CN113171091B - Implantable hydrogel fiber bragg grating glucose sensor, preparation method and measurement system - Google Patents
Implantable hydrogel fiber bragg grating glucose sensor, preparation method and measurement system Download PDFInfo
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/145—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue
- A61B5/1495—Calibrating or testing of in-vivo probes
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/145—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue
- A61B5/14532—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue for measuring glucose, e.g. by tissue impedance measurement
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/145—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue
- A61B5/1455—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue using optical sensors, e.g. spectral photometrical oximeters
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- G—PHYSICS
- G01—MEASURING; TESTING
- G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
- G01N21/00—Investigating or analysing materials by the use of optical means, i.e. using sub-millimetre waves, infrared, visible or ultraviolet light
- G01N21/17—Systems in which incident light is modified in accordance with the properties of the material investigated
- G01N21/41—Refractivity; Phase-affecting properties, e.g. optical path length
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- G—PHYSICS
- G01—MEASURING; TESTING
- G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
- G01N21/00—Investigating or analysing materials by the use of optical means, i.e. using sub-millimetre waves, infrared, visible or ultraviolet light
- G01N21/84—Systems specially adapted for particular applications
Abstract
The invention discloses an implantable hydrogel fiber bragg grating glucose sensor, a preparation method and a measurement system. The glucose detection method adopts a biocompatible glucose sensitive hydrogel material as a base material, and combines a mask method to prepare the fiber grating, thereby realizing the glucose detection related to wavelength. Glucose diffuses into the hydrogel network to be specifically combined with glucose sensitive groups, so that the effective refractive index and period of the fiber grating are changed, and the resonance wavelength shifts. By detecting the wavelength drift amount of the fiber bragg grating, the glucose can be detected in real time and quantitatively. In addition, in order to eliminate the influence of environment and light source instability factors, a measurement system based on double fiber bragg gratings is provided. The hydrogel material fiber grating has soft biomechanical characteristics and excellent biocompatibility, and is suitable for long-term continuous blood glucose monitoring.
Description
(I) the technical field
The invention relates to an implantable hydrogel fiber bragg grating glucose sensor, a preparation method and a measurement system, which are used for long-term continuous blood glucose monitoring and belong to the technical field of bio-optical detection and organic material application.
(II) background of the invention
As one of the most important test contents in medical tests, quantitative analysis of glucose plays an important role in blood tests, and is frequently found in the fields of production and processing of various feeds and foods, biochemistry, and the like. The blood glucose concentration of normal people is 4-8mM, while the blood glucose concentration of diabetic patients is far higher than normal level due to insulin deficiency or failure of normal physiological action of insulin in target cells. Sustained high blood glucose levels can lead to serious complications, including diabetic retinopathy, renal failure, heart disease, stroke, and the like. At present, no method for completely curing diabetes exists. Blood glucose monitoring is an important link in diabetes treatment, and the blood glucose level of a patient is maintained at a normal level by acquiring blood glucose concentration data to adjust the amount of insulin injection. The traditional blood sugar monitoring adopts a single-point glucose sensor, needs to frequently collect finger blood samples for analysis (finger puncture test), brings great physiological pain and a plurality of potential safety hazards to patients, and discrete blood sugar data can influence the normal judgment of doctors on the state of an illness.
Thus, continuous blood glucose monitoring devices have been around. At present, commercial continuous blood glucose monitoring equipment is basically an electrochemical sensing system developed based on glucose oxidation reaction, and glucose concentration change is converted into current change. However, the electrochemical reaction process of the implanted electrode of the sensor is unstable, 3 to 4 times of finger puncture tests are needed for calibration every day, and the physiological pain and the potential safety hazard brought to the patient in the blood glucose monitoring process are not completely solved. The optical fiber glucose sensor is a novel sensor with great potential capable of replacing an electrochemical sensor, has the advantages of no mark, internal calibration, no electromagnetic interference and the like, and has great prospect in the diagnosis and treatment of diabetes. The optical fiber glucose sensor can be divided into an optical fiber evanescent wave type, a surface plasma resonance type, a fluorescence quenching type and an optical fiber grating type. Compared with other light intensity modulation type sensors, the fiber grating type glucose sensor detects the change of the glucose concentration by acquiring the drift amount of the resonant wavelength, and has the advantages of high sensitivity, good stability, quick response and the like. However, the conventional fiber grating is usually formed by writing glass fiber or plastic fiber, has poor biocompatibility, and can cause immune and inflammatory reactions in human bodies after long-term implantation. Moreover, the fiber grating is hard and easy to damage biological tissues.
Disclosure of the invention
Aiming at the challenges faced in the application of the implantable glucose sensor, the invention provides an implantable hydrogel material fiber grating glucose sensor which is used for real-time and quantitative glucose detection.
In order to achieve the above purpose, the technical scheme adopted by the invention is as follows:
the fiber grating glucose sensor is composed of glucose sensitive hydrogel fiber grating, and is characterized in that the sensing fiber grating adopts flexible and biocompatible polyacrylamide (PAAm) hydrogel as a base material, glucose sensitive modification is carried out on the base material, so that the synthesized fiber grating can be specifically combined with glucose, linear and rapid expansion/contraction characteristics are presented, the fiber grating is caused to expand, the effective refractive index of the fiber grating and the resonance wavelength drift caused by grating period change are caused, and the quantitative detection of the glucose is realized by detecting the drift of the resonance wavelength.
The sensing fiber grating is characterized in that the preparation method comprises the following steps:
step (1): acrylamide monomer (AAm), a cross-linking agent (N, N' -methylenebis (BIS)), and 3-acrylamidophenylboronic acid (3-APBA) were mixed into 1mL of a Dimethylsulfoxide (DMSO) solution at a certain molar mass ratio, stirred uniformly, and then added with a photoinitiator (DEAP, 1-2% w/v), and finally diluted with 1mL of deionized water to obtain a precursor solution. Optimally, the molar mass ratio of AAm, BIS and 3-APBA is 78.5:1.5:20mol percent.
Step (2): injecting the precursor solution prepared in the step (1) into a hollow silica gel tube (the inner diameter: 50-125 μm), and polymerizing and curing for 3-5 minutes under an ultraviolet lamp. And then taking out the cured optical fiber in a water injection and injection mode.
And (3): the optical fiber cured in step (2) was washed with deionized water for 5 to 10 minutes and then stored in phosphate buffered saline (PBS, pH = 7.4).
And (4): preparing the fiber grating by ultraviolet irradiation by adopting a mask method, placing a mask plate between an ultraviolet laser beam and the solidified optical fiber, enabling the optical fiber to be close to the mask plate, and periodically irradiating the optical fiber by ultraviolet light, so that the refractive index of the optical fiber is periodically disturbed to form the fiber grating, and placing the prepared fiber grating in PBS for storage.
The optical fiber photoinitiator DEAP has ultraviolet photosensitivity, and the axial periodic change of the refractive index can be generated in the fiber core through ultraviolet exposure.
The fiber grating is a fiber Bragg grating or a long-period fiber grating.
When the fiber bragg grating is adopted, the fiber bragg grating is prepared by a phase mask method, the period of the fiber bragg grating is 200-600nm, the detection wavelength is the reflection wavelength, and the change of the glucose concentration is measured by adopting a reflection type measuring system.
When the fiber grating adopts a long-period fiber grating, the fiber grating is prepared by an amplitude mask method, the period of the fiber grating is 300-600 mu m, the detection wavelength is a transmission wavelength, and a transmission type measurement system is adopted to measure the change of the glucose concentration.
In the preparation process of the fiber bragg grating, in order to realize the coupling fixation of the sensing fiber bragg grating and the optical fiber, before the sensing fiber bragg grating is prepared, the tail end of the quartz optical fiber is directly inserted into one end of a silica gel mold filled with precursor solution, and then the silica gel mold is placed under an ultraviolet lamp for crosslinking and curing to form stable connection.
The invention also provides a measuring system based on the double fiber gratings, which adopts two fiber gratings, wherein one fiber grating is used as a reference fiber grating, and the other fiber grating is used as a detection fiber grating, so that the influence of unstable factors of environment and light sources is eliminated.
1) The reflection type measuring system based on the double fiber Bragg grating glucose sensor adopts the following specific devices: the device comprises a laser 1, an optical fiber coupler 2, a reference fiber Bragg grating 3, a detection sensing fiber Bragg grating 4, a photoelectric detector 5, a data acquisition card 6 and a computer 7, wherein the computer is used for storing and processing acquired data.
The relation of each element of the measuring system is as follows: an optical output port 1-1 of a laser 1 is connected to a port of a coupler 2-1 through a quartz optical fiber, output laser of the port of the coupler 2-2 is coupled into a reference fiber Bragg grating 3 through the quartz optical fiber and enters a detection sensing fiber Bragg grating 4 through the quartz optical fiber, the reference laser and the detection laser are respectively reflected and transmitted to the optical fiber coupler 2 and output through the port of the coupler 2-3, transmission output of the port of the coupler 2-3 is received through a port of a photoelectric detector 5-1 and converted into voltage signals, the voltage signals are collected through a port of a data collection card 6-1, and collection results are sent to a computer 7 for storage processing.
2) The transmission type measuring system based on the double long period fiber grating glucose sensor adopts the following specific devices: the system comprises a laser 1, an optical fiber coupler 11, a reference long-period fiber grating 8, a detection sensing long-period fiber grating 9 and an optical fiber coupler 12; the photoelectric detector 5, the data acquisition card 6 and the computer 7 are used for storing and processing the acquired data.
The relation of each element of the measuring system is as follows: the light output port 1-1 of the laser 1 is connected to the port of the coupler 11-1 through a quartz optical fiber, the output laser of the port of the coupler 11-2 is coupled into the reference long-period fiber grating 8 through the quartz optical fiber and is connected with the port of the coupler 12-1 through the quartz; the output laser of the coupler 11-3 port is coupled into the detection sensing long-period fiber grating 9 through the quartz fiber and is connected with the coupler 12-2 port through the quartz fiber. Laser of the coupler 12-1 port and the coupler 12-2 port is coupled to enter the coupler 12-3 port, is transmitted and output to the photoelectric detector 5-1 port to be received and converted into a voltage signal, the voltage signal is collected by the data collection card 5-1 port, and a collection result is sent to the computer 7 to be stored and processed.
3) In the double-fiber grating measuring system, the laser 1 provides wavelength scanning for the frequency-scanning laser. And a photoelectric detector is adopted to obtain the reflection spectrum of the fiber Bragg grating or the transmission spectrum of the long-period fiber Bragg grating from the time domain, and the glucose concentration is quantitatively analyzed by detecting the drift amount of the reflection or transmission wavelength.
4) In the double-fiber grating measuring system, the reference fiber grating is a conventional silicon-based fiber grating, and the detection sensing fiber grating is a hydrogel fiber grating.
The working principle of the invention is as follows: due to the resonance wavelength shift caused by the effective refractive index of the sensing fiber grating and the grating period change, the quantitative detection of the glucose is realized by detecting the shift of the resonance wavelength. Glucose molecules diffuse into the optical fiber through pores of the hydrogel and are reversibly compounded with the 3-APBA group, so that the phenylboronic acid equilibrium is promoted to move towards the dissociation direction. This process causes an increase in the concentration of phenylboronic acid ions, which leads to swelling of the optical fiber. The volume expansion related to the glucose can cause the effective refractive index of the grating and the resonance wavelength shift caused by the periodic change of the grating, and the quantitative detection of the glucose is realized by detecting the shift of the wavelength. Therefore, the quantitative detection of the glucose can be realized by establishing the relation that the wavelength drift of the fiber grating changes along with the change of the glucose concentration.
Compared with the prior art, the invention has the advantages that:
1) The glucose-sensitive hydrogel fiber bragg grating is prepared by adopting the biocompatible PAAm hydrogel as a matrix material, and the problems of light guiding and biocompatibility in-vivo implantation detection can be solved at the same time.
2) Compared with a glass or plastic optical fiber with hard material, the sensing optical fiber grating is soft in texture, and the good mechanical property can reduce the risk of damaging biological tissues in the process of implantation or human body movement.
3) The fiber grating prepared by the mask method can be specifically combined with glucose to cause the effective refractive index of the grating and the periodic change of the grating, so that the wavelength-dependent glucose detection is realized, and the fiber grating can be used for long-term continuous blood glucose monitoring.
(IV) description of the drawings
In order to more clearly illustrate the embodiments of the present invention or the technical solutions in the prior art, the drawings used in the embodiments or the prior art descriptions will be briefly described below, and it is obvious that the drawings in the following description are some embodiments of the present invention, and other drawings can be obtained by those skilled in the art without creative efforts.
FIG. 1 is a schematic diagram of a sensing fiber grating prepared by a mask method.
FIG. 2a is a block diagram of a dual fiber Bragg grating glucose sensor based reflective measurement system.
FIG. 2b is a block diagram of a transmission type measurement system based on a dual long period fiber grating glucose sensor.
Icon:
10: ultraviolet light; 20: a mask plate; 30: an optical fiber; 1: a laser 1;1-1: the output port of the laser 1; 2: a fiber coupler 2;2-1: an input port of the fiber coupler 2; 2-2: an input port of the fiber coupler 2; 2-3: an output port of the optical fiber coupler 2; 3: a reference fiber bragg grating; 4: detecting a sensing fiber Bragg grating; 5: a photodetector; 5-1: a photodetector input port; 5-2: a photodetector output port; 6: a data acquisition card; 6-1: an input port of a data acquisition card; 6-2: an output control port of the data acquisition card; 7: a computer; 8: a reference long-period fiber grating; 9: detecting and sensing the long-period fiber bragg grating; 11: a fiber coupler 11;11-1: an input port of the fiber coupler 11; 11-2: an output port of the fiber coupler 11; 11-3: an output port of the fiber coupler 11; 12: a fiber coupler 12;12-1: an input port of the fiber coupler 12; 12-2: an input port of the fiber coupler 12; 12-3: the fiber coupler 12 inputs the port.
(V) detailed description of the preferred embodiments
To make the objects, technical solutions and advantages of the embodiments of the present invention clearer, the technical solutions of the present invention will be clearly and completely described below with reference to the accompanying drawings, and it is apparent that the described embodiments are some, but not all embodiments of the present invention. All other embodiments, which can be derived by a person skilled in the art from the embodiments given herein without making any creative effort, shall fall within the protection scope of the present invention.
The glucose-sensitive hydrogel material fiber grating prepared by the invention has the following specific preparation process:
synthesizing and preparing a precursor solution: mixing AAm and cross-linking agent BIS,3-APBA according to the ratio of 78.5:1.5:20mol% molar mass ratio was mixed into 1mL of dimethyl sulfoxide (DMSO) solution, stirred uniformly, then 2% w/v DEAP photoinitiator was added, and finally 1mL of deionized water was added for dilution.
Step (2), preparing a sensing optical fiber: injecting the precursor solution prepared in the step (1) into a hollow silica gel tube (inner diameter: 125 μm) through an injector, and polymerizing and curing for 5 minutes under an ultraviolet lamp. And then taking out the cured optical fiber in a water injection and injection mode.
Step (3), cleaning chemical residues: washing the optical fiber obtained in the step (2) with deionized water for 10 minutes, and then storing the optical fiber in a phosphate buffer solution (PBS, pH = 7.4).
And (4) preparing the fiber grating, placing a mask plate between the ultraviolet laser beam and the cured optical fiber, enabling the optical fiber to be close to the mask plate, and enabling ultraviolet light to periodically irradiate the optical fiber, so that the refractive index of the optical fiber is periodically disturbed to form the fiber grating, as shown in fig. 1. Subsequently, the prepared fiber grating was stored in PBS.
The invention also provides a measurement system based on the double fiber bragg grating, and fig. 2 is a block diagram of the measurement system, wherein fig. 2a is a block diagram of a reflection-type measurement system based on a double fiber bragg grating glucose sensor, and fig. 2b is a block diagram of a transmission-type measurement system based on a double long-period fiber bragg grating glucose sensor.
The reflection type measuring system based on the double fiber Bragg grating glucose sensor adopts the following specific devices: the splitting ratio of the laser 1 and the optical fiber coupler 2 is 50:50, the reference fiber Bragg grating 3 is used as a reference fiber Bragg grating, the detection sensing fiber Bragg grating 4 is used as a detection fiber Bragg grating, the response wavelength range of the photoelectric detector 5 is 900-2600nm, the sampling speed of the acquisition card 6 is 200kS/s, and the computer 7 is used for storing and processing the acquired data.
The specific process of the embodiment is as follows:
an optical output port 1-1 of a laser 1 is connected to a port of a coupler 2-1 through a quartz optical fiber, output laser of the port of the coupler 2-2 is coupled into a reference fiber Bragg grating 3 through the quartz optical fiber and enters a detection sensing fiber Bragg grating 4 through the quartz optical fiber, the reference laser and the detection laser are respectively reflected and transmitted to the optical fiber coupler 2 and output through the port of the coupler 2-3, transmission output of the port of the coupler 2-3 is received through a port of a photoelectric detector 5-1 and converted into voltage signals, the voltage signals are collected through a port of a data collection card 6-1, and collection results are sent to a computer 7 for storage processing.
The transmission type measuring system based on the double long period fiber grating glucose sensor adopts the following specific devices: the splitting ratio of the laser 1 and the optical fiber coupler 11 is 50:50, taking the reference long-period fiber grating 8 as a reference fiber grating, taking the detection sensing long-period fiber grating 9 as a detection fiber grating, setting the splitting ratio of the fiber coupler 12 to be 50, setting the response wavelength range of the photoelectric detector 5 to be 900-2600nm, setting the sampling speed of the acquisition card 6 to be 200kS/s, and using the computer 7 to store and process the acquired data.
The specific process of the embodiment is as follows:
the light output port 1-1 of the laser 1 is connected to the port of the coupler 11-1 through a quartz optical fiber, the output laser of the port of the coupler 11-2 is coupled into the reference long-period fiber grating 8 through the quartz optical fiber and is connected with the port of the coupler 12-1 through the quartz; the output laser of the coupler 11-3 port is coupled into the detection sensing long-period fiber grating 9 through the quartz fiber and is connected with the coupler 12-2 port through the quartz fiber. Laser of the coupler 12-1 port and the coupler 12-2 port is coupled to enter the coupler 12-3 port, is transmitted and output to the photoelectric detector 5-1 port to be received and converted into a voltage signal, the voltage signal is collected by the data collection card 6-1 port, and a collection result is sent to the computer 7 to be stored and processed.
The invention adopts a biocompatible glucose sensitive hydrogel material as a base material, and prepares the glucose sensitive hydrogel material fiber bragg grating by combining ultraviolet curing and a mask method, thereby realizing the wavelength-dependent glucose detection. The fiber binds specifically to glucose, causing the fiber to expand, thereby changing the effective refractive index of the grating and the grating period. By adopting a laser time domain frequency sweeping method, the change of the resonant wavelength of the fiber bragg grating is obtained in real time, and the dynamic detection of the glucose concentration can be realized. In addition, compared with the traditional glass or plastic material fiber grating, the hydrogel fiber grating is soft in texture, biocompatible and suitable for long-term implantable glucose monitoring.
Claims (11)
1. An implantable hydrogel fiber grating glucose sensor is used for long-term continuous blood glucose monitoring; the fiber grating glucose sensor is characterized in that a biocompatible polyacrylamide PAAm hydrogel material is adopted as a matrix material of a fiber core; glucose molecules are specifically combined with glucose sensitive functional groups in the fiber bragg grating to cause effective refractive index and period change of the fiber bragg grating, so that the resonant wavelength of the fiber bragg grating is shifted, and quantitative detection of glucose is realized by detecting the shift amount of the resonant wavelength;
the fiber grating is characterized in that the preparation method comprises the following steps:
step (1): mixing an acrylamide monomer AAm, a bisacrylamide cross-linking agent BIS and 3-acrylamidophenylboronic acid 3-APBA into 1mL of dimethyl sulfoxide DMSO solution according to a certain molar mass ratio, uniformly stirring, adding a photoinitiator DEAP, wherein the content of the photoinitiator DEAP is 1-2 w/v, and finally adding 1mL of deionized water to dilute to obtain a precursor solution; the molar mass ratio of AAm to BIS to 3-APBA is 78.5:1.5:20mol percent;
step (2): injecting the precursor solution prepared in the step (1) into a hollow silicone tube, wherein the inner diameter of the hollow silicone tube is as follows: 125 mu m, polymerizing and curing for 3-5 minutes under an ultraviolet lamp, and then taking out the cured optical fiber in a water injection and jetting manner;
and (3): washing the optical fiber cured in the step (2) by deionized water for 5-10 minutes, and then placing the optical fiber in phosphate buffer PBS for storage, wherein the pH value of the PBS is 7.4;
and (4): preparing the fiber grating by ultraviolet irradiation by adopting a mask method, placing a mask plate between an ultraviolet laser beam and the solidified optical fiber, enabling the optical fiber to be close to the mask plate, and periodically irradiating the optical fiber by ultraviolet light, so that the refractive index of the optical fiber is periodically disturbed to form the fiber grating, and placing the prepared fiber grating in PBS for storage.
2. The implantable hydrogel fiber grating glucose sensor of claim 1, wherein the PAAm hydrogel fiber core is modified with glucose-sensitive phenylboronic acid groups so that the PAAm hydrogel fiber core can specifically bind to glucose and exhibits linear and rapid expansion/contraction characteristics.
3. The implantable hydrogel fiber grating glucose sensor of claim 1, wherein the diameter of the optical fiber is 50-125 μm, and the length of the grating region of the fiber grating is 1-4cm.
4. The implantable hydrogel fiber grating glucose sensor as claimed in claim 1, wherein the fiber photoinitiator DEAP has ultraviolet photosensitivity, and the axial periodic refractive index change can be generated in the fiber core by ultraviolet light exposure.
5. The implantable hydrogel fiber grating glucose sensor of claim 1, wherein to couple and fix the optical fiber and the quartz optical fiber, before the optical fiber is prepared, the tail end of the quartz optical fiber is directly inserted into one end of a silica gel mold filled with a precursor solution, and then the silica gel mold is placed under an ultraviolet lamp to be cross-linked and cured to form a stable connection.
6. The implantable hydrogel fiber grating glucose sensor of claim 1, which is a fiber Bragg grating or a long-period fiber grating.
7. The implantable hydrogel fiber grating glucose sensor according to claim 4, wherein the implantable hydrogel fiber grating glucose sensor is prepared by a phase mask method when a fiber Bragg grating is adopted, the period of the fiber grating is 200-600nm, the detection wavelength is a reflection wavelength, and a reflection measurement system is adopted to measure the change of the glucose concentration.
8. The implantable hydrogel fiber grating glucose sensor according to claim 4, wherein the implantable hydrogel fiber grating glucose sensor is prepared by an amplitude mask method when a long-period fiber grating is adopted, the period of the fiber grating is 300-600 μm, the detection wavelength is a transmission wavelength, and the change of the glucose concentration is measured by a transmission measurement system.
9. A measurement system comprising the implantable hydrogel fiber grating glucose sensor according to claim 1, wherein the measurement system is based on a double fiber grating, and two fiber gratings are adopted, wherein one fiber grating is used as a reference fiber grating, and the other fiber grating is used as a detection fiber grating, so that the influence of unstable factors of environment and light sources is eliminated, and the detection fiber grating is prepared by the preparation method according to claim 1.
10. The measurement system according to claim 9, based on fiber bragg grating, using a reflective measurement system based on dual fiber bragg grating glucose sensor, comprising: the device comprises a laser (1), an optical fiber coupler (2), a reference fiber Bragg grating (3), a detection sensing fiber Bragg grating (4), a photoelectric detector (5), a data acquisition card (6) and a computer (7), wherein the computer (7) is used for storing and processing acquired data;
the optical output port (1-1) of the laser (1) is connected to one coupler port (2-1) through a quartz optical fiber, output laser of the other coupler port (2-2) is coupled into a reference optical fiber Bragg grating (3) through the quartz optical fiber and enters a detection sensing optical fiber Bragg grating (4) through the quartz optical fiber, the reference laser and the detection laser are respectively reflected and transmitted to the optical fiber coupler (2) and output through a third coupler port (2-3), the transmission output of the third coupler port (2-3) is received through a photoelectric detector port (5-1) and converted into a voltage signal, the voltage signal is collected through a data collection card port (6-1), and the collection result is sent to a computer (7) for storage processing.
11. The measurement system of claim 9, based on a long-period fiber grating, employing a transmissive measurement system based on a dual long-period fiber grating glucose sensor, comprising: the device comprises a laser (1), an optical fiber coupler (11), a reference long-period optical fiber grating (8), a detection sensing long-period optical fiber grating (9), another optical fiber coupler (12), a photoelectric detector (5), a data acquisition card (6) and a computer (7), wherein the computer (7) is used for storing and processing acquired data;
wherein, the optical output port (1-1) of the laser (1) is connected to one port (11-1) of the optical fiber coupler (11) through a quartz optical fiber, the output laser of the other port (11-2) of the optical fiber coupler (11) is coupled into the reference long-period fiber grating (8) through the quartz optical fiber and is connected with one port (12-1) of the other optical fiber coupler (12) through the quartz; the output laser of a third port (11-3) of the optical fiber coupler (11) is coupled into a detection sensing long-period optical fiber grating (9) through a quartz optical fiber and is connected with the other port (12-2) of the other optical fiber coupler (12) through the quartz optical fiber, the laser of one port (12-1) of the other optical fiber coupler (12) and the laser of the other port (12-2) of the other optical fiber coupler (12) are coupled into the third port (12-3) of the other optical fiber coupler (12), are transmitted and output to a photoelectric detector port (5-1) to be received and converted into voltage signals, the voltage signals are collected through a data collection card port (6-1), and the collected results are sent to a computer (7) to be stored and processed.
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