WO2001040757A2 - Cavites optiques resonnantes destinees a des biodetecteurs a grande sensibilite et a haut rendement et procedes utilisant ces biodetecteurs - Google Patents

Cavites optiques resonnantes destinees a des biodetecteurs a grande sensibilite et a haut rendement et procedes utilisant ces biodetecteurs Download PDF

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WO2001040757A2
WO2001040757A2 PCT/US2000/041138 US0041138W WO0140757A2 WO 2001040757 A2 WO2001040757 A2 WO 2001040757A2 US 0041138 W US0041138 W US 0041138W WO 0140757 A2 WO0140757 A2 WO 0140757A2
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resonant optical
optical cavity
cavity
biosensor
cylindrical
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PCT/US2000/041138
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English (en)
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WO2001040757A3 (fr
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Steven M. Blair
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University Of Utah Research Foundation
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Priority to JP2001542173A priority Critical patent/JP2003515737A/ja
Priority to CA002384977A priority patent/CA2384977A1/fr
Priority to AU45032/01A priority patent/AU4503201A/en
Priority to EP00992472A priority patent/EP1221051A4/fr
Priority to US10/089,497 priority patent/US7384797B1/en
Publication of WO2001040757A2 publication Critical patent/WO2001040757A2/fr
Publication of WO2001040757A3 publication Critical patent/WO2001040757A3/fr

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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
    • G01N21/62—Systems in which the material investigated is excited whereby it emits light or causes a change in wavelength of the incident light
    • G01N21/63—Systems in which the material investigated is excited whereby it emits light or causes a change in wavelength of the incident light optically excited
    • G01N21/64—Fluorescence; Phosphorescence
    • G01N21/6428—Measuring fluorescence of fluorescent products of reactions or of fluorochrome labelled reactive substances, e.g. measuring quenching effects, using measuring "optrodes"
    • B—PERFORMING OPERATIONS; TRANSPORTING
    • B82—NANOTECHNOLOGY
    • B82Y—SPECIFIC USES OR APPLICATIONS OF NANOSTRUCTURES; MEASUREMENT OR ANALYSIS OF NANOSTRUCTURES; MANUFACTURE OR TREATMENT OF NANOSTRUCTURES
    • B82Y30/00—Nanotechnology for materials or surface science, e.g. nanocomposites
    • 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
    • G01N21/62—Systems in which the material investigated is excited whereby it emits light or causes a change in wavelength of the incident light
    • G01N21/63—Systems in which the material investigated is excited whereby it emits light or causes a change in wavelength of the incident light optically excited
    • G01N21/64—Fluorescence; Phosphorescence
    • G01N21/645—Specially adapted constructive features of fluorimeters
    • G01N21/6452—Individual samples arranged in a regular 2D-array, e.g. multiwell plates
    • 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
    • G01N21/62—Systems in which the material investigated is excited whereby it emits light or causes a change in wavelength of the incident light
    • G01N21/63—Systems in which the material investigated is excited whereby it emits light or causes a change in wavelength of the incident light optically excited
    • G01N21/64—Fluorescence; Phosphorescence
    • G01N21/645—Specially adapted constructive features of fluorimeters
    • G01N21/648—Specially adapted constructive features of fluorimeters using evanescent coupling or surface plasmon coupling for the excitation of fluorescence
    • 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
    • G01N21/75—Systems in which material is subjected to a chemical reaction, the progress or the result of the reaction being investigated
    • G01N21/77—Systems in which material is subjected to a chemical reaction, the progress or the result of the reaction being investigated by observing the effect on a chemical indicator
    • G01N21/7703—Systems in which material is subjected to a chemical reaction, the progress or the result of the reaction being investigated by observing the effect on a chemical indicator using reagent-clad optical fibres or optical waveguides
    • G01N21/7746—Systems in which material is subjected to a chemical reaction, the progress or the result of the reaction being investigated by observing the effect on a chemical indicator using reagent-clad optical fibres or optical waveguides the waveguide coupled to a cavity resonator

Definitions

  • the present invention relates generally to optical biosensors and, particularly, to high throughput optical biosensors More particularly, the optical biosensors of the present invention include structures that facilitate the use of whispering gallery modes for enhancing the sensitivity of the optical biosensors.
  • the present invention also relates to methods for fabricating the optical biosensors, as well as to diagnostic methods that employ the optical biosensors.
  • Optical waveguides are often used in low sample concentration, high throughput immunoassays (IA) and molecular diagnostic assays (MDx).
  • IA immunoassays
  • MDx molecular diagnostic assays
  • the waveguide is illuminated with one or more wavelengths of electromagnetic radiation (e.g., light) to facilitate a determination of presence, absence, or amount of one or more particular analytes of interest in a sample.
  • electromagnetic radiation e.g., light
  • Numerous optical techniques have been developed to employ the evanescent wave from optical waveguides in biosensing applications.
  • optical waveguides for high-throughput sensing can be achieved using either mass (Silzel et al., 1998) or fluorescence (Stimpson et al., 1995; Wadkins et al., 1998; Plowman et al., 1999) sensing techniques. Both of these sensing techniques have been demonstrated as useful in waveguides for conducting immunoassays (Silzel et al., 1998; Wadkins et al., 1998; Plowman et al., 1999) and genetic screenings (Stimpson et al., 1995).
  • the presence of a captured analyte may be detected or measured by, first, measuring a baseline absorption or refractive index of a capture molecule on or adjacent a surface of the waveguide prior to exposing the capture molecule to a sample and, second, following exposure of the capture molecule to a sample, determining the difference in absorption or refractive index of the capture molecule and any analyte bound, or hybridized, thereto.
  • the measured signal changes upon hybridization of capture molecules with analytes in the sample.
  • the signal change is in proportion to the mass that lies within the evanescent field of the waveguide.
  • Waveguide mass sensing techniques typically rely on surface plasmon resonance (SPR) 5, which has been used extensively in optical biosensing (Liedberg et al., 1987).
  • SPR surface plasmon resonance
  • a surface plasmon can exist at the interface between two media, one of which has a negative dielectric constant (Peyghambarian et al., 1993), such as a metal, and can be resonantly excited using a ruled optical grating or prism to obtain phase matching.
  • the index perturbation of the analyte disturbs this resonance, with greater perturbation provided with larger molecular weight.
  • Affinity sensitivities can be in the nM range (Morgan and Taylor, 1992) for large analyte molecular weight, and 50 ⁇ M (Karlsson and Stahlberg, 1995) for small analyte molecular weight, and a sensitivity per unit area of 20 fM/mm 2 was measured using resonant mirrors (Watts et al., 1995). Nanoparticles coated with the analyte have also been used to increase mass, leading to a sensitivity of 0.1 pM (Kubitschko et al., 1997).
  • waveguide mass sensors are based on light scatter (Stimpson et al., 1995), interferometry (Schneider et al., 1997), and waveguide absorption spectroscopy (Mendes and Saavedra, 1999).
  • electromagnetic radiation may be used to create an evanescent wave within an optical waveguide that excites a fluorescent dye, which is also referred to as a fluorophore tag, or a similar tag bound, for example, to a molecule that competes with an analyte of interest for a binding site on a capture molecule immobilized on or adjacent to a surface of the waveguide.
  • the fluorophore tag gives off emitted electromagnetic radiation, the intensity of which is indicative of the presence, absence, or amount of the analyte in the sample.
  • the sensitivity depends on affinity strength between each analyte and its corresponding capture molecule, as well as upon the absorption coefficient and fluorescence quantum yield of the fluorophore tag. Fluorescence sensing techniques are generally more sensitive and more specific than mass sensing techniques.
  • the waveguide may include independent sensing zones on or adjacent to which different types of capture molecules are immobilized. All of the discrete sensing zones of a segmented waveguide can be interrogated in parallel by use of a charge-coupled device (“CCD") array, which can capture the full time dynamics of the affinity interaction.
  • CCD charge-coupled device
  • the array size is limited by the patterning of immobilized capture molecules (Silzel et al., 1998) and the sensitivity is limited by the number of captured analytes per sensitivity zone and by the sensing technique employed. Nonetheless, with new patterning techniques, the densities of sensing zones of optical waveguides are continuing to increase (Morgan et al., 1995; Stimpson et al., 1998).
  • the sizes of the sensing zones of segmented waveguides are ever-decreasing.
  • the decrease in sizes of the sensing zones of segmented waveguides are proportional reductions in the sensitivities with which analytes can be detected by the waveguide. Accordingly, the system requirements of segmented waveguides are becoming ever more stringent.
  • the use of a segmented waveguide is somewhat undesirable since the excitation radiation is not confined within the plane of the waveguide.
  • the electomagnetic radiation emitted from one sensing zone may interfere with the electromagnetic radiation emitted from one or more adjacent sensing zones, thereby reducing the optical efficiency of a segmented waveguide and, thus, the degree of confidence with which each analyte may be detected when the segmented waveguide is used.
  • the area of each sensing zone to which capture molecules are secured or to which a sample is introduced may be limited to less than 25% of the total area of the sensing zone. As a result, segmented waveguides are relatively insensitive.
  • Biochips which may be fabricated using self-assembled monolayer or similar patterning techniques, may have very large arrays of sensing zones (e.g., up to 100,000 or more sensing zones).
  • a sample is applied to a biochip, one or more analytes of interest in the sample bind capture molecules on the biochip, and the presence, absence, or amount of each analyte or the hybridization characteristics of the capture substrate with a corresponding analyte is detected in much the same manner as that which is used when segmented waveguides are employed to detect analytes.
  • fiber optic probes, scanning near-field microscopes, or confocal microscopes may be used to direct one or more wavelengths of electromagnetic radiation into each sensing zone of a biochip to excite fluorescent dyes within the sensing zone.
  • the fiber optic probe or confocal microscope may then be used to detect the electromagnetic radiation emitted from fluorescent labels within each sensing zone.
  • the biochip may be raster-scanned, one sensing zone at a time. The sensing zones of a biochip can be closely spaced since the probe itself provides lateral optical confinement, which leads to the possibility of biochips with very high sensing zone densities.
  • microspheres effecting different chemical reactions on the surfaces of microspheres (Micheal et al., 1998).
  • the microspheres are deposited into individual wells etched into the distal end of an imaging fiber bundle. Cavity effects of the wells are masked by incoherent illumination, but the use of a CCD to sense reactions on the surfaces of the microspheres may be used in parallel with the imaging fiber bundle.
  • Flat, or planar, cylindrical microcavities have been used in low-threshold lasers
  • cylindrical microcavities have been fabricated from a variety of materials, including semiconductor materials (e.g., silicon) and glass. Studies have shown that planar cylindrical microcavities with cavity diameters of 10.5 ⁇ m may have free spectral ranges (FSRs) of greater than 35 nm and cavity Q values of greater than 8000.
  • FSRs free spectral ranges
  • biosensors that include resonant optical cavities that facilitate the use of whispering gallery modes to provide enhanced sensitivity and that have quality factors of at least about 10 4 .
  • WGMs Whispering gallery modes
  • MDRs morphology-dependent resonances
  • QNMs quasi-normal modes
  • WGMs Whispering gallery modes
  • MDRs morphology-dependent resonances
  • QNMs quasi-normal modes
  • WGMs Whispering gallery modes
  • electromagnetic radiation e.g., light
  • two-dimensional whispering gallery modes are said to occur. If the electromagnetic radiation is reflected within an optical cavity in such a manner that the electromagnetic radiation is not restricted to a single plane, three- dimensional whispering gallery modes are said to occur.
  • the present invention includes biosensors that include resonant optical cavities that generate and exploit whispering gallery modes, as well as methods of using the biosensors.
  • Biosensors including resonant optical cavities incorporating teachings of the present invention are configured for rapid, high throughput diagnostic assays, as well as in any application where conventional optical biosensors have been employed.
  • the resonant optical cavity is a microfabricated structure that includes a flat, or planar, cylinder fabricated upon a substantially planar substrate.
  • the cylinder of the biosensor is referred to herein as a cylindrical optical cavity or simply as a cylindrical cavity.
  • the exposed surface of the cylindrical cavity which is located opposite the substrate, is substantially planar and substantially free of surface defects.
  • a peripheral edge of the cylindrical cavity tangentially abuts at least one electromagnetic radiation transmission port, such as a strip waveguide which, in turn, communicates with a source of electromagnetic radiation, such as a laser.
  • Capture substrates having a known specificity for one or more particular analytes are immobilized on at least a portion of the exposed surface of the cylindrical cavity.
  • a sample including the analyte or analytes for which the capture substrates are specific is introduced onto the exposed surface of the cylindrical cavity, at least some of the analyte or analytes in the sample bind to, or hybridize with, capture substrates.
  • electromagnetic radiation travels through the transmission port into the cylindrical cavity to facilitate sensing of the binding of analyte in the sample to the capture substrate on the exposed surface of the cylindrical cavity.
  • resonant optical cavity includes a bulk cylindrical substrate, such as an optical fiber, with a cylindrical resonant optical cavity formed at an end thereof.
  • the bulk cylindrical cavity may be tangentially abutted by at least one electromagnetic transmission port, such as a strip waveguide, which, in turn, communicates with a source of electromagnetic radiation.
  • Capture substrates that are disposed on an exposed surface of the cylindrical cavity bind analyte, if present in a sample. Such binding may be detected by introduction of electromagnetic radiation into the cylindrical cavity via the source and transmission port.
  • cylindrical optical cavities incorporating teachings of the present invention facilitate the generation of whispering gallery modes.
  • electromagnetic excitation radiation is preferably introduced into a cylindrical cavity through a peripheral edge of the cavity, facilitating the generation of two-dimensional whispering gallery modes within the cylindrical cavity at a substantially planar surface thereof.
  • Whispering gallery modes prolong the exposure of molecules and molecule hybrids on the exposed surface of a cylindrical cavity to electromagnetic excitation radiation.
  • the cylindrical cavities of the biosensors of the present invention also have very high (e.g., about 10 4 and greater) quality factors (Q).
  • An optical cavity with a high quality factor typically represents that the intrinsic material absorption of the optical cavity is low, that the contrast between the refractive index of the cavity core and the refractive index of material within the plane of and surrounding the optical cavity is high, and that the cavity diameter, which reduces diffraction losses, is relatively large.
  • the quality factor of an optical cavity is also higher when scattering caused by roughness on the exposed surface of an optical cavity is relatively low and when the coupling strength between the optical cavity and the adjacent transmission port (e.g., a strip waveguide) is relatively high.
  • the quality factor of an optical cavity depends upon the particular whispering gallery mode of the cavity.
  • cylindrical cavities that are useful in biosensors incorporating teachings of the present invention have sensitivities that are at least about an order of magnitude greater than the sensitivities of state of the art waveguides.
  • Biosensors including resonant optical cavities of other configurations that generate sufficient WGMs to provide very high quality factors and increased sensitivities over that of state of the art waveguides, such as spherical optical cavities, are also within the scope of the present invention.
  • Biosensors that incorporate teachings of the present invention are useful in various applications, including, without limitation, clinical diagnostics, environmental and food testing, genomic research, and genetic screening, as well as in other applications where waveguides, biochips, and other assay tools may be employed.
  • the present invention also includes methods for fabricating resonant optical cavities incorporating teachings of the invention, as well as methods for using biosensors including the resonant optical cavities.
  • FIG. 1 is a schematic representation of an embodiment of biosensor of the present invention, including a microfabricated cylindrical resonant optical cavity;
  • FIGs. 1 A- IF schematically depict a method for microfabricating the resonant optical cavity shown in FIG. 1 ;
  • FIGs. 2A and 2B are schematic representations illustrating exemplary manners in which transmission ports may supply electromagnetic radiation to each of the resonant optical cavities of FIG. 1 included in an array of resonant optical cavities;
  • FIG. 3 is a schematic representation of another embodiment of biosensor of the present invention, including a bulk cylindrical resonant optical cavity;
  • FIG. 3A schematically illustrates a method for fabricating the resonant optical cavity shown in FIG. 3;
  • FIG. 3B schematically illustrates the inclusion of a plurality of different sensing zones on a surface of the resonant optical cavity shown in FIG. 3;
  • FIG. 4 is a schematic representation of a spherical resonant optical cavity incorporating teachings of the present invention.
  • FIG. 5 depicts the use of a reflection port with the biosensor shown in FIG. 1 to facilitate the use of mass sensing techniques.
  • Resonant optical cavities incorporating teachings of the present invention are designed to take advantage of two-dimensional whispering gallery modes (WGMs) which possess quality factors (Q) that exceed the quality factors of conventional waveguides.
  • the Q of an optical cavity typically increases with a decrease in the intrinsic absorption of electomagnetic radiation by the material of the optical cavity, an increase in the contrast between the refractive index of the optical cavity and that of the surrounding index that lies in the plane of the optical cavity (which leads to stronger guidance), and an increase in the diameter of the optical cavity (which reduces diffraction losses).
  • the Q of an optical cavity also increases with reduction of surface roughness scattering due to etching of the cavity boundary and reduction of the coupling strength with the adjacent strip waveguide and strongly depends on the particular whispering gallery mode of the optical cavity.
  • the resonant optical cavities of the present invention are designed to have quality factors of at least about 10 4 and as high as about 10 9 or greater. Such high quality factors generally increase the length of time that a photon (i.e., electromagnetic radiation) remains with the optical cavity, which, in turn leads to an increased intensity of electromagnetic radiation within the optical cavity, as well as to an increase in the rate at which electromagnetic radiation is spontaneously emitted from the cavity.
  • resonant optical cavities according to the invention may be designed such that high-Q resonance occurs at the peaks of both the wavelengths of electromagnetic excitation radiation that excite, or are absorbed by, fluorescent tags and the fluorescence, or emitted wavelengths, of electromagnetic radiation given off by the fluorescent tags.
  • the free-spectral range (FSR) of an optical cavity is the frequency separation between adjacent longitudinal modes. Enhancement of fluorescent yield occurs when the free-spectral range of the cavity exceeds the linewidth of electromagnetic radiation emitted from the fluorescent tags.
  • the free-spectral range of an optical cavity is determined by the cavity size and refractive index. Fluorescent yield may be optimized through designing the optical cavity to have a particular free-spectral range and Q and by selecting fluorescent tags with a desirable fluorescence linewidth, which is ideally narrow and matched to the resonance linewidth of electromagnetic excitation radiation within the optical cavity.
  • solvent e.g., the aqueous solution of a sample
  • solvation dynamics may counteract this effect through dynamic spectral narrowing, through spectral diffusion, of the electromagnetic emitted radiation, which may enhance fluorescence yield and cause the linewidth of the fluorescent, emitted radiation to more closely match the linewidth of the excitation radiation.
  • the Q of a particular radial mode, or path of electromagnetic radiation through pattern of motion through the cylindrical cavity depends upon the closeness of the radial mode to the peripheral edge of the cylindrical cavity, or the radial mode number.
  • Lower numbered, or order, radial nodes are predominantly confined near the peripheral edge of the cylindrical cavity and have higher Qs.
  • the paths of higher order radial modes extend more centrally within the cylindrical cavity and, while these radial modes have lower Qs, they provide for a greater sensing area on a surface of the cylindrical cavity.
  • Various factors affect the radial modes of electromagnetic radiation through a cylindrical cavity, including, but not limited to, the characteristics of the cylindrical cavity, characteristics of a transmission port coupled to the cylindrical cavity, such as the width and effective refractive index of the transmission port, the size of the gap or space between the transmission port and the cylindrical cavity, and the spectral bandwidth of a source of electromagnetic radiation communicating with the cylindrical cavity through the transmission port.
  • the various radial modes of electromagnetic radiation through a cylindrical cavity can be controlled by controlling the characteristics and manner in which an electromagnetic radiation transmission port is associated with the cylindrical cavity, the characteristics of the cylindrical cavity, and the characteristics of the source of electromagnetic radiation.
  • the sensitivity of the cylindrical cavity may be maximized by determining the optimal distribution of, or balance between, modes with high Qs and modes that cover a large surface area along a planar surface of the cylindrical cavity. Such an optimal distribution may be determined, for example, through analytical results and finite-difference time-domain (FDTD) simulations.
  • FDTD finite-difference time-domain
  • capture substrates immobilized relative to a planar surface of the cylindrical cavity and any adhesion facilitator necessary to immobilize the capture substrate may also have an effect on the initial Q (i.e., Q prior to the binding of analyte by the capture substrate) of the cylindrical cavity.
  • the effects of the capture substrate and adhesion facilitator on the Q of a cylindrical cavity may be caused by the capture substrate and adhesion facilitator having a lower refractive index than that of the cylindrical cavity (e.g., a capture substrate monolayer of neutravidin coupled to a biotin-T3 oligonucleotide has a fixed refractive index of about 1.33, while a silicon oxynitride optical cavity has a refractive index of about 1.5 to about 2.2).
  • the loss of radiation may lower Q and alter the positions of resonances with the optical cavity.
  • the loss of radiation from the optical cavity may cause a greater portion of each radial mode with the optical cavity to be involved in the sensing process, effectively increasing the sensitivity of the optical cavity.
  • a cylindrical cavity of the present invention may be designed so as to account for these effects of radiation loss, which may be evaluated by way of known processes, such as numerical simulation with experimental feedback.
  • the loss of radiation may then be appropriately controlled by regulating the thickness of the optical cavity and the refractive indices of the optical cavity and an underlying contrasting layer.
  • biosensor 10 includes a resonant optical assay structure 12, at least one transmission port 14 in communication with resonant optical assay structure 12, and a source 16 of electromagnetic radiation 18 in communication with transmission port 14.
  • Resonant optical assay structure 12 may include a substrate 22 of glass, quartz, silicon, or another semiconductive material (e.g., gallium arsenide or indium phosphide), a contrasting layer 24 over substrate 22, and a flat, cylindrical resonant optical cavity, which is also referred to herein as a cylindrical cavity 26, positioned over contrasting layer 24.
  • Contrasting layer 24 is preferably formed from a material that has a refractive index that contrasts the refractive index of the material that forms cylindrical cavity 26. Cylindrical cavity 26 may be laterally surrounded by a material layer 25.
  • the contrast between the refractive indices of cylindrical cavity 26 and contrasting layer 24 be greater than about 1 : 1 (i.e., that cylindrical cavity have a refractive index that exceeds the refractive index of contrasting layer 24) and is preferably at least about 1.5: 1.
  • silica i.e., doped SiO 2 , such as borosilicate glass, phosphosilicate glass, or borophosphosilicate glass
  • silicon oxynitride SiO x N y or SiON
  • SiON unlike most popular semiconductor compatible media, has very low loss (0.2 dB/cm or lower, including material and scattering losses) in the visible spectrum of electromagnetic radiation. This gives tremendous flexibility in the choice of optical wavelengths that can be utilized when cylindrical cavity 26 is formed from SiON.
  • the diameter of cylindrical cavity 26 preferably imparts cylindrical cavity with the desired quality factor.
  • Small cylindrical cavity 26 diameters facilitate the fabrication of large, dense sensor arrays.
  • Exemplary cylindrical cavities 26 incorporating teachings of the present invention have diameters of about 10 ⁇ m to about 50 ⁇ m, which facilitates the fabrication of sensor arrays having densities of up to about 500 * 500 cylindrical cavities 26 per square centimeter (cm 2 ).
  • Capture substrates 34 including, but not limited to, antibodies, antigens, other polypeptides, nucleotides (RNA or DNA), and cells, that are specific for one or more analytes of interest may be immobilized on or adjacent to surface 28 of each cylindrical cavity 26.
  • substrate 22 may be provided as a full or partial wafer of semiconductive material (e.g., silicon, gallium arsenide, or indium phosphide), or as a silicon-on-insulator (SOI) type substrate (e.g., silicon on glass (SOG), silicon on sapphire (SOS), or silicon on ceramic (SOC)).
  • SOI silicon-on-insulator
  • contrasting layer 24 of a desired material may be formed on substrate 22 by known processes.
  • SiO 2 of a desired depth may be formed on an active surface 23 of substrate 22 by use of known oxidation processes (e.g., thermally, by exposing active surface 23 to oxidants, etc.).
  • the SiO 2 of contrasting layer 24 may be deposited onto active surface 23 by known processes, such as by chemical vapor deposition (CVD).
  • a material layer 25 from which cylindrical cavity 26 will subsequently be formed may be disposed over contrasting layer 24 by known processes.
  • a layer 25 of silica, or glass may be formed over contrasting layer 24 by known processes, such as by use of known CVD or spin-on glass (SOG) techniques.
  • a layer 25 of SiON may be fabricated, for example, by known CVD processes.
  • Layer 25 may also be patterned by known processes.
  • a photomask 29 covering the regions of the underlying layer 25 to be patterned which is known as either a positive or a negative photomask, may be formed by disposing a photoresist by way of known photolithography processes, including, without limitation, the use of a reticle or photomask having high resolution (e.g., about 0.5 ⁇ m or smaller), or e-beam lithography, which may be used to facilitate the formation of cylindrical cavities 26 of small dimensions (e.g., about 10 ⁇ m to about 50 ⁇ m in diameter) with high resolution (i.e., minimized radiation scattering).
  • high resolution e.g., about 0.5 ⁇ m or smaller
  • e-beam lithography which may be used to facilitate the formation of cylindrical cavities 26 of small dimensions (e.g., about 10 ⁇ m to about 50 ⁇ m in diameter) with high resolution (i.e., minimized radiation scattering).
  • apertures 30 through photomask 29 may be filled with another mask material 31 , such as a metal or SiO 2 , that will withstand the process that will be used to etch layer 25.
  • Mask material 30 is removed from locations overlying photomask 29 by known techniques, such as wet dip processes or mechanical or chemical-mechanical polishing processes, to form a hard mask 32, as shown in FIG. IE.
  • Photomask 29 is then removed from layer 25, also by known processes, such as by use of resist strippers.
  • peripheral edges 27 of cylindrical cavities 26 be oriented substantially perpendicularly relative to the plane of substrate 22
  • known anisotropic etching techniques such as reactive ion etching (RIE) may be used to remove the material of layer 25 through hard mask 32 to form cylindrical cavities 26 from the material of layer 25.
  • RIE reactive ion etching
  • the material of hard mask 32 may then be removed from above cylindrical cavities 26 by known processes, such as by use of etching processes that are selective over the material from which cylindrical cavities 26 are formed.
  • Transmission port 14 may be fabricated on substrate 22 in the same manner as its corresponding cylindrical cavity 26, either simultaneously with the fabrication of cylindrical cavity 26 or separately therefrom.
  • a separately fabricated transmission port 14 such as a known strip waveguide or optical fiber, may be assembled with resonant optical assay structure 12 so as to abut a peripheral edge 27 of at least one cylindrical cavity 26 formed on substrate 22.
  • transmission port 14 may be coupled to or otherwise communicate with source 16 as known in the art.
  • FIGs. 2A and 2B examples of the manner in which a transmission port 14 may feed excitation electomagnetic radiation to an array 11 of microfabricated cylindrical cavities 26 are illustrated.
  • transmission port 14 may comprise an optical distribution network that feeds each cylindrical cavity 26 of array 11.
  • transmission port 14 includes a single optical bus that feeds each cylindrical cavity 26 in series, making 180° turns at the end of each column of array 11 of cylindrical cavities 26.
  • transmission port 14' may include a separate waveguide 14a, 14b, 14c, etc., to feed electromagnetic excitation radiation into cylindrical cavities 26 of each column or row of array 11.
  • Transmission port 14' is also referred to as a "tree-bus network”.
  • an adhesion facilitator 33 may be applied to a surface 28 of each cylindrical cavity 26 to facilitate the immobilization of one or more capture substrates 34 to surface 28.
  • neutravidin may be adsorbed to surface 28 to facilitate the immobilization of biotinylated nucleic acids (e.g., RNA or DNA, including oligonucleotides) adjacent to surface 28.
  • biotinylated nucleic acids e.g., RNA or DNA, including oligonucleotides
  • Capture substrates 34 including, without limitation, proteins (e.g., antibodies and antigens), peptides, nucleic acids (e.g., DNA and RNA), other biomolecules, and microorganisms such as bacteria and viruses, may be disposed and immobilized on or adjacent to surface 28 of each cylindrical cavity 26 by known processes.
  • proteins e.g., antibodies and antigens
  • peptides e.g., peptides
  • nucleic acids e.g., DNA and RNA
  • microorganisms such as bacteria and viruses
  • any adhesion facilitator 33 thereon, and capture substrates 34 may then be exposed to an appropriate temperature for an appropriate amount of time to immobilize capture substrate 34 relative to surface 28 (i.e., a temperature and duration that will facilitate adsorption of capture substrates 34 to surface 28 or to a adhesion facilitator 33 on surface 28 without degrading capture substrates 34 or adversely affecting the ability of capture substrates 34 to bind to, or hybridize with, an analyte of interest).
  • known epoxysilane chemistries may be useful for immobilizing capture substrates 34, such as nucleotides (i.e., DNA and RNA) and other biomolecules, to surface 28.
  • an atomic layer of gold may be applied to surface 28, a biotinylated thiol adsorbed to the gold, and hydrophobic silane applied laterally around cylindrical cavity 26, or between adjacent cylindrical cavities 26 of an array.
  • the biotinylated thiol which is hydrophilic, facilitates the immobilization of capture substrates 34 relative to surface 28, while the hydrophobic silane prevents capture molecules from adsorbing to features that are laterally adjacent to surface 28, as well as preventing lateral cross- contamination of different types of capture molecules 34, such as those secured to adjacent cylindrical cavities 26.
  • Other heterologous immobilization techniques i.e., techniques that facilitate the application of different types of capture molecules 34 to dense arrays of optical cavities
  • Biosensor 10' includes a resonant optical cavity 12' in the form of a bulk cylindrical cavity 26' formed on an end of a bulk cylindrical substrate 22'. At least one transmission port 14 abuts or is disposed adjacent a peripheral edge 27' of bulk cylindrical cavity 26' so as to communicate with optical cavity 12'. Transmission port 14 also communicates with a source 16 of electromagnetic radiation 18.
  • FIG. 3 A illustrates that a rod 25 ' formed from a suitable material may be diced into several thin disk-shaped segments 25a', 25b', 25c', etc., each of which will eventually comprise a bulk cylindrical cavity 26'.
  • Rod 25' may be either a solid fiber or a hollow, capillary fiber. While rod 25 ' is preferably formed from glass, any other suitable waveguide material may be used. While rod 25 ' may have any diameter, it is preferred that rod 25 ' have a diameter of about 1 mm to about 10 mm and, more preferably, of about 5 mm.
  • Each segment 25a', 25b', 25c', etc. preferably has a height of about 2 mm, although different segment 25a', 25b', 25c', etc. heights are also within the scope of the present invention.
  • a flat surface 28', or end, of each of disk-shaped segments 25a', 25b', 25c', etc., is polished by known techniques.
  • This polished, flat surface 28' is then diffused, or doped, with a suitable material, such as potassium ions (K + ), sodium ions (Na + ), or a combination thereof, using known an ion-exchange waveguide fabrication techniques, to form bulk cylindrical cavity 26' at surface 28'.
  • Surface 28' is preferably diffused with such a material to a depth of a few microns.
  • capture molecules 34 may be immobilized relative to surface 28' in the same manner as that disclosed with respect to the microfabricated embodiment of cylindrical cavity 26 discussed previously herein with reference to FIG. 1.
  • surface 28' may have a much larger area that surface 28 of cylindrical cavity 26, different types of capture molecules 34 (i.e., different analyzing chemistries) may be immobilized relative to different reaction regions 28a', 28b', 28c', etc. of surface 28'.
  • different types of capture molecules 34 i.e., different analyzing chemistries
  • Both biosensor 10 and biosensor 10' may include a sensor 40 associated with each cylindrical cavity 26, 26' thereof.
  • sensor 40 includes a CCD array operatively associated with a processor 50 (e.g., a PENTIUM-class microprocessor manufactured by Intel Corporation of Santa Clara, California).
  • processor 50 e.g., a PENTIUM-class microprocessor manufactured by Intel Corporation of Santa Clara, California.
  • each cylindrical cavity 26 of an array is aligned with at least one corresponding pixel 42 of the CCD array of sensor 40.
  • a conventional CCD array may be used to screen as many as about 10 5 or more cylindrical cavities 26 of an array.
  • each reaction region 28a', 28b', 28c', etc. of surface 28 is aligned with at least one corresponding pixel 42.
  • processor 50 collects data from the one or more corresponding pixels 42 of sensor 40 and, based upon stored information regarding the type of capture substrate 34 immobilized relative to the corresponding surface 28 or reaction region 28a', 28b', 28c', etc., generates and outputs data regarding the presence of one or more analytes in a sample, the quantity of analyte in the sample, or the hybridization kinetics between capture substraet 34 and a corresponding analyte in the sample.
  • sensors may also be employed with biosensors 10, 10' to detect electromagnet radiation emitted from cylindrical cavities 26, 26'.
  • Resonant optical cavity 26" is spherical in shape and includes a suitable substrate (e.g., doped or undoped SiO 2 , SiON, etc.), the surface 28" of which is diffused, or doped, with a suitable material, such as potassium ions (K + ), sodium ions (Na + ), or a combination thereof, using known an ion-exchange waveguide fabrication techniques.
  • a suitable substrate e.g., doped or undoped SiO 2 , SiON, etc.
  • a suitable material such as potassium ions (K + ), sodium ions (Na + ), or a combination thereof, using known an ion-exchange waveguide fabrication techniques.
  • Resonant optical cavity 26" may be substantially completely doped, or only the portions of cavity 26" proximate surface 28" may be doped.
  • a capture substrate 34 may be applied to surface 28" as described previously herein.
  • Resonant optical cavities 26" may be held within a carrier of desired shape and associated with at least one transmission port 14, source 16, and sensor 40 (See, e.g., FIG. 3).
  • any of the embodiments of resonant optical cavities disclosed herein may be reused by stripping capture substrate 34 from surfaces 28, 28', 28", then applying capture substrate of the same or a different type to surfaces 28, 28', 28".
  • biosensors incorporating teachings of the present invention may employ mass sensing techniques, such as in surface-plasmon resonance (SPR) techniques, to determine whether one or more analytes are present in a sample, to quantify the one or more analytes in a sample, or to evaluate the hybridization kinetics between a capture substrate and a corresponding analyte.
  • SPR surface-plasmon resonance
  • the average refractive index of capture substrate and any adhesion faciliator on a surface of a resonant optical cavity according to the present invention is increased as analyte binds, or hybridizes with, the capture substrate.
  • This increase in the refractive index of an optical cavity causes a shift in the resonance of the optical cavity, lowering the Q of the optical cavity at the wavelength of electromagnetic radiation used to detect the presence of analyte, an effect which is referred to as "Q-spoiling".
  • Known processes such as spectroscopic or intensity measurements of electromagnetic radiation attenuated by the capture substrate and any analyte hybridized therewith, may be used to detect such a shift of the resonance of the optical cavity.
  • Mass sensing is particularly useful in applications where it is not desirable to label an analyte or a molecule that competes with the analyte for a binding site on the capture substrate.
  • An alternative and more practical method to detect the presence of the analyte bound to the capture substrate is to position a reflection port 14" (e.g., a strip waveguide) adjacent to a surface of the optical cavity (e.g., cylindrical cavity 26), as shown in phantom in FIG. 5.
  • This reflection port 14" couples light out of cylindrical cavity 26.
  • the change in the ratio of the intensity of electromagnetic radiation exiting cylindrical cavity 26 through reflection port 14" to the intensity of electromagnetic radiation introduced into cylindrical cavity 26 by transmission port 14 may be related to the affinity concentration of the analyte bound by capture substrate 34.
  • biosensors of the present invention need only include resonant optical cavities that resonate at that one wavelength of electromagnetic radiation. Fluorescence Sensing Fluorescence sensing techniques may also be used with biosensors of the present invention to determine the presence of an analyte in a sample, the amount of analyte in a sample, or the hybridization kinetics between a capture substrate and a corresponding analyte in a sample.
  • an analyte molecule or a molecule that competes with the analyte for binding sites on the capture substrate is labeled with a fluorescent tag, which preferably emits electromagnetic radiation of a different wavelength than that which excites the fluorescent tag.
  • the wavelength of electromagnetic excitation radiation should lie within the absorption band, or range of absorbable wavelengths, of the fluorescent tag.
  • the optimal wavelength of electromagnetic radiation for exciting fluorescent tags may lies somewhere in the blue-green to green portion of the spectrum.
  • the resonant optical cavities of these biosensors prolong the lifetimes of photons of the electromagnetic excitation radiation. These long photon lifetime result in an effective sensing length that is much longer than the actual distance across the surface of the cavity, but within a surface area that is considerably smaller than that of a conventional slab waveguide sensor, for which femtomolar (fM) (10 15 M) sensitivity has been achieved.
  • fM femtomolar
  • the high intensity of excitation radiation within a resonant optical cavity of the present invention may induce fluorescent tags to absorb multiple photons of excitation radiation, which may provide the further advantages of substantially background-free and high sensitivity detection of analytes.
  • fluorescence sensing techniques be used with resonant optical cavities according to the present invention that resonate at the wavelength peaks of both the excitation radiation and the radiation emitted from the chosen fluorescent tags.
  • the large buildup of excitation radiation within a resonant optical cavity results in high intracavity intensity of the excitation radiation, which can induce fluorescent tags to emit when two-photons are absorbed.
  • the wavelength of fluorescent, emitted radiation is significantly smaller than the wavelength of absorbed, excitation radiation such that any one-photon scatter from the excitation source, such as surface scatter, Raleigh scatter, inelastic scatter, or any source of one-photon fluorescence, can be completely removed by a high-pass optical filter.
  • any one-photon scatter from the excitation source such as surface scatter, Raleigh scatter, inelastic scatter, or any source of one-photon fluorescence
  • two-photon fluorescence from unbound oligonucleotides is a negligible source of interference.
  • Different fluorescent tags are studied to obtain the highest two-photon cross-section for maximum sensitivity.
  • the wavelength of the source of electromagnetic radiation should be longer than the wavelength peak for one-photon abso ⁇ tion by the fluorescent tag, but shorter than two times the wavelength peak for one-photon absorption. This condition places some constraints on the source and the fluorescent tag. Due to the commercial availability of 980 nm laser diodes with single-mode powers up to about 200 mW, candidate fluorescent tags include fluorescein, which has an abso ⁇ tion peak of 490 nm, and R6G, which has an abso ⁇ tion peak of 530 nm, among many others. The two- photon cross-section of these fluorescent tags is studied in order to maximize interaction with the evanescent wave of the resonant optical cavity.
  • the resonant optical cavity for a two-photon sensing technique is designed such that resonance is obtained at the appropriate wavelength of excitation radiation.
  • Two-photon fluorescence scales as the square of the intensity of excitation radiation, which varies due to the change in position of the fluorescent tag with respect to the evanescent field.
  • Two-photon abso ⁇ tion provides more surface selectivity and noise immunity (i.e., signal to background ratio) than one-photon techniques.
  • the sensitivity and specificity of the two-photon technique are believed to be the highest of the three microcavity mechanisms studied.
  • Biosensors inco ⁇ orating teachings of the present invention and the resonant optical cavities thereof may be used in any application that employs a biomolecular affinity interaction.
  • the biosensors of the invention are useful in a variety of practical applications, including, without limitation, in clinical diagnostics, environmental testing, food testing, genetic screening, and nucleic acid or protein sequencing.
  • Biosensors according to the present invention may, for example, be embodied as immunoassays (IA) or as nucleic acid hybridization assays, which are also referred to as molecular diagnostic assays (MDx).
  • resonant optical cavities inco ⁇ orating teachings of the present invention may be fabricated in arrays that are comparable to the array sizes of current biochip technology, but with much higher sensitivity than that currently available with current biochip technology and the capability for parallel detection of hybridization kinetics, resonant optical cavity arrays of the present invention may also be used in place of biochips.
  • the lifetime of a photon within such an optical cavity is about 3.4 picoseconds (ps) (3.4 x 10 "12 s), which leads to an effective interaction length between the photon and fluorescent tags on molecules immobilized by the capture substrate to a surface of the resonant optical cavity of about 500 ⁇ m, or an effective sensing area of about 500 (dJ2) ⁇ m 2 , where the cavity diameter, in ⁇ m, which may be smaller than 10 ⁇ m.
  • L is the width of an array of these cylindrical resonant optical cavities
  • the number of cavities, or zones, within the device is L 2 /(2d c ) 2 , where the cavity center-to- center spacing is 2d c is small due to the strong lateral confinement provided by the cavities and strip waveguides.
  • the sensing area per zone for a slab waveguide is approximately fd 2 ⁇ m 2 , where f, the sensing zone fill fraction, is equal to 0.25, d is the diameter of the sensing zone, and the number of zones is given by L 2 /(2d) 2 .
  • an array of cylindrical resonant optical cavities of the present invention has a density advantage by a factor of about 1000/c? c over a conventional slab waveguide and, for the same array size, the microcavities have a sensitivity advantage of 1000/ ⁇ f c over the conventional slab waveguide.
  • bulk cylindrical cavities inco ⁇ orating teachings of the present invention can be patterned with multiple monolayers, or analyzing chemistries, bulk cylindrical cavities are believed to have the same desirable properties as microfabricated arrays of cylindrical cavities.
  • bulk cylindrical cavities of the type described previously herein may be designed and fabricated so as to have Qs on the order of about 10 6 to 10 7 .
  • small glass spheres with an ion-exchange waveguide surface may be designed and fabricated in accordance with teachings of the present invention so as to have Qs on the order of about 10 7 or greater.
  • R is the radius of the cylindrical cavity
  • inc is the incident power in the cylindrical cavity.
  • ⁇ consists of contributions from diffraction, scattering, and abso ⁇ tion losses within the optical cavity, abso ⁇ tion, and scattering from the bioselective capture substrate, and abso ⁇ tion by the fluorescent tag.
  • ⁇ is the cavity lifetime in the absence of the analyte and ⁇ , ' is the lifetime at a given analyte affinity concentration, which is different than ⁇ , due to abso ⁇ tion by the fluorophore, then Q « ⁇ , and Q' ⁇ ⁇ , '.
  • the intensity of the emitted, fluorescent radiation is proportional to the quantum efficiency, which is defined as the fraction of absorbed power into the fluorescent tag, and can be written:
  • a slab waveguide region of length L 2 ⁇ R (equal to the cavity circumference)
  • a cylindrical resonant optical cavity of the same circumference has a quantum efficiency that is enhanced by a factor of ⁇ Q/2 ⁇ R, which is the same as predicted by equation (2).
  • a conventional slab waveguide must be relatively long.
  • a bulk cylindrical cavity having about the same area as a slab waveguide will have a quantum efficiency of about 100 times that of the slab waveguide, which leads to a sensitivity advantage by a factor of about 10 (i.e., about one order of magnitude).
  • a factor of about 10 i.e., about one order of magnitude.
  • smaller sample sizes having lower analyte concentrations may be assayed with resonant optical cavities inco ⁇ orating teachings of the present invention.
  • Similar arguments hold for the smaller, microfabricated cylindrical cavities which may have diameters of about 50 ⁇ m or less. Assuming that a microfabricated cylindrical cavity has a Q of about 10 4 , the equivalent length of a slab waveguide would be about 5 mm, which is a practical size. Nonetheless, due to its small size, the microfabricated cylindrical cavity may be included in a dense array of cylindrical cavities. Accordingly, a number of hybridization reactions may be effected simultaneously and detected with at least the same sensitivity of a much larger slab waveguide.
  • the cavity free-spectral range (FSR) and Q of the cylindrical cavities are measured and compared with the results obtained through FDTD simulation.
  • Nucleic Acid Probe Assay After proper device characterization, nucleic acid assay studies are performed. Nucleic acid probes are chosen because they stand to benefit the most from the high throughput capability of the microfabricated array embodiment of biosensor disclosed previously herein.
  • the T3 RNA polymerase promotor site is the model system for nucleic acid hybridization. These synthetics mimic single-stranded oligonucleotides amplified from human DNA using polymerase chain reaction (PCR) and, while T3 has minimal clinical relevance, the T3 hybridization process has been well characterized and serves as an ideal baseline for initial studies, which can be readily extrapolated to assays with clinical relevance.
  • PCR polymerase chain reaction
  • Capture oligonucleotides (T3 for the baseline studies) are immobilized relative to the substantially planar surface of a SiON cylindrical cavity by coating the substantially planar surface with neutravidin using a simple puddle coating technique and immobilizing biotinylated T3 to the neutravidin-coated surface.
  • the capture olignonucleotides are exposed to a solution including a known concentration of the complementary oligonucleotides, referred to as "anti-T3", which hybridize with the capture oligonucleotides.
  • Oligonucleotide primers for the T3 sequence and the complementary anti-T3 sequence are commercially available, and have been fluorescently labeled.
  • the hybridization kinetics are interrogated using the mass, fluorescence, or two- photon abso ⁇ tion sensing techniques described previously herein.
  • the hybridization kinetics of binding between T3 and anti-T3 is probed by the evanescent field of the cylindrical cavity mode, where the excitation radiation is strobed for about 10 to about 15 seconds for detection at periodic time intervals of about 1 minute over the course of about 5 minutes.
  • the rate of hybridization, to within a constant that depends on the properties of the biosensor is determined based on measurements taken with each illumination of the cylindrical cavity.
  • the constant referred to as a "sensor gain factor" has a much larger value for a biosensor including a microfabricated cylindrical cavity than for a conventional slab waveguide and produces the increase in analytical sensitivity of the resonant optical cavity of the present invention.
  • the fluorescence yield of Cy5 is measured versus temperature down to 77° K. As the temperature is lowered, the number of occupied phonon levels is reduced, causing narrowing of the inhomogeneous linewidth.
  • B- phycoerythrin has an emission peak at 575 nm with spectral width of about 20 nm.
  • the broad abso ⁇ tion peak is centered about 546 nm (which can still be accessed efficiently by a doubled Nd: YAG laser at 532 nm), such that the expected enhancement factor is about 2, assuming that double resonance is obtained at 575 nm and 532 nm with FSR 42 nm and that all the fluorescence couples into a cavity mode-it is expected that less than half of the fluorescence will couple into the cavity.
  • the abso ⁇ tion and emission spectra overlap such that fluorescence into the cavity is reabsorbed by the fluorescent tag.
  • This "photon recycling" effect of doubly resonant optical cavities may provide a larger enhancement of the fluorescence yield than that predicted by the enhanced spontaneous emission considerations alone.
  • the analyte is fluorescently labeled with a Cy5 fluorescent tag.
  • the evanescent field of the cavity optical mode induces fluorescence from the fluorescent tag, where the high Q of the cylindrical cavity leads to an effective path length much greater than the circumference of the cylindrical cavity.
  • Picomolar sensitivity is possible using detection of fluorescence emitted upward from the broad area of the cavity cladding (i.e., the capture substrate). Since the area of the substantially planar surface of a microfabricated cylindrical cavity of the present invention is on the order of 0.001 mm 2 or less, the sensitivity per area is significantly larger than for a conventional slab waveguide of comparable sensitivity..
  • Cy5 has a high figure of merit (i.e., abso ⁇ tion coefficient times fluorescence quantum yield), and has peak abso ⁇ tion accessible by inexpensive laser diodes that emit excitation radiation of about 649 nm. The fluorescence peak is in the red at 670 nm.
  • Fluorescence emitted from the top of the device is imaged onto a low-noise photoreceiver.
  • the sensitivity of the receiver is defined as the minimum average received power needed to obtain a signal-to-noise ratio of unity. Received power is a function of the imaging optics, the optical energy stored within the cavity, and the analyte affinity concentration. Again, the sensitivity per unit area is determined and compared with measurements made using a planar slab waveguide. If necessary, additional cavity optimization is performed to increase the sensitivity over the cavity surface area to the pM regime. The response of this sensing mechanism to non-specific binding must also be determined. In this case, the hybridization rate is measured for the non-specific binding as mentioned for mass sensing, and for the additional situation of mismatched bases. These results do not differ from those of a slab waveguide. Again, high throughput with excellent sensitivity is achieved.
  • the reduced array size is used to simplify fabrication and the heterogeneous patterning of capture substrates and to reduce the number of labeled oligonucleotides that are required.
  • initial studies using 4 * 5 cavity arrays are performed with homogeneous monolayer patterning. This means that the complementary, synthetic olignucleotide solution hybridizes at the surface of each cylindrical cavity.
  • the next step is heterogeneous patterning.
  • the model system chosen for these studies, HIV-1 has tremendous clinical relevance. HIV-1 is known to have about 18 sub-types, or genotypes, which can clearly demonstrate the potential of the microcavity array technology.
  • Synthetic, oligonucleotide capture substrates that are complementary to each of these 18 genotypes are patterned, by "stamping", onto the substantially planar surfaces of the cylindrical cavities. Stamping employs an array of micropipettes to deposit capture substrates. The substantially planar surfaces of two of the cylindrical cavities are patterned only with neutravidin. These two cavities serve as references and will indicate nonspecific binding rates.
  • the surfaces of the cylindrical cavities are then exposed to a sample analyte solution that includes a known combination and concentrations of the 18 synthetic oligonucleotides.
  • the fluorescence emissions at the surfaces of each of the cylindrical cavities are measured substantially simultaneously using a CCD array to determine the uniformity in response. If the response is highly nonuniform, the optical distribution network is redesigned.
  • this example illustrates the individual hybridization rates, estimates the viral load, and demonstrates that high sensitivity detection can still be performed in the presence of multiple non-specific binding processes.
  • the FSR between azimuthal modes at a wavelength of excitation radiation of 0.5 ⁇ m is about 13 GHz, while for a Q of 10 6 , the resonance linewidth is 600 MHz.
  • These values are well within the tuning range and long-term frequency stability of commercial tunable laser diodes. Due to the large number of radial modes (many lOOO's) for cylindrical cavity of this size (i.e., a diameter of about 5 mm), individual modes may not be resolvable due to strong overlapping of the resonance linewidths. As both the frequency and azimuthal momentum of a mode must be matched for efficient excitation, the polish of the coupling fiber will determine which modes can be observed.
  • a capture substrate comprising a monoclonal antibody monolayer specific for E. coli O157:H7 will be physically adsorbed onto the substantially planar sensing surface of the bulk cylindrical cavity. This capture substrate monolayer is not expected to significantly disturb the resonances of the cylindrical cavity, but additional measurements will be taken to verify this prediction.
  • the analyte i.e., E. coli O157:H7
  • E. coli O157:H7 is prepared in solution with a concentration of C Compute, where n is the trial number, and will specifically bind with the capture substrate.
  • a fluorophore is introduced using a (Cy5-labeled) monoclonal tracer antibody, which specifically binds to E. coli O157:H7.
  • Cy5 is an indicator dye with an abso ⁇ tion peak at 649 nm, and is commonly used as a fluorescent label.
  • Up to 10 6 tracer antibodies may bind to a bacterium, which is one advantage of immunoassay with multivalent antigens over molecular diagnostic assay, which requires polymerase chain reaction (PCR) to label and amplify a single DNA strand, in that fluorescence detection of a single bound bacterium may be possible. Fluorescence emission from the top of the cavity will be imaged onto a low-noise photodetector, with signal strength proportional to bound analyte concentration and optical excitation power.
  • PCR polymerase chain reaction
  • the parameter of ultimate interest in these studies, and the parameter for which comparisons can be made, is the concentration of the analyte in solution, which is proportional to the concentration of analyte bound by the capture substrate.
  • resonant optical cavities in accordance with the present invention can achieve array sizes comparable with biochips, while maintaining high sensitivity per sensing zone so as to facilitate the detection of low concentrations of analytes. It is believed that the inventive resonant optical cavities have a sensitivity of about 10 times or greater sensitivity than that obtainable with planar slab waveguides having substantially the same surface areas.
  • the resonant optical cavities of the present invention also have the important capabilities of real-time (for hybridization dynamics), parallel (for high throughput) readout capability of waveguide sensors.

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Abstract

L'invention concerne des biodétecteurs comprenant des cavités optiques résonnantes. Ces cavités optiques résonnantes ont une forme qui leur permet de générer des modes de voûtes acoustiques qui augmentent les facteurs qualité des cavités et facilite la détection des substances à analyser d'un échantillon avec une plus grande sensibilité. L'utilisation des cavités optiques résonnantes dans des ensembles de détection haute densité pouvant être lus en temps réel et en parallèle est facilitée par leur taille. Ainsi, les cavités optiques résonnantes sont utiles pour la détection de petites concentrations d'échantillons en temps réel et à haut rendement. L'invention concerne également différents modes de réalisation des biodétecteurs ainsi que des procédés utilisant ces biodétecteurs.
PCT/US2000/041138 1999-10-14 2000-10-12 Cavites optiques resonnantes destinees a des biodetecteurs a grande sensibilite et a haut rendement et procedes utilisant ces biodetecteurs WO2001040757A2 (fr)

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CN110763654A (zh) * 2019-11-29 2020-02-07 江西师范大学 一种倾斜型高品质光学传感器及其制备方法

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CA2384977A1 (fr) 2001-06-07
WO2001040757A3 (fr) 2002-03-14
EP1221051A2 (fr) 2002-07-10

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