CN114689547A - D-type photonic crystal fiber biosensor with graphene coated gold film - Google Patents
D-type photonic crystal fiber biosensor with graphene coated gold film Download PDFInfo
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Abstract
The invention discloses a D-type photonic crystal fiber biosensor with a graphene-coated gold film, which comprises a fiber core, a cladding, a gold film layer, a graphene layer, analyte liquid to be detected and a perfect matching layer, wherein the fiber core is arranged on the cladding; the material of the fiber core and the cladding is quartz with the refractive index equal to 1.45, and the cladding is composed of three air holes with different diameters which are periodically and symmetrically arranged. According to the invention, a metal film is plated on the polished surface of the D-type photonic crystal fiber to generate a surface plasma effect, five layers of graphene are respectively coated on the upper surface and the lower surface of the metal film, the adsorption capacity of the sensor on biomolecules can be increased under the action of the graphene layers, so that the sensor can be applied to the field of biosensing, the outermost layer is to-be-detected analyte liquid, and the sensor is completely immersed in a liquid analyte when in use. The invention can be widely applied to the fields of life science, drug screening, environment monitoring, drug monitoring and the like.
Description
(I) technical field
The invention relates to the field of optical fiber sensing, in particular to a surface plasma photonic crystal optical fiber sensor for low-refractive-index sensing, which can sense liquid analytes or biomolecules with high accuracy.
(II) background of the invention
The Photonic Crystal Fiber (PCF) has flexible structural design and excellent optical characteristics, and has huge development potential and wide application prospect in the fields of photoelectrons, optical fiber communication systems, optical fiber nonlinearity and the like. Surface Plasmon Resonance (SPR) is an optical phenomenon that occurs at the interface of a medium and a metal. The optical sensor based on the SPR effect has the advantages of high sensitivity, no label, real-time online detection and the like. But the further application is limited by the problems of poor equipment compatibility, large volume, difficult integration and the like. By combining the excellent optical characteristics of PCF with SPR technology, SPR-based photonic crystal fiber sensors which are small in size, light in weight and easy to integrate are available. With the continuous development of surface plasma photonic crystal fiber sensors, it is a design goal to obtain sensors with large detectable refractive index range, high sensitivity, high resolution and commercialization.
Wang et al propose a dual-core PCF biosensor. Between the two fiber cores of the sensor, there is an air hole filled with liquid, and its inner wall has a layer of silver-graphene. The highest spectral sensitivity is 10000nm/RIU within the detection range of 1.43-1.46 RI. Zhang et al reported a selectively gold plated and liquid filled six-core PCF sensor by selectively removing six of the second cladding air holes. The spectral sensitivity was 3300 nm/RIU. However, in order to successfully realize the selective coating and filling of the circular micropores, the required operation process is complicated, and the uniformity of the coating film is difficult to ensure. To eliminate these problems, some D-type photonic crystal fiber sensors based on the surface plasmon resonance effect have been proposed.
Lu proposes a D-type photonic crystal fiber refractive index sensor based on gold grating. The result shows that the sensitivity can reach 3340nm/RIU within the range of 1.36-1.38 RI. Gangwar et al designed D-type photonic crystal fiber based on surface plasmon resonance effect, with sensitivity of 7700nm/RIU and resolution of 1.30 × 10-5RIU。
Disclosure of the invention
In order to overcome the defects of the prior art, the invention provides a D-type photonic crystal fiber biosensor with a graphene coated gold film. The transmission characteristics of photonic crystal fibers coated with graphene-clad gold films on polished planes were studied using a finite element method of Perfectly Matched Layers (PML). On one hand, the uniformity of the coating can be ensured; on the other hand, the probe can be directly immersed into liquid to be detected for real-time detection. By introducing the graphene layer, on one hand, the adsorption capacity of the sensor to biomolecules is improved, so that the sensor can be better applied to the field of biosensing; on the other hand, the loss peak value is obviously improved, and the sensitivity of the sensor is greatly improved.
The technical scheme adopted by the invention is as follows:
the D-type photonic crystal fiber biosensor structurally comprises a fiber core (4), a cladding (7), a gold film layer (2), a graphene layer (1), analyte liquid to be detected (8) and a perfect matching layer (9).
The cladding is provided with an arc curved surface and a polished plane, and a plurality of air holes are formed in the cladding along the axial direction of the fiber core.
The cladding air holes comprise inner air holes and two layers of air holes arranged on the periphery of the inner air holes, the inner air holes are air holes (3) located right above the fiber core (4) and two air holes (5) located right below the fiber core (4), and the two layers of air holes comprise air holes (5) which are close to the inner air holes and symmetrically arranged in a U shape and air holes (6) which are partially symmetrically arranged in a regular hexagon shape at the outermost layer.
The arrangement of the outer layer air holes is used for adjusting and controlling the relative refractive index difference between the cladding and the fiber core, so that light is limited to be conducted in the fiber core according to the total internal reflection principle.
The air hole (3) is arranged for enhancing leakage of an evanescent field in the y polarization direction.
The gold film layer is arranged on the polishing plane of the cladding, the upper surface and the lower surface of the gold film layer are respectively provided with 5 graphene layers, the gold film provides induction for the surface plasma resonance effect, the graphene layers can enable the loss peak value to be remarkably improved, and the sensitivity and the application range of the sensor are greatly improved.
When the fiber optic detector is used, the optical fiber is immersed in analyte liquid to be detected, and the perfect matching layer is positioned outside the analyte liquid to be detected and is a calculation boundary added when the optical fiber is subjected to performance simulation.
According to the scheme, the diameter d of the air hole (3)0＝0.5um。
According to the scheme, the diameter d of the air hole (5)11.1um, spacing Λ of adjacent air holes in the x-directionx1.6um, pitch Λ in the y-directiony＝1.2um。
According to the scheme, the diameter d of the air hole (6)21.6um, and the pitch Λ of the adjacent air holes 2.2 um.
According to the scheme, the gold film is made of gold, and the thickness t of the gold film layer is 45 nm.
According to the scheme, the number of layers of the graphene is five layers above and below the gold film according to the linear relation between the light absorption rate of the graphene and the number of layers, and the thickness of each layer of the graphene is 0.34 nm.
According to the scheme, the distance D between the center of the fiber core and the polishing plane of the cladding11.9um, the distance D between the center of the fiber core and the center of the cladding arc curved surface2＝1.2um。
According to the scheme, the material of the core and the cladding is quartz with the refractive index of 1.45.
According to the scheme, the radius R of the cladding circular arc curved surface is 5.8 um.
According to the scheme, the working wavelength range of the incident light is 620 nm-950 nm.
According to the scheme, the sensitivity can be detected by changing the refractive index of the external environment, and the external analyte changes between 1.33 and 1.38 RI.
Compared with the prior art, the invention has the following advantages:
1. the sensor is based on the structural design of the D-type photonic crystal fiber, and compared with the mode of plating gold in the air hole, the mode of plating gold on the polishing plane is simpler in operation and process production, and the uniformity of gold film coverage is more controllable.
2. The sensor adopts a refractive index type photonic crystal fiber structure, the light guiding principle is the same as that of a refractive index step type fiber, and the light is guided based on the total internal reflection principle. However, the photonic crystal fiber has an excellent nonlinear effect and an excellent birefringence effect.
3. On the basis of only one layer of gold film originally, 5 layers of graphene are added on the upper side and the lower side of the gold film, so that on one hand, the adsorption capacity of the sensor on biomolecules is improved, and the sensor can be better applied to the field of biosensing; on the other hand, the loss peak value is obviously improved, and the sensitivity of the sensor is greatly improved.
4. The sensor adopts a U-shaped air hole arrangement in the structure, and is provided with the air holes (3) for enhancing the leakage of an evanescent field in the y polarization direction so as to enhance the detection performance of the sensor.
The working principle of the graphene-coated gold film D-type photonic crystal fiber biosensor is as follows: when incident light is transmitted in the photonic crystal fiber, main light is concentrated in the fiber core, when the incident light is transmitted to the side-polished plane, a part of light of the incident light can become evanescent wave to resonate with surface plasma wave in metal, the energy of the evanescent wave can be coupled into the surface plasma wave, so that the energy of the incident light is absorbed, the energy of the detected reflected light is directly reduced greatly, and a minimum peak, namely a resonant absorption peak, is detected in a reflected light intensity response curve. When the external environment refractive index on the surface of the gold film changes, the position of the resonance absorption peak is influenced to change, and the change of the external refractive index is calculated by measuring the change quantity delta lambda of the resonance absorption peak.
(IV) description of the drawings
FIG. 1 is a schematic cross-sectional view of an optical fiber according to an embodiment of the present invention.
FIG. 2 is a diagram of the mode field distribution of the y-pol fundamental mode in an embodiment of the present invention.
FIG. 3 is a diagram of the mode field distribution for the x-pol fundamental mode in an embodiment of the present invention.
FIG. 4 is a graph showing the variation of the sensitivity and the quality factor FOM obtained by varying the thickness of the gold film while fixing other structural parameters in the present example.
FIG. 5 is a loss spectrum of an external measurement medium having refractive indices of 1.33 and 1.34 under the conditions of a gold film thickness of 45nm and a number of graphene layers of 5.
FIG. 6 is a graph of the loss spectrum of the present invention under an external measurement medium of 1.33-1.38 RI.
The reference numbers illustrate: (1) is a graphene layer; (2) is a gold film layer; (3) is a diameter d0The air hole of (2); (4) is a fiber core; (5) is a diameter d1The air hole of (2); (6) is a diameter d2The air hole of (2); (7) is a cladding; (8) is the analyte liquid to be tested; (9) is a perfect matching layer.
(V) detailed description of the preferred embodiments
The invention is further described below with reference to examples and drawings to highlight the advantages of the invention.
Referring to fig. 1, the invention discloses a graphene-coated metal D-type photonic crystal fiber biosensor; the cross section of the photonic crystal fiber as a carrier comprises a core (4) and a cladding (7). The core and the cladding are made of quartz material with refractive index n equal to 1.45, the cladding has a circular arc surface and a polished plane, the radius R of the circular arc surface of the cladding is 5.8um, and the distance D between the center of the core and the polished plane of the cladding is11.9um, the distance D between the center of the fiber core and the center of the cladding arc curved surface21.2 um. The cladding contains three types of air holes (3), (5), (6), the diameter d of the air hole (3)00.5um, diameter d of air hole (5)11.1um, diameter d of air hole (6)21.2um, wherein the spacing Λ of adjacent air holes (5) in the x-directionx1.6um, pitch Λ in the y-directiony1.2 um. The distance Lambda between the adjacent air holes (6) is 2.2um, the outer layer air holes (6) are arranged in a U shape, and the air holes (5) are symmetrically arranged around the fiber core. The gold film layer (2) is arranged on a polishing plane of the cladding, the upper layer and the lower layer of the gold film are respectively provided with the graphene layers (1), the number of layers is 5, and the thickness of each layer is 0.34 nm. Analyte liquid (8) to be detected is arranged outside the cladding, and when the optical fiber is used, the optical fiber is immersed in the analyte liquid to be detected. The outermost layer is perfectA matching layer (9) which is a calculation boundary added when the performance of the optical fiber is simulated.
In order to enhance the leakage of the evanescent field in the y polarization direction and to enhance the performance of the sensor, air holes (3) are provided, the diameter of which is smaller than the other two types of air holes.
The design and performance analysis of the sensor is based on the optical waveguide theory, the equivalent refractive index theory, the Sellmeier formula and the finite element method. When a finite element method is used, a Maxwell vector equation is solved by combining a perfect matching layer condition and a transition boundary condition, a propagation constant of a certain mode can be obtained, the effective refractive index of the corresponding mode can be obtained through the obtained propagation constant, the constraint loss of the corresponding mode can be calculated, and the sensitivity and the resolution of the sensor can be calculated through the drift amount of the resonant wavelength. And (4) carrying out numerical calculation and structural optimization on the designed model by using finite element method analysis software.
Carbon atoms in the graphene can form a large pi bond after hybridization, so that the graphene is endowed with excellent conductivity and optical characteristics. The conductivity of the graphene is up to 15000cm at room temperature2V & (V &); the absorption rate of the single-layer graphene to light is about 2.3%, and the absorption rate to light and the number of layers of the graphene are in a linear relationship under certain conditions, which shows that in the optical fiber SPR sensor based on the graphene, the sensitivity of the sensor can be improved by changing the number of the layers of the graphene.
The optical refractive index expression of the graphene is as follows:
where C is 5.446um-1 and λ is the wavelength of the incident light.
The thickness of the single layer graphene is 0.34 nm.
Fig. 2 is a mode field distribution diagram of the y-pol base mode at the phase matching point in this embodiment, which is drawn by using finite element software, when the condition of phase matching is reached, the energy of the incident light is transferred from the base mode to the plasma body mode, and at this time, the imaginary part value of the effective refractive index of the base mode reaches the maximum, that is, the confinement loss reaches the maximum, and the wavelength corresponding to this point is the resonant wavelength.
FIG. 3 is a diagram of the mode field distribution of the x-pol base mode, and since the confinement loss in the y-direction is much larger than that in the x-direction, the corresponding value of the mode field of the y-pol base mode should be used in the calculation.
In the embodiment of the invention, the position of the resonance absorption peak is influenced by changing the structural parameters such as the side-throwing depth, the thickness of a gold film, the refractive index of an external analyte, the diameter of an air hole, the hole spacing and the number of layers of graphene; by calculating the red shift variation delta lambda of the resonance absorption peak, the sensitivity of the sensor at the moment can be intuitively calculated; therefore, the structural parameters of the sensor can be reasonably set, and the sensor can obtain the optimal sensitivity.
The sensitivity is calculated as:
wherein, Delta lambda is the variation of resonance wavelength, Delta n is the variation of refractive index of the analyte to be detected
When the loss peak is very large, it has a certain negative effect on the resolving power of the sensor, so another parameter quality factor FOM is needed to make a request for the width of the loss peak, which is calculated by the following expression:
where S (λ) is the sensitivity at that time, FWHM is full width at half maximum, and a greater value of FOM indicates a greater resolving power.
In the embodiment of the invention, the optimal performance of the sensor can be obtained only by reasonably setting corresponding structural parameters and selecting proper sensitivity and corresponding quality factor FOM. Thus, the number of graphene layers, the diameter of the air hole, the gold film thickness t, the cladding arc radius, and D of the examples of the invention1And D2Are all obtained by control variable simulation experimentRelative to the optimal parameters.
FIG. 4 shows the values of the corresponding sensitivity and quality factor FOM obtained by changing the thickness of the gold film at intervals of 5nm for the change of the refractive index n of the analyte to be detected from 1.34 to 1.35 for the gold film between 30nm and 55nm, with the other structural parameters fixed as above. As is clear from the figure, the optimum thickness of the gold film of the present example was selected to be 45 nm.
FIG. 5 is a loss spectrum of the wavelength change of the refractive index of the analyte under test under the condition of the thickness of the gold film being 45nm, 5 layers of graphene and other relatively optimal structural parameters under the condition of the refractive index change of 1.33 and 1.34; it is understood that the sensitivity was 2401nm/RIU when the wavelength change amount Δ λ was 24.01nm under these conditions and the position of the resonance absorption peak was red-shifted from 660.58nm to 684.59 nm.
FIG. 6 shows that the refractive index n of the analyte to be measured is changed from 1.33 to 1.38 under the fixed relative optimal parameters, the obtained loss spectrum has the refractive index between 1.33 and 1.34, the resonant absorption peak depth is shallow, and the SPR phenomenon is not obvious, so that the sensor of the invention has the most suitable sensing measurement range of 1.35 to 1.38, and the sensitivity of the sensor under the corresponding refractive index n is 3785nm/RIU, 4920nm/RIU and 10950 nm/RIU. The average sensitivity in the optimal measurement range of the sensor is 6552 nm/RIU.
Claims (10)
1. A D-type photonic crystal fiber biosensor with a graphene-coated gold film is characterized in that: the detection device comprises a fiber core (4), a cladding (7), a gold film layer (2), a graphene layer (1), analyte liquid to be detected (8) and a perfect matching layer (9);
the cladding is provided with an arc curved surface and a polished plane, and a plurality of air holes are formed in the cladding along the axial direction of the fiber core;
the cladding air holes comprise inner air holes and two layers of air holes arranged on the periphery of the inner air holes, the inner air holes are air holes (3) positioned right above the fiber core (4) and two air holes (5) right below the fiber core (4), and the two layers of air holes comprise air holes (5) which are close to the inner air holes and symmetrically arranged in a U shape and air holes (6) which are partially symmetrically arranged in a regular hexagon shape at the outermost layer;
the outer layer air hole is used for adjusting and controlling the relative refractive index difference between the cladding and the fiber core, so that light is limited to be conducted in the fiber core according to the total internal reflection principle;
the air hole (3) is arranged for enhancing the leakage of an evanescent field in the y polarization direction;
the gold film layer is arranged on the polishing plane of the cladding, 5 graphene layers are respectively arranged on the upper surface and the lower surface of the gold film layer, the gold film provides induction for the occurrence of surface plasma resonance effect, the graphene layers can obviously improve the loss peak value, and the sensitivity and the application range of the sensor are greatly improved; when the fiber optic detector is used, the optical fiber is immersed in analyte liquid to be detected, and the perfect matching layer is positioned outside the analyte liquid to be detected and is a calculation boundary added when the optical fiber is subjected to performance simulation.
2. The graphene-coated metal D-type photonic crystal fiber biosensor of claim 1, wherein: the diameter d of the air hole (3)0＝0.5um。
3. The graphene-clad metal D-type photonic crystal fiber biosensor of claim 1, wherein: the diameter d of the air hole (5)11.1um, spacing Λ of adjacent air holes in the x-directionx1.6um, pitch Λ in the y-directiony＝1.2um。
4. The graphene-coated metal D-type photonic crystal fiber biosensor of claim 1, wherein: diameter d of the air hole (6)21.6um, and the pitch Λ of the adjacent air holes 2.2 um.
5. The graphene-coated metal D-type photonic crystal fiber biosensor of claim 1, wherein: the gold film is made of gold, and the thickness t of the gold film layer is 45 nm.
6. The graphene-coated metal D-type photonic crystal fiber biosensor of claim 1, wherein: the number of layers of the graphene is five layers above and below the gold film, and the thickness of each layer of the graphene is 0.34 nm.
7. The graphene-coated gold-film D-type photonic crystal fiber biosensor of claim 1, wherein: the distance D between the center of the fiber core and the polished plane of the cladding11.9um, the distance D between the center of the fiber core and the center of the cladding arc curved surface2＝1.2um。
8. The graphene-coated gold film type D photonic crystal fiber biosensor of claim 1, wherein: the material of the core and the cladding is quartz with the refractive index equal to 1.45.
9. The graphene-coated gold film type D photonic crystal fiber biosensor of claim 1, wherein: the radius R of the cladding circular arc curved surface is 5.8 um.
10. The graphene-coated gold film type D photonic crystal fiber biosensor of claim 1, wherein: according to the characteristic that the sensor is extremely sensitive to the slight change of the refractive index of an external medium, when the refractive index of the external environment on the surface of the metal film changes, the position of a resonance absorption peak is changed, and the change of the external refractive index is calculated by measuring the variation of the wavelength of the position corresponding to the resonance absorption peak.
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Cited By (2)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN115826127A (en) * | 2022-11-23 | 2023-03-21 | 华北理工大学 | Gold-coated D-type microstructure optical fiber large-tolerance polarization filter |
| CN116661052A (en) * | 2023-06-01 | 2023-08-29 | 华北理工大学 | D-type micro-structure optical fiber with large tolerance sensing function and preparation method thereof |
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Cited By (3)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN115826127A (en) * | 2022-11-23 | 2023-03-21 | 华北理工大学 | Gold-coated D-type microstructure optical fiber large-tolerance polarization filter |
| CN116661052A (en) * | 2023-06-01 | 2023-08-29 | 华北理工大学 | D-type micro-structure optical fiber with large tolerance sensing function and preparation method thereof |
| CN116661052B (en) * | 2023-06-01 | 2024-03-15 | 华北理工大学 | D-type micro-structure optical fiber with large tolerance sensing function and preparation method thereof |
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