CN102507503A - Fiber surface plasmon resonance glucose sensor with temperature self-compensation - Google Patents
Fiber surface plasmon resonance glucose sensor with temperature self-compensation Download PDFInfo
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Abstract
The invention relates to a fiber surface plasmon resonance glucose sensor with temperature self-compensation. The fiber surface plasmon resonance glucose sensor comprises a fiber core; a fiber cladding wraps the periphery of the fiber core; a fiber grating is written in a 10-30mm section of the fiber core; and a chromium layer, a gold film and a glucose molecule specific adsorption layer are arranged on the periphery of a 15-30mm section of the fiber cladding from inside to outside. Fiber is single mode fiber; the fiber grating is a long-period fiber grating or a tilted fiber grating; the thickness of the chromium layer is 3-5 nm; and the thickness of the gold film is 30-60 nm. The fiber surface plasmon resonance glucose sensor has the advantages of simple structure, small volume, anti-electromagnetic interference and corrosion resistance, can be easily combined with a tissue fluid transdermal extraction chip so as to manufacture a miniaturized instrument, and meanwhile, is suitable for implanted measurement. With the adoption of the fiber surface plasmon resonance glucose sensor with temperature self-compensation, the measurement errors arising from temperature and the interference on measurement caused by external environments can be reduced.
Description
Technical field
The present invention relates to a kind of optical fiber surface plasmon resonance (SPR) glucose sensor.Particularly relate to a kind of optical fiber surface plasmon resonance glucose sensor that comprises fiber core, fibre cladding, fiber grating, chromium layer, golden film, glucose molecule specific adsorption layer with temperature self-compensation.
Background technology
The Along with people's growth in the living standard, the change of life style, the increase of aging population and fat incidence, the incidence of disease of diabetes is ascendant trend year by year.Diabetes are a kind of chronic diseases of metabolism, are characteristic with the hyperglycaemia.The long-term hyperglycaemia of diabetes tends to cause many tissues, and especially the damage of eye, nerve, heart and blood vessel causes its functional defect and depletion.Therefore the World Health Organization (WHO) classifies it and tumour, cardiovascular and cerebrovascular diseases as worldwide three big difficult and complicated illness together.At present also there is not thoroughly to effect a radical cure the medical means of diabetes clinically; The target of treating diabetes now is to measure blood sugar concentration as much as possible so that be used for implementing insulin control; Avoid blood sugar for human body too high, prevent or alleviate the generation and the symptomatic treatment complication of complication.So dynamic continuous detecting of human blood glucose concentration; From the information that detects, reflect the situation of change of patient's illness; Meet patient self thereby formulate, to have more the therapeutic scheme of hommization, to diabetes-alleviating with and complication; The misery of reduction of patient has positive meaning, also is the prerequisite and the basis of prevention with the following treatment of diabetes.
Employed blood sugar test is technological in the blood sugar monitoring process, and can be divided into by its wound degree to body has wound, Wicresoft and do not have the wound detection.Having wound to detect generally to be finger tip to get blood touches blood vessel and causes wound with nerve and cause and keenly feel; The nothing wound is meant based on optical technology and detects sugared change in concentration, body is had no damage; Though Wicresoft is meant little wound, do not touch blood vessel with neural, the patient is no pain almost.There is the wound blood sugar monitoring to adopt vein haemospasia and quick finger tip tip blood to detect blood sugar more.Because the restriction of detection method; Blood sugar monitoring can only be accomplished at isolated time point; What its result reflected is the moment blood sugar in certain several moment in one day; Moment blood glucose value be disperse can not reflect the full detail of human body at a certain period blood sugar, formulate the mitigation scheme of diabetes with these discrete measurement points, exist certain one-sidedness and inaccuracy; And repeatedly blood drawing not only consumes a large amount of test paper, expends time in, and also brings certain psychological burden and physiological pain to the patient.Various Woundless blood sugar detection methods based on optical technology are mostly still immature, are in the experimental study stage can not be applied to clinically, can not be applied to instrumentation production, can't satisfy dynamically, the requirement of human body blood sugar concentration continuously.And, still have no of the authentication of non-invasive blood-sugar detecting instrument device so far through U.S. FDA.
Wicresoft's blood sugar test technology is exactly to adopt the method painless from human body skin (or hypodynia) of Wicresoft to extract tissue fluid; Use biosensor technique to measure the glucose content in the tissue fluid then; Last correlativity according to concentration of glucose in concentration of glucose in the tissue fluid and the blood; And then infer the concentration of glucose in the blood of human body, also belong to the research category of Wicresoft's blood sugar concentration detection technique through the method for concentration of glucose in subcutaneous implantable miniature sensor measurement tissue fluid.The inconvenience that Wicresoft's blood sugar test technology can either avoid the wound blood sugar test to bring to greatest extent; Its method detects again than Woundless blood sugar and realizes more easily; And realize instrumentation production more easily, therefore received giving more sustained attention and extensive studies of people, have very high researching value.
Surface plasma resonance (SPR) sensor refractive index and material concentration are extremely responsive, can satisfy the detection requirement of concentration of glucose in Wicresoft's blood sugar.Surface plasma body resonant vibration (SPR) is a kind of physical optics phenomenon, is interacted and is produced by the free electron on incident light wave and metallic conductor surface.If there is thickness in light when at the interface of optically denser medium and optically thinner medium total reflection taking place between the two media interface be the metallic film of tens nanometers; The P polarized component of the evanescent wave that produces during total reflection so will get into metallic film; The surface plasma wave (SPW) that is produced with free electron vibration in the metallic film interacts, and when the angle of incident light or wavelength during to a certain particular value, evanescent wave resonates at the component and the surface plasma wave (SPW) of X-direction; The catoptrical energy of total reflection descends suddenly; Resonance absorbing peak appears on reflectance spectrum, this moment incident light angle or wavelength, be called resonance angle or the resonant wavelength of SPR.The character on the resonance angle of SPR or resonant wavelength and metallic film surface is closely related; If at metallic film surface attachment measured matter; Can cause the variation of metallic film surface refractive index; Thereby cause the variation of SPR spectrum, change the character (refractive index, concentration) that just can measure golden film surface mass according to these.The optical fiber probe advantages of small volume, portable strong, anti-electromagnetic interference (EMI) combines with the tissue fluid transdermal extraction chip easily and makes the miniaturization instrument, also is applicable to concentration of glucose in the subcutaneous implantable miniature sensor measurement tissue fluid simultaneously.But because tissue fluid other complicated components except containing glucose, measurement is interfered easily; Simultaneously, optical fiber is measured and is also received the influence that ambient temperature changes, and measuring error is bigger.
Summary of the invention
Technical matters to be solved by this invention is, provide a kind of have get rid of other materials and disturb, can satisfy in real time, the optical fiber surface plasmon resonance glucose sensor that requires of Wicresoft's blood sugar test continuously with temperature self-compensation.
The technical scheme that the present invention adopted is: a kind of optical fiber surface plasmon resonance glucose sensor with temperature self-compensation; Comprise fiber core; The periphery of described fiber core is enclosed with fibre cladding; Write fiber grating on one section of 10～30mm of said fiber core, be disposed with chromium layer, golden film and glucose molecule specific adsorption layer from inside to outside on one section the periphery of 15～30mm of described fibre cladding.
Described optical fiber is single-mode fiber.
Described chromium layer is that the mode through vacuum coating is deposited on the outer peripheral face of fibre cladding equably, and thickness is 3～5nm; Described golden film is that the mode through vacuum coating is deposited on the chromium layer equably, and thickness is 30～60nm.
Described glucose molecule specific adsorption layer adopts the mode of static self assembly layer by layer to be fixed in golden film surface.
Described fiber grating is LPFG or inclined optical fiber grating.
When described fiber grating adopts LPFG; The cycle of fiber grating is 300～600um; Length is 10～30mm, and described fiber grating is in the different place, shaft part position of fiber core with described chromium layer, golden film and glucose molecule specific adsorption layer.
When described fiber grating adopts inclined optical fiber grating; The cycle of fiber grating is 200～600nm; Length is 10～20mm; The angle of inclination is 5 °～10 °, and described fiber grating is in the identical place, shaft part position of fiber core with described chromium layer, golden film and glucose molecule specific adsorption layer.
Described chromium layer, golden film and glucose molecule specific adsorption layer are to be wrapped in successively on the outer circumference surface of fibre cladding from inside to outside.
Be formed with the surface level that length is 15～30mm on the outer peripheral face of described fibre cladding, described chromium layer, golden film and glucose molecule specific adsorption layer are to be successively set on from inside to outside on described this surface level.
Two and plural optical fiber surface plasmon resonance glucose sensor with temperature self-compensation adopt the mode of fiber grating surface plasma resonance cascade to form the differential type measurement structure.
Optical fiber surface plasmon resonance glucose sensor with temperature self-compensation of the present invention has following characteristics:
1, the present invention is made up of optical fiber, and simple in structure, advantages of small volume, anti-electromagnetic interference (EMI), corrosion-resistant combine with the tissue fluid transdermal extraction chip easily and make the miniaturization instrument, also are applicable to the implanted measurement simultaneously.
2, the present invention introduces and a kind of glucose molecule is had the borate polymkeric substance of specific adsorption effect, that this polymkeric substance is made is simple, stable in properties, be easy to preserve, with low cost.Employing static self-assembling method layer by layer is bundled in sensor surface with it, and binding procedure is simple, can relatively easily control the structure and the thickness of self-assembled film, thus control survey scope and sensitivity.Because the tissue fluid complicated component, except measuring object glucose, also have a lot of other materials, the glucose molecule of glucose specific adsorption layer in can selective adsorption tissue fluid got rid of other materials and disturbed, and increases the precision of measuring.
3, the present invention writes one section grating in fiber core.Environment temperature can change in measuring process; Bigger by the temperature variation errors caused; Therefore the fiber grating temperature variation of environment to external world has very high measurement sensitivity, utilizes fiber grating to carry out that temperature compensation can reduce Yin Wendu and the measuring error that causes.
4, the present invention can adopt the structure of fiber grating and optical fiber zone cascade to carry out the differential type measurement, reduces the interference of external environment to measuring, and can effectively reduce measuring error.
Description of drawings
Fig. 1 is the structural representation of LPFG SPR glucose sensor;
Fig. 2 is the structural representation of side polishing LPFG SPR glucose sensor;
Fig. 3 is the structural representation of inclined optical fiber grating SPR glucose sensor;
Fig. 4 is the structural representation of side polishing inclined optical fiber grating SPR glucose sensor;
Fig. 5 is the mechanism synoptic diagram of borate polymkeric substance and glucose;
Fig. 6 is the structural representation of fiber grating cascade difference SPR glucose sensor;
Fig. 7 utilizes optical fiber principle refractometry principle schematic;
Fig. 8 is the LPFG structural representation;
Fig. 9 is skew ray grid structural representations;
Figure 10 is an optical fiber glucose sensor measuring system synoptic diagram.
Wherein:
1: fiber core 2: fibre cladding
3: LPFG 4: the chromium layer
5: golden film 6: glucose specific adsorption layer
7: inclined optical fiber grating 8: optical fiber
9: tissue fluid 10: metal film
11: the horizontal wave vector of surface plasma-wave 12:P polarized light
13:P polarized light 14: metal film
15: emergent light 16: light source
17: the polarizer 18: spectrometer
19: the optical fiber glucose sensor
Embodiment
Below in conjunction with embodiment and accompanying drawing the optical fiber surface plasmon resonance glucose sensor with temperature self-compensation of the present invention is made detailed description.
Like Fig. 1～shown in Figure 4; Optical fiber surface plasmon resonance (SPR) glucose sensor with temperature self-compensation of the present invention; Comprise fiber core 1, the periphery of described fiber core 1 is enclosed with fibre cladding 2, and described optical fiber is single-mode fiber; On a section of 10～30mm of fiber core 1, write fiber grating 3, described fiber grating 3 is LPFG or inclined optical fiber grating.On one section the periphery of 15～30mm of described fibre cladding 2 chromium layer 4, golden film 5 and glucose molecule specific adsorption layer 6 are arranged successively from inside to outside.Be fixed with one deck has specific adsorption to glucose glucose adsorbed layer 6 at golden film 5 outside surfaces; Main working substance is for there being the borate polymkeric substance of very strong affinity to glucose molecule; This material very easily adsorbs the combination glucose molecule, does not have effect with other materials in measuring.
Described chromium layer 4 is that the mode through vacuum coating is deposited on the outer peripheral face of fibre cladding 2 equably, and thickness is 3～5nm; Described golden film 5 is that the mode through vacuum coating is deposited on the chromium layer 4 equably, and thickness is 30～60nm.Described glucose molecule specific adsorption layer 6 adopts the mode of static self assembly layer by layer to be fixed in golden film 5 surfaces.
Like Fig. 1, shown in Figure 2; When described fiber grating 3 adopts LPFG; The cycle of fiber grating 3 is 300～600um; Length is 10～30mm, and described fiber grating 3 and described chromium layer 4, golden film 5 and glucose molecule specific adsorption layer 6 are in the different place, shaft part position of fiber core 1.
Like Fig. 3, shown in Figure 4; When described fiber grating 3 adopts inclined optical fiber grating; The cycle of fiber grating is 200～600nm; Length is 10～20mm, and the angle of inclination is 5 °～10 °, and described fiber grating 3 and described chromium layer 4, golden film 5 and glucose molecule specific adsorption layer 6 are in the identical place, shaft part position of fiber core 1.
Like Fig. 1, shown in Figure 3, in the optical fiber surface plasmon resonance glucose sensor with temperature self-compensation of the present invention, described chromium layer 4, golden film 5 and glucose molecule specific adsorption layer 6 are to be wrapped in successively on the outer peripheral face of fibre cladding 2 from inside to outside.
Like Fig. 2, shown in Figure 4; In the optical fiber surface plasmon resonance glucose sensor with temperature self-compensation of the present invention can also be; On the outer peripheral face of described fibre cladding 2, be formed with the surface level that length is 15～30mm, described chromium layer 4, golden film 5 and glucose molecule specific adsorption layer 6 are to be successively set on from inside to outside on described this surface level.
Optical fiber surface plasmon resonance glucose sensor with temperature self-compensation of the present invention is applicable to glucose concentration measurement in the transdermal extraction tissue fluid, also can be used for human body implantation type tissue fluid glucose concentration measurement.
Concrete method for making below in conjunction with four kinds of different structures of the description of drawings optical fiber surface plasmon resonance glucose sensor with temperature self-compensation of the present invention:
(1) as shown in Figure 1: as with the single-mode fiber (NA 0.22, refractive index 1.4681) that a core diameter is 8.3um, to use the sulfuric acid corrosion coat, expose covering and make the smooth cleaning of its cladding surface through the polishing cleaning then.In fiber core, adopt point-to-point writing method to write LPFG, fiber grating cycle 300～600um, length 10～30mm.Use vacuum coating equipment outside the exposed covering circumference of a segment length, to plate the chromium layer of one deck 3nm, again at the golden film of chromium laminar surface plating one deck 30～60nm as 15-30mm.In the fixing one deck glucose molecule specific adsorption layer of golden film surface by utilizing static layer-by-layer.
(2) as shown in Figure 2: as with the single-mode fiber (NA 0.22, refractive index 1.4681) that a core diameter is 8.3um, to use the sulfuric acid corrosion coat, expose covering and make the smooth cleaning of its cladding surface through the polishing cleaning then.In fiber core, adopt point-to-point writing method to write LPFG, fiber grating cycle 300～600um, length 10～30mm.Is the surface level of 15-30mm in another section of optical fiber zone along the fibre core vertical direction segment length of polishing, and the residue cladding thickness is 3～5nm.Use the chromium layer of vacuum coating equipment plating one deck 3nm on the surface level of polishing, plate the golden film of one deck 30～60nm again at the chromium laminar surface.In the fixing one deck glucose molecule specific adsorption layer of golden film surface by utilizing static layer-by-layer.
(3) as shown in Figure 3: as with the single-mode fiber (NA 0.22, refractive index 1.4681) that a core diameter is 8.3um, to use the sulfuric acid corrosion coat, expose behind the covering to clean and make the smooth cleaning of its cladding surface through polishing.In fiber core, adopt point-to-point writing method to write inclined optical fiber grating, fiber grating cycle 200～600um, length 10～20mm, 5 °～10 ° at angle of inclination.Using vacuum coating equipment surrounding layer horizontal length outside fiber grating is the chromium layer of plating one deck 3nm on the periphery of 15-30mm, plates the golden film of one deck 30～60nm again at the chromium laminar surface.In the fixing one deck glucose molecule specific adsorption layer of golden film surface by utilizing static layer-by-layer.
(4) as shown in Figure 4: as with the single-mode fiber (NA 0.22, refractive index 1.4681) that a core diameter is 8.3um, to use the sulfuric acid corrosion coat, expose behind the covering to clean and make the smooth cleaning of its cladding surface through polishing.In fiber core, adopt point-to-point writing method to write inclined optical fiber grating, fiber grating cycle 200～600um, length 10～20mm, 5 °～10 ° at angle of inclination.Is the surface level of 15-30mm in this zone along the fibre core vertical direction segment length of polishing, and the residue cladding thickness is 3～5nm.Using vacuum coating equipment surrounding layer horizontal length outside fiber grating is the chromium layer of plating one deck 3nm on the periphery of 15-30mm, plates the golden film of one deck 30～60nm again at the chromium laminar surface.In the fixing one deck glucose molecule specific adsorption layer of golden film surface by utilizing static layer-by-layer.
The borate polymkeric substance that optical fiber surface plasmon resonance glucose sensor with temperature self-compensation of the present invention is introduced and the action principle of glucose: as shown in Figure 5, have the powerful group-hydroxyl that combines with glucose molecule on the boric acid.Boric acid can become with the neutral three-legged structure of water reaction in water is with electronegative four-corner structure, and discharges an electronics.The hydroxyl on WS mesoboric acid salt polymkeric substance and the hydroxyl generation condensation reaction of glucose molecule combine, and this reaction is reversible reaction.
The preparation and the binding method of the borate polymkeric substance that the present invention introduces are following:
Launch to process the borate monomer with boric acid through ethyl acetate earlier, form the borate polymkeric substance through acrylamide polymerization again, the borate polymkeric substance is bundled in the golden film surface of sensor through the method for static self assembly layer by layer.Static self assembly layer by layer is to construct multi-layer film structure with weak interaction (interionic electrostatic interaction) as the expulsive force alternating deposit, and the introducing of borate polymkeric substance wherein is fixed on golden film surface.One section optical fiber that at first will be coated with golden film immerses in the said polycation solution, takes out absorption one deck polycation on the optical fiber SPR sensor after leaving standstill a period of time.At this moment, on the optical fiber SPR sensor with electric charge just become owing to the absorption of polycation; Secondly water washes sensor surface, removes the polycation of excessive adsorption, and it is carried out drying; Then the sensor is transferred in the electronegative borate polymer solution, optical fiber face surface charge reverts to negative; Washing at last, drying.Repeat polycation/polyanion ultrathin membrane that above operation just can obtain multilayer.
Optical fiber surface plasmon resonance glucose sensor with temperature self-compensation of the present invention can be through the mode of fiber grating cascade; Form the differential type measurement structure; Carry out differential type and measure, reduce the interference of external environment, can effectively reduce measuring error measuring.Wherein a kind of structure is as shown in Figure 6: with the single-mode fiber (NA 0.22, refractive index 1.4681) that a core diameter is 8.3um, use the sulfuric acid corrosion coat, expose covering and make the smooth cleaning of its cladding surface through the polishing cleaning then.In fiber core, adopt point-to-point writing method to write two segment length's cycle optical fiber or inclined optical fiber gratings.The use vacuum coating equipment plates the chromium layer of one deck 3nm on the surrounding layer periphery outside fiber grating, plate the golden film of one deck 30～60nm again at the chromium laminar surface.In the fixing one deck glucose molecule specific adsorption layer of golden film surface by utilizing static layer-by-layer.The optical fiber glucose spr sensor of other structures of the present invention also can carry out cascade with reference to Fig. 6 structure.
Optical fiber surface plasmon resonance glucose sensor with temperature self-compensation of the present invention, the concentration of glucose method is following in the measurement tissue fluid:
As shown in Figure 7, the vibration of metal 10 surface plasmas produces a kind of electromagnetic wave and is called surface plasma wave 11, and surface plasma wave 11 is propagated along the interface, and the decay that presents index, and its wave vector is expressed as K
SPP polarized light 13 is propagated in optical fiber, and at the interphase generation total reflection phenomenon of optical fiber 8 with metal 10, the P polarized light continues in the metal surface to propagate, and its horizontal wave vector 12 is expressed as K
xWork as K
SP=K
xThe time, the surface plasma resonance phenomenon takes place, SPR resonance angle 14 does
In the formula: ε
dBe tissue fluid 9 specific inductive capacity, ε
mBe metal 10 specific inductive capacity, ε
pBe optical fiber 8 specific inductive capacity.
The measurement of concentration of glucose is the corresponding relation that obtains SPR angle and concentration of glucose through experiment in the tissue fluid, obtains concentration value through methods such as interpolation, matches then.
Optical fiber surface plasmon resonance glucose sensor with temperature self-compensation of the present invention, the method for carrying out temperature compensation through fiber grating measurement temperature is following:
(1) LPFG temperature compensation: as shown in Figure 8, because LPFG relates to core mode and cladding mode, be that core mode is coupled in the different cladding modes, so during account temperature, the phase-matching condition of LPFG can be written as
β wherein
Co(λ, T) with
Representing the propagation constant of core mode and cladding mode when temperature is T respectively, all is functions of λ and T; Λ is the fiber grating cycle 3 of temperature when being T, Λ=(1+ α Δ T) Λ
0
Can obtain the temperature control K of LPFG according to phase-matching condition (1) and
.Where
and
respectively, the fiber core and the effective refractive index of the cladding.
Wherein γ is the waveguide dispersion factor, λ
ResBe resonance wavelength, and be similar to 1 (1+ α Δ T) ≈ 1, ζ
EffEffective thermo-optical coeffecient for core mode or cladding mode.
(2) inclined optical fiber grating temperature compensation: for common single mode FBG, the transmission peaks expression formula that satisfies Bragg condition is: λ
Sragg=2
Neff, coreΛ (4)
In the formula, n
Eff, coreBe the effective refractive index of fibre core, Λ is the cycle along fibre core direction grid.
As shown in Figure 9, the skew ray grid are owing to its grid face tilt angle θ, along fibre core direction grid cycle Λ
gBecome:
Λ
g＝Λ/cosθ (5)
Bringing formula (4) into formula (3) obtains the bragg wavelength that the skew ray grid propagate and is in fibre core:
Because grid face tilt, the incident light of forward conduction satisfy the back to the core mode of conduction of Bragg condition except part is coupled as, part also will be coupled as the cladding mode of back to conduction. cladding mode resonant wavelength expression formula is:
When TFBG temperature variation of living in, thermal expansion effects can cause the grating cycle to change, and thermo-optic effect can cause fibre core and cladding-effective-index to change, thereby the wavelength of core mode and each cladding mode is drifted about.Wherein, the wave length shift of core mode is formulated as
The wave length shift of each rank cladding mode of TFBG can be expressed as
Wherein, Δ T representes temperature variation;
The thermo-optical coeffecient of expression fibre core;
The thermal expansivity of expression core material;
Represent the thermo-optical coeffecient that i rank cladding mode is corresponding.
The drift of inclined optical fiber grating under temperature effect mainly caused by thermo-optical coeffecient, because A
iWith the α approximately equal, and core mode also is identical with the corresponding thermal expansivity of cladding mode, has essentially identical temperature control so can infer core mode and cladding mode.
The present invention is a kind of, and to have optical fiber surface plasmon resonance (SPR) the glucose sensor measuring system and the measuring method of temperature self-compensation following:
Optical fiber glucose sensor measuring system is shown in figure 10.(light of 1528nm～1610nm) send becomes the P polarized light through the polarizer 17 and enters into optical fiber glucose sensor 19 ASE light source 16.Fiber grating is coupled to light in the fibre cladding by fiber core, on golden film surface surface plasma resonance takes place then.Light enters into spectrometer 18 after through optical fiber glucose sensor 19, and (detect wavelength coverage 600～1700nm), spectrometer 18 detects transmission spectrum.When concentration of glucose in the tissue fluid 11 changed, the position of surface plasma resonance resonance peak changed in the transmission spectrum, thereby can measure the glucose of variable concentrations.Harmonic peak variation through fiber grating in the transmission spectrum can be measured the variation of temperature amount, thereby carries out temperature compensation.
The present invention is made up of optical fiber, and simple in structure, advantages of small volume, anti-electromagnetic interference (EMI), corrosion-resistant combine with the tissue fluid transdermal extraction chip easily and make the miniaturization instrument, also are applicable to concentration of glucose in the implanted measurement tissue fluid simultaneously.
The present invention is open and that disclose, and all combinations can produce through using for reference this paper disclosure; Although combination of the present invention is described through detailed implementation process; But those skilled in the art obviously can be spliced device as herein described in not breaking away from content of the present invention, spirit and scope or change; Or increase and decrease some parts; More particularly, the replacement that all are similar and change apparent to those skilled in the artly, they are regarded as and are included among spirit of the present invention, scope and the content.
Claims (10)
1. optical fiber surface plasmon resonance glucose sensor with temperature self-compensation; Comprise fiber core (1); It is characterized in that; The periphery of described fiber core (1) is enclosed with fibre cladding (2), has write fiber grating (3) on one section of 10～30mm of said fiber core (1), is disposed with chromium layer (4), golden film (5) and glucose molecule specific adsorption layer (6) on one section the periphery of 15～30mm of described fibre cladding (2) from inside to outside.
2. the optical fiber surface plasmon resonance glucose sensor with temperature self-compensation according to claim 1 is characterized in that described optical fiber is single-mode fiber.
3. the optical fiber surface plasmon resonance glucose sensor with temperature self-compensation according to claim 1; It is characterized in that; Described chromium layer (4) is that the mode through vacuum coating is deposited on the outer peripheral face of fibre cladding (2) equably, and thickness is 3～5nm; Described golden film (5) is that the mode through vacuum coating is deposited on the chromium layer (4) equably, and thickness is 30～60nm.
4. the optical fiber surface plasmon resonance glucose sensor with temperature self-compensation according to claim 1 is characterized in that, described glucose molecule specific adsorption layer (6) adopts the mode of static self assembly layer by layer to be fixed in golden film (4) surface.
5. the optical fiber surface plasmon resonance glucose sensor with temperature self-compensation according to claim 1 is characterized in that described fiber grating (3) is LPFG or inclined optical fiber grating.
6. the optical fiber surface plasmon resonance glucose sensor with temperature self-compensation according to claim 5; It is characterized in that; When described fiber grating (3) adopts LPFG; The cycle of fiber grating (3) is 300～600um, and length is 10～30mm, and described fiber grating (3) is in the different place, shaft part position of fiber core (1) with described chromium layer (4), golden film (5) and glucose molecule specific adsorption layer (6).
7. the optical fiber surface plasmon resonance glucose sensor with temperature self-compensation according to claim 5; It is characterized in that; When described fiber grating (3) adopted inclined optical fiber grating, the cycle of fiber grating was 200～600nm, and length is 10～20mm; The angle of inclination is 5 °～10 °, and described fiber grating (3) is in the identical place, shaft part position of fiber core (1) with described chromium layer (4), golden film (5) and glucose molecule specific adsorption layer (6).
8. the optical fiber surface plasmon resonance glucose sensor with temperature self-compensation according to claim 1; It is characterized in that described chromium layer (4), golden film (5) and glucose molecule specific adsorption layer (6) are to be wrapped in successively on the outer circumference surface of fibre cladding (2) from inside to outside.
9. the optical fiber surface plasmon resonance glucose sensor with temperature self-compensation according to claim 1; It is characterized in that; Be formed with the surface level that length is 15～30mm on the outer peripheral face of described fibre cladding (2), described chromium layer (4), golden film (5) and glucose molecule specific adsorption layer (6) are to be successively set on from inside to outside on described this surface level.
10. the optical fiber surface plasmon resonance glucose sensor with temperature self-compensation according to claim 1; It is characterized in that two and plural optical fiber surface plasmon resonance glucose sensor with temperature self-compensation adopt the mode of fiber grating surface plasma resonance cascade to form the differential type measurement structure.
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| CN107741409A (en) * | 2017-09-15 | 2018-02-27 | 武汉理工大学 | A kind of cancer markers detection means and method based on slant Bragg grating |
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