• 专利附录
  • 专利说明
  • 权利要求
  • 类似技术
  • 同族专利
  • 引用文献
  • 法律状态
  • 优先权
    • 专利摘要:
    Summary The present invention relates to an apparatus and method for simultaneously feeding, in a submerged microchannel environment, the characteristics of molecular bonds such as low molecular weight biomaterials and the like and the refractive index of a buffer solution using ellipsometry. More specifically, the present invention relates to a device for simultaneous feeding, with high probability, the change of the refractive index of a buffer release and the binding dynamics properties of a biomaterial by allowing polarized incident light to be received on an adsorption layer of the biomaterial, which adsorption layer is formed on a semiconductor substrate. or the like, to satisfy a p-wave antireflection state by using a prismatic structure and a microchannel; and a food process using the same.
    公开号:SE1550597A1
    申请号:SE1550597
    申请日:2013-09-27
    公开日:2015-05-08
    发明作者:Hyun Mo Cho；Yong Jai Cho；Won Chegal
    申请人:Korea Res Inst Of Standards；
    IPC主号:
    专利说明:

    [19] [19] Hereinafter, the features and limitations of the biomaterial analysis sensor according to the foregoing patent will be described with reference to Fig. 3 and Fig. 4. Fig. 3 shows a graph of ellipsometric constants y and A on light entering angle steering wheel in the submerged microchannel structure. in the sensor according to the preceding patent. As in Fig. 1, a silicon substrate and a light source 40 having a wavelength of 655nm were used.
    [20] [20] Thicknesses of 4nm and 5nm of the adsorption layer of the bio-thin layer including a thickness of a self-assembled monolayer were measured, respectively. The adsorption layer with a refractive index n of 1.45 was measured, and buffer solutions with a refractive index n of 1,333 and 1,334 were measured. As shown in Fig. 3, a change in tp due to the thickness change of the thin layer is relatively larger than a change of qi due to the change in the refractive index. Thus it can be seen that the fiesta y-values are caused by the thickness variation.
    [25] [25] This problem arises when the refractive index change of the buffer solution during injection of the sample is relatively larger than the signal shift in the sensor caused by the binding characteristics of the biomaterial. This problem is especially caused when a solvent with a large difference in refractive index compared to the buffer solution is used when mixing the sample with the buffer solution, or other materials used to increase the binding efficiency and which have a large difference in refractive index compared to the buffer solution. The conventional SPR sensor exhibits the foregoing problems even when the refractive index change is small during injection of the sample. Furthermore, even if essentially the same solutions are injected, the SPR signal shift is significantly greater than the binding characteristics of the biomaterial, and acts as a fundamental factor causing a food defect.
    [26] [26] To correct the refractive index change of the buffer solution 34 and avoid an error due to diffusion between the sample 32 and the buffer solution 34, a correction method has been proposed such as using a probable valve device, an air injection device and two or more channels, where one channel is used as the reference channel. However, it is different to distinguish the refractive index change of the buffer solution from a change due to pure adsorption-dissociation property, and it can always act as a factor causing a food defect. Indeed, depending on the said limitations when feeding with the conventional sensor, when the refractive index change of the buffer solution is relatively larger when injecting the sample, there is a fundamental responsibility when feeding dissociation properties.
    [27] [27] Furthermore, the conventional method can only correct a signal that varies with time and space when the reference channel and other channels have a constant sensor probability, and a small change in probability can act as a food error factor. In particular in the SPR sensor, a thin metal layer such as gold (Au), silver (Ag) and similar high production costs, a large deviation in refractive index due to manufacturing processes compared with a semiconductor substrate such as silicon, and unstable optical property. Consequently, the SPR sensor has a problem that an error is caused by different probabilities at different positions in relative comparison with a reference channel. Detailed description Technical object The present invention aims to solve previous problems. An object of the present invention is to provide an apparatus and method for simultaneously feeding the characteristic of the molecular bonds and the refractive index of a buffer solution, which can feed only pure binding kinetics excluding an effect of the refractive index of the buffer solution, by simultaneously feeding a change of the refractive index of buffer buffer and binding kinetics has a biomaterial in a submerged microchannel environment, when a signal shift in a sensor due to the refractive index change has buffer buffer is relatively larger than a signal shift due to binding kinetics has biomaterial during injection of a pray, and which can feed binding in the biomaterial with high probability by counteracting the refractive index change has the buffer release and thus an angle of incidence change, when a signal shift has a sensor through the refractive index change has the buffer solution is relatively larger than a signal shift through the binding kinetics, the biomaterial is present when the sample is injected.
    [32] [32] An additional dielectric thin film can be used between the substrate and the adsorption layer on top of the substrate. The dielectric thin layer is made of a transparent semiconductor oxide layer or a glass layer, the thickness of which is greater than 0 - 1000 nm.
    [38] [38] Furthermore, the light source can be a laser or laser diode which has a variable wavelength shape.
    [39] [39] The polarizing light generating member comprises at least one of: a collimator lens providing parallel light to the polarizer; a focusing lens for converging the parallel lights passing through the polarizer to drive the quantity of incident light; and a first compensator for effecting a phase shift of the polarized components has the incident light. 9 The polarizer and the first compensator may be rotatable or they may have an additional polarization modulation device.
    [42] [42] When the prismatic structure is a prism, an incident surface of the prism allows light to be received at an approximately angular angle. In addition, a light emitting surface, which forms a spruce surface with the buffer solution, allows light to be received on a substrate at an inclined angle which can meet the anti-reflection state of the P-carriage, but not light which enters perpendicular to the buffer solution. A top surface of the prismatic structure may be shaped in a trapezoidal shape, or have a free shape. It is important that light is received on the spruce surface at an inclined angle. A flat plate can also be used instead of the prismatic structure.
    [43] A fourth object of the present invention can be achieved by a microchannel structure unit which is used for a device for simultaneously feeding the characteristics of non-molecular bonds and the refractive index of a buffer solution, the microchannel structure unit comprising a substrate; a substrate made of a semiconductor or a dielectric material and formed on one side of the substrate; a dielectric thin layer provided on top of the substrate; a roof part with a prismatic structure mounted on the substrate; and a microchannel formed either in a top of the substrate or in a bottom of the roof portion; wherein the buffer solution containing a biomaterial sample is injected into the microchannel to form an adsorption layer on the dielectrically thin layer on top of the substrate, incident light, polarized through an incident surface is prism, irradiated on the adsorption layer at an angle of incidence of an anti-reflection state and has a P-wave light reflected from the adsorption layer is emitted through a reflecting surface of the prism.
    [44] [44] The microchannel has a plurality of inflow vesicles formed on one side of the substrate and a plurality of effluent vesicles formed on the other side. The influx waves and the ufflOcles waves are respectively connected by a plurality of partitions which are formed at the bottom of the prism.
    [48] [48] The light detector may be one of a CCD-type solid-state imaging element, a photomultiplier and a silicon photodiode.
    [62] [62] Fig. 4 is a schematic view illustrating a problem with the conventional technique, that the inherent adsorption and dissociation kinetics have a pray in an adsorption and dissociation process of the sample mixed with the refractive index change of a buffer solution.
    [63] [63] Fig. 5 is a cross-sectional view showing a configuration of the device for simultaneous feeding of the molecular binding characteristic and the refractive index having a buffer solution according to an example of the present invention.
    [64] [64] Fig. 6 is a perspective view of a multi-channel type of microchannel structure unit according to an example of the present invention.
    [65] [65] Fig. 7 is an exploded view of a multi-channel type of microchannel structure unit according to an example of the present invention.
    [74] [74] 112: Forced part 120: substrate
    [75] [75] 130: thin dielectric layer 132: self-assembled monolayer 14 140: roof part 142: prism 143: incident surface 144: reflection surface 146: partition 150: microchannel 152: influx weak 154: discharge weak
    [80] [80] 160: adsorption layer 200: sample spray portion 210: buffer release 300: polarized light generating portion 310: light source 320: polarizer 330: collimator lens 340: focusing lens 350: first compensator 400 polarized light detection portion
    [85] [85] 410: analyzer 420: light detector 430: processor 440: second compensator 450: spectrometer Preferred embodiments for practicing the invention
    [88] [88] Below, preferred examples are described in detail with reference to the accompanying drawings in order that a person skilled in the art may readily practice the present invention. A specific description of a candidate relevant function or component may be omitted by describing an embodiment mechanism with respect to the preferred examples without clarifying the present invention.
    [89] [89] Throughout the drawings, the same reference numerals have been assigned parts with a similar function. In addition, throughout the specification, when one part is coupled to other parts, it includes a direct coupling as well as an indirect coupling with other elements therebetween. Furthermore, it means that when a component is included, other components may be further included but exclude other components unless otherwise stated.
    [105] [105] [106] Fig. 8 is a perspective view showing another example of the multichannel type of the nichro channel structure unit according to the present invention. As shown in Fig. 8, the multi-channel type of microchannel structure unit 100 may have a trapezoidal cross-section of the prism 142. In this case, the polarizing light generating portion 300 and the polarized light detecting portion 400, as shown in Fig. 5, are securely fixed in a position so that incident light or reflected light incident on the incident surface 143 or the reflection surface 144, at a perpendicular angle or at an angle nearly perpendicular, does not significantly alter the polarization of the light. A flat plate can be used as a simple and flexible structure instead of the prismatic structure, even if a flat plate shows a loss of incident light.
    [107] Fig. 9 is an exploded perspective view showing an example of a single channel type of microchannel structure unit according to the present invention. As shown in Fig. 9, the single-channel type of the microchannel structure unit 100 has a microchannel 150. Ie. the roof portion 140 has the prism 142 and a pair of partitions 146 formed in the spirit of the bottom of the prism;
    [108] [108] A plurality of different self-assembling monolayers (SAM) 132 are formed on the substrate, or different adsorption layers are formed on identical self-assembled monolayers. The self-assembling monolayer 132 is formed of spontaneously arranging monomers which are composed of a main group and a duck group by chemical adsorption of the molecules. The interface characteristics of each of the self-assembled monolayers 132 can be altered by chemical transformation of a functional group in the duck group of the individual self-assembled monolayer 132. Ie. varying adsorption and dissociation kinetics of biomaterials can be fed simultaneously because each of the self-assembled monolayers 132 has a sensor mechanism having different adsorption and dissociation for a sample.
    [109] [109] As shown in Fig. 5, the sample spray portion 200 injects the buffer solution 210, containing samples (not shown) of low molecular weight biomaterial, into the inflow trough 152 of the microchannel 150. The sample spray portion 200 is arranged to unload the sample into the buffer solution 210 in a constant concentration, and has a valve device (not shown) for injecting or stopping the injection of the buffer solution 210 into the microchannel 150.
    [110] [110] The sample injection member 200 can inject the buffer solution 210 into each microchannel 1 at different concentrations or at a time interval. When the buffer solution 210 is injected into the microchannel 150, a portion of the samples (not shown) are adsorbed on the thin dielectric layer 130 to form an adsorption layer 160 of a desired thickness. The adsorption layer 160 may be a multilayer layer, consisting of the self-assembling monolayer 132 lamped for varying bonding characteristics of various biomaterials, a fixing material, 18 and various biomaterials comprising low molecular weight materials bonded to the fixing material.
    [113] [113] The light source 310 emits monochromatic light having the same wavelength band as infrared rays, visible rays or ultraviolet rays or white light. The light source 310 can be various lamps, light emitting diodes (LEDs), lasers, laser diodes (LE) or the like. The light source 310 may have a structure capable of varying the wavelength depending on an optical system. On the other hand, an optical signal in the reflected light may have relatively less intensity near the described state with non-reflective p-waves. In this case, the signal-to-noise ratio can be increased by irradiating light with a high proportion of light using a laser or a laser diode (LD), in order to achieve a high-power supply.
    [116] [116] [117] As shown in Fig. 5, the polarized light detecting portion 400 receives light reflected from the reflection surface 144 of the prism 142, in the adsorption layer 160, and detects a change in the polarization of the reflected light. The polarized light detecting portion 400 must include an analyzer 410, a light detector 420 and a processor 430 and may optionally include a second compensator 440 and a spectrometer 450.
    [120] [120] The second compensator 440 controls the polarized components of the reflected light by providing phase distortion. The second compensator 440 may be rotatable, or may additionally include other polarization modulation devices.
    [121] [121] The spectrometer 450 is used in cases where the light source 310 emits white light. In this case, it dissolves the reflected light and separates the reflected light having a wavelength in a narrow area, to transmit it to the light detector 420. The light detector 420 may be a 2-dimensional sensor such as a CCD-type solid-state imaging element for to obtain optical data regarding a distribution of reflected light.
    [122] [122] [123] [Simultaneous feeding of the molecular binding characteristic and the refractive index has a buffer solution] A procedure for simultaneously feeding the molecular binding characteristic and the refractive index has a buffer reading and these principles will be described with reference to the accompanying drawings. .
    [131] [131] In the fourth stage S400, the light reflected by the adsorption layer 160 enters the polarized light detecting portion 400 through the prism 142 of the microchannel structure unit 100. The reflected light is in an elliptically polarized state.
    [132] [132] In the fifth step S500, the polarized light detecting portion 400 detects the polarization of the reflected light. In particular, the elliptically polarized reflected light is first received on the adsorption layer 160 through the analyzer 410 and opposite only light for polarization.
    [138] [138] [Example of experiment]
    [139] [139] Fig. 11 is a graph illustrating a change in the ellipsometric constants ip and A according to an angle of incidence at the angular rate of incidence in the previous patent, when the buffer solution 210 has different refractive indices. In this experiment, the wavelength of the light source 310 is 655 nm, the adsorption layer of the bio-thin layer including the self-assembled monolayer is 4 nm, and the refractive index n of the prism is 1,721 (SF10). In this case, it has been discovered that an angle of incidence corresponding to the antireflection state of the β-wave is approximately 70.85 ° when a value of the ellipsometric constant changes abruptly.
    In Fig. 11, the buffer release 210 shows the refractive index 1.3330 in the solid line graph, and the refractive index 1.3332 in the dotted line graph. The bag-shaped graph shows a change of the ellipsometric constant tti according to an amplitude ratio, and the linear graph shows a change of the ellipsometric constant A according to a phase difference. In Fig. 11, the ellipsometric constants qi and A show a minor change according to the refractive index change of the buffer solution.
    However, light enters a spruce surface at an inclined angle of about O 2 = 70.85 °, as in Fig. 12, when light is absorbed by a prismatic incident mechanism. When the light is received from the prism to the buffer solution, the angle shows the change of approximately 0.024 ° through the refractive index change of the buffer solution (0.0002). Since the non-reflective state of the p-wave is approximately O 2 = 70.85 ° and the angle is changed to 70.826 ° by the refractive index change of the buffer solution, which is 0.024 ° less than the previous angle, Lp and A-graphs are designed as shown in Fig. 13. Since the angle in the non-reflective state of the p-carriage changes slightly according to the refractive index change, the 11J and A values are determined at 70,826 °, a 0.024 ° smaller angle. In Fig. 13, when the buffer solution 210 has different refractive indices, the buffer solution 210 has the refractive index 1.3330 in the solid line graph, and the refractive index 1.3332 in the dotted line graph. As shown in Fig. 13, from the results measured according to a change of angle of incidence using the prismatic mechanism, it has been found that the ip value is slightly changed because the smaller change at the perpendicular condition of incidence is more counteracted, while the A value is much changed. In other words, the ellipsometric constant A of a phase difference is probable for the refractive index change of the buffer solution, but is only slightly affected by the binding characteristic, and the refractive index change of the buffer solution can be determined with high probability. The ellipsometric constant A changes a lot because the thin layer has a smaller thickness. Consequently, when used in a study to analyze a change in physical properties or bonding properties of a material by observing the refractive index change, it is possible to feed a refractive index with an ultra-high probability compared to the conventional SPR method. In addition, the pure binding kinetics and the refractive index change have the buffer solution fed simultaneously, because before a continuous feed buffer solution and a refractive index buffer solution changed by a solvent or the like and used in a sample fed to the sensor through the microchannel, a minimal mixture of these two solutions is obtained by a valve device.
    In addition, the bonding characteristic of the sample can be measured correctly based on a value has the ellipsometric constant tp on an amplitude ratio, since the ellipsometric constant qi on an amplitude ratio is changed with high probability according to the bonding characteristic has a sample. Furthermore, it can be seen, as shown in Fig. 11, that the ellipsoometric constant qi on an amplitude ratio is slightly changed according to the refractive index change has the buffer solution (1.3330 -> 1.3332) at an angle of incidence of 70.85 °.
    In particular, it can be seen that the angle changes at an angle of about 0.024 ° less than the perpendicular angle of incidence of the prismatic mechanism of incidence, and a change in the ip value before and after the injection of the buffer solution has decreased in relation to a change in the ip value by the refractive index. of the buffer release at the perpendicular incidence condition. This situation is caused by a positive change in the refractive index (1.3330 -> 1.3332). In most experiments for feeding binding kinetics, a refractive index often has a solvent or an added material - used for dissolving a sample - higher than that of a pure buffer solution. In this case, it is possible to reduce a food error due to the refractive index change has the buffer solution by minimizing a change in the 4J value of the refractive index change has the buffer solution before and after injection.
    权利要求:
    Claims (22)
    [1]
    An apparatus for simultaneously feeding molecules bonding characteristic and refractive index of a buffer solution, comprising a microchannel structural unit provided with a substrate made of a substrate and a semiconductor or a dielectric material formed on the substrate, a roof portion having a prismatic structure fixed to the substrate and a microchannel formed either in a top of the substrate or in a bottom of the roof portion; a sample spray portion for injecting a buffer debris containing a biomaterial sample into the microchannel to form an adsorption layer of the sample on the substrate; a polarized light generating member for straining incident light, polarized through an incident surface of the prism on the adsorption layer at an angle of incidence of a p-wave anti-reflection state; and a polarized light detecting member for detecting a change in the polarization of reflected light.
    [2]
    The device for simultaneously feeding molecules bonding characteristic and refractive index of a buffer defrost according to claim 1, further comprising a thin dielectric layer disposed between the substrate and the adsorption layer, and the thin dielectric layer is made of a transparent semiconductor oxide layer or a glass layer, and its thickness is larger than 0 —1000 nm.
    [3]
    Device for simultaneous feeding of molecular bonding characteristic and refractive index of a buffer solution, comprising a microchannel structural unit provided with a substrate made of a substrate and a semiconductor or a dielectric material formed on the substrate, a roof portion with a flat plate structure fixed to the substrate and a microchannel formed either at a top of the substrate or at a bottom of the roof portion; a sample spray portion for injecting a buffer debris containing a biomaterial sample into the microchannel to form an adsorption layer of the sample on the substrate; a polarized light generating member for straining incident light, polarized through an incident surface of the planar plate to the adsorption layer at an angle of incidence of a p-wave anti-reflection state; and a polarized light detecting member for detecting a change in the polarization of reflected light when the reflected light enters a reflecting surface of the planar plate from the adsorption layer.
    [4]
    The device for simultaneously feeding molecules bonding characteristic and refractive index of a buffer solution according to claim 1 or 2, wherein the adsorption layer is a multilayer layer consisting of a self-assembled monolayer for binding characteristics of varying biomaterials, an immobilizing substance and a bonding material .
    [5]
    The device for simultaneously feeding molecules the binding characteristic and refractive index of a buffer solution according to claim 1 or 2, wherein the generating part for polarized light comprises a light source configured to stratify a desired light and a polarizer configured to polarize the radiated light.
    [6]
    The device for simultaneous feeding of molecular binding characteristics and refractive index of a buffer solution according to claim 5, wherein the light source is arranged to stratify monochromatic light or white light.
    [7]
    The device for simultaneously feeding motekylar bonding characteristic and refractive index of a buffer solution according to claim 5, wherein the light source is a laser or a laser diode.
    [8]
    The device for simultaneously feeding molecules the binding characteristic and refractive index of a buffer solution according to claim 5, wherein the light source is a laser or a laser diode, which has a variable wavelength shape.
    [9]
    The device for simultaneously feeding molecules the binding characteristic and refractive index of a buffer solution according to claim 5, wherein the generating part for polarized light comprises at least one of a collimator lens, for providing parallel light to the polarizer; a focusing lens for converting the parallel lights passing through the polarizer to increase the quantity of incident light; and a first compensator for effecting phase shift in polarized components of the incident light.
    [10]
    The device for simultaneous feeding of molecular binding characteristics and refractive index of a buffer solution according to claim 9, wherein the polarizer and the first compensator are rotatable or have an additional polarization modulation device.
    [11]
    A microchannel structural unit for use in an apparatus for simultaneously feeding molecular bonding characteristics and refractive indices of a buffer solution, the microchannel structural unit comprising a substrate; a substrate made of a semiconductor or a dielectric material and formed on one side of the substrate; a tack part with a prismatic structure fixed to the substrate; and a microchannel formed either in a top of the substrate or in a bottom of the roof portion; wherein the buffer solution containing a biomaterial sample is injected into the microchannel to form an adsorption layer on the substrate, incident light polarized through an incident surface of the prism is irradiated on the adsorption layer at an angle of incidence of a 26 p-way anti-reflection state, and light reflected by adsorption surface of the prism.
    [12]
    A microchannel structure unit for use in a device for simultaneously feeding molecules bonding characteristics and refractive index of a buffer solution, the microchannel structure unit comprising a substrate; a substrate made of a semiconductor or a dielectric material and formed on one side of the substrate; a thin dielectric layer provided on the substrate; a tack part with a prismatic structure fixed to the substrate; and a microchannel formed either in a top of the substrate or in a bottom of the roof portion; wherein the buffer solution containing a biomaterial sample is injected into the microchannel to form an adsorption layer on the thin dielectric layer on the substrate, incident light polarized by an incident surface of the prism is irradiated on the adsorption layer at an angle of incidence of a p-wave anti-reflection state, and light reflection state. from the adsorption layer is emitted through a reflecting surface of the prism.
    [13]
    The microchannel structure unit according to claim 11 or 12, wherein the microchannel is a multichannel type of microchannel having a plurality of inflow waves and a plurality of effluent waves, respectively formed on one side and the other side of the substrate, and having a valve arranged to prevent the sample from mixing with the buffer solution and a plurality of partitions formed at the bottom of the prism through which respective inflow valves and outflow valves are connected.
    [14]
    The microchannel structural unit of claim 12, wherein the microchannel is formed as a single channel type of microchannel, and a plurality of different self-assembled monolayers are disposed on the thin dielectric layer to adsorb the sample.
    [15]
    A system for simultaneous analysis of molecular bonding characteristic and refractive index of a buffer solution, comprising a microchannel structure unit provided with a substrate made of a substrate and a semiconductor or a dielectric material formed on the substrate, a roof portion having a prismatic structure fixed to the substrate and a microchannel formed either in a top of the substrate or in a bottom of the roof portion; a sample spray portion for injecting a buffer solution containing a biomaterial sample into the microchannel to form an adsorption layer of the sample on the substrate; a polarizing light generating member for straining incident light, polarized through an incident surface of the prism on the adsorption layer at an angle of incidence of a p-wave anti-reflection state; and a polarized light detecting portion for detecting a change in the polarization of reflected light when the reflected light enters a reflecting surface of the prism tan adsorption layer; and an analyzing means electrically coupled to the polarized light detecting member for analyzing the refractive index of the buffer laser and the molecular binding characteristic of the sample based on the polarization change.
    [16]
    The system for simultaneous analysis of molecular bonding characteristic and refractive index of a buffer laser according to claim 15, wherein the polarizing light detecting part comprises an analyzer configured to polarize reflected light, and a light detector which detects the polarized and reflected light to obtain optical data.
    [17]
    The system simultaneously analyzes molecular binding characteristics and refractive indices of a buffer solution according to claim 16, wherein the light detector is one of a CCD type solid state imaging element, a photomultiplier tube and a silicon photodiode.
    [18]
    The system for simultaneous analysis of molecular bonding characteristic and refractive index of a buffer solution according to claim 16, wherein the analyzing means comprises a processor which is electrically connected to the light detector for calculating the value based on the optical data, and wherein the processor calculates an ellipsometric constant on a phase difference in ellipsometry to determine the refractive index of the buffer solution, and calculates an ellipsometric constant on an amplitude ratio to determine the value including an adsorption concentration of the sample, an adsorption and dissociation constant of the sample.
    [19]
    The system for simultaneous analysis of molecular binding characteristics and refractive index has a buffer solution according to claim 15, wherein the polarized light detecting part further comprises at least one of a second compensator for phase rotation of polarized components has the reflected light and a spectrometer to dissolve it. reflected the light.
    [20]
    The system for simultaneous analysis of molecular binding characteristics and refractive index has a buffer solution according to claim 19, wherein the analyzer and the second compensator are rotatable, or have an additional polarization modulation device.
    [21]
    A method for simultaneously feeding molecules bonding characteristics and refractive index has a buffer solution comprising a first step (S100) by injecting a buffer solution containing low molecular weight biomaterial samples, into a microchannel having a microchannel structure unit, through a sample spray portion; a second step (S200) of forming an adsorption layer by adsorption of the sample on a substrate having the microchannel structure unit; a third step (S300) of polarizing a desired light through a polarizing light generating member and receiving the light on the adsorption layer at an angle of incidence satisfying a p-wave anti-reflection state through an incident surface having a prism of the microchannel structure unit; a fourth step (S400) of polarizing desired light through the polarized light generating member and receiving light reflected from the adsorption layer on the polarized light detecting member at an angle of incidence satisfying the anti-reflection state of the p-path through an incident window of the microchannel structure unit; and a fifth step (S500) of detecting the polarization has the reflected light through the polarized light detecting part using ellipsometry or reflectometry.
    [22]
    The method for simultaneously feeding the molecular binding characteristic and refractive index of a buffer solution according to claim 21, wherein the fifth step (S500) comprises the steps of polarizing the reflected light with an analyzer, detecting the polarized and reflected light with a light detector for obtaining the desired optical data, and observing an ellipsometric constant on a phase difference in ellipsometry by means of analysis based on the optical data, to determine the refractive index of the buffer solution, and calculating an ellipsometric constant on an amplitude ratio to determine the value of adsorption including the sample, an adsorption and dissociation constant of the sample.
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    引用文献:
    公开号 | 申请日 | 公开日 | 申请人 | 专利标题
    AT30780T|1981-06-22|1987-11-15|Battelle Memorial Institute|METHOD FOR DETERMINING BIOACTIVE SUBSTANCES.|
    US4999014A|1989-05-04|1991-03-12|Therma-Wave, Inc.|Method and apparatus for measuring thickness of thin films|
    US5501637A|1993-08-10|1996-03-26|Texas Instruments Incorporated|Temperature sensor and method|
    US6277330B1|1996-09-30|2001-08-21|Aventis Research & Technologies Gmbh & Co K.G.|Optical sensor for detecting chemical substances dissolved or dispersed in water|
    FR2809491B1|2000-05-26|2008-07-04|Production Rech S Appliquees|METHOD AND APPARATUS FOR ELLIPSOMETRIC METROLOGY FOR SAMPLE CONTAINED IN A CHAMBER OR THE LIKE|
    DE10126152C2|2001-05-30|2003-12-24|Inst Mikrotechnik Mainz Gmbh|Spatially resolved ellipsometry method for the quantitative and / or qualitative determination of sample changes, biochip and measuring arrangement|
    CN1195230C|2003-06-27|2005-03-30|清华大学|Protein microarray surface plasma resonance imaging detection system and detection method|
    CN1312476C|2004-08-27|2007-04-25|清华大学|Method and system for detecting biological chip by space phase modulation interference array|
    KR100742982B1|2006-06-22|2007-07-26|케이맥|Focused-beam ellipsometer|
    GB0721482D0|2007-11-01|2007-12-12|Univ Exeter|Plasmon resonance based sensor|
    JP5422841B2|2008-07-08|2014-02-19|国立大学法人長岡技術科学大学|Determination method and determination apparatus for determining biocompatibility between biomolecules and ceramics|
    KR101105328B1|2009-11-23|2012-01-16|한국표준과학연구원|Apparatus and method for quantifying the binding and dissociation kinetics of molecular interactions|CN104568767A|2015-01-19|2015-04-29|国家纳米科学中心|Microfluidic in-situ liquid environment measurement system based on ellipsometer as well as measurement method and application of system|
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    申请号 | 申请日 | 专利标题
    KR1020120114097A|KR101383652B1|2012-10-15|2012-10-15|Apparatus and method for simultaneously quantifying the binding kinetics and refractive index of molecular interactions|
    PCT/KR2013/008656|WO2014061924A1|2012-10-15|2013-09-27|Apparatus and method for simultaneously measuring characteristics of molecular junctions and refractive index of buffer solution|
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