Microcavity laser multi-tumor marker sensor based on air-clad optical fiber

Abstract

The application discloses a microcavity laser multi-tumor marker sensor based on an air-clad optical fiber, relates to the technical field of optical fiber laser sensors, and comprises an optical module, a microcavity regulation and sample detection module and a signal processing module; the microcavity regulation and sample detection module comprises an air-clad optical fiber, a polytetrafluoroethylene capillary hose and a micro-injection pump; the pure quartz core of the air-clad optical fiber is surrounded by a ring of closely arranged microchannels, which is an air cladding of the optical fiber, and a gain liquid with a higher refractive index than quartz is filled in the air cladding; the liquid-quartz interface of the cross section of the optical fiber forms total internal reflection, thereby constituting an optical fiber microcavity and enhancing the interaction between light and matter; the pump light emitted by the optical module is vertically incident on the surface of the air-clad optical fiber, and the generated laser signal enters the signal processing module; the microcavity laser multi-tumor marker sensor based on the air-clad optical fiber solves the problems of low sensing sensitivity and difficulty in realizing high-sensitivity marker detection of multiple markers in the prior art.

Description

Technical Field

[0001] This invention relates to the field of fiber laser sensor technology, and in particular to a microcavity laser multitumor marker sensor based on air-clad fiber. Background Technology

[0002] Chemiluminescence immunoassay is one of the most widely used and sensitive immunoassay methods in clinical practice. It utilizes the high specificity of antigen-antibody binding to recognize target molecules, using enzymes (such as horseradish peroxidase) to label the detection antibodies. The enzyme catalyzes the substrate to produce a chemiluminescent substance; a single enzyme molecule can catalyze the generation of thousands of photons, amplifying the detection signal. However, chemiluminescence methods suffer from limitations such as a broad emission spectrum and a limited range of luminescent materials, resulting in poor wavelength reuse and making it difficult to achieve the labeling and detection of multiple biomarkers.

[0003] In applications of highly sensitive tumor marker screening, highly sensitive detection is required, and standardized detection of multiple markers with different abundances is necessary. However, existing immunoassay methods are difficult to implement on the same platform for detecting multiple markers with different detection ranges. Summary of the Invention

[0004] The purpose of this invention is to provide a microcavity laser multi-tumor biomarker sensor based on air-clad optical fiber, which solves the problems of low sensing sensitivity and difficulty in achieving high-sensitivity labeling and detection of multiple biomarkers in the existing technology.

[0005] To achieve the above objectives, the present invention provides a microcavity laser multitumor marker sensor based on air-clad optical fiber, comprising: an optical module, a microcavity modulation and sample detection module, and a signal processing module;

[0006] The microcavity control and sample detection module includes an air-clad fiber, a polytetrafluoroethylene (PTFE) capillary tube, and a micro-injection pump. The air-clad fiber is connected to the micro-injection pump via the PTFE capillary tube. From the inside out, the air-clad fiber consists of a pure quartz core, an air cladding, and a quartz protective layer. The air cladding is a ring of tightly packed air microchannels surrounding the pure quartz core. The air cladding is filled with a gain liquid with a refractive index higher than that of quartz. The liquid at the cross-section of the pure quartz fiber and the quartz interface form total internal reflection, constituting the fiber microcavity and enhancing the interaction between light and matter. By adjusting the refractive index of the filling gain liquid, the Q value of the fiber microcavity and the output laser wavelength can be controlled.

[0007] The pump laser emitted from the optical module is incident perpendicularly on the surface of the air-clad fiber, supporting laser resonance similar to the whispering gallery mode. The generated laser signal output passes through the optical module and then enters the signal processing module.

[0008] When the sensor is used for marker concentration detection, the refractive index of the filling liquid is adjusted to make the sensor work within the required dynamic range of the marker, and the generated laser spectrum signal is integrated.

[0009] When the sensor is used for tagging, the longitudinal mode wavelength and intensity information in the generated laser spectrum are encoded into a binary string to form a QR code containing the sensor's dynamic range information.

[0010] By utilizing air-clad fiber microcavities to enhance the interaction between light and matter, highly sensitive tumor marker detection can be achieved. By adjusting the effective refractive index of the filling liquid using liquid crystal, the wavelength of the emitted laser and the Q value of the microcavity can be controlled, enabling wavelength labeling and multi-dynamic-range detection of various tumor markers.

[0011] Preferably, the optical module includes a laser pulser, a beam splitter, an energy meter, a dichroic mirror, and a microscope objective. The pulsed laser outputs a pump laser, which is split into two perpendicular pump laser beams after passing through the beam splitter. One pump laser beam is incident on the energy meter to monitor the beam energy in real time, while the other pump laser beam is reflected by the dichroic mirror and converged by the microscope objective before being incident perpendicularly on the microcavity control and sample detection module.

[0012] Preferably, the signal processing module includes a collection element, a transmission optical fiber, a spectrometer, and a computer; the collection element is connected to the spectrometer via the transmission optical fiber, the spectrometer transmits the spectral results to the computer, and the computer performs data processing according to the required functions.

[0013] Preferably, the laser signal generated by the microcavity control and sample detection module is focused by the microscope objective and separated from the pump laser direction by the dichroic mirror. The laser signal is then collected by the collecting element and coupled into the transmission optical fiber.

[0014] Preferably, when detecting the concentration of biomarkers, the refractive index of the liquid filling the air envelope is adjusted to detect biomarkers of different abundances, and the resulting spectral results are integrated.

[0015] Preferably, adjusting the refractive index of the filling liquid results in the optimal Q value of the fiber microcavity under the optimal refractive index condition, which is used to detect low-abundance markers; reducing the refractive index of the filling liquid reduces the Q value of the fiber microcavity, causes a blue shift in the output wavelength, and shifts the sensing dynamic range towards higher concentrations, which is used to detect high-abundance markers.

[0016] The method to obtain the optimal refractive index when adjusting the refractive index of the filling liquid is as follows: mix the liquid crystal and the gain liquid in different volume ratios, measure the integrated intensity of the output spectrum under the same pumping conditions, and the volume ratio at which the integrated intensity of the spectrum is the strongest is the optimal volume ratio, and the refractive index at this time is the optimal refractive index.

[0017] Preferably, the process for detecting marker concentration is as follows:

[0018] S11. Using the magnetic microparticle chemiluminescence method, the standard was diluted in a 10-fold concentration gradient. Equal amounts of the target biomarker at each concentration were mixed with magnetic bead suspensions coated with target biomarker-capturing antibodies. After incubation at room temperature for 30 minutes, unbound target biomarkers were washed away. The standard was the target biomarker at a known concentration.

[0019] S12. Mix the magnetic bead suspension with the horseradish peroxidase-labeled detection antibody, incubate at room temperature for 30 minutes, and then wash away the unbound detection antibody.

[0020] S13. Add the chemiluminescent substrate and react for 20 minutes before adding the stop solution.

[0021] S14. Obtain a supernatant without magnetic beads using magnetic separation technology, mix the supernatant with liquid crystal at an optimized volume ratio, and fill the air-encapsulated layer using a micro-injection pump.

[0022] S15. Calculate the spectral integral intensity of the analyte at each concentration to obtain the curve of the spectral integral intensity changing with the concentration of the analyte.

[0023] S16. For different markers, repeat steps S11-S15, and adjust the refractive index of the filling liquid according to the required detection dynamic range to obtain the curve of the spectral integral intensity of the marker sample with different abundance as a function of the marker concentration.

[0024] S17. After pretreating the liquid marker to be detected, inject it into the air envelope through a micro-injection pump, start the pulsed laser, and the computer integrates the received spectrum to obtain the spectral integral intensity. Substitute the spectral integral intensity into the curve of the corresponding marker to obtain the concentration of the marker to be detected.

[0025] Preferably, when marking a certain sensing dynamic range, the longitudinal mode wavelength and intensity information in the spectrum are encoded into a binary string to form a QR code representing the sensing dynamic range information;

[0026] The process of converting spectral signals into barcode labels is as follows:

[0027] S21. Select the amplitude with the highest laser longitudinal mode intensity in the spectrum, set 50% of the amplitude as the threshold, and select the wavelength positions in the spectrum where the laser longitudinal mode intensity is not lower than the threshold.

[0028] S22. Divide the wavelength into 50 wavelength intervals with the longitudinal mode free spectrum range as the interval, each corresponding to 50 binary characters. The first 49 intervals are left-closed and right-open intervals, and the last interval is a closed interval.

[0029] S23. The rule for obtaining a binary barcode label with an encoding capacity of 50 is: if the wavelength position obtained in S1 is within a certain wavelength range, then the bit corresponding to that range is the digit "1", otherwise it is the digit "0".

[0030] Preferably, the pulsed laser has an output wavelength of 532nm and an output laser energy of 0-5. Continuously adjustable within the range.

[0031] Preferably, the obtained binary barcode labels are matched one-to-one with the types of tumor markers to be tested and their detection dynamic range.

[0032] When an air-clad optical fiber is filled with a high-refractive-index liquid, the liquid undergoes total internal reflection at the surrounding quartz interface, creating an echo-gallery-like optical feedback that supports laser resonance. The resonant light is confined within the liquid, increasing the interaction between the light and the analyte and improving sensing sensitivity. The refractive index of the liquid can be controlled by a microfluidic control system consisting of a PTFE capillary tube and a micro-injection pump. This allows for the control of the output laser wavelength and the Q-value of the fiber microcavity. Furthermore, the wavelength can be used to create a binary barcode label, marking the dynamic range and markers of the corresponding fiber microcavity sensor.

[0033] Therefore, the microcavity laser multi-tumor marker sensor based on air-clad optical fiber used in this invention has the following beneficial effects:

[0034] (1) The microcavity structure of air-clad optical fiber enhances the interaction between light and matter, improves the sensing sensitivity, can regulate the sensing dynamic range, and can solve the high-sensitivity detection of tumor markers and the detection of multiple markers with different abundances in tumor marker screening application scenarios by using wavelength coding labeling.

[0035] (2) Using air-clad optical fiber as a sensing unit, the micro-porous ring structure in the cross-section air cladding can support a similar whispering gallery mode, enhance the interaction between light and matter, and improve sensing sensitivity.

[0036] (3) The dynamic range of sensing can be controlled by adjusting the refractive index of the filling liquid, the output laser wavelength and the Q value of the fiber microcavity, and the wavelength can be used to realize the mark detection.

[0037] The technical solution of the present invention will be further described in detail below with reference to the accompanying drawings and embodiments. Attached Figure Description

[0038] Figure 1 This is a schematic diagram of the structure of the microcavity laser multitumor marker sensor based on air-clad optical fiber according to the present invention;

[0039] Figure 2This is a schematic diagram of fiber microcavity resonance according to an embodiment of the present invention.

[0040] Figure Labels

[0041] 1. Pulsed laser; 2. Beam splitter; 3. Energy meter; 4. Dichroic mirror; 5. Microscope objective; 6. Air-clad fiber; 61. Pure quartz fiber core; 62. Air cladding; 63. Quartz protective layer; 7. PTFE capillary tube; 8. Micro-injection pump; 9. Collection element; 10. Transmission fiber; 11. Spectrometer; 12. Computer. Detailed Implementation

[0042] The following detailed description of embodiments of the invention provided in the accompanying drawings is not intended to limit the scope of the claimed invention, but merely to illustrate selected embodiments of the invention. All other embodiments obtained by those skilled in the art based on the embodiments of the invention without inventive effort are within the scope of protection of the invention.

[0043] Please see Figure 1-2 A microcavity laser multi-tumor biomarker sensor based on air-clad fiber includes: an optical module, a microcavity modulation and sample detection module, and a signal processing module;

[0044] The optical module includes a laser pulser 1, a beam splitter 2, an energy meter 3, a dichroic mirror 4, and a microscope objective 5. The pulsed laser 1 outputs a pump laser, which is split into two perpendicular pump laser beams by the beam splitter 2. One pump laser beam is incident on the energy meter 3 for real-time beam energy monitoring. The other pump laser beam is reflected by the dichroic mirror 4 and converged by the microscope objective 5 before being perpendicularly incident on the microcavity control and sample detection module. The pulsed laser 1 has an output wavelength of 532nm and an output laser energy between 0-5... Continuously adjustable within the range.

[0045] The microcavity control and sample detection module includes an air-clad fiber 6, a polytetrafluoroethylene (PTFE) capillary tube 7, and a micro-injection pump 8. The air-clad fiber 6 is connected to the micro-injection pump 8 via the PTFE capillary tube 7. The air-clad fiber 6 includes a pure quartz fiber core 61, an air cladding 62 surrounding the pure quartz fiber core 61, and a quartz protective layer 63 surrounding the air cladding 62. The air cladding 62 is a ring of micropores tightly arranged around the pure quartz fiber core 61, forming an air microchannel. The air cladding 62 is filled with a gain liquid with a refractive index higher than that of quartz. The liquid at the cross-section of the pure quartz fiber core 61 and the quartz interface form total internal reflection, constituting a fiber microcavity and enhancing the interaction between light and matter. By adjusting the refractive index of the filling gain liquid, the Q value of the fiber microcavity and the output laser wavelength are controlled.

[0046] The light emitted from the optical module is incident perpendicularly on the surface of the air-clad fiber 6, generating a laser signal output; the laser signal enters the signal processing module after passing through the optical module.

[0047] The signal processing module includes a collection element 9, a transmission optical fiber 10, a spectrum analyzer 11, and a computer 12. The collection element 9 is connected to the spectrum analyzer 11 through the transmission optical fiber 10. The spectrum analyzer 11 transmits the spectral results to the computer 12, and the computer 12 performs data processing according to the required functions.

[0048] The laser signal generated by the microcavity control and sample detection module is focused by the microscope objective 5 and separated from the laser direction by the dichroic mirror 4. The laser signal is collected by the collecting element 9 and coupled into the transmission optical fiber 10.

[0049] When detecting the concentration of biomarkers, the refractive index of the liquid filling the air envelope 62 is adjusted to detect biomarkers of different abundances, and the resulting spectral results are integrated.

[0050] Adjusting the refractive index of the filling liquid allows the Q value of the fiber microcavity to reach the upper threshold under optimal refractive index conditions, which is used to detect low-abundance markers. Decreasing the refractive index of the filling liquid lowers the Q value of the fiber microcavity, causes a blue shift in the output wavelength, and shifts the sensing dynamic range towards higher concentrations, which is used to detect high-abundance markers.

[0051] The method to obtain the optimal refractive index is as follows: mix liquid crystal and gain liquid in different volume ratios, measure the integrated intensity of the output spectrum under the same pumping conditions, and the volume ratio at which the integrated intensity of the spectrum is strongest is the optimal volume ratio, and the refractive index at this time is the optimal refractive index.

[0052] The process for detecting biomarker concentration is as follows:

[0053] S11. Using the magnetic microparticle chemiluminescence method, the standard was diluted in a 10-fold concentration gradient. Equal amounts of the target biomarker at each concentration were mixed with magnetic bead suspensions coated with target biomarker-capturing antibodies. After incubation at room temperature for 30 minutes, unbound target biomarkers were washed away. The standard was the target biomarker at a known concentration.

[0054] S12. Mix the magnetic bead suspension with the horseradish peroxidase-labeled detection antibody, incubate at room temperature for 30 minutes, and then wash away the unbound detection antibody.

[0055] S13. Add the chemiluminescent substrate and react for 20 minutes before adding the stop solution.

[0056] S14. Obtain a supernatant without magnetic beads using magnetic separation technology, mix the supernatant with liquid crystal at an optimized volume ratio, and fill it into the air-encapsulated layer 62 through a micro-injection pump 8.

[0057] S15. Calculate the spectral integral intensity of the analyte at each concentration to obtain the curve of the spectral integral intensity changing with the concentration of the analyte.

[0058] S16. For different markers, repeat steps S11-S15, and adjust the refractive index of the filling liquid according to the required detection dynamic range to obtain the curve of the spectral integral intensity of the marker sample with different abundance as a function of the marker concentration.

[0059] S17. After pretreatment of the liquid marker to be detected, it is injected into the air envelope 62 through the micro-injection pump 8. The pulsed laser 1 is started, and the computer 12 integrates the received spectrum to obtain the spectral integral intensity. Substituting the spectral integral intensity into the curve of the corresponding marker, the concentration of the marker to be detected can be obtained.

[0060] When marking, the longitudinal mode wavelength and intensity information in the spectrum are encoded into a binary string to form a QR code representing the dynamic range information of the sensor;

[0061] The process of converting spectral signals into barcode labels is as follows:

[0062] S21. Select the amplitude with the highest laser longitudinal mode intensity in the spectrum, set 50% of the amplitude as the threshold, and select the wavelength positions in the spectrum where the laser longitudinal mode intensity is not lower than the threshold.

[0063] S22. Divide the wavelength into 50 wavelength intervals with the longitudinal mode free spectrum range as the interval, each corresponding to 50 binary characters. The first 49 intervals are left-closed and right-open intervals, and the last interval is a closed interval.

[0064] S23. The rule for obtaining a binary barcode label with an encoding capacity of 50 is: if the wavelength position obtained in S1 is within a certain wavelength range, then the bit corresponding to that range is the digit "1", otherwise it is the digit "0".

[0065] The obtained binary barcode labels are matched one-to-one with the types of tumor markers to be tested and their detection dynamic range.

[0066] When the air-clad optical fiber 6 is filled with a high-refractive-index liquid, the liquid forms total internal reflection at the interface with the outer quartz protective layer 63, creating an echo-gallery-like optical feedback that supports laser resonance. The resonant light is confined within the filling liquid, increasing the interaction between the light and the analyte and improving the sensing sensitivity. The refractive index of the filling liquid can be controlled by a microfluidic control system consisting of a polytetrafluoroethylene capillary tube 7 and a micro-injection pump 8. This allows for the control of the output laser wavelength and the Q value of the fiber microcavity. The wavelength is then used to form a binary barcode label, marking the dynamic range and markers of the corresponding fiber microcavity sensor.

[0067] Therefore, this invention employs the aforementioned microcavity laser multi-tumor biomarker sensor based on air-clad optical fiber. This sensor utilizes the microcavity structure of the air-clad optical fiber to enhance light-matter interaction, improve sensing sensitivity, and control the dynamic range of the sensing. Furthermore, it utilizes wavelength-encoded labeling to address the high-sensitivity detection of biomarkers and the need for multi-biomarker labeling detection with varying abundances in tumor biomarker screening applications. By using the air-clad optical fiber as the sensing unit, the microporous ring structure within the air cladding can support a whispering-gallery-like mode, enhancing light-matter interaction and improving sensing sensitivity. The dynamic range of the sensing can be controlled by adjusting the refractive index of the filling liquid, regulating the output laser wavelength, and controlling the Q-value of the fiber microcavity. Finally, wavelength-encoded labeling detection is achieved.

[0068] Finally, it should be noted that the above embodiments are only used to illustrate the technical solutions of the present invention and not to limit them. Although the present invention has been described in detail with reference to preferred embodiments, those skilled in the art should understand that modifications or equivalent substitutions can still be made to the technical solutions of the present invention, and these modifications or equivalent substitutions cannot cause the modified technical solutions to deviate from the spirit and scope of the technical solutions of the present invention.

Claims

1. A microcavity laser multi-tumor marker sensor based on air-clad optical fiber, characterized in that, include: Optical module, microcavity control and sample detection module, and signal processing module; The microcavity control and sample detection module includes an air-clad optical fiber, a polytetrafluoroethylene capillary tube, and a micro-injection pump; The air-clad optical fiber is connected to a micro-injection pump via a polytetrafluoroethylene capillary tube. From the inside out, the air-clad optical fiber consists of a pure quartz core, an air cladding, and a quartz protective layer. The air cladding is a ring of tightly packed air microchannels surrounding the pure quartz core. The air cladding is filled with a gain liquid with a refractive index higher than that of quartz. The liquid-quartz interface at the fiber cross-section forms total internal reflection, constituting a fiber microcavity that enhances the interaction between light and matter. By adjusting the refractive index of the filling gain liquid, the Q value of the fiber microcavity and the output laser wavelength can be controlled. The optical module includes a laser pulser, a beam splitter, an energy meter, a dichroic mirror, and a microscope objective. The pump laser emitted from the optical module is incident perpendicularly on the surface of the air-clad fiber, and the resulting laser signal output passes through the microscope objective and the dichroic mirror before entering the signal processing module. When the sensor is used for marker concentration detection, the refractive index of the filling liquid is adjusted to make the sensor work within the required dynamic range of the marker, and the generated laser spectrum signal is integrated. When marking a certain sensing dynamic range, the longitudinal mode wavelength and intensity information in the spectrum are encoded into a binary barcode label, forming a binary barcode label containing the sensing dynamic range information.

2. The microcavity laser multi-tumor marker sensor based on air-clad optical fiber according to claim 1, characterized in that: The pulsed laser outputs a pump laser, which is split into two vertical pump laser beams after passing through a beam splitter. One pump laser beam is incident on the energy meter, while the other pump laser beam is reflected by a dichroic mirror and converged by a microscope objective before being incident vertically on the microcavity control and sample detection module.

3. The microcavity laser multi-tumor marker sensor based on air-clad optical fiber according to claim 2, characterized in that: The signal processing module includes a collection element, a transmission optical fiber, a spectrum analyzer, and a computer. The collection element is connected to the spectrum analyzer via the transmission optical fiber. The spectrum analyzer transmits the spectral results to the computer, which then processes the data according to the required functions.

4. The microcavity laser multi-tumor marker sensor based on air-clad optical fiber according to claim 3, characterized in that: The laser signal generated by the microcavity control and sample detection module is focused by the microscope objective and separated from the pump laser direction by the dichroic mirror. The laser signal is then collected by the collecting element and coupled into the transmission optical fiber.

5. The microcavity laser multi-tumor marker sensor based on air-clad optical fiber according to claim 4, characterized in that: When detecting the concentration of biomarkers, the refractive index of the liquid filling the air envelope is adjusted to detect biomarkers of different abundances, and the resulting spectral results are integrated.

6. The microcavity laser multi-tumor marker sensor based on air-clad optical fiber according to claim 5, characterized in that: Adjusting the refractive index of the filling liquid results in the optimal Q value of the fiber microcavity under the optimal refractive index condition, which is used to detect low-abundance markers. Decreasing the refractive index of the filling liquid reduces the Q value of the fiber microcavity, causes a blue shift in the output wavelength, and shifts the sensing dynamic range towards higher concentrations, which is used to detect high-abundance markers. The method to obtain the optimal refractive index is as follows: mix liquid crystal and gain liquid in different volume ratios, measure the integrated intensity of the output spectrum under the same pumping conditions, and the volume ratio at which the integrated intensity of the spectrum is strongest is the optimal volume ratio, and the refractive index is the optimal refractive index.

7. The microcavity laser multi-tumor marker sensor based on air-clad optical fiber according to claim 6, characterized in that, The process for detecting biomarker concentration is as follows: S11. Dilute the standard in a 10-fold concentration gradient. Mix equal amounts of each concentration of the target biomarker with magnetic bead suspensions coated with the target biomarker capture antibody. Incubate at room temperature for 30 minutes, then wash away any unbound target biomarkers. The standard is the target biomarker at a known concentration. S12. Mix the magnetic bead suspension with the horseradish peroxidase-labeled detection antibody, incubate at room temperature for 30 minutes, and then wash away the unbound detection antibody. S13. Add the chemiluminescent substrate and react for 20 minutes before adding the stop solution. S14. Obtain a supernatant without magnetic beads using magnetic separation technology, mix the supernatant with liquid crystal at an optimized volume ratio, and fill the air-encapsulated layer using a micro-injection pump. S15. Calculate the spectral integral intensity of the analyte at each concentration to obtain the curve of the spectral integral intensity changing with the concentration of the analyte. S16. For different markers, repeat steps S11-S15, and adjust the refractive index of the filling liquid according to the required detection dynamic range to obtain the curve of the spectral integral intensity of the marker sample with different abundance as a function of the marker concentration. S17. After pretreating the liquid marker to be detected, inject it into the air envelope through a micro-injection pump, start the pulsed laser, and the computer integrates the received spectrum to obtain the spectral integral intensity. Substitute the spectral integral intensity into the curve of the corresponding marker to obtain the concentration of the marker to be detected.

8. The microcavity laser multi-tumor marker sensor based on air-clad optical fiber according to claim 7, characterized in that: The process of encoding the longitudinal mode wavelength and intensity information in the spectrum into a binary barcode label is as follows: S21. Select the amplitude with the highest laser longitudinal mode intensity in the spectrum, set 50% of the amplitude as the threshold, and select the wavelength positions in the spectrum where the laser longitudinal mode intensity is not lower than the threshold. S22. Divide the wavelength into 50 wavelength intervals with the longitudinal mode free spectrum range as the interval, each corresponding to 50 binary characters. The first 49 intervals are left-closed and right-open intervals, and the last interval is a closed interval. S23. The rule for obtaining a binary barcode label with an encoding capacity of 50 is: if the wavelength position obtained in S1 is within a certain wavelength range, then the bit corresponding to that range is the digit "1", otherwise it is the digit "0".

9. The microcavity laser multi-tumor marker sensor based on air-clad optical fiber according to claim 8, characterized in that: The pulsed laser has an output wavelength of 532nm and its output laser energy is continuously adjustable in the range of 0-5μJ.

10. The microcavity laser multi-tumor marker sensor based on air-clad optical fiber according to claim 9, characterized in that: The obtained binary barcode labels are matched one-to-one with the types of tumor markers to be tested and their detection dynamic range.

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