WO2010013335A1 - Dispositif réactionnel et procédé associé - Google Patents

Dispositif réactionnel et procédé associé Download PDF

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Publication number
WO2010013335A1
WO2010013335A1 PCT/JP2008/063744 JP2008063744W WO2010013335A1 WO 2010013335 A1 WO2010013335 A1 WO 2010013335A1 JP 2008063744 W JP2008063744 W JP 2008063744W WO 2010013335 A1 WO2010013335 A1 WO 2010013335A1
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WO
WIPO (PCT)
Prior art keywords
magnetic field
magnetic body
capillary
magnetic
sample
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Application number
PCT/JP2008/063744
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English (en)
Japanese (ja)
Inventor
アダルシュ サンドゥー
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株式会社フォスメガ
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Priority to PCT/JP2008/063744 priority Critical patent/WO2010013335A1/fr
Publication of WO2010013335A1 publication Critical patent/WO2010013335A1/fr

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    • B—PERFORMING OPERATIONS; TRANSPORTING
    • B01—PHYSICAL OR CHEMICAL PROCESSES OR APPARATUS IN GENERAL
    • B01L—CHEMICAL OR PHYSICAL LABORATORY APPARATUS FOR GENERAL USE
    • B01L3/00—Containers or dishes for laboratory use, e.g. laboratory glassware; Droppers
    • B01L3/50—Containers for the purpose of retaining a material to be analysed, e.g. test tubes
    • B01L3/502—Containers for the purpose of retaining a material to be analysed, e.g. test tubes with fluid transport, e.g. in multi-compartment structures
    • B01L3/5027—Containers for the purpose of retaining a material to be analysed, e.g. test tubes with fluid transport, e.g. in multi-compartment structures by integrated microfluidic structures, i.e. dimensions of channels and chambers are such that surface tension forces are important, e.g. lab-on-a-chip
    • B01L3/50273—Containers for the purpose of retaining a material to be analysed, e.g. test tubes with fluid transport, e.g. in multi-compartment structures by integrated microfluidic structures, i.e. dimensions of channels and chambers are such that surface tension forces are important, e.g. lab-on-a-chip characterised by the means or forces applied to move the fluids
    • B—PERFORMING OPERATIONS; TRANSPORTING
    • B01—PHYSICAL OR CHEMICAL PROCESSES OR APPARATUS IN GENERAL
    • B01F—MIXING, e.g. DISSOLVING, EMULSIFYING OR DISPERSING
    • B01F31/00—Mixers with shaking, oscillating, or vibrating mechanisms
    • B01F31/42—Mixers with shaking, oscillating, or vibrating mechanisms with pendulum stirrers, i.e. with stirrers suspended so as to oscillate about fixed points or axes
    • B—PERFORMING OPERATIONS; TRANSPORTING
    • B01—PHYSICAL OR CHEMICAL PROCESSES OR APPARATUS IN GENERAL
    • B01F—MIXING, e.g. DISSOLVING, EMULSIFYING OR DISPERSING
    • B01F33/00—Other mixers; Mixing plants; Combinations of mixers
    • B01F33/30—Micromixers
    • B—PERFORMING OPERATIONS; TRANSPORTING
    • B01—PHYSICAL OR CHEMICAL PROCESSES OR APPARATUS IN GENERAL
    • B01F—MIXING, e.g. DISSOLVING, EMULSIFYING OR DISPERSING
    • B01F33/00—Other mixers; Mixing plants; Combinations of mixers
    • B01F33/45—Magnetic mixers; Mixers with magnetically driven stirrers
    • B01F33/453—Magnetic mixers; Mixers with magnetically driven stirrers using supported or suspended stirring elements
    • 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
    • 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
    • G01N33/54366—Apparatus specially adapted for solid-phase testing
    • B—PERFORMING OPERATIONS; TRANSPORTING
    • B01—PHYSICAL OR CHEMICAL PROCESSES OR APPARATUS IN GENERAL
    • B01L—CHEMICAL OR PHYSICAL LABORATORY APPARATUS FOR GENERAL USE
    • B01L2400/00—Moving or stopping fluids
    • B01L2400/04—Moving fluids with specific forces or mechanical means
    • B01L2400/0403—Moving fluids with specific forces or mechanical means specific forces
    • B01L2400/043—Moving fluids with specific forces or mechanical means specific forces magnetic forces
    • B—PERFORMING OPERATIONS; TRANSPORTING
    • B01—PHYSICAL OR CHEMICAL PROCESSES OR APPARATUS IN GENERAL
    • B01L—CHEMICAL OR PHYSICAL LABORATORY APPARATUS FOR GENERAL USE
    • B01L2400/00—Moving or stopping fluids
    • B01L2400/04—Moving fluids with specific forces or mechanical means
    • B01L2400/0475—Moving fluids with specific forces or mechanical means specific mechanical means and fluid pressure
    • B01L2400/0484—Cantilevers

Definitions

  • the present invention relates to a reaction apparatus and method using a capillary in which probe molecules that cause a specific binding reaction with a target substance are fixed on the inner surface.
  • Patent Document 1 discloses an affinity detection / analysis chip and a detection system having a structure in which a plurality of capillaries each having a probe molecule that causes a specific binding reaction with an analyte to be immobilized are bundled. Is disclosed.
  • a sample containing a molecule to be detected is caused to flow inside a plurality of capillaries, and a specific binding reaction is caused with a probe molecule on the inner surface of the capillary to cause the molecule to be detected to be detected. Connect to the inner surface of the capillary. Then, the presence or absence of binding inside the capillary is observed and analyzed using an absorption observation device.
  • the target substance is contained inside the capillary. It is necessary to provide a general pump such as a syringe pump or a piston pump outside the capillary in order to flow a fluid (sample).
  • the present invention has been made in view of such circumstances, and a binding reaction can be obtained in a short throughput time using a capillary in which probe molecules that cause a specific binding reaction with a target substance are immobilized on the inner surface. It is another object of the present invention to provide a new reaction apparatus and method which can efficiently react with a small amount of sample.
  • the reaction apparatus of the present invention is arranged in the fluid in a state where a capillary in which probe molecules that cause a specific binding reaction with the target substance are fixed on the inner surface and a fluid containing the target substance is introduced into the capillary
  • end motion means for moving the fluid to stir.
  • the end motion means applies an AC magnetic field so that the direction of the magnetic field rotates 360 ° in a plane including the flow path, and the magnetic body operates like a conical pendulum with the one end as a fulcrum. Further, the other end can be moved in a substantially circular motion within the plane.
  • the columnar magnetic body may be generated by magnetically coupling a plurality of magnetic particles into a columnar shape by the DC magnetic field.
  • a columnar magnet disposed in the fluid is introduced in a state where a fluid containing the target substance is introduced into a capillary in which probe molecules that cause a specific binding reaction with the target substance are fixed on the inner surface.
  • An end fixing step of fixing one end of the body within the target device using a DC magnetic field, and the other end of the columnar magnetic body moving so as to stir the fluid using an AC magnetic field A stirring step.
  • reaction apparatus and method of the present invention it is possible to efficiently react with a small amount of sample using a capillary in which probe molecules that cause a specific binding reaction with a target substance are fixed on the inner surface.
  • FIG. 1 (A) is a diagram schematically showing a schematic configuration of a reaction apparatus 1 according to an embodiment of the present invention.
  • the reaction apparatus 1 includes a microcapillary tube 10 having probe molecules 51 that cause a specific binding reaction with a target substance 50 (for example, a physiologically active substance such as protein or DNA) fixed to the inner surface, and a microcapillary.
  • a flow path (circulation path) 11 that connects both ends of the tube 10 is provided.
  • a plurality of microcapillary tubes 10 may be integrated and used.
  • the X axis is assigned in the direction from the left to the right of the drawing, the Y axis in the direction from the bottom to the top, and the Z axis in the direction from the near side to the back.
  • the microcapillary tube 10 can be manufactured using a conventional technique (for example, Patent Document 1). Specifically, the microcapillary tube 10 is manufactured using a material such as a glassy material (quartz glass, borosilicate glass), an organic material, a plastic material (polyetheretherketone, polyethylene, polypropylene), or a carbon nanotube.
  • the size may be, for example, an inner diameter of about 10 to 100 micrometers and a length of about 1 mm to 5 mm.
  • the channel 11 is a channel for circulating a fluid (for example, gas, liquid, gel, etc .; selected according to the purpose; hereinafter referred to as “sample”) containing the target substance 50, and the microcapillary tube 10.
  • sample for example, gas, liquid, gel, etc .; selected according to the purpose; hereinafter referred to as “sample”
  • the sample discharged from one end (outlet end 12) is allowed to flow to the other end (inlet end 13).
  • the flow path 11 can be formed using various materials such as glass, silicon, and plastic as in the prior art, and the size can be determined according to the size of the microcapillary tube 10.
  • An inlet path 14 for introducing a sample into the reaction apparatus 1 is connected to the vicinity of the inlet end 13 of the microcapillary tube 10 so that the sample does not flow into the inlet path during circulation.
  • a valve (not shown) is provided.
  • FIG. 1 (B) is a diagram schematically showing the state of the microcapillary tube 10 in a state where the sample is introduced into the reaction apparatus 1.
  • the probe molecule 51 may be a complementary molecule that causes a specific binding reaction with the target substance 50, and can be appropriately selected according to the design as in the prior art. Specifically, DNA, RNA, antigen, antibody, enzyme, protein or the like can be used depending on the target substance 50.
  • the probe molecule 51 can be fixed to the inner surface of the microcapillary tube 10 with a linker substance, as in the prior art.
  • a linker substance for example, glutaraldehyde
  • a reactive group for example, a silanol group
  • a mode in which a linker substance (for example, succinic acid) is bonded to the reacted group and the probe molecule 51 is synthesized on the linker substance can be considered.
  • the reaction apparatus 1 of the present embodiment further introduces a sample into the reaction apparatus 1 (specifically, into the microcapillary tube 10 and the flow path 11).
  • the magnetic body 20 arranged in the sample in the state, and an end fixing means 31 and an end motion means 32 are provided as a control device 30 for controlling the behavior of the magnetic body 20.
  • the end fixing means 31 is arranged on the Z axis plus direction side in the drawing with respect to the microcapillary tube 10, and the end movement means 32 is arranged on the Y axis minus direction side in the drawing.
  • These means can be arranged at arbitrary positions according to the design as long as they can apply a DC magnetic field 40 and AC magnetic fields 41 and 42 described later.
  • FIG. 2 schematically shows the structure of the magnetic body 20.
  • the magnetic body 20 is formed by magnetically coupling a plurality of magnetic particles 21 in a columnar shape, and includes two end portions 22 and 23 corresponding to both ends of the column.
  • One end 22 of the magnetic body 20 is fixed in contact with the microcapillary tube 10 by an end fixing means 31 as described later.
  • the other end 23 of the magnetic body 20 is not fixed, and is controlled so as to reciprocate by the end motion means 32 as will be described later.
  • the magnetic particles 21 can be manufactured using conventional techniques, and may be particles of a composition containing a magnetic material in addition to particles of the magnetic material itself.
  • the magnetic particles 21 can take various shapes such as granular, plate-like, box-like, and needle-like (for example, magnetic carbon nanotube (CNT)).
  • the size is the size of the microcapillary tube 10 and the type of sample. It can be determined according to the required liquid feeding ability and stirring ability (in this application, the term “liquid feeding” is used even when the sample is other than liquid).
  • the end fixing means 31 is a device that applies a DC magnetic field 40 in a direction substantially perpendicular to the pipe line direction of the microcapillary tube 10 (for example, the Z-axis minus direction in the coordinate system shown in FIG. 1) (FIG. 3 ( A)).
  • a DC magnetic field 40 in a direction substantially perpendicular to the pipe line direction of the microcapillary tube 10 (for example, the Z-axis minus direction in the coordinate system shown in FIG. 1) (FIG. 3 ( A)).
  • Such a device can be realized by controlling a permanent magnet, an electromagnet, and the like with a controller, as in the prior art.
  • the magnetic body 20 of the present embodiment is formed using the above phenomenon. That is, after the magnetic particles 21 are introduced and dispersed in the sample, the DC fixing magnetic field 40 is applied to the microcapillary tube 10 by the end fixing means 31 in a direction substantially orthogonal to the pipe direction of the microcapillary tube 10. The magnetic particles 21 are magnetically coupled in a columnar shape with the magnetic field incident side as the bottom (fixed end 22), and the magnetic body 20 is formed.
  • a magnetic particle or a magnetic thin film may be provided in advance on the magnetic field incident side of the microcapillary tube 10.
  • the attaching method can use a conventional technique such as adhesion.
  • the magnetic particles 21 are magnetically coupled so that the magnetic particles attached in advance are at the bottom of the column, the formation position of the magnetic body 20 can be designated in advance.
  • the end motion means 32 applies an alternating magnetic field 41 substantially parallel to the pipe direction of the microcapillary tube 10 (the Y-axis direction in the coordinate system shown in FIG. 1), and also has a predetermined plane (for example, FIG. 1).
  • the AC magnetic field 42 is applied so that the direction of the magnetic field rotates 360 ° within the XY plane in the coordinate system shown in FIG. 3 (see FIGS. 3B and 3C).
  • Such a device can be realized by controlling a magnetic field generated by an alternating current with a controller, as in the prior art.
  • the end portion 23 of the magnetic body 20 is not fixed to the microcapillary tube 10 and therefore moves under the influence of the alternating magnetic field 41 applied by the end motion means 32.
  • the end moving means 32 can be fixed to the microcapillary tube 10 under the influence.
  • the strength of the DC magnetic field 40 applied by the end fixing means 31 is set to be sufficiently larger than the strength of the AC magnetic field 41 applied by.
  • Example 1 In Example 1, the reaction efficiency is improved by causing the magnetic body 20 to act as a nanopump.
  • magnetic particles 21 are mixed and dispersed in a sample containing the target substance 50 (step 1).
  • the sample in which the magnetic particles 21 are dispersed is introduced into the reaction apparatus 1 (microcapillary tube 10) from the introduction path (step 2).
  • a DC magnetic field 40 is applied by the end fixing means 31 in a direction substantially orthogonal to the pipe line direction of the microcapillary tube 10 (step 3).
  • the DC magnetic field 40 is applied in the negative Z-axis direction in the coordinate system shown in FIG.
  • the magnetic particles 21 dispersed in the sample are fixed (bottomed) on the back side surface (the surface on the Z-axis plus direction side) of the microcapillary tube 10 on which the DC magnetic field is incident.
  • the magnetic body 20 is formed by magnetic coupling in the form of a column as the end 22).
  • the distance (interval between the end portions 22) and the height (number of bonds of the magnetic particles 21) of the magnetic bodies 20 formed on the back side surface of the microcapillary tube 10 are the diameter, magnetic moment, and type (Fe, Co, Ni, etc.).
  • the specific spacing and height can be determined according to the size of the microcapillary tube 10, the type of sample, the required liquid feeding ability and stirring ability, the density of the probe molecules 51, and the like. it can.
  • an alternating magnetic field 41 is applied by the end motion means 32 in the liquid feeding operation mode (step 4).
  • an alternating magnetic field 41 is applied substantially in parallel to the pipe line direction of the microcapillary tube 10 (Y-axis direction in the coordinate system shown in FIG. 1).
  • the end portion 23 of the magnetic body 20 causes the direction of the AC magnetic field 41, that is, the Y-axis minus direction (liquid feeding direction) and the Y-axis plus direction (liquid feeding direction) in the coordinate system shown in FIG. Reciprocate in the opposite direction).
  • the reciprocating motion of the end portion 23 can be controlled by the waveform of the alternating magnetic field 41 to be applied.
  • the moving speed of the end portion 23 during the forward movement is higher than the moving speed during the backward movement.
  • the waveform of the AC magnetic field 41 can be set. Specifically, during the forward movement, the waveform of the AC magnetic field 41 is set so that a relatively steep magnetic field gradient (change in magnetic flux density) is generated, and the end 23 is controlled to move at a relatively high speed. To do. Further, during the backward movement, the waveform of the AC magnetic field 41 is set so that a relatively gentle magnetic field gradient is generated, and the end portion 23 is controlled to move at a relatively slow speed.
  • the magnetic body 20 is like a pendulum with the fixed end portion 22 as a fulcrum. It works to feed the sample (functions as a nanopump). By such a liquid feeding action, the sample circulates through the microcapillary tube 10 and the flow path 11 in a certain direction.
  • FIG. 4 schematically shows how the magnetic body 20 in the sample functions as a nanopump.
  • 4A is a view of the columnar magnetic body 20 viewed from the side
  • FIG. 4B is a view of the columnar magnetic body 20 viewed from above.
  • the magnetic body 20 in each drawing is schematically shown, and the dimensional ratio is not limited to the illustrated ratio.
  • the moving speed difference of the reciprocating motion in the liquid feeding operation mode can be determined according to the type of sample and the required liquid feeding capacity. Moreover, what is necessary is just to stop the application of the alternating current magnetic field 41, when a liquid feeding effect becomes unnecessary. Since the reaction apparatus 1 of Example 1 can send a sample according to the behavior of the magnetic body 20 in the sample, a conventional pump apparatus is unnecessary. As a result, the sample that passes through the piping in the pump device, which has been necessary in the past, is no longer necessary, so that the sample utilization efficiency can be improved. Further, since the mechanical part called the pump device can be eliminated, it is possible to avoid shortening the apparatus life due to a failure of the mechanical part.
  • the magnetic body 20 acting as a nanopump is dispersed in the sample in the microcapillary tube 10, the liquid feeding can be accurately controlled over the entire microcapillary tube 10, and as a result, the microcapillary tube 10. Since the sample can be smoothly circulated in the inside, the throughput time until the binding reaction is obtained can be shortened.
  • the target substance 50 and the probe molecule can be obtained without increasing the amount of sample introduced into the reaction apparatus 1.
  • the chance of combining with 51 can be increased.
  • Example 2 In Example 2, the reaction efficiency is improved by causing the magnetic body 20 to act as a nanopump and a nanostirrer.
  • steps 1 to 4 are the same as those in the first embodiment.
  • the end motion means 32 switches between step 4 and the following step 5 and repeatedly executes both steps.
  • step 5 the AC magnetic field 42 is applied by the end motion means 32 in the stirring operation mode.
  • the application direction and strength of the AC magnetic field 42 in the stirring operation mode can be determined according to the type of sample and the required stirring ability.
  • the waveform of the AC magnetic field 42 can be set so that the end 23 rotates 360 degrees in a predetermined plane (for example, the XY plane in the coordinate system shown in FIG. 1) (FIG. 3). (See (C)).
  • a predetermined plane for example, the XY plane in the coordinate system shown in FIG. 1
  • FIG. 3 See (C)
  • the end portion 23 of the magnetic body 20 moves in a substantially circular motion within the plane.
  • the magnetic body 20 operates like a conical pendulum with the fixed end 22 as a fulcrum, and acts to stir the fluid (functions as a nanostirrer).
  • FIG. 5 schematically shows how the magnetic body 20 in the sample functions as a nanostirrer.
  • 5A is a view of the columnar magnetic body 20 viewed from the side
  • FIG. 5B is a view of the columnar magnetic body 20 viewed from above.
  • the magnetic body 20 in each drawing is schematically shown, and the dimensional ratio is not limited to the illustrated ratio.
  • the rotation speed of the magnetic field in the stirring operation mode can be determined according to the type of sample and the required stirring ability. Further, when the stirring action becomes unnecessary, the application of the alternating magnetic field 42 may be stopped. Moreover, the execution time of step 4 and step 5 may be different, and the execution time of each step may be changed with the passage of time. .
  • the reaction apparatus 1 of Example 2 can exhibit the same operational effects as Example 1. Furthermore, by controlling the alternating magnetic field 42 applied to the microcapillary tube 10, the magnetic body 20 can function as a nanostirrer and the sample can be stirred in the microcapillary tube 10, so that it is introduced into the reaction apparatus 1. The binding chance between the target substance 50 and the probe molecule 51 can be increased without increasing the amount of the sample.
  • the present invention is not limited to the above embodiment and can be applied in various modifications.
  • the AC magnetic fields 41 and 42 are uniformly applied to the entire microcapillary tube 10, but a configuration in which an AC magnetic field is locally applied may be employed.
  • an AC magnetic field may be applied uniformly or locally to the flow path 11. That is, a DC magnetic field is applied in a direction substantially orthogonal to the liquid feeding direction of the flow path 11 by the end fixing means, and an AC magnetic field is applied in a direction corresponding to the liquid feeding direction of the flow path 11 by the end moving means.
  • the magnetic body 20 arranged in the sample in the flow channel 11 can act as a nanopump or a nanostirrer.
  • Example 1 describes an aspect in which the magnetic body 20 acts as a nanopump
  • Example 2 describes an aspect in which the magnetic body 20 acts as a nanopump and a nanostarr. You may employ
  • the reaction apparatus may be configured to have a configuration for detecting the presence or absence of binding of the target substance in the microcapillary tube 10 and a configuration for processing the detection result.
  • a method for detecting the presence or absence of binding an aspect using an absorption observation device as in the prior art, an aspect in which the amount of binding is determined based on a change in impedance of the microcapillary tube 10, and the like can be considered.
  • the liquid feeding function and the agitation function can be realized by controlling the behavior of the magnetic body 20 in the sample, so that it can be widely applied to various reaction apparatuses using capillaries. Can be used.
  • FIG. 1 is a diagram illustrating a schematic configuration of a microcapillary tube 10 in a state where a reaction apparatus 1 according to an embodiment of the present invention and a sample are introduced into the reaction apparatus 1.
  • FIG. FIG. 6 is a diagram for explaining a magnetic body 20. It is a figure for demonstrating the DC magnetic field 40 and the AC magnetic fields 41 and 42 which are applied by the edge part fixing means 31 and the edge movement means 32.
  • FIG. It is a figure for demonstrating the magnetic body 20 which functions as a nanopump. It is a figure for demonstrating the magnetic body 20 which functions as a nanostirrer.

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Abstract

La présente invention concerne un dispositif réactionnel inédit et un procédé par lequel une réaction peut être efficacement mise en œuvre en utilisant une petite quantité d'échantillon grâce à l'utilisation d'un capillaire comportant une molécule sonde capable d'induire une réaction de liaison spécifique avec une substance cible, ladite molécule sonde ayant été fixée sur la face intérieure du capillaire. Plus précisément, l'invention concerne un dispositif réactionnel comprenant un capillaire comportant une molécule sonde capable d'induire une réaction de liaison spécifique avec une substance cible, ladite molécule sonde ayant été fixée sur la face intérieure du capillaire ; un corps magnétique en forme de tige, à cause duquel lorsqu'un fluide contenant la substance cible décrite ci-dessus est introduit dans le capillaire décrit ci-dessus, dans le fluide décrit ci-dessus, une unité de fixation d'une extrémité permettant de fixer une extrémité du corps magnétique en forme de tige comme décrit plus haut dans le capillaire décrit plus haut au moyen d'un champ magnétique continu et une unité de déplacement d'une extrémité permettant de déplacer l'autre extrémité du corps magnétique en forme de tige comme décrit plus haut en utilisant un champ magnétique alternatif permettent l'agitation du fluide décrit ci-dessus.
PCT/JP2008/063744 2008-07-31 2008-07-31 Dispositif réactionnel et procédé associé WO2010013335A1 (fr)

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Cited By (4)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
WO2013170048A1 (fr) * 2012-05-09 2013-11-14 Advanced Animal Diagnostics, Inc. Détection rapide d'analytes dans des échantillons liquides
US9052315B2 (en) 2012-05-09 2015-06-09 Advanced Animal Diagnostics, Inc. Rapid detection of analytes in liquid samples
US9797893B2 (en) 2013-05-09 2017-10-24 Advanced Animal Diagnostics, Inc. Rapid detection of analytes in liquid samples
US10359614B2 (en) 2012-07-03 2019-07-23 Advanced Animal Diagnostics, Inc. Diagnostic apparatus

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JPS601793Y2 (ja) * 1980-08-25 1985-01-18 日本電気ホームエレクトロニクス株式会社 液体の撹拌装置
JP2003504195A (ja) * 1999-07-19 2003-02-04 オルガノン・テクニカ・ベー・ヴエー 磁性粒子を流体と混合するための装置および方法
JP2003248008A (ja) * 2001-12-18 2003-09-05 Inst Of Physical & Chemical Res 反応液の攪拌方法
JP2004534243A (ja) * 2001-07-09 2004-11-11 ビオムリュー、エス．エー 磁性粒子の処理方法及び磁石を用いた生物学的分析装置
WO2006079998A1 (fr) * 2005-01-31 2006-08-03 Koninklijke Philips Electronics N.V. Biodetection rapide et sensible

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Publication number Priority date Publication date Assignee Title
JPS52100657A (en) * 1976-02-20 1977-08-23 Gorou Yabe Mixing method and apparatus therefor
JPS601793Y2 (ja) * 1980-08-25 1985-01-18 日本電気ホームエレクトロニクス株式会社 液体の撹拌装置
JPS58210863A (ja) * 1982-06-03 1983-12-08 株式会社富士電機総合研究所 移動磁界式処理装置のワ−キングピ−ス
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WO2006079998A1 (fr) * 2005-01-31 2006-08-03 Koninklijke Philips Electronics N.V. Biodetection rapide et sensible

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WO2013170048A1 (fr) * 2012-05-09 2013-11-14 Advanced Animal Diagnostics, Inc. Détection rapide d'analytes dans des échantillons liquides
US9052315B2 (en) 2012-05-09 2015-06-09 Advanced Animal Diagnostics, Inc. Rapid detection of analytes in liquid samples
US9482670B2 (en) 2012-05-09 2016-11-01 Advanced Animal Diagnostic, Inc. Rapid detection of analytes in liquid samples
US10359614B2 (en) 2012-07-03 2019-07-23 Advanced Animal Diagnostics, Inc. Diagnostic apparatus
US9797893B2 (en) 2013-05-09 2017-10-24 Advanced Animal Diagnostics, Inc. Rapid detection of analytes in liquid samples

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