CN215179686U

CN215179686U - Endoscopic Raman spectrum detection system for early cancer screening

Info

Publication number: CN215179686U
Application number: CN202120685572.3U
Authority: CN
Inventors: 黄霞; 张礼豪
Original assignee: Suzhou Institute of Biomedical Engineering and Technology of CAS
Current assignee: Suzhou Institute of Biomedical Engineering and Technology of CAS
Priority date: 2021-04-02
Filing date: 2021-04-02
Publication date: 2021-12-14
Anticipated expiration: 2031-04-02

Abstract

The utility model discloses an peep raman spectrum detecting system for early screening of cancer, include: an endoscope; a light source module for providing illumination light and Raman laser light; the channel module comprises a biopsy channel for the endoscope body to pass through and a light path channel provided with a light source optical fiber and a collection optical fiber; the device comprises a light splitting module, a white light camera, a Raman spectrometer and a computer. The light beam emitted by the illumination light source and the Raman laser in the utility model is in the same light source optical fiber and enters through a channel, so that the consistency of the Raman detection point and the observation point can be ensured, and the detection accuracy is improved; the utility model can prevent the Raman exciting light from irradiating the human tissue all the time and damaging the human tissue by setting the light screen to control the on-off of the Raman laser light path; the utility model discloses can realize quick real-time health condition to human tissue and examine to can be real-timely provide accurate human tissue information for the operation, improve the success rate of operation.

Description

Endoscopic Raman spectrum detection system for early cancer screening

Technical Field

The utility model relates to a raman spectroscopy detects the field, in particular to peep raman spectroscopy detecting system for early screening of cancer.

Background

Cancer is the first killer threatening human health at present, and the death caused by cancer is the first cause of death of residents in China according to the national cancer statistical report. The cure rate of the cancer is closely related to the stage of cancer discovery, and the cure rate of the cancer is greatly improved when the cancer is discovered at an early stage.

The fiberscope is a medical instrument widely applied in clinic, can enter a cavity or an operation incision of a human body without damage and quickly and determines the position of a lesion in the cavity of the human body. However, the pathological form of early cancer is not obvious and is difficult to be directly observed, and the clinical diagnosis is difficult. Raman spectroscopy is an inelastic scattering spectrum that can be used to distinguish between different material structures by detecting the vibrational spectra characteristic of molecules. And because the Raman scattering signal of water in the biological tissue is extremely weak, the interference on detection is small, and the Raman spectrum can accurately identify and analyze the content and distribution of components such as protein, amino acid, lipid, nucleic acid, glycogen and the like, thereby quickly, nondestructively, in situ and accurately realizing the early diagnosis of cancer.

The fiber endoscope commonly used at present consists of three pipelines, namely an illumination light source channel, an image transmission channel and a biopsy channel, and a plurality of endoscope control lines. The existing equipment and method for combining an endoscope with Raman spectroscopy integrates an illumination light source channel, an image transmission channel and a Raman spectroscopy detection channel in the endoscope to realize Raman detection on tissues in a cavity. But is limited by the width of the endoscope channel, and cannot be simultaneously placed into a biopsy channel, so that the diseased tissue cannot be excised.

Another method of combining endoscopy with Raman spectroscopy is to share the same channel for Raman detection and biopsy, and replace the biopsy device for surgical resection after Raman detection of diseased tissue. However, the method cannot cut the detected lesion tissue in real time, and after the device is replaced, the position of the cut lesion tissue is more prone to shift than the position of the Raman detection, so that the accuracy of cutting the edge of the lesion tissue cannot be guaranteed.

In addition, in the existing method, the illumination light source channel and the raman detection channel are two independent channels, which easily causes that white light and raman laser cannot be focused on the same plane at the same time, so that white light imaging is blurred or the raman detection signal is weakened or a signal deeper in the tissue is detected instead of a target tissue signal.

Therefore, a method is found, a Raman detection channel and a biopsy channel coexist, and surgical excision can be carried out while pathological tissues are observed; and the observation point and the Raman detection point of the illumination light source can be consistent and focused on the same horizontal plane, so that the accuracy and the precision of the operation are ensured, and the problem to be solved is solved.

SUMMERY OF THE UTILITY MODEL

The technical problem to be solved by the present invention is to provide an endoscopic raman spectroscopy detection system for early screening of cancer, which is not enough in the prior art.

In order to solve the technical problem, the utility model discloses a technical scheme is: an endoscopic raman spectroscopy detection system for early screening of cancer comprising:

an endoscope including an endoscope body and an operation end for controlling the endoscope body;

a light source module for providing illumination light and Raman laser light;

the channel module comprises a biopsy channel for the endoscope body to pass through and a light path channel provided with a light source optical fiber and a collection optical fiber;

a light splitting module that splits incident light into a first beam and a second beam according to wavelength;

a white light camera for imaging the second beam;

a raman spectrometer for receiving the first beam to obtain raman spectral data;

and a computer;

the illumination light and the Raman laser emitted by the light source module are transmitted to target tissues through the light source optical fibers, the illumination light reflected by the target tissues and the generated Raman light are collected by the collecting optical fibers and are incident to the light splitting module, and the illumination light and the generated Raman light are divided into a first beam larger than the wavelength of the Raman excitation light and a second beam not larger than the wavelength of the Raman excitation light; and the first beam is incident to the Raman spectrometer to obtain Raman spectrum data and transmits the Raman spectrum data to the computer.

Preferably, the light source module includes a three-color LED light source, a filter wheel, an illumination fiber, a raman laser and a raman fiber, the three-color LED light source emits mixed white light with three wavelengths of 605nm, 540nm and 415nm, and the filter wheel has a first narrow band filter which is annularly and uniformly arranged at an interval and can only pass through narrow band green light with the wavelength of 540nm, a second narrow band filter which can only pass through narrow band blue light with the wavelength of 415nm, and a hollow circular hole which can pass through the mixed white light with the three wavelengths of 605nm, 540nm and 415 nm.

Preferably, the first narrow band filter, the second narrow band filter and the hollow circular hole have the same size.

Preferably, the filter wheel is controlled by a motor to rotate, so that incident light emitted by the three-color LED light source is periodically divided into three emergent lights, namely narrow-band blue light with a wavelength of 415nm, narrow-band green light with a wavelength of 540nm and mixed white light, and the emergent light is guided into the light source optical fiber by the illumination optical fiber;

and the Raman optical fiber guides the Raman laser emitted by the Raman laser into the light source optical fiber.

Preferably, the Raman laser is a single-frequency laser with adjustable power and 633 nm.

Preferably, the optical fiber laser further comprises a light shielding plate arranged between the Raman laser and the Raman fiber.

Preferably, the light source optical fibers are arranged in the middle of the light path channel, and the collecting optical fibers comprise a plurality of light source optical fibers arranged at the periphery of the light source optical fibers at uniform intervals.

Preferably, the rotation speed of the filter wheel is 3000 r/min.

Preferably, the light splitting module includes a sideband filter, light with a wavelength of more than 633nm in the incident light passes through the sideband filter to form a first beam to enter the raman spectrometer, and light with a wavelength of not more than 633nm in the incident light is reflected by the sideband filter to form a second beam to enter the white light camera.

The utility model has the advantages that:

1. the utility model adopts the three-color LED light source as the lighting source, the wavelength of the emitted light is 605nm, 540nm and 415nm, the wavelength of the Raman excitation light is 633nm, the two can not interfere with each other, and the realization of the NBI technology and the detection of the Raman spectrum are ensured; the two can be carried out simultaneously, and when the tissue is observed by using a white light image, the Raman detection can be carried out on the tissue; and the wavelength of 633nm is longer, and the damage to human tissues is smaller compared with Raman exciting light (such as 488nm blue light and 532nm green light) with shorter wavelength, so that the Raman detecting device is more suitable for performing Raman detection on the human tissues.

2. The utility model controls the on-off of the Raman laser light path through the light screen, when the white light imaging observation is carried out, the light screen is closed, and only the illumination light source irradiates the human tissue at the moment; when the suspected pathological tissue is observed, the light screen is opened again, and the Raman excitation light irradiates the human tissue; therefore, the Raman exciting light can be prevented from irradiating the human tissue all the time to damage the human tissue.

3. The light beam emitted by the illumination light source and the Raman laser in the utility model is in the same light source optical fiber and enters through a channel, so that the consistency of the Raman detection point and the observation point can be ensured, and the detection accuracy is improved; the defect that in the prior art, white light and Raman laser which enter a human body cavity through two channels for detection have deviation in focusing depth and are not easy to focus on the same plane due to the fact that an illumination light source and a Raman light source enter the human body cavity through the two channels, so that white light imaging is fuzzy, or Raman detection signals are weakened, or signals deeper in tissues are detected instead of target tissue signals is overcome.

4. The utility model adopts the collecting optical fiber to collect the illumination light signal and the Raman scattering light signal at the same time, which can reduce the number of channels and the diameter of the conduit of the channel module; and a plurality of collection optical fibers are uniformly distributed around the light source optical fiber, so that the intensity of the collected optical signals can be increased, meanwhile, the optical signals of excitation points can be completely and uniformly collected, and the quality of the collected signals is improved.

Drawings

Fig. 1 is a schematic structural diagram of an endoscopic raman spectroscopy detection system for early cancer screening according to the present invention;

fig. 2 is a schematic structural diagram of a light source module according to the present invention;

fig. 3 is a schematic structural diagram of the channel module of the present invention.

Description of reference numerals:

1-endoscope; 2-a light source module; 3-a channel module; 4, a light splitting module; 5-a white light camera; 6-Raman spectrometer; 7-a computer; 21-three color LED light source; 22-filter wheel; 23-an illumination fiber; 24-a raman laser; 25-a visor; 26-raman fiber; 31 — biopsy channel; 32-optical path channel; 33-source fiber; 34-a collection fiber; 41-sideband filter; 221 — a first narrow band filter; 222-a second narrow band filter; 223 — a hollow circular hole.

Detailed Description

The present invention is further described in detail below with reference to examples so that those skilled in the art can implement the invention with reference to the description.

It will be understood that terms such as "having," "including," and "comprising," as used herein, do not preclude the presence or addition of one or more other elements or groups thereof.

Example 1

As shown in fig. 1 to 3, an endoscopic raman spectroscopy detection system for early cancer screening according to the present embodiment includes:

an endoscope 1 including an endoscope body and an operation end for controlling the endoscope body, movement and biopsy operation of the endoscope 1 being controlled by the operation end;

a light source module 2 for supplying illumination light and raman laser light;

a channel module 3 including a biopsy channel 31 for passing the endoscope body and an optical path channel 32 provided with a light source optical fiber 33 and a collection optical fiber 34;

a light splitting module 4 that splits incident light into a first beam and a second beam according to wavelength;

a white light camera 5 for imaging the second beam;

a raman spectrometer 6 for receiving the first beam to obtain raman spectral data;

and a computer 7;

the illumination light and the raman laser emitted by the light source module 2 are transmitted to the target tissue through the light source optical fiber 33, the illumination light reflected by the target tissue and the generated raman light are collected by the collection optical fiber 34 and are incident to the light splitting module 4, and are split into a first beam larger than the wavelength of the raman excitation light and a second beam not larger than the wavelength of the raman excitation light; the second beam is incident to the white light camera 5 for imaging and displaying the white light image in the computer 7, and the first beam is incident to the raman spectrometer 6 for obtaining raman spectrum data and transmitting the raman spectrum data to the computer 7.

Referring to fig. 2, in the present embodiment, the light source module 2 includes a three-color LED light source 21, a filter wheel 22, an illumination fiber 23, a raman laser 24 and a raman fiber 26, the three-color LED light source 21 emits mixed white light with three wavelengths of 605nm, 540nm and 415nm, the filter wheel 22 has a first narrow band filter 221, a second narrow band filter 222 and a hollow circular hole 223, wherein the first narrow band filter 221, the second narrow band filter and the hollow circular hole 223 are annularly and uniformly spaced, and can only pass narrow-band green light with a wavelength of 540nm, narrow-band blue light with a wavelength of 415nm, and the mixed white light with three wavelengths of 605nm, 540nm and 415 nm. And the first narrowband filter 221, the second narrowband filter 222 and the empty circular hole 223 have the same size. The filter wheel 22 is controlled by a motor to rotate, so that incident light emitted by the three-color LED light source 21 is periodically divided into three emergent lights, namely narrow-band blue light with the wavelength of 415nm, narrow-band green light with the wavelength of 540nm and mixed white light, and the emergent light is guided into the light source optical fiber 33 by the illumination optical fiber 23; the raman fiber 26 guides the raman laser light emitted from the raman laser 24 to the light source fiber 33.

In a preferred embodiment, the filter wheel 22 rotates at 3000 r/min.

In a preferred embodiment, the raman laser 24 is a single frequency 633nm laser that is power tunable.

In a preferred embodiment, the optical fiber Raman spectrometer further comprises a light shielding plate 25 arranged between the Raman laser 24 and the Raman fiber 26, and the light shielding plate 25 is used for controlling the on-off of the Raman laser light path. Because the stable laser emitted by the raman laser 24 needs a certain time, when the Raman spectrometer works, the raman laser 24 is kept normally open, and the on-off of the raman laser light path is controlled by the light shielding plate 25, so that the Raman excitation light can be prevented from irradiating human tissues all the time and damaging the human tissues.

Referring to fig. 3, in a preferred embodiment, the channel module 3 is an integrated catheter, in which a biopsy channel 31 and an optical channel 32 are arranged, and in which an optical source fiber 33 and a collecting fiber 34 are arranged in the optical channel 32. In a further preferred embodiment, the light source fibers 33 are disposed in the middle of the light path channel 32, and the collection fibers 34 comprise a plurality of light source fibers 33 disposed at regular intervals around the periphery thereof. The white light signal and the raman signal of the observation point can be uniformly and completely collected by uniformly distributing the plurality of collecting optical fibers 34.

In a preferred embodiment, the splitting module 4 includes a side band filter 41 through which light having a wavelength greater than a set value is transmitted and light having a wavelength less than the set value is reflected. In this embodiment, light with a wavelength of more than 633nm in the incident light passes through the sideband filter 41 to form a first beam and enters the raman spectrometer 6, light with a wavelength of not more than 633nm in the incident light is reflected by the sideband filter 41 to form a second beam and enters the white light camera 5 for imaging, and a white light image is displayed by the computer 7.

The second beam contains three kinds of light of periodic narrow-band blue light with the wavelength of 415nm, narrow-band green light with the wavelength of 540nm and mixed white light, and the different kinds of light are respectively processed and displayed in the computer 7. Due to the absorption characteristics of the mucosa and the blood vessels to green (540nm) light and blue (415nm) light, the blood vessels can be displayed more clearly, so that NBI (narrow Band imaging) narrow-Band imaging is realized, the contrast of the image can be improved, more blood vessel distribution details are displayed in a white light image of the tissue, and the local blood supply condition of the lesion tissue is reflected. It should be understood that NBI narrowband imaging is conventional prior art, and is not the focus of the present invention, and therefore the principle thereof is not repeated.

The raman spectrometer 6 is a conventional product including a CCD detector and a grating. The first beam is collected by the CCD detector after being split by the spectrometer, and a Raman spectrum signal is transmitted into the computer 7, and the computer 7 judges the collected Raman spectrum to distinguish whether the detected tissue is normal tissue or cancerated tissue and carry out identification display in a white light image. It should be understood that the present invention is focused on providing a hardware structure of an endoscopic raman spectroscopy detection system for early cancer screening, wherein the above-mentioned means for analyzing raman spectra can be realized by a conventional computer with the above-mentioned functions, and the present invention is not limited thereto.

Example 2

In the present embodiment, the working principle of the present invention will be described in detail by taking a gastroscope as an example.

During detection, the catheter-shaped channel module 3 is guided into the stomach of a human body, the endoscope body is arranged in the biopsy channel 31, and the lens of the endoscope body is aligned with gastric mucosa tissue to be detected. The three-color LED light source 21 in the light source module 2 provides illumination light for detection, light emitted by the three-color LED light source 21 is transmitted through the illumination optical fiber 23, and is guided into the gastric mucosa tissue to be detected through the light source optical fiber 33 after being combined with the Raman optical fiber 26, wherein the rotating speed of the filter wheel 22 is 3000r/min, namely the illumination light is narrow-band blue light with the wavelength of 415nm and narrow-band green light with the wavelength of 540nm with the period of 20ms, and is mixed white light. The collection optical fiber 34 collects the reflected light of the tissue to be detected, the reflected light enters the white light camera 5 through the light splitting module 4, the white light camera 5 transmits imaging data to the computer 7, the computer 7 respectively processes and images the signals collected under the three light sources with the period of 20ms according to the types of the light sources, and white light images of the gastric mucosa tissue with high contrast and more details are displayed on the screen of the computer 7 through an NBI technology.

For example, in an alternative embodiment, a physician may perform raman detection of morphologically suspect tissue after viewing it in a white light image. At this time, the light shielding plate 25 is opened (the raman laser 24 is turned on in advance to keep stable output), laser with wavelength of 633nm emitted by the raman laser 24 is transmitted through the raman optical fiber 26, and enters the human body cavity through the light source optical fiber 33 after being combined with the illumination optical fiber 23, and the gastric mucosa tissue to be detected is measured; raman scattered light generated by the gastric mucosa tissue is collected by the collecting optical fiber 34 and enters the Raman spectrometer 6 through the light splitting module 4, and the Raman spectrometer 6 transmits Raman spectrum data after light splitting processing and collection to the computer 7 for processing so as to judge whether the tissue is normal. It should be understood, however, that the processing of the raman spectral data by the computer 7 is prior art and is not limited to or modified by the present invention. For example, in an alternative scheme, after receiving the current raman spectrum data, the computer compares the raman spectrum with raman spectrum data of normal cells and cancerous cells of gastric mucosal tissue in a database pre-stored in the computer, and finally obtains a discrimination result, and displays a corresponding detection part in a white light image in real time to guide a doctor to perform the next operation.

If the result is normal gastric mucosa tissue, the light screen 25 is closed, and the observation is continued to find other possible canceration parts. If the result of the display is a cancerous gastric mucosal tissue, the doctor performs a surgery such as sampling or removal of the cancerous tissue using a medical instrument through the biopsy channel 31. In the operation process, whether the gastric mucosa tissue is cancerous or not can be detected in real time, so that the edge of the cancerous tissue can be accurately cut.

In the prior art, due to the excessive number of channels, four channels, namely an illumination light source channel, an image transmission channel, a raman spectrum detection channel and a biopsy channel 31, cannot enter the body cavity of a human body through the channel module 3 at the same time. In the existing technology combining the endoscope 1 and the raman detection, one channel only comprises an illumination light source channel, an image transmission channel and a raman spectrum detection channel, and the real-time detection of a white light image observation point can be realized. But the lack of a biopsy channel 31 removes the important advantage of the endoscopic 1 technique in that it allows for non-destructive and rapid removal of diseased tissue. The other is that the raman spectrum detection channel and the biopsy channel 31 share the same channel, and after raman detection is completed, the raman spectrum detection channel is extracted and replaced by the biopsy channel 31 for biopsy operation, but the detected lesion tissue cannot be excised in real time. And after the device is replaced, the position for cutting off the pathological change tissue is easy to deviate, and the accuracy for cutting off the edge of the pathological change tissue cannot be ensured. The illumination light source and the Raman laser light source are combined in one light source optical fiber 33 and enter through one channel, so that the real-time Raman detection can be carried out on human tissues, meanwhile, the surgical excision can be carried out according to the real-time detection result, and the accuracy of excision of the edges of the pathological tissues is ensured.

While the embodiments of the invention have been disclosed above, it is not limited to the applications listed in the description and the embodiments, which are fully applicable in all kinds of fields where the invention is suitable, and further modifications may readily be made by those skilled in the art, and the invention is therefore not limited to the specific details without departing from the general concept defined by the claims and the scope of equivalents.

Claims

1. An endoscopic raman spectroscopy detection system for early screening of cancer, comprising:

a light source module for providing illumination light and Raman laser light;

a white light camera for imaging the second beam;

and a computer;

2. The endoscopic raman spectroscopy detection system for early cancer screening according to claim 1, wherein the light source module includes a tri-color LED light source emitting a mixed white light of three wavelengths 605nm, 540nm and 415nm, a filter wheel having a first narrow band filter capable of passing only a narrow band green light of 540nm wavelength, a second narrow band filter capable of passing only a narrow band blue light of 415nm wavelength, and a hollow circular hole capable of passing the mixed white light of three wavelengths 605nm, 540nm and 415nm, which are annularly and uniformly spaced.

3. The endoscopic raman spectroscopy detection system for early screening of cancer according to claim 2, wherein the first narrowband filter, the second narrowband filter and the empty circular aperture are all the same size.

4. The system according to claim 2, wherein the filter wheel is controlled by a motor to rotate, so as to periodically divide incident light emitted from the three-color LED light source into three kinds of emergent light, namely narrow-band blue light with a wavelength of 415nm, narrow-band green light with a wavelength of 540nm and mixed white light, and the illuminating fiber guides the emergent light into the light source fiber;

5. The endoscopic raman spectroscopy detection system for early screening of cancer according to claim 2, wherein the light source optical fiber is disposed in a middle portion of the light path channel, and the collection optical fiber comprises a plurality of pieces disposed at a periphery of the light source optical fiber at regular intervals.

6. The endoscopic raman spectroscopy detection system for early cancer screening according to claim 2, wherein the raman laser is a single frequency laser at 633nm with adjustable power.

7. The endoscopic raman spectroscopy detection system for early cancer screening according to claim 4, further comprising a shutter plate disposed between the raman laser and raman fiber.

8. The endoscopic raman spectroscopy detection system for early screening of cancer according to claim 4, wherein the rotation speed of the filter wheel is 3000 r/min.

9. The endoscopic raman spectroscopy detection system for early cancer screening according to claim 5, wherein the light splitting module comprises a sideband filter through which light with a wavelength greater than 633nm of the incident light is transmitted to form a first beam into the raman spectrometer, and wherein light with a wavelength not greater than 633nm of the incident light is reflected by the sideband filter to form a second beam into the white light camera.