RU2432568C1 - Sensor based on planar and cylindrical hollow light guides with integrated interferometric system - Google Patents

Abstract

FIELD: physics. ^ SUBSTANCE: invention relates to fibre-optic devices (sensors) designed to analyse composition and concentration of gaseous and liquid substances, as well as thin layers of molecules, based on planar and cylindrical hollow light guides, including hollow microstructured waveguides. In order to detect low concentrations of substances and biochemical processes, an anti-resonance interferometric system (Fabry-Perot interferometre type) is integrated into the waveguide. ^ EFFECT: invention enables integration of a single chip on a platform and enables to create a system for simultaneous rapid monitoring of several bioanalytes, increases sensitivity for detecting small changes in the refraction index of the analyte and detecting monolayers of biomolecules immobilised on the surface of the waveguide cladding. ^ 5 cl, 7 dwg

Description

The invention relates to fiber-optic devices (sensors) for analyzing the composition and concentration of gaseous and liquid substances, as well as thin layers of molecules (including biological).

Currently existing sensory waveguide devices are usually based on the use of one of two principles: (i) optical excitation of the analyte by an evanescent field, i.e. part of the waveguide mode propagating outside the core of the waveguide, and (ii) recording a small change in the propagation constant of the waveguide mode, resulting from a change in the refractive index of the analyte or immobilization of (bio) molecules on the waveguide shell.

Consider a few examples of fiber optic sensor devices. US Patent Application US2004057647 (LYONS DANALD R (US). APPARATUS FOR AND METHODS OF SENSING EVANESCENT EVENTS IN A FLUID FIELD) describes a circuit in which a fiber sensor device has a round core and a D-shaped sheath, with a flat section of the sheath possesses a diffraction grating. An evanescent field penetrates the test substance, applied to the place of a flat cut of the D-shaped shell. The conditions for the propagation of laser radiation change with a change in the state of the test substance, which is then recorded using a registration system. US Pat. No. 5,436,167 (ROBILLARD JEAN J (US), FIBER OPTICS GAS SENSOR) discloses a fiber optic sensor in which one portion of this sensor is coated with a transparent semiconductor material that functions as a gas absorber. This semiconductor material can absorb the atoms and molecules of the test gas, which changes its refractive index. Laser radiation is directed into an optical fiber with a known state of polarization. When the refractive index of the semiconductor shell changes, the state of polarization of the transmitted light changes. The change in the polarization of light determines the presence and concentration of the test gas.

Microstructured (photonic-crystalline) optical fibers (JCKnight, J. Broeng, T.A. Birks, and P.St. J. J. Russell, Science 282, 1476 (1998); P.St.J are increasingly used to implement sensor systems Russell, Science 299, 358 (2003); JCKnight, Nature 424, 847 (2003); AMZheltikov, Optics of microstructured fibers (Moscow, Nauka, 2004); AMZheltikov, Uspekhi Fizicheskikh Nauk, 177 (2007)). Planar integrated waveguide systems based on antiresonance reflection provide high sensitivity for recording biochemical processes in the analyte and can be used for direct monitoring of biomolecular processes. Microstructured fibers are of significant interest for the development of new optical sensors (T.M. Monro, W. Belardi, K. Furusawa, J.C. Baggett, NGR Broderick, and DJ Richardson, Meas. Sci. Technol. 12, 854 (2001) ; L. Rindorf, JB Jensen, M. Dufva, LH Pedersen, PE Høiby, and O. Bang, Opt. Express 14, 8224 (2006)). In sensors based on microstructured (MS) fibers, demonstrated by M.T. Myaing, JYYe, T.V. Norris, T.Thomas, JRBaker, Jr., WJWadsworth, G. Bouwmans, JCKnight, and PSJ Russell, Opt. Lett. 28, 1224 (2003), the exciting radiation is delivered to the object through the core of the MS fiber. The inner part of the MS shell has openings with dimensions of the order of a micrometer and serves to deliver a scattered or fluorescent signal through the fiber from the object under study to the radiation receiver, which can be located next to the radiation source. This fiber design provides high sensing efficiencies of chemical and biological solutions using single-photon and two-photon luminescence methods. The microstructured fiber sheath can also be used as a system of microcapillaries filled with an extremely small volume of the test solution. Radiation propagating along the fiber core causes luminescence of the detected molecules (S. Konorov, A. Zheltikov, and M. Scalora, Opt. Express 13, 3454 (2005)). Such fiber sensors can be integrated into chemical and biological data storage and processing systems, including biochips, for reading and converting stored information.

Sensors based on MS fibers that excite an analyte with an evanescent field are described in the following European Basic Patent EP 1236059 (PHOTONIC CRYSTAL FIBER GUIDING A FIRST MODE AND A PUMP BEAM, RUSSELL, PHILIP ST JOHN (GB); BIRKS, TIMOTHY ADAM (GB ); KNIGHT, JONATHAN CAVE (GB); MANGAN, BRIAN JOSEPH (GB)). Sensor devices based on recording changes in the propagation constant of the waveguide mode in hollow photonic crystal fibers are described in Chinese patent CN 1900696 (XUE CHENYANG ZHANG (CN), HOLLOW CORE PHOTON CRYSTAL FIBER-OPTIC FIBER GAS SENSOR). The patent proposes a gas sensor using a hollow photonic crystal fiber. This device has a photonic crystal fiber having relatively low light losses during the propagation of light in its core compared to conventional hollow fibers. There is another support arm of the sensor containing a reference gas cell through which the reference light beam passes. The registration system measures and compares both beams of light, i.e. this scheme has an external system for comparing fiber transmission conditions (in essence, this is an external interferometric scheme that uses reference and studied light beams). When filling the hollow core of the photonic crystal fiber with the gas under study or changing its concentration, the conditions for the passage of light in the core of the hollow fiber change, and the registration system records these changes.

The subject of this patent are sensor devices and systems of a new type based on hollow fibers, including MS fibers. The principle of operation of these sensors is based on the high sensitivity of the waveguide modes of the final sheath of planar and cylindrical hollow waveguides to the thickness of the sheath structure and to the refractive index of the medium filling the air holes of this waveguide structure. The developed sensor devices are designed, firstly, to record thin layers of molecules (including biological ones) immobilized on the surface of the shell, and secondly, to record small changes in the refractive index of the analyte filling the air holes of the waveguide structure.

The objective of the invention is to provide a sensor device based on hollow optical fibers.

A sensor device based on hollow optical fibers contains a light source, an optical hollow fiber, a registration system that measures the change in the conditions of light propagation in the fiber in the presence of a test analyte, characterized in that it contains an antiresonance interferometric system directly integrated into the fiber cladding. The antiresonant interferometric system integrated into the cladding of the fiber makes it possible to simplify the sensor device due to the fact that an external interferometer is not needed and to reduce the size of the device.

The antiresonant interferometric system is a Fabry-Perot interferometer formed by the internal boundary of a hollow fiber layer, a glass sheath of finite dimensions comparable to the wavelength of light, and an outer sheath. An embodiment of the interferometric system integrated into the optical fiber cladding is a Fabry-Perot interferometer.

The antiresonant interferometric system is designed so that when light propagates in the system, it forms narrow lines in the transmission spectrum of the fiber, which are formed due to antiresonant multipath interference due to the interaction of the waveguide modes of the hollow core and the glass shell. The position of the line in the transmission spectrum of the fiber depends on the presence of analyte in the hollow fiber. The narrow lines in the transmission spectrum of the fiber allow increasing the detection sensitivity of small changes in the refractive index of the analyte and, therefore, increasing the detection sensitivity of monolayers of biomolecules (including DNA molecules) immobilized on the surface of the waveguide sheath.

The sensor device has planar geometry.

The sensor device has a cylindrical geometry. Options for the execution of the sensor device are planar or cylindrical geometry.

The registration system is designed to detect changes in the position of narrow lines in the transmission spectrum of the fiber, determined by the antiresonant interferometric system. The analyte is detected by measuring changes in the position of lines in the transmission spectrum of a hollow fiber, the spectrum of which is determined by the Fabry-Perot interferometer integrated into the cladding. Such an interferometer is sensitive to small changes in the conditions of light propagation associated with the presence of the test substance on the walls or inside the hollow core. In other words, the detection is carried out due to the high sensitivity of the modes of the final cladding of hollow waveguides to the thickness of the annular structure of the cladding and to the refractive index of the medium filling the air holes of the waveguide structure.

The sensor device contains at least two optical hollow fibers integrated on a single chip platform. This allows you to create a sensor device for parallel rapid monitoring of several bio (analytes).

The technical result of the development of a sensor device based on optical hollow optical fibers is:

- higher than the available analogues sensitivity of recording small changes in the refractive indices of the analyte;

- higher in comparison with existing analogues sensitivity of registration of monolayers of biomolecules (including DNA molecules) immobilized on the surface of the waveguide sheath;

- lack of an external interferometer, because an interferometric system (such as a Fabry-Perot interferometer) is integrated into the waveguide,

- the possibility of creating a system for parallel rapid monitoring of several (bio) analytes.

Figure 1 Schematic illustration of a cylindrical hollow optical sensor device with a built-in Fabry-Perot interferometer.

- постоянная распространения волноводной моды, k₀=2π/λ, λ - длина волны, волноводной мод, h - собственное значение волноводной моды падения и преломления.Figure 2. The geometrical-optical picture of the waveguide propagation of radiation in a hollow waveguide: n ₁ , n _c1 are the refractive indices of the core and the sheath, θ ₁ , θ ₂ are the angles that the incident and refracted rays form normal to the interface between the core and the sheath, t is the transverse dimension cores

is the propagation constant of the waveguide mode, k ₀ = 2π / λ, λ is the wavelength, waveguide mode, and h is the eigenvalue of the waveguide mode of incidence and refraction.

Figure 3. The transmission spectrum of the planar (solid and dashed lines) and cylindrical (dash-dotted lines) hollow waveguides with a single antiresonant layer in the cladding. The refractive index of the waveguide sheath was calculated using the Sellmeier formula for fused silica. The core refractive index n ₁ = 1. The transverse dimension of the core of the waveguide is t = 10 μm, the thickness of the antiresonance layer is d = 0.5 μm, and the length of the waveguide is L = 2 cm.

Figure 4. The transmission spectra of a hollow cylindrical waveguide filled with an analyte with a refractive index n ₁ = 1.33 in the absence of (1, 2) and in the presence of (3, 4) a layer of biomolecules with a thickness of 10 nm. The thickness of the waveguide sheath d = 400 nm, the sheath refractive index n ₂ = 1.46. The transverse size of the waveguide core is t = 15 μm (1, 3), 100 μm (2, 4).

Figure 5. The transmission spectra of a hollow cylindrical waveguide filled with an analyte with a refractive index of n ₁ = 1.33 (solid line) and n ₁ = 1.34. The thickness of the waveguide sheath d = 400 nm, the sheath refractive index n ₂ = 1.46. The transverse size of the core of the waveguide is t = 100 μm.

6. Cross-sectional image of a hollow fiber with a microstructured sheath (a). Fiber transmission spectrum (b): solid line — experimental data, dashed line — calculation result for t = 20 μm, d = 1.4 μm.

7. A cross-sectional image of a waveguide structure consisting of a system of hollow waveguides, which allows parallel detection of various biochemical processes in a solution on a single chip platform.

The principle of operation of the touch device

Consider a hollow waveguide of a general form, consisting of a core with a refractive index n ₁ and a uniform infinite sheath with a refractive index n _c1 . In terms of representations of geometric optics, the eigenmode of the waveguide corresponds to a light beam propagating along a zigzag path (Fig. 2), the break points of which correspond to the points of partial reflection of the beam from the interface between the core and the waveguide sheath. The attenuation of this mode is due to incomplete reflection of radiation from the interface between the core and the shell. The attenuation coefficient α can be calculated (A. Yariv, P. Yeh, Optical Waves in Crystals, New York, Wiley, 1984) using the following formula:

where r is the reflection coefficient of the interface,

is the number of fracture points of the zigzag trajectory of the light beam along the length L, θ ₁ is the angle that the light beam forms with a normal to the interface between the core and the shell (figure 2).

, где k₀=2π/λ, λ - длина волны, волноводной мод, h - собственное значение волноводной моды (фиг.2), имеемFor waveguide mode with propagation constant

where k ₀ = 2π / λ, λ is the wavelength of the waveguide mode, h is the eigenvalue of the waveguide mode (Fig. 2), we have

For a planar waveguide with a thickness of the central layer (core) t

where m is an integer.

Due to the fact that an acceptable level of losses in the hollow waveguide is ensured for the eigenmodes corresponding to the mode of sliding incidence at the interface between the core and the cladding, we set h << k ₀ n ₁ and transform expression (2) to the form

The reflection coefficient in the expression (1) is determined according to the Fresnel formulas, which, when the condition h << k ₀ n ₁ is satisfied, leads to the following relation:

where θ ₂ is the angle that the refracted beam forms with a normal to the interface (figure 2).

Logarithm of formula (1) and using the relation ln (1 + ξ) ≈ξ, which is true for small ξ, we obtain

The attenuation coefficient of the eigenmodes of a cylindrical hollow waveguide with a diameter t (Fig. 1) can be obtained by multiplying expression (7) by the factor (2u ₁ / πm) ² , where u _l is the limit value of the eigenvalue of the eigenmode of a cylindrical waveguide (for the main mode l = 0, J ₀ (u ₀ ) = 0).

We now consider a waveguide structure with a hollow core with a refractive index n ₁ and thickness t and a cladding containing a layer of finite thickness d with a refractive index n ₂ . For simplicity, we assume that outside this layer the refractive index of the shell is close to the refractive index of the core. To calculate the reflection coefficient from the interface between the core and the shell in expression (1), we use the well-known result for the reflection coefficient of the Fabry-Perot interferometer

Here

where r _F is the reflection coefficient calculated by the Fresnel formulas (6).

In the sliding falling mode, θ ₁ << 1, h << β, expressions (9) and (10) take the form

The solid line in Fig. 3 shows the transmission spectrum T (λ) = exp (-αL) for the fundamental eigenmode (m = 1) of a planar hollow waveguide of the type under consideration, calculated using formulas (1), (5), (8) - (10). The refractive index of the waveguide sheath was determined by the Sellmeyer formula for fused silica. Other parameters of the waveguide were selected as follows: n ₁ = 1, t = 10 μm, d = 0.5 μm, L = 2 cm.

When performing equality

where l is an integer, the conditions for resonant excitation of the waveguide cladding modes are identical, which are identical to the modes of the Fabry-Perot interferometer. In this mode, the core mode is resonantly coupled to the core modes and experiences strong attenuation. When condition (13) is fulfilled, thus, pronounced minima are observed in the transmission spectrum of the waveguide (see Fig. 3).

When the condition is met

where j is an integer, the connection between the modes of the core and the shell is minimal. The modes of the Fabry-Perot interferometer forming the cladding of the waveguide under consideration, when equality (14) is fulfilled, are antiresonant to the core modes. The transmission of the waveguide under these conditions reaches a maximum (figure 3).

Substitution of expression (8) into formula (1) when condition (14) is satisfied taking into account expressions (6) and (10) leads to the following result:

антирезонансная оболочка волновода обеспечивает также существенно более высокую, по сравнению с бесконечной оболочкой, эффективность подавления высших волноводных мод (ср. формулы (7) и (15)).As follows from expression (15), the loss coefficient of a hollow waveguide with an antiresonant sheath changes in proportion to the third degree of the radiation wavelength and inversely to the fourth degree of the transverse size of the core. The transmittance for such a waveguide is shown by a dash-dot line in FIG. For higher waveguide modes, as follows from expression (15), the damping coefficient increases in proportion to the third power of the index of the waveguide mode m. Thus, the antiresonant sheath of the waveguide leads to a significant (in the order of magnitude in λm / t times) decrease in the loss of the eigenmodes of the waveguide as compared with the loss of a hollow waveguide with a continuous infinite sheath. Thanks to addiction

the antiresonant cladding of the waveguide also provides a significantly higher, compared with the infinite cladding, suppression of higher waveguide modes (cf. formulas (7) and (15)).

The expression for the attenuation coefficient of the eigenmodes of a cylindrical hollow waveguide with a diameter t (Fig. 1) can be obtained by multiplying the loss coefficient for a planar hollow waveguide by a factor (2u ₁ / πm) ³ , where u ₁ is the limit value of the eigenvalue of the eigenmode of the cylindrical waveguide . The calculated transmission spectrum of a hollow waveguide having the form of a cylinder with an inner diameter of t = 10 μm and an external diameter of 11 μm for n ₁ = 1 and L = 2 cm is represented by a dashed line in Fig. 3.

Thus, the sensor device combines two functions: (i) detection of thin layers of molecules (including biological) and atoms deposited on the walls of a hollow waveguide; (ii) detecting small changes in the refractive index of the analyte filling the hollow core.

The principle of operation of the sensor of the first type is illustrated in figures 1, 4. The formation of a layer of biomolecules on the surface of the annular sheath of a hollow fiber as a result of biochemical processes in a solution of analyte filling the air holes of the waveguide (see figure 1) leads to a shift of the minimum in the transmission spectrum of the waveguide (figure 5). When developing sensors for layers of biomolecules containing DNA, it must be taken into account that direct immobilization of DNA molecules on the surface of fused silica is impossible due to the fact that the surface of the quartz carries a negative charge, and DNA molecules contain negatively charged phosphate groups. Poly-L-lysine is often used to immobilize DNA molecules (L. Rindorf, J. B. Jensen, M. Dufva, LH Pedersen, P. E. Høiby, and O. Bang, Opt. Express 14, 8224 (2006)) , which contains positively charged amino groups that contribute to the formation of a molecular monolayer on the negatively infected surface of quartz. The formation of such a layer allows immobilizing DNA molecules on the surface of the quartz shell of the waveguide (Fig. 1) with the formation of a layer with a thickness of the order of 10 nm with a refractive index (1.45-1.48) close to the refractive index of quartz. The formation of such a layer in a solution introduced into the air holes of the waveguide structure can be detected by the spectral shift of the transmission bands of a hollow waveguide with an annular sheath (Fig. 4).

The key parameter determining the sensitivity of a biochemical sensor based on recording the minimum shift in the transmission spectrum of a hollow fiber with an antiresonant sheath is factor F, given by expression (10). In its physical sense, this factor determines the sharpness of the interference pattern of Newtonian bands formed by the Fabry-Perot modes of the annular waveguide sheath. For the eigenmodes of a hollow cylindrical waveguide corresponding to the regime of sliding incidence at the interface between the core and the cladding, θ ₁ << 1, h << β, the factor F is calculated according to formula (12). As follows from this expression, for a large t / λ ratio, dips in the transmission spectrum of a hollow waveguide are characterized by the presence of narrow dips corresponding to resonant excitation of the Fabry-Perot modes in the annular shell of the waveguide. In this mode, it is possible to register ultrathin layers formed on the shell of the waveguide as a result of biochemical processes.

(фиг.1) с показателем преломления, близким к показателю преломления оболочки. При этом можно считать, что толщина оболочки полого волновода увеличилась на

. В окрестности резонанса (13) с модами Фабри-Перо кольцевой оболочки, обеспечивающего минимум пропускания волновода, имеем δ/2=πl+ξ/2, где

- малый параметр, так что sin²(δ/2)≈ξ²/4. Минимальный сдвиг минимума в спектре пропускания волновода, который еще может быть зарегистрирован, определим равным спектральной ширине δλ минимума пропускания, которая может быть найдена в приближенном виде из соотношения Fsin²(δ/2)≈Fξ²/4=1.Suppose that as a result of DNA immobilization on a monolayer of poly-L-lysine, a layer is formed on both surfaces of the waveguide sheath

(figure 1) with a refractive index close to the refractive index of the shell. In this case, it can be assumed that the sheath thickness of the hollow waveguide increased by

. In the vicinity of resonance (13) with the Fabry-Perot modes of the annular shell, which ensures the minimum transmission of the waveguide, we have δ / 2 = πl + ξ / 2, where

- a small parameter, so that the sin ² (δ / 2) ≈ξ ^2/4. Minimum minimum shift in the transmission spectrum of the waveguide, which can still be registered, define equal spectral width δλ transmission minimum, which can be found in the approximate form of the ratio Fsin ² (δ / 2) ≈Fξ ^2/4 = 1.

. Для полого волновода, заполненного аналитом с показателем преломления n₁≈1.33 и имеющим оболочку с показателем преломления n₂≈1.46 (фиг.1), минимальная регистрируемая толщина слоя иммобилизуемых биомолекул составляет

. При λ=0.5 мкм, t=100 мкм имеем

нм.Thus, we arrive at the following relation for the minimum detectable thickness of a layer of biomolecules formed on the surface of a waveguide sheath:

. For a hollow waveguide filled with analyte with a refractive index of n ₁ ≈1.33 and having a shell with a refractive index of n ₂ ≈1.46 (Fig. 1), the minimum recorded thickness of the layer of immobilized biomolecules is

. For λ = 0.5 μm, t = 100 μm, we have

nm

нм на обеих поверхностях оболочки световода приводит к сдвигу минимума пропускания световода на

нм (фиг.5).For a waveguide with n ₁ ≈1.33, n ₂ ≈1.46 and an undisturbed cladding thickness d = 400 nm, a transmission minimum corresponding to l = 1 is observed at a wavelength of λ ₁ ≈ 480 nm (curves 1 and 3 in Fig. 4). The formation of a layer of immobilized DNA molecules with a thickness

nm on both surfaces of the fiber sheath leads to a shift in the minimum transmittance of the fiber by

nm (figure 5).

. Для малого изменения показателя преломления аналита в окрестности резонанса (13) с модами Фабри-Перо кольцевой оболочки, обеспечивающего минимум пропускания волновода, имеем δ/2=πl+ζ/2, где

- малый параметр, так что sin²(δ/2)≈ζ²/4. Минимальное изменение показателя преломления, которые могут быть зарегистрированы с помощью такого сенсора, определяется параметром F и находится из уравнения Fsin²(δ/2)≈Fζ²/4=1. Решение этого уравнения с учетом выражения (12) приводит к следующему результату: |δn|≈λ²(2πn₁dt)^-1. Для n₁=1.33, λ=0.5 мкм, d=0.4 мкм, t=100 мкм имеем |δn|≈7·10^-4. Важно отметить, что, в отличие от многих интегральных антирезонансных волноводных сенсоров (F.Prieto, L.M.Lechuga, A.Calle, A.Llobera, and С.Dominguez, J. Lightwave Technol. 19, 75 (2001)), рассматриваемый тип сенсора не требует для измерений внешнего интерферометра, т.к. интерферометр Фабри-Перо по сути встроен в оболочку волновода, являющегося основой сенсорного устройства.The waveguide sensor of the second type is designed to detect small changes in the refractive index of the analyte filling the air holes of the waveguide structure. Changing the refractive index of the analyte by a small value of δn leads to a shift in the minimum in the transmission spectrum of a hollow waveguide with an annular sheath (Fig. 5). The magnitude of this shift Δλ can be found by differentiating expression (13) with respect to n ₁ . This operation produces the following result:

. For a small change in the refractive index of the analyte in the vicinity of resonance (13) with the Fabry-Perot modes of the annular shell, which ensures the minimum transmission of the waveguide, we have δ / 2 = πl + ζ / 2, where

- a small parameter, so that the sin ² (δ / 2) ≈ζ ^2/4. The minimum refractive index change that can be detected by such a sensor, the parameter F is determined and stored from the equation Fsin ² (δ / 2) ≈Fζ ^2/4 = 1. The solution of this equation taking into account expression (12) leads to the following result: | δn | ≈λ ² (2πn ₁ dt) ^-1 . For n ₁ = 1.33, λ = 0.5 μm, d = 0.4 μm, t = 100 μm, we have | δn | ≈7 · 10 ^-4 . It is important to note that, unlike many integrated antiresonant waveguide sensors (F. Prieto, LMLechuga, A. Calle, A. Llobera, and C. Dominguez, J. Lightwave Technol. 19, 75 (2001)), the considered type of sensor is not requires an external interferometer for measurements, as The Fabry-Perot interferometer is essentially integrated into the shell of the waveguide, which is the basis of the sensor device.

Figure 6 (a) shows a representative image of a hollow waveguide with an MS cladding. For waveguides of this class, the most important part is played by the part of the sheath closest to the core, which has the shape of a ring with a thickness of 1-2 microns. The solid line in Fig. 6 (b) shows the characteristic transmission spectrum measured for such a waveguide structure. A distinctive feature of the presented transmission spectrum is the presence of a sequence of pronounced maxima and minima, the position of which is described with high accuracy in the framework of the above model of a hollow fiber with an annular cladding (dashed line in Fig. 6 (b)). The sequence of maxima and minima in the transmission spectrum of the waveguide of the type in question corresponds to the Newtonian series of colors of a thin film, the role of which in the waveguide structure is played by the glass ring bounding the core (Fig. 6 (a)). Fig. 7 shows a structure that integrates hollow waveguides of various diameters and thereby allows parallel detection of various biochemical processes in a solution on a single chip platform.

Claims (5)

1. A sensor device based on hollow optical fibers, containing a light source, an optical hollow fiber, an antiresonance interferometric system directly integrated into the sheath of the fiber, a recording system that measures the change in the propagation conditions of the light in the fiber with a test analyte, characterized in that the antiresonant interferometric system made so that when the light propagates in the system, it forms narrow lines in the transmission spectrum of the fiber, formed by resonant multipath interference in the interaction of the guided modes of a hollow core and a glass cladding, the registration system is configured to detect a change in the position of narrow lines in the spectrum of the optical fiber transmission defined antiresonant interferometer system. 2. The sensor device according to claim 1, characterized in that the antiresonant interferometric system is a Fabry-Perot interferometer formed by the inner boundary of the hollow fiber layer, a glass sheath of finite dimensions comparable to the wavelength of light, the outer boundary of the glass sheath. 3. The sensor device according to claim 2, characterized in that the sensor device has planar geometry. 4. The sensor device according to claim 2, characterized in that the sensor device has a cylindrical geometry. 5. The sensor device according to claim 1, characterized in that it contains at least two optical hollow fibers.

Images