Endotoxin detection system

Abstract

The utility model relates to the technical field of endotoxin monitoring, in particular to an endotoxin detection system. The utility model aims to solve the problem that the detection efficiency of the creotoxin is low. The endotoxin detection system comprises a light source emitting device, an incident light lead, a microfluidic channel, an optical fiber biochemical sensor, an emergent light lead and a spectral analysis device, the optical fiber biochemical sensor is arranged inside the microfluidic channel, the optical fiber biochemical sensor is provided with a sample groove, the microfluidic channel is provided with at least two sample inlets and at least one sample outlet, and a microfluidic channel area between any sample inlet and any sample outlet covers the sample groove; one end of the incident light lead is connected with the light source generating device, the other end of the incident light lead penetrates into the micro-fluidic channel and is connected to the optical fiber biochemical sensor, one end of the emergent light lead is connected with the optical fiber biochemical sensor, and the other end of the emergent light lead penetrates out of the micro-fluidic channel and is connected to the spectral analysis device.

Description

Technical Field

[0001] This utility model relates to the field of endotoxin monitoring technology, and more specifically, to an endotoxin detection system. Background Art

[0002] Endotoxins, also known as lipopolysaccharides (LPS), are major components of the outer membranes of Gram-negative bacteria and some cyanobacteria. Bacterial cells can release large amounts of LPS during cell death or small amounts during normal metabolism, thus exerting toxicity on humans. LPS is a significant pollutant in the pharmaceutical, food, healthcare, and environmental monitoring industries. The rabbit fever test (RPT) is considered the oldest and simplest endotoxin detection technique; however, it has been heavily criticized due to its requirement for in vivo testing and large sample sizes, as well as its relatively low sensitivity and accuracy compared to other methods.

[0003] The LAL (Limulus Amebocyte Lysate) assay, using reagents derived from horseshoe crab blood that coagulate upon contact with endotoxins, was developed to address this issue. It is more accurate than the RPT (Reactive Protein Test) and eliminates the need for live testing. The Chinese Pharmacopoeia, the United States Pharmacopeia, and the U.S. Food and Drug Administration have approved this test method as an endotoxin testing strategy for oral / injectable drugs, hospital USP-grade water, and medical devices, and it is widely recognized as the official endotoxin testing method. Despite its significant application, LAL assays frequently encounter chemical or physical interferences. These interferences are typically addressed by continuously diluting the test sample until the interference no longer affects the detection level. This not only prolongs the testing time but also increases labor costs and sample consumption. Utility Model Content

[0004] The present invention aims to overcome at least one of the defects of the prior art and provide an endotoxin detection system to solve the problem of low detection efficiency.

[0005] The technical solution adopted by this utility model is to provide an endotoxin detection system, including a light source emitting device, an incident light lead, a microfluidic channel, an optical fiber biochemical sensor, an outgoing light lead, and a spectral analysis device.

[0006] The fiber optic biochemical sensor is located inside the microfluidic channel with a gap between it and the inner wall of the microfluidic channel. The fiber optic biochemical sensor is equipped with a sample slot. The microfluidic channel is equipped with at least two inlets and at least one outlet. The microfluidic channel area between any inlet and any outlet covers the sample slot.

[0007] One end of the incident light lead is connected to the light source generator, and the other end of the incident light lead passes through the microfluidic channel and is connected to the fiber optic biochemical sensor. One end of the outgoing light lead is connected to the fiber optic biochemical sensor, and the other end of the outgoing light lead passes through the microfluidic channel and is connected to the spectral analysis device.

[0008] In this scheme, the sample solution to be tested and the standard horseshoe crab reagent solution enter the microfluidic channel through two inlets, and then the two are rapidly and uniformly mixed. Since the sample cell of the fiber optic biochemical sensor is located between the inlet and outlet, the mixed solution can fully cover the sample cell before flowing out of the outlet. The mixed solution gradually solidifies, causing a change in refractive index, which in turn causes a spectral change in the emitted signal light output from the fiber optic biochemical sensor. Since the spectral change pattern is related to the endotoxin content, the endotoxin content in the sample solution can be obtained by analyzing the spectral data of the emitted signal light through a spectral analysis device.

[0009] Furthermore, the incident light lead is fixedly connected to the microfluidic channel, and the outgoing light lead is fixedly connected to the microfluidic channel.

[0010] This design allows the fiber optic biochemical sensor to be stabilized in the region between the inlet and outlet, ensuring that the fiber optic biochemical sensor can reliably receive the mixed solution of the sample liquid and the standard Limulus amebocyte lysate (LAL) reagent solution.

[0011] Furthermore, the fiber optic biochemical sensor includes a first single-mode fiber, a hollow fiber, and a second single-mode fiber connected in sequence. The hollow fiber is used to set up a sample cell, with the inlet located upstream of the sample cell and the outlet located downstream of the sample cell.

[0012] A mixture of sample liquid and standard Limulus amebocyte lysate (LAL) reagent solution is placed in a sample well. When signal light is input into the first single-mode fiber and output to the hollow fiber via its end face, the mixed solution and the cladding of the hollow fiber form an anti-resonance reflective waveguide structure. This structure exhibits periodic conduction and leakage modes. The mixed solution filling the hollow fiber restricts certain wavelengths of light, enabling more complete interaction with the mixed solution. The output signal light then enters the end face of the second single-mode fiber and is coupled back to the fiber core, subsequently exiting from its end. This constitutes a fiber optic refractive index sensor that directly interacts with the mixed solution. Because the sample liquid allows for low-loss transmission waveguide operation, and slight changes in refractive index cause spectral shifts, higher sensitivity can be achieved.

[0013] Furthermore, the length of the hollow optical fiber is 0.5-2.5 mm.

[0014] The length of this design is sufficient to ensure that the sensing principle of the fiber optic biochemical sensor is based on the anti-resonance effect.

[0015] Furthermore, the injection port includes a first injection port and a second injection port, which are positioned opposite each other on both sides of the flow direction of the microfluidic channel.

[0016] This design ensures that the sample solution and the labeled horseshoe crab reagent solution introduced through the first and second injection ports have relative incident directions, which helps to achieve rapid mixing.

[0017] Furthermore, a micro-injection pump connected to the injection port is also provided.

[0018] Furthermore, the outer surface of the microfluidic channel is also provided with a drainage tube that is connected to the injection port, and the injection port is connected to a micro-injection pump through the drainage tube.

[0019] This solution facilitates connection to a microinjection pump via a drainage tube, enhancing connection strength and helping to maintain sample input accuracy.

[0020] Furthermore, the drainage tube is tilted relative to the microfluidic channel, with the tilt direction being from the sample inlet towards the direction away from the fiber optic biochemical sensor.

[0021] This design ensures that the sample enters the microfluidic channel with an initial velocity toward the fiber optic biochemical sensor, guaranteeing that the sample solution and standard Limulus amebocyte lysate (LAL) reagent solution are thoroughly mixed before being guided to the fiber optic biochemical sensor.

[0022] Furthermore, the microfluidic channel is cuboid in shape, with a length of 5-50 mm, a width of 5-20 mm, and a thickness of 2-10 mm; and / or,

[0023] The orifice diameter of the injection port is 1-2 mm; and / or,

[0024] The diameter of the sample outlet is 1-2 mm.

[0025] Furthermore, the light source emitting device is a supercontinuum laser source or a tunable laser source; and / or,

[0026] The wavelength range of the light source emitting device is 450–2400 nm, and the output power is 5–20 dBm.

[0027] Furthermore, the spectral analysis device has a resolution of 10-20 pm, a test wavelength range of 600-1700 nm, a wavelength resolution of 0.03-1 nm, a dynamic range of 40-60 dB, and a scan speed of 20-40 nm / s.

[0028] Compared with existing technologies, the advantages of this invention are as follows: by using a microfluidic channel in conjunction with a micro-injection pump, the test sample and standard horseshoe crab reagent solution are injected into the system in a micro-volume with high precision. The reaction solution is contained in the hollow optical fiber of the fiber optic biochemical sensor, and the spectral data is recorded and analyzed in real time using a spectrometer, thereby quantifying the endotoxin concentration. This provides a new solution for the high-sensitivity, low-sample-consumption, and rapid quantitative detection of endotoxins in the fields of medicine, drug research, food safety, and environmental pollution. Attached Figure Description

[0029] Figure 1 This is a structural diagram of an endotoxin detection system.

[0030] Figure 2 This is a structural diagram of a fiber optic biochemical sensor.

[0031] Figure 3 This is a cross-sectional view of a fiber optic biochemical sensor.

[0032] Figure 4 This is a diagram of a microfluidic channel structure.

[0033] Reference numerals: light source emitting device 100, incident light lead 200, microfluidic channel 300, first sample inlet 310, second sample inlet 320, sample outlet 330, drainage tube 340, base 350, output tube 360, fiber optic biochemical sensor 400, first single-mode fiber 410, first polishing area 411, hollow fiber 420, sample tank 421, second single-mode fiber 430, second polishing area 431, fiber core 440, outgoing light lead 500, spectral analysis device 600, micro-injection pump 700. DETAILED DESCRIPTION

[0034] The technical solutions of this utility model will be clearly and completely described below with reference to the embodiments of this utility model. Obviously, the described embodiments are only some embodiments of this utility model, and not all embodiments. Based on the embodiments of this utility model, all other embodiments obtained by those of ordinary skill in the art without creative effort are within the protection scope of this utility model.

[0035] Example 1

[0036] like Figure 1-4 As shown, this embodiment provides an endotoxin detection system, including a light source emitting device 100, an incident light lead 200, a microfluidic channel 300, an optical fiber biochemical sensor 400, an outgoing light lead 500, and a spectral analysis device 600.

[0037] The fiber optic biochemical sensor 400 is disposed inside the microfluidic channel 300 and has a gap between it and the inner wall of the microfluidic channel 300. The fiber optic biochemical sensor 400 is provided with a sample groove 421. The microfluidic channel 300 is provided with at least two inlets and at least one outlet 330. The area of ​​the microfluidic channel 300 between any inlet and any outlet 330 covers the sample groove 421. That is, the inlet and outlet 330 are located at the two ends of the sample groove, so that when the sample is injected into the microfluidic channel 300 from the inlet, it can flow completely through the sample groove 421 before being output from the outlet 330.

[0038] One end of the incident light lead 200 is connected to the light source generator, and the other end of the incident light lead 200 passes through the microfluidic channel 300 and is connected to the fiber optic biochemical sensor 400. One end of the exit light lead 500 is connected to the fiber optic biochemical sensor 400, and the other end of the exit light lead 500 passes through the microfluidic channel 300 and is connected to the spectral analysis device 600. The incident light lead 200 and the microfluidic channel 300 are fixedly connected, and the exit light lead 500 is also fixedly connected to the microfluidic channel 300.

[0039] In practice, the incident light lead 200 is introduced from the front opening of the microfluidic channel 300, and the exit light lead 500 is led out from the rear opening of the microfluidic channel 300. By sturdying the incident light lead 200 and the exit light lead 500 inside the microfluidic channel 300, and encapsulating the incident light lead 200 in the front opening of the microfluidic channel 300 and the exit light lead 500 in the rear opening of the microfluidic channel 300, a good fixing effect can be formed on the incident light lead 200, the fiber optic biochemical sensor 400, and the exit light lead 500. Thus, the fiber optic biochemical sensor 400 is stabilized in the area between the sample inlet and the sample outlet 330, ensuring that the fiber optic biochemical sensor 400 can reliably receive the mixed solution after the sample liquid and the standard Limulus amebocyte lysate (LAL) reagent solution are mixed. Furthermore, since the fiber optic biochemical sensor 400 needs to be cleaned after each sample test, in a preferred embodiment, the incident light lead 200 and the exit light lead 500 are both detachably fixed to the microfluidic channel 300, thus facilitating the installation and removal of the fiber optic biochemical sensor 400. In addition, to improve the stability of optical signal transmission, both the incident light lead 200 and the exit light lead 500 can be implemented using fiber optic patch cords.

[0040] During testing, the sample solution to be tested and the standard horseshoe crab reagent solution are injected into the microfluidic channel 300 through two inlets. The two solutions are then rapidly and uniformly mixed through the microfluidic channel 300. Since the sample tank 421 is located between the inlet and outlet 330, the mixed solution can fully cover the sample tank 421 before flowing out of the outlet 330. The mixed solution gradually solidifies, causing a change in refractive index, which in turn causes a spectral change in the light signal output from the fiber optic biochemical sensor 400. Since the spectral change pattern is related to the endotoxin content, the endotoxin content in the sample solution can be obtained by analyzing the spectral data of the emitted signal light through the spectral analysis device 600.

[0041] In specific implementation, to improve detection sensitivity, the fiber optic biochemical sensor 400 used in this embodiment is prepared according to Examples 1-5 of patent document CN114965359A (A refractive index fiber optic sensor and its manufacturing method). Specifically, refer to... Figure 2-3The fiber optic biochemical sensor 400 includes a first single-mode fiber 410, a hollow fiber 420, and a second single-mode fiber 430 connected in sequence. The hollow fiber 420 is provided with a sample slot 421, which is combined with... Figure 1 To understand this, the sample inlets are all located in the microfluidic channel 300 upstream of the sample reservoir 421, and the sample outlets 330 are all located in the microfluidic channel 300 downstream of the sample reservoir 421. The first single-mode fiber 410 and the second single-mode fiber 430 are both side-polished, forming a first polished area 411 and a second polished area 431, respectively. The hollow fiber 420 is fused between the first single-mode fiber 410 and the second single-mode fiber 430. The first polished area 411, the hollow fiber 420, and the second polished area 431 together form a D-shaped groove. The D-shaped groove facilitates the collection of the mixed solution within the microfluidic channel 300, allowing the mixed solution to quickly and fully fill the sample reservoir 421. Simultaneously, it ensures the transmission power of the first single-mode fiber 410 and the second single-mode fiber 430, improving the efficiency of exciting multi-order modes in the mixed solution waveguide, thereby improving detection speed and accuracy. In some embodiments, such as... Figure 1 As shown, the internal space of the microfluidic channel 300 is significantly larger than that of the fiber optic biochemical sensor 400. The fiber optic biochemical sensor 400 is positioned in the middle of the microfluidic channel 300, with the inlet located upstream of the fiber optic biochemical sensor 400 and the outlet located downstream of the fiber optic biochemical sensor 400. Thus, the area between the inlet and outlet 330 completely covers the entire fiber optic biochemical sensor 400. In this way, as long as the total amount of the sample solution to be tested and the standard Limulus amebocyte lysate (LAL) reagent solution is sufficient to fill the entire microfluidic channel 300, the mixed solution can be guaranteed to completely fill the sample tank 421. This arrangement reduces the size matching requirements between the fiber optic biochemical sensor 400 and the microfluidic channel 300, requiring only that the internal space of the microfluidic channel 300 is sufficient to completely accommodate the fiber optic biochemical sensor 400.

[0042] refer to Figure 3 The inner diameter of the sample well 421 is larger than the diameter of the core 440 of the first single-mode fiber 410 and the second single-mode fiber 430. Thus, when the mixed solution completely covers the sample well 421, it can also completely cover the diameters of the first and second single-mode fibers 410 and 430, preventing light leakage at the core 440 from affecting the detection results. It should be noted that the sensitivity of this detection system is independent of the volume of the filling solution. Therefore, as long as the mixed solution completely fills the sample well 421, the detection objective can be achieved; the volume of other external solutions has no impact on the sensitivity of the detection system.

[0043] During detection, sample reservoir 421 contains a mixture of sample liquid and standard Limulus amebocyte lysate (LAL) reagent solution. When signal light is input into the first single-mode fiber 410 and outputs through its end face to the hollow fiber 420, the mixed solution and the cladding of the hollow fiber form an anti-resonance reflection waveguide structure. This structure exhibits periodic conduction and leakage modes. The mixed solution filling the hollow fiber restricts certain wavelengths of light, enabling more complete interaction with the mixed solution. The mixed solution acts as a multimode waveguide for fiber transmission. Subsequently, the signal light enters the end face of the second single-mode fiber 430. The low-loss, specific wavelength light restricted by the mixed solution is coupled back to the core 440 of the second single-mode fiber 430 and output from its end, forming a fiber refractive index sensor that directly interacts with the mixed solution. Because the sample liquid acts as a multimode waveguide, higher sensitivity can be achieved.

[0044] In some embodiments, the length of the hollow optical fiber 420 is 0.5-2.5 mm, for example, 1.6 mm, the remaining thickness of the hollow optical fiber 420 is between 62.5-75 μm, and the inner diameter (equivalent to the inner diameter of the sample groove 421) is 10-100 μm, specifically 30 μm. This ensures that the sensing principle of the fiber optic biochemical sensor 400 is based on the anti-resonance effect and also has good sensitivity. Furthermore, the diameter of the first single-mode optical fiber 410 and the second single-mode optical fiber 430 can be selected as 8-9 μm, for example, 8.2 μm, and the cladding outer diameter is 125-150 μm, preferably 125 μm. The length of the first single-mode optical fiber 410 and the second single-mode optical fiber 430 can be adaptively set according to the actual length of the microfluidic channel 300 used, ensuring that the microfluidic channel 300 is sufficiently large to stably assemble the fiber optic biochemical sensor 400.

[0045] refer to Figure 4 In some embodiments, the microfluidic channel 300 is cuboid in shape, with a length L1 of 5-50 mm, a width L2 of 5-20 mm, and a thickness L3 of 2-10 mm, thereby enabling the assembly of fiber optic biochemical sensors 400 with lengths typically ranging from 1-50 mm. Furthermore, the inlet and outlet ports 330 have apertures of 1-2 mm, which helps reduce liquid tension at the inlet and outlet ports 330, making it easier for the solution to be injected into the microfluidic channel 300. For specific implementation details, please refer to [reference needed]. Figure 4 and Figure 1 To improve structural stability, the microfluidic channel 300 is embedded in the base 350. The microfluidic channel 300 and the base 350 can be made of the same material, such as polydimethylsiloxane (PDMS), polymethyl methacrylate (PMMA), silicate glass, borosilicate glass or metal.

[0046] refer to Figure 1 and 4In this embodiment, a first inlet 310 and a second inlet 320 are provided. The first inlet 310 and the second inlet 320 are arranged opposite to each other on both sides of the flow direction of the microfluidic channel 300. Thus, the sample liquid and the labeled horseshoe crab reagent solution introduced into the first inlet 310 and the second inlet 320 respectively have relative incident directions, which helps to achieve a rapid mixing effect.

[0047] like Figure 1 As shown, to achieve precise sample injection, a micro-injection pump 700 connected to the injection port is also provided. Specifically, the micro-injection pump 700 can be in a dual-channel configuration, resulting in two connecting tubes that connect to the first injection port 310 and the second injection port 320 respectively, facilitating precise control to maintain consistent injection volumes at both ports. In some embodiments, the micro-injection pump 700 has a capacity of 0.5-60 mL, an injection rate of 0.008 nL / h-1246 L / min, an injection accuracy of ±0.5%, and a reproducibility of ±0.2%.

[0048] In addition, refer to Figure 1 To enhance the connection strength between the micro-injection pump 700 and the inlet, a drainage conduit 340 communicating with the inlet is provided on the outer surface of the microfluidic channel 300. In some embodiments, the drainage conduit 340 is integrally formed on the surface of the microfluidic channel 300 and is made of the same material as the microfluidic channel 300, thus ensuring a high-strength connection between the drainage conduit 340 and the microfluidic channel 300, providing stable drainage for the solution input by the micro-injection pump 700. Similarly, an output conduit 360 can be connected to the outlet 330 to facilitate the discharge of sample liquid from the microfluidic conduit 300.

[0049] Furthermore, such as Figure 1 As shown, the drainage tube 340 is inclined relative to the microfluidic channel 300, with the inclination direction being from the sample inlet toward the direction away from the fiber optic biochemical sensor 400. In this way, the sample liquid and the standard Limulus amebocyte lysate (LAL) reagent solution have an initial velocity toward the fiber optic biochemical sensor 400 when they are input into the microfluidic channel 300, which can ensure that the sample liquid and the standard LAL reagent solution are mixed and then guided to the fiber optic biochemical sensor 400.

[0050] In specific implementation, the light source emitting device 100 is a supercontinuous laser light source or a tunable laser light source. The wavelength range of the light source emitting device 100 is 450-2400nm, and the output power is 5-20dBm. This provides the endotoxin detection system with high reliability, wide spectral range and high output power, which is sufficient to meet the requirements of different specifications of fiber optic biochemical sensors 400 for light sources.

[0051] The 600 spectral analysis device uses a spectrometer with a resolution of 10-20 pm, a test wavelength range of 600-1700 nm, a wavelength resolution of 0.03-1 nm, a dynamic range of 40-60 dB, and a scan speed of 20-40 nm / s. This provides rapid, high-resolution, and high-dynamic-range equipment support for acquiring detection spectra.

[0052] refer to Figure 1-4 The working method of this utility model is as follows: The input end of the fiber optic biochemical sensor 400 (i.e., the front end of the first single-mode fiber 410) is connected to the output end of the light source generator through a fiber optic jumper, and the output end of the fiber optic biochemical sensor 400 (i.e., the rear end of the second single-mode fiber 430) is connected to the input end of the spectrometer through a fiber optic jumper; the test solution and the standard horseshoe crab reagent solution are placed in the micro-injection pump 700 respectively, and the two solutions are injected into the microfluidic channel 300 through the first injection port 310 and the second injection port 320 respectively within 10 seconds according to a preset volume ratio (e.g., 1:1). During the rapid and uniform mixing of the two solutions and their flow towards the sample outlet 330, the mixed solution completely covers the sample slot 421 of the fiber optic biochemical sensor 400. At the same time as the test solution and the standard horseshoe crab reagent solution are injected, the light source generator and the spectrometer are turned on, and the spectral changes of the light signal emitted from the fiber optic biochemical sensor 400 are recorded to evaluate the concentration of endotoxin in the sample solution being tested.

[0053] In practice, the time required for the spectral valley value to shift to a specific wavelength can be extracted from sample solutions containing botulinum toxin at different concentrations. Based on this, a fitting curve can be plotted to assess the endotoxin concentration of the sample to be tested.

[0054] Obviously, the above embodiments of this utility model are merely examples for clearly illustrating the technical solution of this utility model, and are not intended to limit the specific implementation of this utility model. Any modifications, equivalent substitutions, and improvements made within the spirit and principles of the claims of this utility model should be included within the protection scope of the claims of this utility model.

Claims

1. An endotoxin detection system, characterized in that, It includes a light source emitting device, an incident light lead, a microfluidic channel, an optical fiber biochemical sensor, an outgoing light lead, and a spectral analysis device; The fiber optic biochemical sensor is located inside the microfluidic channel with a gap between it and the inner wall of the microfluidic channel. The fiber optic biochemical sensor is equipped with a sample slot. The microfluidic channel is equipped with at least two inlets and at least one outlet. The microfluidic channel area between any inlet and any outlet covers the sample slot. One end of the incident light lead is connected to the light source generator, and the other end of the incident light lead passes through the microfluidic channel and is connected to the fiber optic biochemical sensor. One end of the outgoing light lead is connected to the fiber optic biochemical sensor, and the other end of the outgoing light lead passes through the microfluidic channel and is connected to the spectral analysis device.

2. The endotoxin detection system according to claim 1, characterized in that, The incident light lead is fixedly connected to the microfluidic channel, and the outgoing light lead is fixedly connected to the microfluidic channel.

3. The endotoxin detection system according to claim 1, characterized in that, The fiber optic biochemical sensor includes a first single-mode fiber, a hollow fiber, and a second single-mode fiber connected in sequence. The hollow fiber is equipped with a sample groove, with the sample inlet located upstream of the sample groove and the sample outlet located downstream of the sample groove.

4. The endotoxin detection system according to claim 3, characterized in that, The length of hollow optical fiber is 0.5-2.5mm.

5. The endotoxin detection system according to claim 1, characterized in that, The injection ports include a first injection port and a second injection port, which are positioned opposite each other on both sides of the flow direction of the microfluidic channel.

6. The endotoxin detection system according to claim 1, characterized in that, It is also equipped with a micro-injection pump connected to the injection port.

7. The endotoxin detection system according to claim 6, characterized in that, The outer surface of the microfluidic channel is also provided with a drainage tube that connects to the injection port, and the injection port is connected to a micro-injection pump through the drainage tube.

8. The endotoxin detection system according to claim 7, characterized in that, The drainage tube is tilted relative to the microfluidic channel, with the tilt direction being from the sample inlet towards the direction away from the fiber optic biochemical sensor.

9. The endotoxin detection system according to any one of claims 1-8, characterized in that, The microfluidic channel is rectangular, with a length of 5-50 mm, a width of 5-20 mm, and a thickness of 2-10 mm; and / or, The orifice diameter of the injection port is 1-2 mm; and / or, The diameter of the sample outlet is 1-2 mm.

10. The endotoxin detection system according to any one of claims 1-8, characterized in that, The light source emitting device is a supercontinuum laser source or a tunable laser source; and / or, The wavelength range of the light source emitting device is 450–2400 nm, and the output power is 5–20 dBm; and / or, The spectral analysis device has a resolution of 10-20 pm, a test wavelength range of 600-1700 nm, a wavelength resolution of 0.03-1 nm, a dynamic range of 40-60 dB, and a scan speed of 20-40 nm / s.

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