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WO2013002193A1 - Puce de capteur pour mesurer les interactions intermoléculaires, qui a été soumise à un traitement inhibant les adsorptions non spécifiques au moyen d'un tensioactif, procédé de production de ladite puce de capteur et procédé de mesure d'interactions intermoléculaires au moyen de ladite puce de capteur - Google Patents

Puce de capteur pour mesurer les interactions intermoléculaires, qui a été soumise à un traitement inhibant les adsorptions non spécifiques au moyen d'un tensioactif, procédé de production de ladite puce de capteur et procédé de mesure d'interactions intermoléculaires au moyen de ladite puce de capteur Download PDF

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WO2013002193A1
WO2013002193A1 PCT/JP2012/066209 JP2012066209W WO2013002193A1 WO 2013002193 A1 WO2013002193 A1 WO 2013002193A1 JP 2012066209 W JP2012066209 W JP 2012066209W WO 2013002193 A1 WO2013002193 A1 WO 2013002193A1
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sensor chip
surfactant
intermolecular interaction
measurement
measuring
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English (en)
Japanese (ja)
Inventor
義一 栗原
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Konica Minolta Advanced Layers Inc
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Konica Minolta Advanced Layers Inc
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    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
    • G01N33/00—Investigating or analysing materials by specific methods not covered by groups G01N1/00 - G01N31/00
    • G01N33/48—Biological material, e.g. blood, urine; Haemocytometers
    • G01N33/50—Chemical analysis of biological material, e.g. blood, urine; Testing involving biospecific ligand binding methods; Immunological testing
    • G01N33/53—Immunoassay; Biospecific binding assay; Materials therefor
    • G01N33/543—Immunoassay; Biospecific binding assay; Materials therefor with an insoluble carrier for immobilising immunochemicals
    • G01N33/54393—Improving reaction conditions or stability, e.g. by coating or irradiation of surface, by reduction of non-specific binding, by promotion of specific binding
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
    • G01N21/00—Investigating or analysing materials by the use of optical means, i.e. using sub-millimetre waves, infrared, visible or ultraviolet light
    • G01N21/17—Systems in which incident light is modified in accordance with the properties of the material investigated
    • G01N21/41—Refractivity; Phase-affecting properties, e.g. optical path length
    • G01N21/45—Refractivity; Phase-affecting properties, e.g. optical path length using interferometric methods; using Schlieren methods
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
    • G01N21/00—Investigating or analysing materials by the use of optical means, i.e. using sub-millimetre waves, infrared, visible or ultraviolet light
    • G01N21/17—Systems in which incident light is modified in accordance with the properties of the material investigated
    • G01N21/55—Specular reflectivity
    • G01N21/552—Attenuated total reflection
    • G01N21/553—Attenuated total reflection and using surface plasmons
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
    • G01N33/00—Investigating or analysing materials by specific methods not covered by groups G01N1/00 - G01N31/00
    • G01N33/48—Biological material, e.g. blood, urine; Haemocytometers
    • G01N33/50—Chemical analysis of biological material, e.g. blood, urine; Testing involving biospecific ligand binding methods; Immunological testing
    • G01N33/53—Immunoassay; Biospecific binding assay; Materials therefor
    • G01N33/543—Immunoassay; Biospecific binding assay; Materials therefor with an insoluble carrier for immobilising immunochemicals
    • G01N33/551—Immunoassay; Biospecific binding assay; Materials therefor with an insoluble carrier for immobilising immunochemicals the carrier being inorganic
    • G01N33/553—Metal or metal coated
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
    • G01N27/00—Investigating or analysing materials by the use of electric, electrochemical, or magnetic means
    • G01N27/26—Investigating or analysing materials by the use of electric, electrochemical, or magnetic means by investigating electrochemical variables; by using electrolysis or electrophoresis
    • G01N27/28—Electrolytic cell components
    • G01N27/30—Electrodes, e.g. test electrodes; Half-cells
    • G01N27/327—Biochemical electrodes, e.g. electrical or mechanical details for in vitro measurements
    • G01N27/3275—Sensing specific biomolecules, e.g. nucleic acid strands, based on an electrode surface reaction

Definitions

  • the present invention relates to a non-labeled intermolecular interaction measurement method, particularly RIFS (Reflectometric Interference Spectroscopy) and non-specific adsorption to the sensor chip.
  • RIFS Reflectometric Interference Spectroscopy
  • a sensor chip in which one molecule (ligand, eg, antibody) involved in the intermolecular interaction is immobilized on the surface is used, and this ligand is involved in the intermolecular interaction.
  • the other molecule analyte, for example, antigen
  • various molecules other than the analyte contained in the sample solution are often non-specific on the surface of the sensor chip due to electrostatic interactions and hydrophobic interactions. Adsorbs. Such non-specific adsorption causes a signal that becomes noise in the measurement method based on the intermolecular interaction, and causes a decrease in measurement accuracy.
  • the surface of the sensor chip is treated with a substance for suppressing nonspecific adsorption (nonspecific adsorption inhibitor) before contacting the sample solution. ing.
  • Patent Document 1 proteins represented by BSA and the like are commonly used as non-specific adsorption inhibitors in intermolecular interaction measurement methods and measurement methods targeting other biological substances
  • Patent Document 2 heparin, dextran sulfate and the like have been proposed for use as blocking agents
  • Patent Document 3 Various polymers such as a specific acrylamide polymer (Patent Document 3) have also been proposed for use as non-specific adsorption inhibitors.
  • the ligand immobilized on a certain sample is used. After the analyte is bound and measured, the analyte bound to the ligand is peeled off using the regeneration solution, and the analyte is bound to the immobilized ligand for the next sample. In addition, measurement may be repeatedly performed using a single sensor chip.
  • Non-Patent Document 1 when conventional BSA or the like is used as a blocking agent, it is known that when a regeneration solution is added, not only the analyte peels from the ligand, but also the blocking agent partially peels from the sensor chip surface ( Non-Patent Document 1), the effect of the blocking agent is diminished, and the measurement value may be varied to impair measurement accuracy. In this case, it is conceivable to add a blocking treatment step to replenish the peeled blocking agent, but this is not preferable because it complicates the measurement step.
  • the blocking agent not only coats the site on the sensor chip surface where the ligand is not immobilized, but also coats the ligand in a superimposed manner. In exchange for the effect of preventing local adsorption, there is a possibility that the intermolecular interaction between the ligand and the analyte may be inhibited. Taking into consideration that a polymer is generally defined as having a molecular weight of 10,000 or more, it is considered that inhibition of intermolecular interaction occurs like a blocking agent such as BSA due to the size of the molecule.
  • the present invention provides improved non-specific adsorption prevention that does not cause problems such as peeling caused by contact with a regenerating solution and inhibition of intermolecular interaction between a ligand and an analyte, as seen with conventional blocking agents such as BSA. It is an object of the present invention to provide an intermolecular interaction measurement means that can use an agent.
  • the present inventors have used a surfactant, for example, polyoxyethylene sorbitan monolaurate known as a trade name “Tween 20” in general solutions in various solutions used in conventional methods for measuring intermolecular interactions. It has been found that by treating the surface of the sensor chip with an aqueous solution containing a concentration lower than the concentration, the surface can be coated with the surfactant and function as a nonspecific adsorption inhibitor. Furthermore, it has been found that such a surfactant as a nonspecific adsorption inhibitor does not cause problems such as peeling due to contact with a regeneration solution and inhibition of intermolecular interaction between a ligand and an analyte. It came to complete.
  • a surfactant for example, polyoxyethylene sorbitan monolaurate known as a trade name “Tween 20” in general solutions in various solutions used in conventional methods for measuring intermolecular interactions. It has been found that by treating the surface of the sensor chip with an aqueous solution containing a concentration lower than the
  • the present invention includes the following inventions.
  • the nonionic surfactant is selected from polyoxyethylene sorbitan monolaurate, polyoxyethylene sorbitan monopalmitate, polyoxyethylene sorbitan monostearate, polyoxyethylene sorbitan monooleate and polyoxyethylene sorbitan trioleate.
  • each of the regeneration treatment step (B) and the further sample solution contact step (A) in which the regeneration solution for peeling the analyte bound to the ligand is brought into contact is performed at least once.
  • the intermolecular interaction according to [7] or [8], wherein the sample solution, the regeneration solution, or both further contains the surfactant described in any one of [1] to [3].
  • Action measurement method. [10] The method according to any one of [7] to [9], wherein the concentration of the surfactant contained in the sample solution, the regeneration solution, or both is 0.0001 wt% or more and 0.1 wt% or less.
  • the treatment of the sensor chip surface with the surfactant is first carried out as a predetermined non-specific adsorption prevention treatment step, but even after the regeneration treatment step, the surfactant coated on the sensor chip surface is Since it does not peel substantially (so as to affect the measurement value), the measurement can be continued using the same sensor chip without reducing the measurement accuracy without providing an additional non-specific adsorption prevention treatment step.
  • the intermolecular interaction between the ligand immobilized on the sensor chip surface and the analyte is not inhibited, so that the measurement sensitivity can be improved.
  • a surfactant having a molecular weight not as large as that of a protein such as BSA is used at a low concentration, so that there is no adverse effect on the measurement other than the aqueous solution used for the non-specific adsorption prevention treatment step. They may be used while dissolved in a sample solution or a stripping solution, and the effect of preventing nonspecific adsorption can be further maintained.
  • FIG. 1 is a schematic diagram showing an example of an embodiment of the present invention of an intermolecular interaction measurement method based on RIfS.
  • FIG. 2 is a graph showing the change over time of the measured value ( ⁇ ) obtained in Example 1.
  • FIG. 3 is a graph showing the change over time of the measured value ( ⁇ ) obtained in Comparative Example 1.
  • the sensor chip for the intermolecular interaction measurement method used in the present invention is provided with a layer made of SiN, Ta 2 O 5 , Nb 2 O 5 , HfO 2 , ZrO 2 or ITO (indium tin oxide). is there. These layers refer to an optical thin film formed on the outermost surface of an unmodified sensor chip for RIfS.
  • the intermolecular interaction measurement method is not limited to RIfS, but “a layer made of SiN, Ta 2 O 5 , Nb 2 O 5 , HfO 2 , ZrO 2 or ITO (indium tin oxide). As long as the sensor chip is formed on the surface, the present invention can be applied to a method for measuring intermolecular interactions other than RIfS.
  • a ligand is immobilized on at least a part of the surface of a predetermined layer (optical thin film) as described above, and this measures a predetermined signal. It is considered as a measurement site.
  • non-specific adsorption prevention treatment is performed on such a measurement site by forming a film made of a surfactant (covering with a surfactant).
  • the method of non-specific adsorption prevention treatment that is, the method of forming a film comprising a surfactant is not particularly limited, but there is a method in which an aqueous solution of a surfactant is brought into contact with a measurement site according to the procedure described below. Is preferred.
  • a surfactant is used as a non-specific adsorbent, that is, a substance that covers the surface of the measurement member in order to prevent non-specific adsorption of a biological substance. Any one of the surfactants exemplified below may be used alone, or two or more thereof may be mixed and used as long as the effects of the present invention are not impaired.
  • Surfactants include ionic surfactants, including anionic (anionic) surfactants, cationic (cationic) surfactants and amphoteric surfactants, and nonionic (nonionic) surfactants.
  • a nonionic surfactant is suitable as the nonspecific adsorption inhibitor.
  • Nonionic surfactants include those of an ester ether type, an ester type, an ether type, etc. Among them, an ester ether type is preferable.
  • ester ether type nonionic surfactants include polyoxyethylene sorbitan monolaurate (Tokyo Chemical Industry Co., Ltd., trade name “Tween 20”), polyoxyethylene sorbitan monopalmitate (“Tween 40”), poly Examples thereof include oxyethylene sorbitan monostearate (same “Tween 60”), polyoxyethylene sorbitan monooleate (same “Tween 80”), and polyoxyethylene sorbitan trioleate (same “Tween 85”).
  • ester ether type nonionic surfactant products have an average number of polyoxyethylenes in one molecule of about 20, and the number of polyoxyethylenes in one molecule is assumed to be 20.
  • the molecular weight is 2000 or less in all cases.
  • ether type nonionic surfactant examples include diethylene glycol monododecyl ether, ethylene glycol monododecyl ether, polyethylene glycol monocetyl ether (n ⁇ 23, where n is the number of oxyethylene units, the same applies hereinafter), polyethylene glycol Examples thereof include monododecyl ether (n ⁇ 25), polyethylene glycol mono-4-octylphenyl ether (n ⁇ 10), tetraethylene glycol monododecyl ether, and triethylene glycol monododecyl ether.
  • the sensor chip for the intermolecular interaction measurement method of the present invention that has been subjected to non-specific adsorption prevention treatment using a surfactant is the surface of the predetermined layer (optical thin film). It can be produced through a non-specific adsorption preventing treatment step in which the measurement site where the ligand is immobilized is brought into contact with the surfactant aqueous solution so that the measurement site is coated with the surfactant.
  • the surfactant as a nonspecific adsorption inhibitor as described above is designed to cover the measurement site by bringing the aqueous solution into contact with the measurement site and to exhibit the performance of preventing nonspecific adsorption. Become.
  • bringing the aqueous solution of the surfactant into contact with the measurement site is a method for preventing nonspecific adsorption of the measurement site by coating the measurement site with the surfactant.
  • the concentration of the surfactant aqueous solution used in the non-specific adsorption preventing treatment step can be appropriately adjusted according to the type of the surfactant and the length of the treatment time. % Or less, more preferably 0.05% by weight or less, preferably 0.01% by weight or less, and generally 0.0001% by weight or more, preferably 0.001% by weight or more.
  • concentration of the surfactant is lower than the above lower limit, or when the concentration is higher than the upper limit although the detailed reason is unknown, there is a possibility that the nonspecific adsorption preventing ability is not exhibited.
  • the concentration of the surfactant is higher than the above upper limit value, bubbles are likely to be generated in the closed flow path, which increases the possibility of adversely affecting the liquid feeding system.
  • aqueous solution of the surfactant there is no particular limitation on the method of bringing the aqueous solution of the surfactant into contact, and the aqueous solution may be brought into contact (moving down), or the aqueous solution may be brought into contact in a stationary state.
  • a sensor chip in use as shown in FIG. 1 is formed by immobilizing a ligand on the surface of an optical thin film and then forming an aqueous solution of a nonspecific adsorption inhibitor by a flow cell. It is preferable that the non-specific adsorption preventing treatment is performed by bringing it into contact with the surface of the sensor chip by introducing from the closed flow path.
  • Such an embodiment requires a shorter time to reach a sufficient level (equilibrium) with the non-specific adsorption preventing ability test substance (A) compared to the latter embodiment described below.
  • a sensor chip in which a ligand is immobilized on the surface of an optical thin film in advance may be simply immersed in an aqueous solution of a nonspecific adsorption inhibitor contained in a container.
  • the treatment time that is, the contact time between the sensor chip surface and the surfactant aqueous solution is not particularly limited, but the time until the sensor chip surface is sufficiently coated with the surfactant (saturation is reached). It is appropriate to ensure
  • the measurement value obtained by the intermolecular interaction measurement method starts to be acquired before the start of the processing step and continuously acquired thereafter.
  • the measured value changes with the lapse of processing time (normally the bottom peak wavelength shifts to the long wavelength side in RIfS), and through the observation of such change, the non-specific adsorption prevention process proceeds, and the surface of the sensor chip is exposed to the surfactant. It can be confirmed at any time how the film is formed. Eventually, the measured value will not change or the fluctuation will be sufficiently small, so that it can be determined that the surface of the sensor chip has reached the saturation point, and the non-specific adsorption prevention treatment process is completed. be able to.
  • the method for producing a sensor chip for the intermolecular interaction measurement method of the present invention which has been subjected to a nonspecific adsorption prevention treatment using a surfactant, is a nonspecific adsorption prevention treatment as described above.
  • various conventional steps can be included.
  • the surface of the sensor chip (optical thin film) is unmodified at the beginning of manufacture, and it is necessary to immobilize a ligand corresponding to the analyte prior to contact with the analyte.
  • the mode of the step of immobilizing the ligand on the surface of the sensor chip is not particularly limited, and can be performed by employing various known methods.
  • the surface of an unmodified optical thin film eg, SiN
  • a silane coupling agent having an amino group at the end to be modified with an amino group
  • NHS N-hydroxysuccinimide
  • the sensor chip with the ligand immobilized on the surface is prepared by binding biotin to the amino group and reacting this biotin with avidin and then reacting with a biotinylated ligand (eg, antibody). can do.
  • a sensor chip having the ligand immobilized on the surface can also be produced by reacting an amino group-containing ligand (typically a protein such as an antibody). .
  • Various treatments for immobilizing such ligands are performed by setting a measuring member consisting of an unmodified sensor chip and flow cell on the detection device, and then sequentially feeding reagents and washing solutions for the treatment. It is also possible to carry out a part of the processing before setting the measurement member on the detection device and to perform the remaining processing after the setting.
  • the measuring device 1 for the intermolecular interaction measuring method mainly includes a measuring member 10, a white light source 20, a spectroscope 30, a light transmission unit 40, a control device 50, and the like.
  • the white light source 20, the spectroscope 30, the light transmission unit 40, and the like are preferably housed in the measurement device main body, and a control device 50 in the form of a PC (Personal Computer), for example, is controllably connected to the measurement device main body. Is done.
  • the measuring member 10 is generally rectangular, and preferably has a form that can be attached to and detached from the measuring apparatus main body.
  • the measurement member 10 is configured based on the sensor chip 12 including at least the substrate 12a and the optical thin film 12b formed on the substrate 12a. Usually, the measurement member 10 further sends various solutions such as the sample solution 60 including the analyte 62.
  • the flow cell 14 is loaded on the sensor chip 12 in order to form the sealed flow path 14b for liquid.
  • the measuring member 10 (sensor chip 12 and flow cell 14) can be of a disposable type.
  • the substrate 12a is typically a Si (silicon) substrate
  • the optical thin film 12b is typically a SiN (silicon nitride) film.
  • the substrate 12a is preferably made of, for example, Si (silicon).
  • the optical thin film 12b is formed of a material having a refractive index and a thickness that is selected according to the material (refractive index) of the substrate and has a bottom peak observed when white light is used. Is done.
  • the substrate 12a is a Si substrate
  • the optical thin film 12b is an oxide film or nitride film such as SiN, Ta 2 O 5 , Nb 2 O 5 , HfO 2 , ZrO 2 , ITO (indium tin oxide). Is preferable, and a SiN film is particularly preferable.
  • Each of these oxide films or nitride films has a refractive index of 1.8 to 2.4 in the visible light region (wavelength range of about 400 to 800 nm), and exhibits performance as an optical thin film formed on the upper layer of the Si substrate.
  • the optical thin film itself has an effect of suppressing nonspecific adsorption to some extent. For example, by setting the thickness of the SiN film to about 45 to 90 nm, the bottom peak can be adjusted to a range of about 400 nm to 800 nm.
  • the flow cell 14 is a transparent member made of, for example, silicone rubber (polydimethylsiloxane: PDMS), and can be brought into close contact with the sensor chip 12.
  • the flow cell 14 is formed with at least one groove 14a.
  • a sealed flow path 14b is formed. Both ends of the groove 14a are exposed from the surface of the flow cell 14, and one end is connected to a liquid feeding part (for example, a syringe pump) to function as an inlet 14c to which various solutions such as the sample solution 60 are supplied.
  • the other end is connected to the waste liquid section and functions as an outlet 14d for various solutions such as the sample solution 60.
  • a ligand 16 that binds to the analyte 62 is immobilized on at least a part of the surface of the sensor chip 12 (upper layer of the optical thin film 12b) located at the bottom of at least one groove 14a of the flow cell 14. Measurement is performed at.
  • an appropriate substance that specifically binds to the analyte 62 to be analyzed is selected.
  • the protein serving as its antibody is a nucleic acid having a complementary base sequence if the analyte 62 is a nucleic acid, and if the analyte 62 is a sugar, A binding lectin (protein) or the like is used as the ligand 16.
  • the light transmission unit 40 is a first optical fiber 41 serving as a first light transmission path for guiding white light from the white light source 20 to the measurement unit 200, and irradiation of white light from the first optical fiber 41.
  • a second optical fiber 42 as a second light transmission path for guiding the reflected light from the measurement unit 200 to the spectroscope 30.
  • the end of the first optical fiber 41 on the white light source 20 side is connected to the connection port of the white light source 20.
  • the optical fiber 41 connected to the connection port is arranged so that the light incident end face faces the halogen lamp 21.
  • the end of the second optical fiber 42 on the spectroscope 30 side is connected to a connection port that receives light from the spectroscope 30.
  • Each of the optical fibers 41 and 42 has a structure in which fine fibers are bundled. And the edge part by the side of the flow cell 14 of the 1st optical fiber 41 and the 2nd optical fiber 42 is faced compoundly so that each fine fiber may become one bundle. That is, the fine fibers constituting the first optical fiber 41 are distributed in the center on the end face on the flow cell 14 side, and the fine fibers constituting the second optical fiber 42 are bundles of fine fibers of the first optical fiber 41. It is distributed around it to surround it.
  • the white light source 20 is composed of a halogen lamp and a housing for storing the halogen lamp.
  • the housing is provided with a connection port for connecting the first optical fiber 41.
  • a white light source is used.
  • the present invention is not limited to this, and any light source may be used as long as it emits light distributed over a wavelength range where a change in reflectance minimum wavelength described later can be detected.
  • the white light source 20 When the white light source 20 is turned on, the white light is irradiated onto the measuring unit 200 via the first optical fiber 41, and the reflected light is guided to the spectroscope 30 via the optical fiber 42.
  • the spectroscope 30 detects the light intensity of the light at fixed wavelength intervals included in the light received by the light receiving unit, and outputs the light intensity to the control device 50 as the spectral intensity.
  • reflected light from the measurement member 10 is received by the spectroscope 30 (reflection type RIfS).
  • a light transmissive member is used as the measurement member 10 and the white light source 20 is used. It is also possible to arrange the spectroscope 30 so as to irradiate the measurement member 10 with the light and to receive the light transmitted through the measurement member 10 and to detect the spectral intensity of the transmitted light.
  • the control device 50 receives an input of detection operation execution from the operator, and outputs a detection operation control execution command to the measurement device 10. Thereby, the control apparatus 50 functions as a control part.
  • control device 50 also functions as a calculation unit.
  • the control device 50 acquires the spectral intensity data of the measurement light from the spectroscope 30 and calculates the reflectance for each wavelength band by dividing the spectral intensity of the measurement light by the spectral intensity of the white light as a reference.
  • the spectral intensity data of the reference light may be previously measured and held at the time of device assembly adjustment, or may be acquired by other means, for example, every measurement.
  • a reflection spectrum is created based on the calculated reflectance, and the reflectance minimum wavelength ( ⁇ ) is determined. It is also possible to obtain the measured change amount ( ⁇ ) of the minimum reflectance wavelength with respect to a certain minimum reflectance wavelength (baseline).
  • the waveform of the reflection spectrum usually has an irregular shape in which minute irregularities are repeated, and it may be difficult to calculate and specify the reflectance minimum wavelength.
  • the waveform is smoothed, and the solution (minimum value) is obtained from the high-order polynomial, and this can be specified as the value of the minimum reflectance wavelength. .
  • a microcomputer (not shown) performs control to switch on / off the white light source 20 according to a control command of the control device 50, or performs temperature control of a temperature control unit according to a set temperature command of the control device 50. To do.
  • the temperature adjusting means includes, for example, a temperature adjusting element that performs heating and cooling, such as a Peltier element, and a temperature detecting element, which are attached to the measuring member 10. And the control apparatus 50 detects the temperature of the measurement member 10 with a temperature detection element through a microcomputer, and performs temperature control so that it may become preset temperature by the heating or cooling by a temperature control element.
  • the measurement member 10 When performing detection, the measurement member 10 is warmed up in advance. That is, the control device 50 sends a command to the microcomputer so that the preset temperature is set in advance, and the microcomputer performs temperature control of the temperature control unit. The analysis is started after the temperature of the measurement member 10 is stabilized by the warm air.
  • Control device 50 determines whether or not to continue the measurement, and if not, ends the process.
  • the measurement time may be set in advance, and it may be determined whether or not the measurement time has elapsed, or the measurement end input is set as a setting for continuing the measurement until the measurement end input is received. The presence or absence may be determined.
  • the control device 50 periodically calculates the reflectance, creates a reflection spectrum and determines the minimum reflectance wavelength, and records the time-series change.
  • the intermolecular interaction measurement method is a sample solution contact step (A) in which a sample solution containing at least an analyte and a nonspecific adsorbate is brought into contact with a measurement site that has been subjected to nonspecific adsorption prevention treatment. including.
  • the analyte 62 is a substance that specifically binds to the immobilized ligand 16.
  • biomolecules such as proteins (including polypeptides, oligopeptides, etc.), nucleic acids (including DNA, RNA, polynucleotides, oligonucleotides, PNA (peptide nucleic acids), etc.), lipids, sugars, drug substances, endocrine disruptions
  • the analyte 62 can be a foreign substance that binds to a biomolecule such as a chemical substance, or other bio-related substance.
  • a tumor marker for example, ⁇ -fetoprotein
  • present in blood which is an important index in cancer diagnosis or the like, is an example of an important analyte.
  • the sample solution containing or possibly containing the analyte 62 to be used in the intermolecular interaction measurement method is generally prepared from a specimen collected from a living body.
  • specimens include blood (serum / plasma) collected from humans and non-human animals (eg, mammals), urine, nasal fluid, saliva, stool, body cavity fluid (spinal fluid, ascites, pleural effusion, etc.) It is done.
  • a specimen may be mixed with various liquids (pure water, physiological saline, buffer solution, reagent solution, etc.) or used as a sample solution after purification treatment, if necessary.
  • Such sample solutions usually contain a wide variety of non-specific adsorbates, especially biomolecules.
  • Typical biomolecules as non-specific adsorbents include proteins, nucleic acids, sugars, and other various biological materials.
  • the surfactant used as the non-specific adsorption inhibitor in the present invention can prevent or sufficiently suppress non-specific adsorption of such a substance to the sensor chip surface.
  • the sample solution may further contain the same surfactant as that used in the non-specific adsorption prevention treatment step.
  • concentration of the surfactant contained in the sample solution is preferably adjusted as appropriate within the same range as the aqueous solution used in the non-specific adsorption prevention treatment step.
  • the regeneration solution as described above is known, and for example, a glycine-HCl solution can be used.
  • the regeneration solution may further contain the same surfactant as that used in the nonspecific adsorption prevention treatment step.
  • concentration of the surfactant contained in the regeneration solution is preferably adjusted as appropriate within the same range as the aqueous solution used in the non-specific adsorption prevention treatment step.
  • the regeneration process step (B) and the sample solution contact step (A) can be repeated to continue the measurement.
  • the regeneration solution contains a surfactant, even if a part of the surfactant covering the surface of the sensor chip is peeled off in the regeneration step, the surfactant in the regeneration solution immediately compensates for the peeling, It is possible to proceed to the next analyte contacting step in a state where the surfactant film is sufficiently formed (saturated state).
  • Example 1 (1. Production process of unmodified sensor chip) On the silicon wafer (100), SiN (silicon nitride) was deposited by CVD to a thickness of 66.5 nm to produce an unmodified sensor chip having an optical thin film made of SiN on the outermost surface.
  • SiN silicon nitride
  • the NHS manufactured by ThermoFisher Scientific KK
  • WSC manufactured by dojindo
  • 25 mM MES buffer pH 5.0
  • the sensor chip modified with the carboxyl group by the above process was immersed at room temperature for 20 minutes to produce a sensor chip in which the carboxyl group was activated esterified. After washing the sensor chip with ultrapure water, water droplets were removed by air blowing.
  • AFP anti- ⁇ fetoprotein
  • the RifS type intermolecular interaction measuring device (trade name “MI-Affinity”, manufactured by Konica Minolta Opto) was turned on and waited for about 20 minutes until the light source was stabilized.
  • a flow cell (manufactured by Konica Minolta Opto Co., Ltd.) having a groove 2.5 mm wide ⁇ 16 mm long ⁇ 0.1 mm deep and a through hole having a diameter of 1 mm at both ends of the groove on the antibody-immobilized sensor chip.
  • the measurement member in which the closed flow path was formed was constructed.
  • the measurement member is set in the measurement device, and a syringe pump (Econoflo 70-2205; manufactured by Harvard Apparatus) is used to send liquid from the outside of the measurement device to the sealed channel through the chip cover provided in the measurement device, The chip surface was brought into contact with the chip surface.
  • a treatment solution was prepared by adjusting “Tween 20” (Tokyo Kasei Kogyo Co., Ltd.), which is a surfactant as a non-specific adsorption inhibitor, to a concentration of 0.001% by weight using the PBS buffer.
  • This non-specific adsorption inhibitor treatment solution was introduced into the closed flow path of the measurement member for 20 minutes at a liquid feed rate of 20 ⁇ L / min by the syringe pump, and the analyte (anti-AFP antibody) was immobilized by the above step.
  • a second analyte contact step was performed in the same manner as in the seventh step after 3000 seconds and 3600 seconds from the start of the measurement by the intermolecular interaction measuring apparatus.
  • a second regeneration solution treatment step was performed in the same manner as in the eighth step, 4200 seconds after the start of the measurement by the intermolecular interaction measuring apparatus.
  • FIG. 2 shows a graph showing the change over time of the measured value ( ⁇ ) obtained in Example 1 (7th to 10th steps).
  • FIG. 3 is a graph showing the change over time of the measured value ( ⁇ ) obtained in Comparative Example 1 (seventh to tenth steps).
  • Example 1 (FIG. 3) using Tween 20 has a higher response ( ⁇ ) at the time of introduction of the analyte and higher sensitivity. You can see that. Further, in Comparative Example 1 (FIG. 2), the baseline after the treatment with the regeneration solution is lower than the initial baseline, and it can be seen that the BSA covering the surface of the sensor chip occurred. On the other hand, in Example 1 (FIG. 3), the baseline after the treatment with the regeneration solution is not lowered from the initial baseline, and is maintained at almost the same level, and the surfactant is peeled off. Even if peeling occurs, it is considered that the surfactant is immediately replenished by the surfactant contained in the treatment liquid. Therefore, it can be said that it is an excellent non-specific adsorption inhibitor that can withstand repeated use.

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Abstract

La présente invention concerne un moyen permettant de mesurer les interactions intermoléculaires, le moyen utilisant un inhibiteur d'absorption spécifique amélioré qui ni ne pèle, même quand il est en contact avec une solution de régénération, ni ne gêne une interaction intermoléculaire entre un ligand et un analyte. Le procédé de production de la puce de capteur comprend une étape de traitement permettant d'inhiber les adsorptions non spécifiques, l'étape consistant à mettre en contact une solution aqueuse contenant un tensioactif avec une partie de mesure constituée d'un ligand immobilisé sur la surface d'une couche composée de SiN, de Ta2O5, de Nb2O5, de HfO2, de ZrO2 ou d'ITO (oxyde d'indium et d'étain), pour ainsi former un film de revêtement composé du tensioactif sur la partie de mesure. De préférence, le tensioactif est un tensioactif non ionique. De préférence, la concentration en tensioactif dans la solution aqueuse est de 0,0001 % en poids à 0,1 % en poids.
PCT/JP2012/066209 2011-06-28 2012-06-26 Puce de capteur pour mesurer les interactions intermoléculaires, qui a été soumise à un traitement inhibant les adsorptions non spécifiques au moyen d'un tensioactif, procédé de production de ladite puce de capteur et procédé de mesure d'interactions intermoléculaires au moyen de ladite puce de capteur Ceased WO2013002193A1 (fr)

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CN103728273A (zh) * 2013-12-11 2014-04-16 王丽红 表面活性剂的作用、表面等离子共振检测低分子量物质的信号放大的方法
CN103728279A (zh) * 2013-12-11 2014-04-16 王丽红 表面活性剂的作用、表面等离子共振检测低分子量物质的信号放大的方法
CN103728278B (zh) * 2013-12-11 2016-06-22 王丽红 表面活性剂的作用、表面等离子共振检测低分子量物质的信号放大的方法
CN103728279B (zh) * 2013-12-11 2016-06-22 王丽红 表面活性剂的作用、表面等离子共振检测低分子量物质的信号放大的方法
JP2017113009A (ja) * 2014-01-31 2017-06-29 凸版印刷株式会社 バックグラウンド低下剤及びその使用
JPWO2015115635A1 (ja) * 2014-01-31 2017-03-23 凸版印刷株式会社 生体分子解析キット及び生体分子解析方法
JP2019141047A (ja) * 2014-01-31 2019-08-29 凸版印刷株式会社 生体分子解析方法及び生体分子解析キット
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EP3187874A4 (fr) * 2014-08-25 2018-05-23 Konica Minolta, Inc. Procédé de réaction, procédé de détection et dispositif de détection
WO2024190866A1 (fr) * 2023-03-15 2024-09-19 積水メディカル株式会社 Procédé et kit de traitement
CN116539694A (zh) * 2023-05-10 2023-08-04 合肥天一生物技术研究所有限责任公司 一种生物传感器及其在维生素c检测方面的应用

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