit, wherein the light emitting unit is used for emitting linear light beams; the steering unit is used for steering the linear light beams and fluorescence passing through samples; the scanning unit is used for adjusting the direction of the steered linear light beams to scan the samples line by line; the detection unit is used for collecting the fluorescence and forming spatial images and spectral information of the samples. The spatial images and spectral information of tissue molecules are obtained by combining the linear light beams with the spectral detection unit so that the imaging speed of the tissue molecules can be greatly increased, and real-time imaging can be achieved; the spectral information can assist in analyzing tissue conditions (such as used for tumor analysis). The scanning unit only performs one-dimensional scanning, so that the stability of a system can be effectively improved.

Description

Rapid tissue molecular spectrum imaging device

The invention relates to the field of medical devices, and more particularly to a rapid tissue molecular spectrum imaging device.

Tumors are major diseases that seriously threaten human health. A large number of studies have shown that more than 90% of tumors originate from epithelial cell lesions, and molecular and cellular levels of variation will occur during the development of cancer. The high-resolution optical endoscopic imaging technology based on fiber optic bundles can achieve micron or sub-micron resolution, making the endoscope magnification up to 1000 times, compared with other medical imaging technologies (such as CT, MRI, PET, etc.) The technical advantages of real-time and in vivo detection of small tumor lesions can better improve the early diagnosis rate of tumors. The probe end of endoscopic imaging can go deep into the living body, complete the micron-level in-vivo non-destructive detection, realize the "in-vivo biopsy" without sampling, and bring new technical methods for early detection of cellular molecular lesions.

The present invention has been made in consideration of the above problems. The invention provides a rapid tissue molecular spectral imaging device, including a light emitting unit, a steering unit, a scanning unit and a spectrum detection unit, wherein the light emitting unit is used to emit a line beam; the steering unit is used to steer the line beam And through the fluorescence of the sample; the scanning unit is used to adjust the direction of the turned line beam to scan the sample line by line; and the spectrum detection unit is used to collect the fluorescence and form a spatial image and spectrum of the sample News.

Exemplarily, the light emitting unit includes: a light source for emitting a collimated light beam; and a beam-expanding line focusr disposed at the exit of the light source for expanding and collimating the collimated light beam in one dimension It is a line beam.

Exemplarily, the steering unit is a dichroic mirror.

Exemplarily, the scanning unit is a single scanning galvanometer, or a spatial light modulator.

Exemplarily, the device further includes a relay unit and an internal view unit provided downstream of the scanning unit, wherein the relay unit is used to focus the line beam scanned by the scanning unit to the internal view unit The inner view unit is used to conduct and focus the focused line beam onto the sample and receive the fluorescent light emitted by the sample; the fluorescent light passes through the relay unit, the scanning unit and the turning unit Then it is collected by the spectrum detection unit.

Exemplarily, the endoscope unit includes a coupling objective lens and an imaging fiber bundle, wherein the coupling objective lens is disposed at one end of the imaging fiber bundle, and is used to couple the focused line beam into the proximal end of the fiber bundle ; And the imaging fiber bundle is used to conduct the incoming line beam.

Exemplarily, the endoscope unit further includes a miniature objective lens, which is disposed at the other end of the imaging fiber bundle and is used to focus the line beam conducted by the fiber bundle onto the sample.

Exemplarily, the detection unit includes a linear array detection unit, a spectral detection unit, and a switching control unit, wherein: the linear array detection unit is used to collect fluorescent light and form a spatial image of the sample; and the spectral detection unit, It is used to collect fluorescence and form spectral information of the sample; the switching control unit is used to switch and select the linear array detection unit and the spectral detection unit.

Exemplarily, the detection unit further includes a first focusing lens disposed between the linear array detection unit and the switching control unit, for focusing the fluorescent light emitted by the sample to The linear array detection unit.

Exemplarily, the spectrum detection unit is a spectrum camera.

Exemplarily, the detection unit further includes a second focusing lens disposed between the spectrum detection unit and the switching control unit, for focusing the fluorescence emitted by the sample to the The spectrum detection unit is described.

Exemplarily, the spectrum detection unit includes a prism-grating-prism, a condensing lens, and a surface array detector arranged in sequence, wherein the prism-grating-prism is used to disperse and split the fluorescent light transmitted by the steering unit; The condensing lens is used to focus the dispersion-divided fluorescent light onto the photosensitive surface of the area array camera; the area array detector is used to form the spectral information.

Exemplarily, the detection unit further includes a first focusing lens and/or a second focusing lens for focusing the fluorescent light emitted from the sample, wherein: the first focusing lens is provided in the linear array detection unit And the switching control unit; the second focusing lens is provided between the spectrum detecting unit and the switching control unit.

The detection unit further includes a second focusing lens and a collimating lens which are sequentially arranged between the switching control unit and the spectrum detecting unit, wherein: the second focusing lens is used to fluoresce the sample Focusing; and the collimating lens is used to collimate the focused fluorescence.

Exemplarily, the detection unit further includes a slit and/or a filter provided downstream of the second focusing lens, wherein: the slit is used to allow only the fluorescence of the focusing plane to pass through; and the filter The optical device is used to filter out stray light.

The rapid tissue molecular spectroscopic imaging device uses a linear light source to excite the sample, a one-dimensional scanning unit (such as a single scanning galvanometer) to scan the linear beam, and a spectral detection unit to detect the sample excitation light to achieve a common one-dimensional direction Focus. Due to the combination of line beam and spectral detection unit to obtain spatial images and spectral information of tissue molecules, not only can the imaging speed of tissue molecules be greatly improved, but also real-time imaging can be achieved, and the analysis of tissue conditions can also be assisted by spectral information (such as for Tumor analysis). Since the scanning unit only performs one-dimensional scanning, the stability of the system can be effectively improved.

In order to make the objectives, technical solutions, and advantages of the present invention more apparent, exemplary embodiments according to the present invention will be described in detail below with reference to the drawings. Obviously, the described embodiments are only a part of the embodiments of the present invention, but not all the embodiments of the present invention. It should be understood that the present invention is not limited by the example embodiments described herein. Based on the embodiments of the present invention described in the present invention, all other embodiments obtained by those skilled in the art without paying creative effort should fall within the protection scope of the present invention.

FIG. 1 schematically shows a block diagram of a rapid tissue molecular spectroscopy imaging apparatus 100 according to an embodiment of the present invention. The rapid tissue molecular spectroscopic imaging device 100 includes a light emitting unit 110, a steering unit 120, a scanning unit 130, and a detection unit 160. The rapid tissue molecular spectroscopic imaging device 100 can be widely applied to tissue molecular imaging of various parts of the digestive tract, respiratory tract, etc., to achieve early diagnosis of tumors.

The light emitting unit 110 is used to emit a line beam. In one embodiment, as shown in FIGS. 2-3, the light emitting unit 110 may include a light source 112 and a beam expander 114. The light source 112 is used to emit a collimated light beam. The light source 112 may be a laser that emits collimated laser light of a specific wavelength. The specific wavelength range may be 20nm-2000nm. Lasers in this wavelength range can excite a wide range of phosphors. The light source 112 may be a quantum well laser, a solid-state laser, a gas laser (for example, an argon ion laser), or a laser diode. The beam-expanding line focus 114 is disposed at the exit of the light source 112, and is used to expand and collimate the collimated beam emitted from the light source 112 into a linear beam in one dimension. The beam expanding focus 114 may include a beam expanding lens and a cylindrical lens. The beam expanding lens may include two L1 and L2, and the two beam expanding lenses L1 and L2 cooperate to expand the collimated light beam emitted by the light source 112 to change the diameter of the collimated light beam. The cylindrical lens includes L3, which one-dimensionally focuses the expanded beam into a line beam and transmits it to the steering unit 120.

The turning unit 120 is located downstream of the light emitting unit 110 and is used to turn the line beam emitted by the light emitting unit 110 and can transmit the fluorescence of the sample. In FIGS. 1-3, the solid line is used to represent the line beam emitted by the light emitting unit 110, and the dotted line is used to represent the fluorescence emitted by the sample. The turning unit 120 is used to separate the light emitted by the light emitting unit 110 from the fluorescence generated by the excitation of the sample. The transmissivity of the turning unit 120 to fluorescent light can reach more than 90%, and the light of other wavelengths is basically totally reflected. Thus, the line beam emitted by the light emitting unit 110 is reflected to the scanning unit 130 after passing through the turning unit 120. The fluorescent light returning along the same optical path as the line beam transmits almost all when passing through the turning unit 120 and is conducted to the detecting unit 160. The steering unit 120 satisfying the above conditions may be a dichroic mirror. Preferably, the wavelength range of the dichroic mirror may be in the wavelength range of 40nm-2200nm.

The scanning unit 130 is located downstream of the steering unit 120, and performs one-dimensional oscillating scanning on the turned line beam, for adjusting the direction of the turned line beam to scan the sample line by line. Specifically, the line light beam may be, for example, a line light beam extending in the X direction, and the scanning unit 130 turns the line light beam to a downstream optical component (for example, the relay unit 140) while performing the Y direction scanning. The Y direction is at a certain angle with the X direction, for example at a right angle of 90 degrees. The scanning unit 130 mainly performs one-dimensional scanning in the Y direction. In this way, the entire image can be formed by performing a one-dimensional scan in conjunction with the X-direction linear beam. It can be seen that the line beam combined with the detection unit 160 can be used for line-by-line imaging, so the imaging speed can be greatly improved compared to the existing point-by-point imaging. Since only one-dimensional oscillating scanning is performed, the scanning unit 130 may be a single scanning galvanometer. The frequency of the scanning galvanometer can be in the frequency range of 10-2000KHz. The use of a single scanning galvanometer can greatly reduce noise, and simplify the composition of the device and the complexity of control, improve the stability of the whole machine, while reducing manufacturing costs and maintenance costs. In addition, the scanning unit 130 may also be a spatial light modulator. Compared with the scanning galvanometer, the spatial light modulator has a relatively high cost.

The rapid tissue molecular spectroscopy imaging apparatus 100 further includes a relay unit 140 and an endoscopy unit 150 disposed downstream of the scanning unit 130. FIG. 2-3 shows an optical path diagram and a block diagram of the rapid tissue molecular spectroscopic imaging device 200 according to a specific embodiment of the present invention. In Figs. 2-3, the same or similar components as those in Fig. 1 are denoted by the same reference numerals. The specific implementation of the relay unit 140, the inner view unit 150, and the detection unit 160 in the specific embodiment of the present invention will be described in detail below with reference to FIGS. 2-3.

The relay unit 140 is used to focus the line beam scanned by the scanning unit 130 to the inner view unit 150. The relay unit 140 is usually a lens group, such as lenses L4 and L5.

The inner view unit 150 is used to conduct and focus the line beam focused by the relay unit 140 onto the sample, and receive the fluorescent light emitted by the sample. The fluorescent light is collected by the detection unit 160 after passing through the relay unit 140 and the steering unit 120. The inner view unit 150 may include a coupling objective lens 152, a mini objective lens 156, and an imaging fiber bundle 154 coupled between the coupling objective lens 152 and the mini objective lens 156. The relay unit 140 may include two relay lenses L4, L5 that cooperate with each other to relay the scanned line beam to the rear pupil of the coupling objective lens 152 in the inner view unit 150. The coupling objective lens 152 is used to couple (eg, focus) the line beam into the proximal end of the imaging fiber bundle 154 (the end near the operator). The imaging fiber bundle 154 is used to guide the line beam to the distal end of the imaging fiber bundle 154 (the end away from the operator). The micro objective lens 156 is used to focus the laser beam conducted by the imaging fiber bundle 154 onto the detection surface of the sample. The detection surface can be located at a desired depth below the sample surface. The fluorophore at the detection surface of the sample is excited to emit fluorescence. The fluorescent signal is collected by the micro-objective lens 156, transmitted through the imaging fiber bundle 154, the coupling objective lens 152, and the relay unit 140, reflected by the scanning unit 130, passes through the steering unit 120, and enters the detection unit 160. The number of optical fiber bundles included in the imaging optical fiber bundle 154 may be greater than ten. The micro objective lens 156 is not necessary. In a case where the definition is not high, optionally, the micro objective lens 156 may be omitted. The micro objective lens 156 may be designed to extend into the digestive tract, respiratory tract, etc., and to contact the surface of the digestive tract, respiratory tract, etc.

The detection unit 160 collects the fluorescent light sequentially returned through the inner view unit 150, the relay unit 140, the scanning unit 130, and the steering unit 120, and forms a spatial image and spectral information of the sample. The spatial image of the sample includes a two-dimensional image of the detection surface of the sample. The spectral information includes the energy distribution of the fluorescent light generated by the sample in different wavelength bands, which is used to illustrate obtaining tissue information (for example, for analyzing tumors). In a specific embodiment, the detection unit 160 may include a line array detection unit 162, a spectrum detection unit 164, and a switching control unit 166, as shown in FIGS. 2-3.

The linear array detection unit 162 is used to collect fluorescent light and form a spatial image of the sample. The linear array detection unit 162 may be various types of linear array cameras, such as a charge coupled device (Charge Coupled Device, CCD for short) linear array camera or a complementary metal oxide semiconductor (Complementary Metal Oxide Semiconductor, CMOS for short) linear array camera. The imaging speed of the line array detection unit 162 is in the range of tens of frames to tens of millions of frames. Preferably, the detection unit 160 further includes a first focusing lens L6, which is disposed between the linear array detection unit 162 and the switching control unit 166, as shown in FIG. 3, for focusing the fluorescent light emitted by the sample to The linear array detection unit 162 can form a clear image.

The spectral detection unit 164 is used to collect fluorescence and form spectral information of the sample. The spectral detection unit 164 will be described in detail later.

The switching control unit 166 is used for switching selection between the linear array detection unit 162 and the spectrum detection unit 164 to selectively acquire spatial images or spectral information. The switching control unit 166, for example, selectively switches the transmission path of the fluorescent light so that the fluorescent light enters the linear array detection unit 162 or the spectrum detection unit 164. Exemplarily, the switching control unit 166 may be a mirror, a digital micromirror device (Digital Micromirror Device, DMD for short), or a spatial light modulator. Among them, the digital micromirror device can realize the projection or reflection of the optical path by controlling the on and off. An embodiment using a digital micromirror device as the switching control unit 166 is schematically shown in FIG. 3. When in use, first control the switching control unit 166 to turn on to make the fluorescent light transmit, and the linear array detection unit 162 performs spatial imaging to find the destination area (such as a tumor); then when specific analysis of the destination area is desired, control the switching The control unit 166 blocks and reflects the fluorescent light to the spectrum detection unit 164, and the spectrum detection unit 164 acquires the spectrum information of the destination area. For the case where the switching control unit 166 adopts a mirror or a spatial light modulator, a person skilled in the art may modify the optical path according to the principles disclosed in this application.

In a preferred embodiment (for example, the embodiment shown in FIGS. 2-3), the spectrum detection unit 164 is a spectrum camera. The spectroscopic camera can be an existing or a variety of spectroscopic cameras that may appear in the future, for example, the Pika L-type spectroscopic camera of the RESONON company in the United States, and the FX10 spectroscopic camera of the Specim company in Finland, etc. , As long as it can form the spectral information of the sample based on the collected fluorescence. Preferably, the detection unit 160 further includes a second focus lens L7, which is disposed between the spectrum detection unit 164 and the switching control unit 166, as shown in FIG. 3, for focusing the fluorescent light emitted by the sample to The spectrum detection unit 164 can obtain more reliable spectrum information.

4-5 illustrate an optical path diagram and a block diagram of a rapid tissue molecular spectroscopic imaging device 300 according to another specific embodiment of the present invention. The spectral detection unit 164 may include prism-grating-prism (Prisim-Grating-Prism) arranged in sequence. , Referred to as PGP) 164a, converging lens 164b and area array detector 164c. After being switched to the spectrum function by the switching control unit 166, the PGP prism 164a is used to disperse and split the fluorescent light transmitted by the steering unit 120. The condenser lens 164b is used to focus the dispersion-divided fluorescent light onto the photosensitive surface of the area camera 166. The number of converging lenses 164b is related to the number of channels of the obtained spectrum, that is, more converging lenses are expected, and more converging lenses are used. The area detector 164c is used to form the spectral information of the sample. The area detector 166 may be various types of area cameras, such as CCD area cameras or CMOS area cameras.

Further preferably, as shown in FIG. 5, on the detection optical path, the detection unit 160 preferably further includes a second focusing lens L7 and a collimating lens L8, which are between the switching control unit 166 and the spectrum detection unit 164, along the optical path direction Set in turn, as shown in Figure 4-5. The second focusing lens L7 is used to focus the fluorescent light emitted by the sample. The fluorescent light emitted by the focused line beam illuminating the sample is received, and by the turning and scanning of the scanning unit 130, the fluorescent light emitted from all lines of the sample is finally received by the detection unit 160, and arranged into spectral cube data according to the scanning trajectory , And can quickly obtain the spectral information of the tissue. The collimating lens L8 is used to collimate the focused fluorescence. Optionally, a slit (not shown) may be provided between the second focusing lens L7 and the collimating lens L8, and the slit is used to allow only the fluorescence of the focusing plane to pass through. The size of the slit can be in the range of tens of nanometers to tens of millimeters. The existence of the slit makes stray light out of the focus plane blocked. Optionally, the detection unit 160 may further include an optical filter. A filter (not shown) is provided downstream of the second focusing lens L7, that is, between the second focusing lens L7 and the collimating lens L8, for filtering stray light. In the slitted embodiment, the optical filter may be disposed between the second focusing lens L7 and the slit.

In summary, the collimated light beam from the light source 112 is expanded by the beam expander 114 and condensed into a linear beam in one dimension. The steering unit 120 bends the linear beam, and the scanning unit 130 couples the linear beam through the relay unit 140 Entering the inner view unit 150 and performing a one-dimensional scan, the inner view unit 150 transmits the laser beam to the sample, excites the fluorescent light and transmits it back to the detection unit 160 to form a spatial image and spectral information.

Exemplarily, the data collected by the detection unit can be sent to a computer, and received and processed by the computer. In addition, the computer can also control the scanning unit (such as the frequency of the galvanometer), the exposure and gain of the detection unit, and the emission power of the light emitting unit.

The rapid tissue molecular spectroscopic imaging device 100 uses a line light source to excite the sample, a one-dimensional scanning unit 130 (eg, a single scanning galvanometer) to scan the line beam, and a detection unit 160 to detect the sample excitation light in a one-dimensional direction Achieve confocal. Since the line beam is combined with the detection unit 160 to obtain spatial images and spectral information of tissue molecules, not only can the imaging speed of tissue molecules be greatly improved, but real-time imaging can also be achieved, and the analysis of tissue conditions can also be assisted by spectral information (such as for Tumor analysis). Since the scanning unit 130 only performs one-dimensional scanning, the stability of the system can be effectively improved.

Although example embodiments have been described herein with reference to the drawings, it should be understood that the above example embodiments are merely exemplary, and are not intended to limit the scope of the present invention thereto. Those of ordinary skill in the art can make various changes and modifications therein without departing from the scope and spirit of the present invention. All such changes and modifications are intended to be included within the scope of the invention as claimed in the appended claims.

In the several embodiments provided in this application, it should be understood that the disclosed device and method may be implemented in other ways. For example, the device embodiments described above are only schematic. For example, the division of the unit is only a logical function division. In actual implementation, there may be another division manner, for example, multiple units or elements may be combined or may Integration into another device, or some features can be ignored, or not implemented.

The specification provided here explains a lot of specific details. However, it can be understood that the embodiments of the present invention can be practiced without these specific details. In some instances, well-known methods, structures, and techniques have not been shown in detail so as not to obscure the understanding of this description.

Similarly, it should be understood that in order to streamline the invention and help understand one or more of the various inventive aspects, in describing the exemplary embodiments of the invention, the various features of the invention are sometimes grouped together into a single embodiment, Figure, or its description. However, the method of the present invention should not be interpreted as reflecting the intention that the claimed invention requires more features than those explicitly recited in each claim. Rather, as reflected in the corresponding claims, the invention lies in that the corresponding technical problems can be solved with less than all the features of a single disclosed embodiment. Therefore, the claims that follow the specific embodiment are hereby expressly incorporated into the specific embodiment, where each claim itself serves as a separate embodiment of the present invention.

Those skilled in the art can understand that, in addition to mutually exclusive features, any combination of all the features disclosed in this specification (including the accompanying claims, abstract, and drawings), as well as all the methods or devices disclosed Processes or units are combined. Unless expressly stated otherwise, each feature disclosed in this specification (including the accompanying claims, abstract and drawings) may be replaced by alternative features serving the same, equivalent or similar purpose.

In addition, those skilled in the art can understand that although some of the embodiments described herein include certain features included in other embodiments but not other features, the combination of features of different embodiments is meant to be within the scope of the present invention And form different embodiments. For example, in the claims, any one of the claimed embodiments can be used in any combination.

It should be noted that the above-mentioned embodiments illustrate the present invention rather than limit the present invention, and those skilled in the art can design alternative embodiments without departing from the scope of the appended claims. In the claims, any reference signs placed between parentheses should not be constructed as limitations on the claims. The word "comprising" does not exclude the presence of elements or steps not listed in a claim. The word "a" or "one" before an element does not exclude the presence of multiple such elements. The invention can be realized by means of hardware including several different components and by means of suitably programmed computers. In the unit claims enumerating several devices, several of these devices may be embodied by the same hardware item. The use of the words first, second, and third does not indicate any order. These words can be interpreted as names.

The above is only the specific embodiments of the present invention or the description of the specific embodiments, the scope of protection of the present invention is not limited to this, any person skilled in the art in the technical scope of the present invention, can easily Changes or replacements should be included in the protection scope of the present invention. The protection scope of the present invention shall be subject to the protection scope of the claims.

100, 200, 300 ‧‧‧ rapid tissue molecular spectroscopic imaging device 110‧‧‧ light emitting unit 112‧‧‧ light source 114‧‧‧ beam-expanding focus 120 120‧‧‧ steering unit 130‧‧‧ scanning unit 140‧‧ ‧Relay unit 150‧‧‧Inner view unit 160‧‧‧ Detection unit L1, L2‧‧‧Expansion lens L3‧‧‧Cylinder lens L4, L5‧‧‧Relay lens, lens L6‧‧‧First focus Lens L7‧‧‧second focusing lens L8‧‧‧collimator lens 152‧‧‧coupling objective lens 154‧‧‧imaging fiber bundle 156‧‧‧mini objective lens 162‧‧‧line array detection unit 164‧‧‧spectrum detection unit 166‧‧‧ switching control unit 164a‧‧‧prism-grating-prism, PGP prism 164b‧‧‧convergent lens 164c‧‧‧area array detector

By describing the embodiments of the present invention in more detail with reference to the accompanying drawings, the above and other objects, features, and advantages of the present invention will become more apparent. The drawings are used to provide a further understanding of the embodiments of the present invention, and form a part of the specification. They are used to explain the present invention together with the embodiments of the present invention, and do not constitute a limitation on the present invention. In the drawings, the same reference numerals generally represent the same or similar parts or steps. 1 shows a schematic block diagram of a rapid tissue molecular spectroscopic imaging device according to an embodiment of the present invention; FIG. 2 shows a schematic block diagram of a rapid tissue molecular spectroscopic imaging device according to a first specific embodiment of the present invention Figure; Figure 3 shows a schematic diagram of the optical path of the rapid tissue molecular spectroscopic imaging device according to the first group of specific embodiments of the present invention; Figure 4 shows a rapid tissue molecular spectroscopic imaging device according to the second group of specific embodiments of the present invention 5 is a schematic block diagram of FIG. 5 shows a schematic diagram of the optical path of the rapid tissue molecular spectroscopic imaging device according to the second group of specific embodiments of the present invention.

100‧‧‧ Rapid tissue molecular spectroscopic imaging device

110‧‧‧Light emitting unit

112‧‧‧Light source

114‧‧‧Expanded beam focus

120‧‧‧Steering unit

130‧‧‧ Scanning unit

140‧‧‧Relay unit

150‧‧‧Inner view unit

160‧‧‧ detection unit

Claims (13)

A rapid tissue molecular spectral imaging device, including a light emitting unit, a turning unit, a one-dimensional scanning unit and a detecting unit, wherein: the light emitting unit is used to emit a line of light beam; the turning unit is used to turn the The linear beam passes through the fluorescence of a sample; the one-dimensional scanning unit performs a one-dimensional sweep of the diverted linear beam for adjusting the direction of the diverted linear beam to scan the sample line by line, wherein The one-dimensional scanning unit is a single scanning galvanometer; and the detection unit is used to collect the fluorescent light and form a spatial image and spectral information of the sample. The device according to item 1 of the scope of the patent application, wherein the light emitting unit includes: a light source for emitting a collimated light beam; and a beam expander focused at an outlet of the light source, It is used to expand and collimate the collimated beam into the linear beam in one dimension. The device according to item 1 of the patent application scope, wherein the steering unit is a dichroic mirror. The device according to item 1 of the patent application scope, wherein the device further includes a relay unit and an internal view unit provided downstream of the one-dimensional scanning unit, wherein: the relay unit is used to The line beam scanned by the one-dimensional scanning unit is focused on the inner viewing unit; The inner view unit is used to conduct and focus the focused line beam onto the sample and receive the fluorescent light emitted by the sample; the fluorescent light passes through the relay unit and the one-dimensional scanning unit After the steering unit is collected by the spectrum detection unit. The device according to item 4 of the patent application scope, wherein the endoscope unit includes a coupling objective lens and an imaging fiber bundle, wherein the coupling objective lens is disposed at one end of the imaging fiber bundle for focusing the Of the line beam is coupled into the proximal end of the imaging fiber bundle; and the imaging fiber bundle is used to conduct the incoming line beam. The device according to item 5 of the patent application scope, wherein the endoscope unit further includes a miniature objective lens, the miniature objective lens is disposed at the other end of the imaging fiber bundle, and is used for conducting the imaging fiber bundle The line beam is focused on the sample. The device according to item 1 of the patent application scope, wherein the detection unit includes a linear array detection unit, a spectrum detection unit, and a switching control unit, wherein: the linear array detection unit is used to collect fluorescent light and form A spatial image of the sample; the spectral detection unit for collecting fluorescence and forming a spectral information of the sample; the switching control unit for detecting the linear array detection unit and the spectrum The unit makes the switch selection. The device according to item 7 of the patent application scope, wherein the detection unit further includes a first focusing lens, the first focusing lens is disposed between the linear array detection unit and the switching control unit, In order to focus the fluorescent light emitted by the sample to the linear array detection unit. The device according to item 7 of the patent application scope, wherein the spectrum detection unit is a spectrum camera. The device according to item 9 of the patent application scope, wherein the detection unit further includes a second focusing lens, the second focusing lens is disposed between the spectrum detection unit and the switching control unit for The fluorescent light emitted from the sample is focused on the spectral detection unit. The device according to item 7 of the patent application scope, wherein the spectrum detection unit includes a prism-grating-prism, a condensing lens, and an area array detector arranged in sequence, wherein the prism-grating-prism is used for The fluorescent light transmitted by the turning unit performs dispersion spectroscopy; the condensing lens is used to focus the dispersion-divided fluorescence onto a photosensitive surface of the area array detector; the area array detector is used to form the spectrum News. The device according to item 11 of the patent application scope, wherein the detection unit further includes a second focusing lens and a collimating lens disposed in order between the switching control unit and the spectrum detection unit, wherein: The second focusing lens is used to focus the fluorescent light emitted by the sample; and the collimating lens is used to collimate the focused fluorescent light. The device according to item 10 or item 12 of the patent application scope, wherein the detection unit further includes a slit and/or a filter disposed downstream of the second focusing lens, wherein: the slit The slit is used to allow only the fluorescence of the focusing plane to pass; and The filter is used to filter out stray light.

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