An endoscopic multi-mode probe based in-situ tumor pathological detection system

Abstract

The application provides an endoscopic multi-mode probe-based tumor in-situ pathological detection system, which comprises a main controller, an SC laser, a DUV laser, a comb filter, a polarizer, a microarray lens head, a multiplexing beam combiner, a conjugate coupling module, an endoscopic optical fiber bundle, a FAST optical fiber bundle, an SC spectrometer and a DUV spectrometer. The application is aimed at G14-grade bronchus navigation surgery robot in-situ pathological detection, and proposes an endoscopic multi-mode optical probe-based detection system, which can realize SC, DUVRS, DUVLIF and mIHC FAST hyperspectral image spectrum integration detection, and output multi-modal hyperspectral fusion images reflecting the spatial distribution of the chemical components of the diagnosis point tissues and corresponding spectral characteristic data, so as to provide real-time, accurate and multi-modal data or information for doctors to diagnose.

Description

TECHNICAL FIELD

[0001] The application belongs to the technical field of photoelectric detection, and particularly relates to a tumor in-situ pathological detection system based on an endoscopic multi-mode probe. BACKGROUND

[0002] With the increasing global environmental and health challenges, there is an urgent need for high-precision and minimally invasive in-vivo tissue analysis technology. At present, endoscopy, as an important in-vivo imaging tool, mainly relies on morphological images for analysis, and lacks the ability to perform real-time and in-situ quantitative analysis of the biochemical components of the target tissue, resulting in a single dimension of information provided and the reliability of the analysis results needing to be improved. On the other hand, although the in-vitro laboratory analysis based on tissue sampling is a benchmark method for component analysis, its process is complex and time-consuming, and it cannot achieve real-time and in-vivo analysis feedback, making it difficult to meet the technical expectations of modern medicine for “integrated detection and intervention”.

[0003] From the perspective of technical implementation, the bronchial structure of the lung is complex and finely graded, from the G1 main bronchus to the G23+ alveoli. To effectively analyze the early lesions in the lung in-situ, the analysis equipment must be able to reach and act on the distal regions of the 14th grade and above, such as the terminal bronchioles and alveoli. However, the technical performance of existing lung analysis equipment is usually only able to reach the 6th-8th grade bronchus, resulting in a huge “depth gap” that severely limits the analysis capability of early targets.

[0004] The existing technical solutions have obvious technical bottlenecks and operational risks. For example, the ultra-fine endoscopic device for G4-G8 grade bronchus, even combined with ultrasound or electromagnetic navigation technology, has a narrow working channel and limited field of view, resulting in an unsatisfactory success rate of sampling and analysis. For more distal -> G8 targets, existing technologies often rely on CT-guided percutaneous puncture or open surgery, which not only exposes the operating object to radiation, but also carries high technical risks such as pneumothorax and bleeding, and is highly invasive. The appearance of the bronchoscope surgery robot NBSR has solved the problem of reaching depth from a mechanical structure, reaching the 14th grade, and its equipped hollow thin tube - about 1mm inner diameter provides a new technical platform for the introduction of in-vivo analysis tools.

[0005] The NBSR robot platform creates conditions for in-vivo analysis, but there is currently a lack of a professional integrated system that can pass through its small working channel and complete multi-mode, high-precision in-situ component analysis in deep and narrow spaces. Therefore, there is an urgent need in the field for a new in-situ component analysis system that can adapt to the NBSR platform to solve the core technical problems of the existing technology, such as inability to reach depth, single dimension of information, non-real-time analysis, and high operational risk. SUMMARY

[0006] The tumor in-situ pathological detection system based on the endoscopic multi-mode probe is matched with the NBSR, and the multi-mode optical probe is combined with three optical detection methods of supercontinuum SC laser reflection (absorption, deep ultraviolet (DUV) laser scattering and polarization hyperspectral multiple fluorescence immunohistochemistry (mIHC), so as to provide data or information for the diagnosis of lung in-situ early pathology, realize multi-modal optical signal acquisition of a target area, and generate a multi-dimensional data set containing tissue scattering characteristics, biological molecule Raman / fluorescence characteristic spectrum and spatial distribution.

[0007] To this end, the above-mentioned purposes of the present application are realized by the following technical solutions.

[0008] A tumor in-situ pathological detection system based on an endoscopic multi-mode probe comprises:

[0009] a main controller;

[0010] a light source module comprising an SC laser and a DUV laser, wherein an exit light path of the SC laser is further sequentially provided with a comb filter and a polarizer;

[0011] a detection module comprising an SC spectrometer and a DUV spectrometer;

[0012] a multiplexing beam combiner, an input end of which is optically connected to the light source module, for receiving and combining beams of original laser from the SC laser, laser processed by the comb filter and the polarizer, and laser from the DUV laser;

[0013] a conjugate coupling module, an input end of which is optically connected to an output end of the multiplexing beam combiner;

[0014] an endoscopic optical fiber bundle, a proximal end of which is optically connected to an output end of the conjugate coupling module, and a distal end of which is provided with a microarray lens head, and the fiber arrangement of the proximal end and the distal end of the endoscopic optical fiber bundle is a square fiber array;

[0015] a FAST optical fiber bundle, a distal end of which is optically connected to the conjugate coupling module, and a proximal end of which forms a FAST proximal fiber arrangement;

[0016] The main controller is electrically connected with the light source module and the detection module, controls the time-sharing working time sequence thereof, and receives and processes spectral data.

[0017] In addition to the above technical solutions, the present application can also adopt or combine the following technical solutions:

[0018] As a preferred technical scheme of the present application: the micro-lens head comprises a main lens, a front lens array and a rear lens array arranged in sequence along the light path, and the lens element arrangement of the front lens array and the rear lens array is the same as and one-to-one corresponding to the arrangement of the square fiber array.

[0019] As a preferred technical scheme of the present application: the fiber end face of the FAST fiber bundle far end is also a square fiber array square array, and is conjugated with the square fiber array of the endoscope fiber bundle far end.

[0020] As a preferred technical scheme of the present application: the SC spectrometer is a high-resolution spectrometer covering from visible light to infrared waveband, which is spliced by multiple sub-modules and is respectively used for detecting visible, near-infrared and mid-infrared waveband.

[0021] As a preferred technical scheme of the present application: the DUV spectrometer is a narrow-spectrum high-resolution spectrometer, which is configured to simultaneously detect deep-ultraviolet Raman scattering signals and laser-induced fluorescence signals.

[0022] As a preferred technical scheme of the present application: the center of the conjugate coupling module is provided with a proportional light splitting plate, which is used for reflecting the signal light from the endoscope fiber bundle to the far end of the FAST fiber bundle.

[0023] As a preferred technical scheme of the present application: the FAST near-end fiber of the FAST fiber bundle near end is arranged in a single column linear arrangement by rotating and splicing the square square array of the far end row by row, which is used for parallel alignment with the entrance slit of the SC spectrometer or the DUV spectrometer.

[0024] Compared with the prior art, the tumor in-situ pathological detection system based on the endoscopic multi-modal probe has the following beneficial effects: the information complementarity of multi-modal optical technology is utilized: four kinds of spectral technologies (SC reflection spectrum, DUV Raman spectrum DUVRS, DUV laser-induced fluorescence DUVLIF, and polarization multiple immunofluorescence mIHC) are integrated in a single probe, the information complementarity of multi-modal optical technology is utilized, the spatial morphology image and the point-by-point chemical composition spectrum of the target are simultaneously obtained in one measurement through the square fiber array and the conjugate light path design, the "image-spectrum integration" capability of the FAST hyperspectral technology is utilized, the limitations of the traditional endoscope only relying on morphological diagnosis are solved, the quantitative information at the molecular level is provided, the molecular-level accurate detection is possible, the problem of "single information" is solved, the information limitations of single optical technology are overcome, the FAST hyperspectral image-spectrum integration detection of SC, DUVRS, DUVLIF and mIHC can be realized, and the multi-modal hyperspectral fusion image reflecting the spatial distribution of the chemical composition of the diagnosis point tissue and the corresponding spectral feature data are output, which provide real-time, accurate and multi-modal data or information for doctors to diagnose.

[0025] In the application, the SC reflection spectrum, polarization mIHC and DUV Raman / fluorescence (DUVRS / DUVLIF) three modes share the same set of endoscopic probes, avoiding the trouble of changing probes, ensuring the consistency of multiple detection positions, obtaining complementary information, and truly integrating multiple modes.

[0026] The FAST fiber bundle converts the square fiber array at the distal end into a single linear array at the proximal end, which is coupled with the spectrometer slit, so that the hyperspectral image (spatial information) and point-by-point spectrum (chemical component information) can be obtained simultaneously in one exposure, realizing seamless connection from "seeing" to "analysis", and providing a "image-spectrum integration" FAST hyperspectral technology.

[0027] In the application, the square fiber array and the microarray lens (front and rear lens arrays) adopt a one-to-one correspondence of conjugate relationship, which maximizes the fidelity and spatial resolution of signal transmission, provides a precise conjugate optical path design, and makes the finally reconstructed hyperspectral image clear and accurate, laying a foundation for accurate Mapping analysis.

[0028] In the application, the flexible laser multiplexing mechanism, the multiplexing combiner, the SC original laser, the SC filtered polarization laser and the DUV laser are combined into the same channel at different times, realizing multi-mode detection under a single physical channel, simplifying the system structure and improving the reliability.

[0029] In the application, DUV laser is used to excite Raman and fluorescence signals simultaneously, and spectral separation is used to realize spectrum division multiplexing, so that two types of key biological information, Raman characteristics and sky fluorescence characteristics, are obtained in one measurement, and the detection efficiency and information amount are greatly improved through the joint detection of deep ultraviolet spectrum. BRIEF DESCRIPTION OF DRAWINGS

[0030] Figure 1 Fig. 1 is a structural schematic diagram of a tumor in-situ pathological detection system based on an endoscopic multi-mode probe according to the application, Figure 2 Fig. 2 is a microarray lens head structure;

[0031] In the drawing, hyperspectral image 1; spectral dimension 2; spatial dimension 3; DUV laser 4; main controller 5; SC laser 6; comb filter 7; polarizer 8; multiplexing combiner 9; conjugate coupling module 10; proximal and distal endoscope fiber arrangement 11; FAST distal fiber arrangement 12; hollow thin catheter 13; NBSR 14; lung bronchus 15; microarray lens head 16; FAST proximal fiber arrangement 17; DUV spectrometer 18; spectrometer detector 19; point-by-point spectrum 20; SC spectrometer 21; square fiber array 22; lung tissue 23; main lens 24; front lens array 25; rear lens array 26; main optical axis 27; diagnostic point 28; endoscope fiber bundle 29; FAST fiber bundle 30; proportional light splitting plate 31; two-dimensional area array 32. DETAILED DESCRIPTION

[0032] The application will be further described in detail with reference to the drawings and specific examples.

[0033] The tumor in-situ pathological detection system based on an endoscopic multi-mode probe of the application is composed of a main controller, an SC laser, a DUV laser, a comb filter, a polarizer, a microarray lens head, a multiplexing combiner, a conjugate coupling module, an endoscope fiber bundle, a FAST fiber bundle, an SC spectrometer and a DUV spectrometer.

[0034] The main controller controls the SC laser, the DUV laser, the SC spectrometer and the DUV spectrometer, sets and adjusts the working time sequence, receives spectral data and hands them over to the system algorithm software for processing and analysis.

[0035] The SC laser cooperates with the SC spectrometer to realize supercontinuum spectrum detection. In addition, the supercontinuum spectrum laser emitted by the SC laser is filtered by the comb filter and then passes through the polarizer to obtain a multiple-polarization fluorescence excitation source required by the mIHC. The multiple-polarization fluorescence excitation source cooperates with the SC spectrometer to realize mIHC detection. The SC spectrometer covers the spectrum from visible to infrared, and is composed of multiple modules to meet the requirements of wide spectrum and high resolution, and realizes visible, near-infrared and mid-infrared spectrum detection, respectively.

[0036] The DUV laser cooperates with the DUV spectrometer to realize the joint detection of deep ultraviolet Raman and laser-induced fluorescence, i.e., DUVRS and DUVLIF. The DUV spectrometer is a narrow-spectrum high-resolution high-signal-to-noise ratio spectrometer. The Stokes wave number frequency shift of deep ultraviolet Raman of most molecules is still located in the medium and short wave ultraviolet segment, while the fluorescence spectrum excited by it at the same time is mostly located in the long wave ultraviolet segment and the visible spectrum segment. Certain separation degree can be achieved in the excitation of Raman and fluorescence spectrum, and the spectrum division multiplexing joint detection of DUVRS and DUVLIF is realized.

[0037] The multiplexing combiner time-division combines the laser light emitted by the SC laser, the laser light filtered by the comb filter, and the laser light emitted by the DUV laser, and outputs the combined light into the conjugate coupling module. The proximal and distal end fibers of the endoscope fiber bundle are arranged in a square fiber array. The distal end of the endoscope fiber bundle is attached to a microarray lens.

[0038] The microarray lens is composed of a main lens, a front lens array, and a rear lens array. The front lens array and the rear lens array have the same square array arrangement as the square fiber array.

[0039] The distal end of the FAST fiber bundle is also a square fiber array arranged in a square array, which is conjugate with the distal end face of the endoscope fiber bundle.

[0040] The endoscope fiber bundle is inserted into the hollow catheter of the NBSR, and the SC laser and the DUV laser are time-division activated. The three types of laser light coupled into the endoscope fiber bundle are emitted by the square fiber array, and then focused point by point by the rear lens array, and then dispersed point by point by the front lens array, and finally focused point by point by the main lens to the diagnosis point of the lung tissue. The three types of signals excited by the target at the diagnosis point are focused point by point by the main lens into the front lens array, and then collected point by point by the rear lens array into the endoscope fiber bundle with a square fiber array arrangement. The signals are transmitted reversely to the conjugate coupling module and reflected by the central proportional beam splitter to the FAST fiber bundle.

[0041] After the signals enter the FAST fiber bundle, they reach the proximal end of the FAST fiber bundle. The FAST proximal end rotates and splices the square array into a single column, i.e., the FAST proximal fiber arrangement, which is parallelly aligned and fixed with the entrance slit of the SC spectrometer and the DUV spectrometer. All the spectrometer detectors are two-dimensional area arrays, including spatial and spectral dimensions. The spatial dimension corresponds to each fiber unit of the FAST proximal fiber arrangement, and the spectral dimension corresponds to the spectral composition of the signal transmitted by each fiber unit. By rotating and rearranging the spatial dimension single column every square fiber array row pixel, the original square fiber array arrangement is restored, and a hyperspectral image can be obtained. At the same time, the target pixel corresponding to each fiber of the FAST fiber bundle can be analyzed individually, and a point-by-point spectrum can be obtained. The hyperspectral image and point-by-point spectrum obtained by the three endoscopic multi-mode optical probes are comprehensive, and objective data or information for diagnosis are provided.

[0042] The endoscopic multi-mode probe based tumor in-situ pathological detection system inserts the endoscopic optical fiber bundle into the hollow thin catheter of the NBSR to reach the bronchus of the patient's lung. The SC laser and the DUV laser are started at different times. The three kinds of laser light coupled into the endoscopic optical fiber bundle are emitted by the square fiber array, focused point by point by the rear lens array one by one along the main optical axis, then dispersed point by point by the front lens array, and finally focused to the lung tissue diagnosis point by the main lens. The in-situ target at the diagnosis point is excited by the three kinds of signals excited by the three kinds of laser light, and the signals are focused point by point into the front lens array by the main lens, and then collected into the endoscopic optical fiber bundle with a square fiber array arrangement by the rear lens array. The signals are reversely transmitted to the conjugate coupling module and reflected to the FAST optical fiber bundle by the central proportional beam splitter.

[0043] After the signals enter the FAST optical fiber bundle, they reach the FAST proximal end. The FAST proximal end rotates and splices the square array into a single column, i.e., the FAST proximal fiber arrangement, which is fixed in parallel with the entrance slit of the SC spectrometer and the DUV spectrometer. All the spectrometer detectors are two-dimensional area arrays, including a spatial dimension and a spectral dimension. The spatial dimension corresponds to each fiber unit of the FAST proximal fiber arrangement, and the spectral dimension is the spectral composition of the signal transmitted by each fiber unit. The spatial dimension is rotated and rearranged every square fiber array row of image elements, and the original square fiber array arrangement is restored, so that a hyperspectral image can be obtained. At the same time, the target image element corresponding to each fiber of the FAST optical fiber bundle can be analyzed individually, and a point-by-point spectrum can be obtained. The hyperspectral image and the point-by-point spectrum obtained by the three kinds of endoscopic multi-mode optical probes are comprehensive, and provide objective data or information for the diagnosis of the tumor in-situ diagnosis point.

[0044] Embodiment 1

[0045] As shown in Figure 1 and Figure 2 , the endoscopic multi-mode probe based tumor in-situ pathological detection system of the present application is composed of a main controller 5, an SC laser 6, a DUV laser 4, a comb filter 7, a polarizer 8, a microarray lens head 16, a multiplexing beam combiner 9, a conjugate coupling module 10, an endoscopic optical fiber bundle 29, a FAST optical fiber bundle 30, an SC spectrometer 21, and a DUV spectrometer 18.

[0046] The main controller 5 controls the SC laser 6, the DUV laser 4, the SC spectrometer 21, and the DUV spectrometer 18, sets and adjusts the working time sequence, receives spectral data, and processes and analyzes the data by the system algorithm software.

[0047] The SC laser 6 (its wavelength range is 400-2500 nm in this embodiment) cooperates with the SC spectrometer 21 (its wavelength range is 400-2500 nm in this embodiment) to realize supercontinuum spectrum detection. In addition, the supercontinuum spectrum laser emitted by the SC laser 6 is filtered by the comb filter 7, and then passes through the polarizer 8 to obtain a multiple polarization fluorescence excitation source required by the mIHC. The multiple polarization fluorescence excitation source cooperates with the SC spectrometer to realize mIHC detection. The SC spectrometer 21 covers the spectrum from visible to infrared (its wavelength range is 400-2500 nm in this embodiment), and is composed of multiple modules (three modules in this embodiment) to meet the requirements of wide spectrum and high resolution, and realizes visible, near-infrared, and mid-infrared spectrum detection.

[0048] The DUV laser 4 (its wavelength is 248.6 nm in this embodiment) cooperates with the DUV spectrometer 18 to realize combined detection of deep ultraviolet Raman and laser-induced fluorescence, i.e., DUVRS and DUVLIF. The DUV spectrometer 18 is an ultraviolet narrow-spectrum high-resolution high-signal-to-noise ratio spectrometer. The Stokes wave number frequency shift of most molecules in deep ultraviolet Raman is still located in the medium and short wave ultraviolet segment, and the fluorescence spectrum excited at the same time is mostly located in the long wave ultraviolet segment and the visible spectrum segment. Certain separation degree is achieved when the Raman and fluorescence spectra are excited at the same time, and the spectrum division multiplexing combined detection of DUVRS and DUVLIF is realized.

[0049] The multiplexing combiner 9 divides time to split and combine the laser emitted by the SC laser 6, the laser filtered by the comb filter 7 after the laser emitted by the SC laser 6, and the laser emitted by the DUV laser 4 into three laser sources, and then outputs the laser into the conjugate coupling module 10. The proximal and distal endoscope fiber arrangement 11 of the endoscope fiber bundle 29 is a square fiber array 22. The microarray lens head 16 is attached to the distal end of the endoscope fiber bundle 29.

[0050] The microarray lens head 16 is composed of a main lens 24, a front lens array 25, and a rear lens array 26. The front lens array 25 and the rear lens array 26 have the same square array arrangement as the square fiber array 22.

[0051] The distal end of the FAST fiber bundle 30 is also a square fiber array 22 with a square array arrangement, which is conjugate with the distal end face of the endoscope fiber bundle 29.

[0052] In the application, the endoscopic multi-mode probe-based in-situ tumor pathological detection system is used to insert the endoscopic fiber bundle 29 into the hollow catheter 13 of the NBSR 14 to reach the bronchus 15 of the patient's lung. The SC laser 6 and the DUV laser 4 are started at different times. The three kinds of laser light coupled into the endoscopic fiber bundle 29 are emitted from the square fiber array 22, are focused one by one along the main optical axis 27 through the rear lens array 26, are diverged one by one through the front lens array 25, and are finally focused one by one to the lung tissue 23 at the diagnosis point 28 through the main lens 24. The in-situ target at the diagnosis point 28 is excited by three kinds of signals: DUVRS, DUVLIF, SC, and mIHC. In this embodiment, the signals are detected at different times to avoid signal interference, are focused one by one into the front lens array 25 through the main lens 24, and are then collected one by one into the endoscopic fiber bundle 29 with the square fiber array 22 arrangement through the rear lens array 26. The signals are reversely transmitted to the conjugate coupling module 10 and are reflected to the FAST fiber bundle 30 by the central proportional beam splitter 31.

[0053] After the signals enter the FAST fiber bundle 30, the FAST proximal end is reached. The FAST proximal end rotates and splices the square matrix into a single column, i.e., the FAST proximal fiber arrangement 17, and is fixed in parallel with the entrance slit of the SC spectrometer 21 and the DUV spectrometer 18. In this embodiment, the signals are detected at different times, i.e., the corresponding spectrometer is connected when the corresponding detection is performed. All the spectrometer detectors 19 are two-dimensional surface arrays 32, including a spatial dimension 3 and a spectral dimension 2. The spatial dimension 3 corresponds to each fiber unit of the FAST proximal fiber arrangement 17, and the spectral dimension 2 is the spectral composition of the signal transmitted by each fiber unit. The spatial dimension 3 is rotated and rearranged every other row of the square fiber array 22, and the original square fiber array 22 arrangement is restored, so that the hyperspectral image 1 can be obtained. Meanwhile, the target pixels corresponding to each fiber of the FAST fiber bundle 30 can be analyzed individually to obtain the point-by-point spectrum 20. The hyperspectral image 1 and the point-by-point spectrum 20 obtained by the three kinds of endoscopic multi-mode optical probes are combined to provide objective data or information for the diagnosis of the in-situ tumor diagnosis point 28.

[0054] In the application, FAST refers to fiber array spectral translation, DUV refers to deep ultra violet, SC refers to Supercontinuum, and NBSR refers to Navigation bronchoscopy surgical robot.

[0055] The above detailed description is merely exemplary in nature and is not intended to limit the application as described herein. Any modification or equivalent arrangement within the spirit or scope of the application should be considered to fall within the scope of the application.

Claims

1. A tumor in situ pathological detection system based on endoscopic multi-mode probes, characterized in that: Main controller; The light source module includes an SC laser and a DUV laser, and the output optical path of the SC laser is also provided with a comb filter and a polarizer in sequence. The detection module includes an SC spectrometer and a DUV spectrometer, wherein the DUV laser works in conjunction with the DUV spectrometer to achieve deep ultraviolet Raman and laser-induced fluorescence; The multiplexer, whose input end is optically connected to the light source module, is used to receive and combine the original laser from the SC laser, the laser processed by the comb filter and polarizer, and the laser from the DUV laser; the laser processed by the comb filter and polarizer is the multipolarized fluorescence excitation source required by mIHC. A conjugate coupling module, the input of which is optically connected to the output of the multiplexer; The endoscopic fiber bundle has its near end optically connected to the output end of the conjugate coupling module, and its far end is provided with a microarray lens head. The fiber arrangement at both the near end and the far end of the endoscopic fiber bundle is a square fiber array. The FAST fiber bundle has its far end optically connected to the conjugate coupling module, and its near end forms a FAST near-end fiber arrangement. The FAST near-end fiber arrangement at the near end of the FAST fiber bundle is a single-column linear arrangement formed by rotating and splicing the far-end square array row by row, which is used to align parallel to the entrance slit of the SC spectrometer or DUV spectrometer. The main controller is electrically connected to the light source module and the detection module, controls their time-division multiplexing operation sequence, and receives and processes spectral data.

2. The tumor in situ pathological detection system based on endoscopic multi-mode probes as described in claim 1, characterized in that: The microarray lens head includes a main lens, a front lens array, and a rear lens array arranged sequentially along the optical path. The lens elements of the front lens array and the rear lens array are arranged in the same way as the square fiber array and correspond one-to-one.

3. The tumor in situ pathological detection system based on endoscopic multi-mode probes as described in claim 1, characterized in that: The fiber end face of the FAST fiber bundle is also a square fiber array, and is conjugate with the square fiber array at the far end of the endoscopic fiber bundle.

4. The tumor in situ pathological detection system based on endoscopic multi-mode probes as described in claim 1, characterized in that: The SC spectrometer is a high-resolution spectrometer covering the visible to infrared bands. It is composed of multiple sub-modules, which are used to detect the visible, near-infrared and mid-infrared bands respectively.

5. The tumor in situ pathological detection system based on endoscopic multi-mode probes as described in claim 1, characterized in that: The DUV spectrometer is a narrow-spectrum, high-resolution ultraviolet spectrometer configured to simultaneously detect deep ultraviolet Raman scattering signals and laser-induced fluorescence signals.

6. The tumor in situ pathological detection system based on endoscopic multi-mode probes as described in claim 1, characterized in that: The conjugate coupling module has a proportional beam splitter at its center, which is used to reflect the signal light from the endoscopic fiber bundle to the far end of the FAST fiber bundle.

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