Source: https://patents.google.com/patent/JP5553367B2/en
Timestamp: 2020-08-07 19:12:01
Document Index: 345835783

Matched Legal Cases: ['Application No. 2007', 'Application No. 2007', 'art 13', 'art 13', 'art 13', 'art 19', 'art 18', 'art 18', 'art 19', 'art 9', 'art 17', 'art 9', 'arts 20', 'art 20', 'art 22', 'art 3', 'art 13', 'art 9', 'art)\n8', 'art 11', 'art 24', 'art 100']

JP5553367B2 - Incubator and gene detection / judgment device - Google Patents
Incubator and gene detection / judgment device Download PDF
JP5553367B2
JP5553367B2 JP2012082488A JP2012082488A JP5553367B2 JP 5553367 B2 JP5553367 B2 JP 5553367B2 JP 2012082488 A JP2012082488 A JP 2012082488A JP 2012082488 A JP2012082488 A JP 2012082488A JP 5553367 B2 JP5553367 B2 JP 5553367B2
JP2012082488A
JP2012125262A (en
正晃 地野
僚子 今川
秀一 明石
栄二 山本
勝博 戸丸
一 茂木
2007-06-29 Priority to JP2007171867 priority Critical
2007-06-29 Priority to JP2007171867 priority
2007-07-20 Priority to JP2007189627 priority
2012-03-30 Application filed by 凸版印刷株式会社, 独立行政法人理化学研究所 filed Critical 凸版印刷株式会社
2012-03-30 Priority to JP2012082488A priority patent/JP5553367B2/en
2012-07-05 Publication of JP2012125262A publication Critical patent/JP2012125262A/en
2014-07-16 Publication of JP5553367B2 publication Critical patent/JP5553367B2/en
238000006243 chemical reaction Methods 0.000 claims description 213
238000001816 cooling Methods 0.000 claims description 97
229920003013 deoxyribonucleic acids Polymers 0.000 description 15
238000003825 pressing Methods 0.000 description 13
238000000504 luminescence detection Methods 0.000 description 2
The present invention relates to an incubator.
This application claims priority based on Japanese Patent Application No. 2007-171867 filed in Japan on June 29, 2007 and Japanese Patent Application No. 2007-189627 filed on July 20, 2007 in Japan. These contents are incorporated herein by reference.
In recent years, it has been clarified that by examining individual DNA polymorphisms and nucleotide sequence polymorphisms, information on the metabolic rate and side effects of individual drugs can be obtained. For this reason, there is an increasing need for genetic diagnosis in the medical field. Among various DNA polymorphisms, single nucleotide polymorphism (SNP) is currently often detected.
As a typing method for determining the SNP, a polymerase chain reaction method (PCR) for amplifying a gene region containing SNP using DNA polymerase, an invader method performed using a structure-specific DNA degrading enzyme, etc. are suitably used alone. Or it is done in combination.
As a determination device for gene diagnosis performed by the above method, a device having a configuration as shown in Patent Document 1 is used. That is, temperature adjustment for gene amplification reaction and temperature adjustment for typing are performed using two heat blocks. Then, the sample after the amplification reaction is transferred using a nozzle and dispensed into a plurality of reaction units in which probes for specifying SNPs are arranged. And it is the structure by which measurements, such as a fluorescence measurement, are performed from the downward direction with respect to the sample arrange | positioned at the reaction part.
PCR (Polymerase Chain Reaction) and polymerase chain reaction are widely used as techniques for amplifying DNA (genes) in large quantities in a short time from biological samples containing nucleic acids such as DNA collected from blood or specimens. Yes.
In the PCR reaction, double-stranded DNA is dissociated into single-stranded DNA at high temperature, and then the temperature is lowered to anneal the primer to single-stranded DNA. Then, double-stranded DNA is newly synthesized by polymerase using single-stranded DNA as a template. By repeating these steps, DNA is amplified. As an example of the temperature cycle, there is one that repeats several tens of times at 95 ° C. for about 1 minute, 37 ° C. for several tens of seconds, and 65 ° C. for several seconds to several minutes as one cycle.
In the PCR reaction, it is necessary to repeatedly raise and lower the temperature of the sample in this way. For this reason, almost the entire reaction time is determined by the number of cycles of temperature increase / decrease required to reach the desired gene amplification amount (number of cycles) and the speed of temperature increase / decrease to the target temperature required for the PCR reaction. Is done.
In addition, after amplifying a gene, the type of the gene may be discriminated by fluorescence emission or electrochemical detection by using a chemical, biological, or electrically acting reagent.
Some gene types are discriminated at a constant temperature. In this case, the heating means used in the PCR reaction is also used for gene type discrimination. Thereby, it is possible to reduce the number of components of the incubator and to realize downsizing of the apparatus.
In recent years, it has been made clear that by examining an individual's genotype, information on the metabolic rate and side effects of the individual drug can be obtained. For this reason, there is an increasing need for small and rapid genetic diagnosis (genotype discrimination) in the medical field.
As such an incubator, for example, a reaction block that holds a reaction sample is moved between a heating block heated by a heater and a cooling block cooled by a cooling device to control the temperature of the reaction sample, thereby performing a PCR reaction. (See Patent Documents 2 and 3).
JP 2006-275820 A JP-A-6-277036 JP 2000-270837 A
However, in the determination apparatus of Patent Document 1, heat blocks are provided at two locations, and a dispensing mechanism for moving the nozzle is also essential. For this reason, there exists a problem that a certain size or more is needed as an apparatus.
In addition, when a sample is dispensed into the reaction part using a nozzle, there is a possibility that so-called contamination occurs in which dirt on the tip of the nozzle or DNA in the air enters the reaction part. As a result, there is also a problem that an error may occur in the measurement result.
In addition, even when a dispensing mechanism is not used, if a reagent or sample is manually dispensed on a reaction vessel such as a DNA chip installed in the above-described determination device in order to perform a plurality of reactions, an operation error, etc. Human error and the above-mentioned contamination may occur.
Further, the conventional incubators such as Patent Documents 2 and 3 have the following problems.
A horizontal movement device for moving the reaction block holding the reaction sample in the horizontal direction to move the reaction block to one of the heating block or the cooling block, and the horizontally moved reaction block in the vertical direction A vertical movement device is required to move and bring the reaction block into contact with the heating block or cooling block and away from them. For this reason, there existed a problem that the structure of an apparatus became complicated and size reduction was difficult.
The reaction sample absorbs and dissipates heat from the heating block or the cooling block through the reaction block. For this reason, the rate of temperature increase or the rate of temperature decrease becomes slow by the heat capacity of the reaction block. For this reason, there existed a problem that PCR reaction time became long and it was difficult to perform a rapid gene diagnosis.
Furthermore, since the heating block and the cooling block are set to target temperatures in advance, when the temperature of the reaction sample approaches the temperature of the heating block or the cooling block, the temperature difference between the sample and the heating block or the cooling block becomes small. . For this reason, there is a problem that it is difficult to raise and lower the temperature of the sample at a high speed.
The present invention has been made in view of such circumstances, and an object thereof is an incubator that can be easily downsized with a simple configuration, and can shorten the PCR reaction time by controlling the temperature of the reaction sample at high speed. Is to provide.
The present invention employs the following configuration.
(1) a container containing a reaction sample; a heat transfer block that holds the container on which the container is placed; a heater that is in close contact with the heat transfer block and heats the heat transfer block; A cooling device provided so as to be movable between a contact position in contact with the heater and a separated position away from the heater, and contacting the heater at the contact position to cool the heat transfer block; and a moving device for moving the contact position and the spaced position; and chip boards retractable recess formed therein said container; wherein the heat transfer block disposed in the chip base of said recess, said An opening opened toward the cooling device is formed in the recess, and the heater is a plate-shaped incubator penetrating the opening.
(2) Moreover, the said incubator may take the following structures.
The heater is in close contact with the lower surface of the heat transfer block, the cooling device contacts the lower surface of the heater at the contact position, and the moving device supports the cooling device from at least one of the lower side and the lateral direction. To do.
(3) Moreover, the said incubator may take the following structures.
The moving device includes an air cylinder.
(4) Moreover, the said incubator may take the following structures.
The moving device includes an electromagnetic actuator.
(5) Moreover, the said incubator may take the following structures.
The heat transfer block includes a heat conductive material.
(6) Moreover, the said incubator may take the following structures.
The heater includes a ceramic material having a high thermal conductivity.
(7) Moreover, the said incubator may take the following structures.
The ceramic material includes aluminum nitride, aluminum oxide, silicon carbide, or silicon nitride.
(8) Moreover, the said incubator may take the following structures.
The cooling device has a contact surface that contacts the heater, and a thermally conductive sheet is attached to the contact surface.
(9) Moreover, the said incubator may take the following structures.
The cooling device includes a heat sink.
(10) The incubator may have the following configuration.
The heat sink has a conduit through which fluid flows, and the heat sink is cooled by cooling water that flows through the conduit and circulates.
(11) The incubator may have the following configuration.
The heat sink has a conduit through which fluid flows, and the heat sink is cooled by a refrigerant having a boiling point lower than a predetermined cooling temperature that circulates through the conduit.
(12) The incubator may have the following configuration.
The cooling device includes a heat sink and a fan that cools the heat sink.
(13) The incubator may have the following configuration.
The cooling device includes: a metal block that transfers heat to the heater; a heat absorption surface that absorbs heat and a heat dissipation surface that dissipates heat, and the heat absorption surface is in contact with the metal block; and is closely attached to the heat dissipation surface of the Peltier element And a heat sink that cools the heat sink.
(14) The incubator may have the following configuration.
The metal block includes a heat conductive material.
(15) The incubator may have the following configuration.
The cooling device includes: a Peltier element having a heat absorbing surface for absorbing heat and a heat radiating surface for radiating heat; a heat sink that is in close contact with the heat radiating surface of the Peltier element; and a fan that cools the heat sink.
The present invention may employ the following configurations.
(16) A container having a reaction vessel and containing a reaction sample; a Peltier element having an endothermic surface that absorbs heat and a heat radiating surface that dissipates heat; a contact position at which the Peltier element and the container are in contact via a thermally conductive sheet And a heat sink provided so that the Peltier element is movable between a spaced position away from the container; a moving device that moves the heat sink to the contact position and the spaced position; and a container installation in which the container is installed And a pair of rails having a gap capable of accommodating the container and holding the container installation part, the container installation part having a frame-like installation part on which the container is installed; The installation part has a holding part that extends horizontally into the frame of the installation part that forms a frame shape and holds the outer peripheral part of the container, and the container installation part includes: , The above In a state that span Le, by the moving mechanism that moves the transport unit for moving the container installation section along the rails, move along the rail, the container in the gap of the pair of rails An incubator for holding the Peltier element toward the Peltier element.
(17) The present invention may employ the following configuration.
The incubator according to (16) above, a moving mechanism that moves the container installation section along the rail, a reaction tank division section that deforms the reaction tank and divides it into a plurality of reaction chambers, and the container installation section And a measurement unit that measures the reaction in each of the reaction chambers, and is provided so as to be movable in parallel with the upper surface of the container installed in the container installation unit.
Further, according to the incubator of the present invention, when the reaction sample is heated, the heat transfer block holding the container for storing the reaction sample is rapidly heated by the heater provided in close contact with the heat transfer block. . At this time, the cooling device is in a separated position away from the heater by the moving device. On the other hand, when the reaction sample is cooled, the moving device immediately moves the cooling device to the contact position with the heater, and the cooling device immediately cools the heat transfer block via the heater. Therefore, the reaction sample can be heated or cooled rapidly, and the temperature of the reaction sample can be controlled at high speed.
Also, only the moving device that moves the cooling device to the contact position and the separation position becomes the movable member. Therefore, the apparatus configuration can be simplified and the apparatus can be easily downsized.
FIG. 1 is a perspective view showing a gene detection / determination apparatus according to a first embodiment of the present invention. FIG. 2 is a perspective view showing a state where the cover of the gene detection / determination apparatus is removed. FIG. 3A is a plan view showing an example of a reaction vessel used in the gene detection / determination apparatus. FIG. 3B is a front view showing an example of a reaction vessel used in the gene detection determination apparatus. FIG. 4 is a perspective view showing a moving table of the gene detection / determination apparatus. FIG. 5 is a block diagram illustrating a configuration of the gene detection determination apparatus. FIG. 6 is a flowchart showing a genetic diagnosis procedure by the gene detection / determination apparatus. FIG. 7A is a diagram illustrating an operation of a sealing unit of the gene detection determination device. FIG. 7B is a diagram illustrating an operation of a sealing unit of the gene detection determination device. FIG. 7C is a diagram illustrating an operation of a sealing unit of the gene detection determination device. FIG. 8 is a diagram illustrating the operation of the temperature adjustment unit of the gene detection determination device. FIG. 9 is a diagram illustrating the operation of the measurement unit of the gene detection determination device. FIG. 10 is a diagram illustrating a configuration of the incubator according to the second embodiment. FIG. 11 is a diagram illustrating a configuration of the incubator according to the third embodiment. FIG. 12 is a diagram illustrating a configuration of the incubator according to the fourth embodiment. FIG. 13 is a diagram illustrating a configuration of an incubator according to the fifth embodiment. FIG. 14 is a diagram illustrating a configuration of the incubator according to the sixth embodiment. FIG. 15 is a diagram illustrating a configuration of an incubator according to the seventh embodiment. FIG. 16 is a diagram illustrating a configuration of an incubator according to the eighth embodiment.
Hereinafter, a gene detection determination apparatus (hereinafter simply referred to as “determination apparatus”) according to a first embodiment of the present invention will be described with reference to FIGS. 1 to 9.
FIG. 1 is a perspective view of the determination apparatus 1. The determination apparatus 1 includes a determination apparatus main body 1A and a personal computer 2 connected to the determination apparatus main body 1A. The personal computer 2 has a display unit 3 such as a display. The upper part of the determination apparatus main body 1A is covered with a cover 4 to prevent contamination and the like. A front portion of the cover 4 is provided with a sample loading door 5 that is opened and closed when a reaction container to be described later is installed, and an instrument display unit 6 that displays the state of the determination device 1. The device display unit 6 displays various states and information such as the presence / absence of an abnormality in the determination apparatus 1 and the current process.
FIG. 2 is a perspective view showing a state in which the cover 4 of the determination apparatus main body 1A is removed. The determination apparatus 1 heats and cools the reaction vessel, a movable table (container installation portion) 7 on which the reaction vessel is installed, a reaction vessel dividing unit 8 that divides a reaction vessel of the reaction vessel described later into a plurality of reaction chambers. A temperature adjusting unit (heating / cooling unit) 9 and a measuring unit 10 for measuring the reaction of the reaction vessel are provided.
The moving table 7 is moved above the reaction tank dividing unit 8 and the temperature adjusting unit 9 along a rail 12 installed on the upper surface of the determination apparatus 1 by a moving mechanism 11 having a known configuration such as a stepping motor or a servo motor. It is configured to be able to. The rail 12 of this embodiment is installed linearly from the vicinity of the sample loading door 5 toward the back.
In addition to the above-described configuration, the moving mechanism 11 is appropriately selected from the configurations of known moving mechanisms such as a combination of a stepping motor and a belt, or a configuration in which the rail 12 and the moving table 7 are moved using magnetic force or the like. Can be used. The moving mechanism 11 of the determination apparatus 1 according to the present embodiment is configured using a stepping motor and an endless belt.
FIG. 3A is a plan view showing an example of a reaction vessel installed in the determination apparatus 1, and FIG. 3B is a front view thereof. In the reaction vessel 100, a plurality of groove-like reaction vessels 102 are arranged on a substrate 101 made of resin or the like in a substantially parallel manner. Each reaction tank 102 is filled with a necessary amount of reagents used for PCR reaction and typing reaction in advance. The upper surface is covered with an upper surface cover 101A made of resin or the like in order to prevent contamination. In addition, a predetermined space is secured so that a sample containing a gene can be added as will be described later.
The reagent may contain an enzyme. These reagents can be placed in a desired shape according to the placement requirement in the reaction vessel, such as dry state (including freeze-drying, heat drying, etc.), gel, powder, etc., and sealed with wax or the like. It may be stopped and arranged.
As shown in FIG. 3A, the upper surface cover 101A at both ends of each reaction vessel 102 is provided with an inlet 103 and an air outlet 104, respectively. When a sample is injected from the inlet 103 by a syringe or the like, air in each reaction tank 102 escapes from the vent 104 and the sample is placed in each reaction tank 102.
The upper surface cover 101A of the reaction vessel 100 is formed of a material that has low autofluorescence and transmits excitation light and fluorescence, and the substrate 101 and the reaction vessel 102 do not transmit excitation light and fluorescence and have good thermal conductivity. Is preferably formed. Instead of selecting the material, the bottom surface may be colored so as not to transmit excitation light or fluorescence. Moreover, it is preferable that the reaction vessel 100 is formed of a material having a certain degree of flexibility so that large deformation and cracking do not occur in the reaction vessel dividing step described later.
FIG. 4 is a perspective view showing the movable table 7. The movable table 7 includes a frame-shaped installation unit 13 on which the reaction vessel 100 is installed, a container cover 14 for fixing the reaction vessel 100 installed on the installation unit 13, and a transport unit 15 installed on the rail 12. Have.
The installation part 13 has a holding part 13A that extends horizontally in the frame, and is fixed to the movable table 7 by holding the outer peripheral part of the reaction vessel 100 on the holding part 13A. Therefore, the lower surface of the reaction vessel 100 is not covered with the moving table 7, and the bottom surface of each reaction vessel 102 is exposed and fixed.
The container cover 14 is fixed to the installation unit 13 so as to be freely opened and closed by a hinge or the like, and fixes the reaction vessel 100 installed in the installation unit 13 from above. The moving table 7 moves along the rails 12 in a state of straddling the plurality of rails 12 as the transport unit 15 on the rails 12 is moved by the moving mechanism 11.
Returning to FIG. 2, the reaction tank dividing unit 8 is provided between the rails 12, that is, on the track on which the moving table 7 moves. The reaction tank dividing unit 8 includes a pressing block 16 that can move in the vertical direction, and an arch portion 17 provided above the pressing block 16.
The pressing block 16 is provided with a plurality of projecting portions that project to a portion positioned directly below each reaction tank 102 when the reaction vessel 100 on the moving table 7 is positioned directly above the pressing block 16. As will be described later, the protruding portion deforms the reaction tank 102 and divides it into a plurality of reaction chambers when the pressing block 16 rises.
The arch portion 17 includes a vertical portion 17A that extends upward from the left and right sides of the rail 12, and a top plate portion 17B that is provided so as to bridge the upper end of the vertical portion 17A. The area of the top plate portion 17B is set to a size that covers the entire reaction vessel 100 installed on the movable table 7, and functions as a press that is abutted when the press block 16 is raised.
The top plate portion 17B may be provided with a convex portion that has substantially the same area as the opening portion of the installation portion 13 of the movable table 7 on which the reaction vessel 100 is installed and protrudes toward the reaction vessel 100 side. In this way, the reaction vessel 100 can be held and pressed more reliably.
The temperature adjusting unit 9 includes an electric heater, a ceramic heater, a laser, a halogen lamp, a heating unit 18 including various heaters such as an infrared type, a microwave type, a warm air type, an induction electric heating (IH) type, and the like. It has the cooling part 19 which is provided under the part 18 and consists of an electric fan, a heat sink, a cold wind type cooler, or the like. As needed, you may comprise the heating part 18 and the cooling part 19 using a Peltier device.
The temperature adjusting unit 9 is installed between the rails 12 separated from the reaction tank dividing unit 8 by a predetermined distance, that is, on the track of the moving table 7 so as to be movable in the vertical direction. And it raises with respect to the moving stand 7 which moved and stopped above the temperature control part 9, and contacts the lower surface of the reaction container 100, ie, the bottom face of each reaction tank 102. The temperature adjusting unit 9 heats or cools the reaction vessel 100 by the heating unit 18 and the cooling unit 19 to realize a temperature cycle necessary for PCR and to maintain a constant temperature necessary for typing reaction (warming).
If necessary, a metal foil, silicon grease, or the like may be disposed between the temperature control unit 9 and the reaction vessel 100 to improve thermal conductivity. The temperature adjustment of the temperature adjustment unit 9 is performed by a control unit described later.
An additional arch 17 is provided on the temperature control unit 9, and the temperature control unit 9 and the reaction vessel 100 are pressed by the temperature control unit 9 and the arch unit 17, thereby ensuring that the temperature control unit 9 and the reaction vessel are in contact with each other. Can do.
Moreover, the arch part 17 can be made into one place, and it can also comprise so that the press block 16 and the temperature control part 9 may move.
Further, the arch portion 17 can be installed so as to cover the temperature adjusting portion 9 and the pressing block 16.
The measurement unit 10 includes a light emission detection unit 20 that introduces excitation light and measures fluorescence, and a measurement unit moving mechanism 21 that moves the light emission detection unit 20.
The light emission detection unit 20 includes several optical fibers for excitation light (not shown) for introducing excitation light, and several detection optical fibers (not shown) for measuring (detecting) fluorescence generated by the excitation light. , It is configured to be bundled together. The determination apparatus 1 is provided with light emission detection units 20 at two locations. The number of the light emission detection parts 20 can be increased / decreased suitably according to the speed required for photometry.
The excitation light source can be appropriately selected from known mechanisms such as a light emitting diode (LED) and a laser diode. In the determination apparatus 1 of the present embodiment, for example, LEDs having a wavelength range of 400 to 600 nanometers are used.
In addition, the wavelength of excitation light can select suitably a wavelength required for the fluorescent pigment | dye (fluorescent substance) of a measuring object.
Connected to the detection optical fiber is a photomultiplier tube (PMT, not shown) that converts the collected fluorescence into voltage or current and measures the fluorescence intensity. The light emission detection unit 20 of the present embodiment includes two systems of PMTs having a wavelength range of 530 and 610 nanometers, for example. The PMT may be appropriately increased or decreased depending on the number of wavelengths to be measured. In place of the PMT, a photoelectric conversion element using a CCD, a photodiode, or the like may be used.
Note that the measurement wavelength of the light emission detector 20 may be changed as appropriate according to the fluorescent dye (fluorescent substance) to be measured.
Moreover, you may install the filter and the lens for condensing in the light emission detection part 20 as needed.
Furthermore, the luminescence detection unit 20 may be configured to detect chemiluminescence, bioluminescence, phosphorescence, or the like instead of fluorescence. In this case, when the light source for excitation becomes unnecessary depending on the detection target, the configuration may be changed as appropriate.
The measurement unit moving mechanism 21 is composed of a known motor or the like, similarly to the moving mechanism 11 that moves the moving table 7. The measurement unit moving mechanism 21 includes an X-axis moving unit 21A that moves the light emission detection unit 20 in the X-axis direction (the forward and backward direction of the moving table 7), and a Y-axis movement that moves in the Y-axis direction (the width direction of the rail 12). The unit 21B is combined. Thus, the light emission detection unit 20 can move above each reaction vessel 102 in parallel with the upper surface of the reaction vessel 100 on the moving table 7 stopped above the temperature adjustment unit 9.
The measurement unit moving mechanism 21 may be configured by further combining a mechanism that moves the light emission detection unit 20 in the Z axis (vertical direction) as necessary so that the position of the light emission detection unit 20 can be finely adjusted.
FIG. 5 is a block diagram illustrating an example of a connection between the units of the determination device 1. As shown in FIG. 5, the device display unit 6, the moving mechanism 11, the reaction tank dividing unit 8, the temperature adjusting unit 9, and the measuring unit 10 are connected to a control unit 22 that controls the entire determination apparatus 1. The control unit 22 is also connected to a determination unit 23 that performs determination based on the fluorescence intensity acquired by the measurement unit 10 and a reading unit 24 that reads information on the reaction vessel 100.
The control unit 22 performs the operation of each of the above-described mechanisms connected, the management of the PCR temperature cycle and the heat insulation temperature in the temperature adjustment unit 9, and the like. The control unit 22 may be provided inside or outside of the determination apparatus main body 1A. When provided inside, it may be mounted in the form of a micro CPU, ROM, RAM, programmable logic controller (PLC), or the like. When provided outside, for example, it may be stored as a control program such as software in the personal computer 2 connected to the determination apparatus main body 1A. Furthermore, the control part 22 may be distributed and installed inside and outside the determination apparatus main body 1A.
The determination unit 23 is stored in the personal computer 2 having the display unit 3. The determination unit 23 includes a determination parameter, an algorithm, a determination database, and the like corresponding to the genetic polymorphism to be measured. The determination unit 23 performs a predetermined determination as to whether the measured SNP site is homo-type or hetero-type based on the fluorescence intensity value obtained by the light emission detection unit 20 of the measurement unit 10 and the above-described determination parameters, etc. The result is displayed on the display unit 3.
The database may not be included in the determination unit 23. For example, a database of another terminal may be searched via the Internet, or a plurality of sites on the Internet may be referred to.
In addition, as information in the above database, there are information that should be considered by doctors during medication, such as information on cases and medications related to measured SNP sites, package inserts and interactions with related drugs, and emergency safety information (doctor letters). May be included. And such information may be displayed on the display part 3 with a determination result.
The reading unit 24 reads various information such as the measurement target of the reaction container and the sample number from the information recording unit provided in the reaction container 100. As the information recording unit, a two-dimensional barcode, RFID (Radio frequency Identification), IC chip, IC tag, or the like can be used. Various types of read information are displayed on the display unit 3 together with the determination result, or used for organizing data such as the determination result. The various types of information may be displayed on the device display unit 6 as necessary.
The operation at the time of use of the determination apparatus 1 configured as described above will be described below.
FIG. 6 is a flowchart showing a genetic diagnosis procedure using the determination apparatus 1. First, in the reaction container installation step of step S1, the reaction container 100 into which the sample has been injected is installed on the installation unit 13 of the moving table 7 by opening the sample loading door 5, and the container cover 14 is installed. After mounting the container cover, the sample loading door 5 is closed.
Sample injection into the reaction vessel 100 is performed by injecting a DNA sample obtained by nucleic acid extraction or the like by applying pressure from the injection port 103 of the reaction vessel 100 with a syringe or the like. The injected sample is arranged substantially uniformly in each reaction vessel 102 and mixed with the reagent in the reaction vessel.
When the reaction vessel has a nucleic acid extraction function, steps such as nucleic acid extraction can be omitted.
The moving table 7 on which the reaction vessel 100 is installed moves on the rail 12 to above the reaction tank dividing unit 8 by the moving mechanism 11 and stops.
Next, in the reaction vessel dividing step of step S2, as shown in FIG. 7A, the pressing block 16 of the reaction vessel dividing unit 8 rises and contacts the lower surface of the reaction vessel 100. The pressing block 16 further moves upward and abuts the reaction vessel 100 against the arch portion 17 with a predetermined pressure.
Each reaction tank 102 is sandwiched between a plurality of projecting portions 16A on the pressing block 16 and the top plate portion 17B of the arch portion 17, and is crushed by pressure and plastically deformed as shown in FIG. 7B. Depending on the material of the reaction vessel 100, the reaction chamber 105 can be formed without plastic deformation.
As a result, each reaction vessel 102 is divided into a plurality of independent reaction chambers 105, and a reaction can be performed in each reaction chamber.
After the formation of the reaction chamber 105, the pressing block 16 is lowered and returned to a predetermined position as shown in FIG. 7C, and the moving table 7 on which the reaction vessel 100 is installed moves the temperature adjustment unit on the rail 12 by the moving mechanism 11. Move to above 9 and stop.
In the subsequent amplification reaction step of step S3, DNA is amplified by PCR by adjusting the temperature, and typing reaction is performed by the invader method.
First, as shown in FIG. 8, the temperature control unit 9 rises and contacts the lower surface of the reaction vessel 100 (not shown). The temperature adjusting unit 9 heats or cools the reaction vessel 100 to a predetermined temperature based on the control of the control unit 22. The heating is performed by energizing the heating unit 18 (not shown), and the cooling is performed by stopping the energization to the heating unit 18 or changing the energization conditions to dissipate heat through the cooling unit 19. .
As will be described later, when a refrigerant is used, the temperature is adjusted by stopping the supply of the refrigerant or changing the supply amount instead of energization. This adjustment amount is separately stored in the control unit 22 in advance.
As a result, the solution in each reaction chamber 105 of the reaction vessel 100 is heated a plurality of times, for example, 30 cycles in a predetermined temperature cycle, and the PCR reaction proceeds, and is kept at a predetermined temperature, for example, about 60 ° C. for about 2 minutes. The typing reaction proceeds. After completion of the typing reaction, the temperature control unit 9 descends and stops.
As an amplification method and a typing reaction method, other known methods such as ICAN method, UCAN method, LAMP (Loop-mediated isothermal Amplification) method may be used in addition to the above-described methods.
In the measurement process of step S4, the sample after the typing reaction in each reaction chamber 105 is irradiated with excitation light from the luminescence detection unit 20, and the fluorescence intensity corresponding to the SNP site is measured.
Specifically, as shown in FIG. 9, the measurement unit 10 is moved while scanning the upper part of each reaction chamber 105 (not shown) of a reaction vessel 100 (not shown), and excitation light is emitted by the light emission detection unit 20. And measure fluorescence. The measurement result acquired by the light emission detection unit 20 is transmitted to the determination unit 23.
The measurement data (measurement result) may be transmitted to the determination unit 23 after measuring all the measurement data, or the measurement data may be sequentially transmitted. When data is accumulated until batch transmission, the determination apparatus 1 may be provided with a storage medium such as a memory. The connection between the determination apparatus main body 1A and the personal computer 2 can be freely selected, such as wireless or wired. However, it is preferable that the determination apparatus main body 1A and the personal computer 2 be wired.
In addition to the above, various external storage devices, USB (Universal Serial Bus) memory, hard disk, CD-ROM, DVD-ROM, etc. can be used as a method for taking out the measurement results from the judgment device main body 1A to the outside (including the personal computer 2). It can also be used.
After the measurement of all the reaction chambers 105 is completed, the measurement unit 10 returns to the original position and stops, and proceeds to the determination process of step S5.
The measurement step may be performed before the typing reaction in the amplification reaction step described above, or may be started at almost the same time as the start and the scan may be performed a plurality of times until the typing reaction sufficiently proceeds.
Further, the measurement step may be performed after the PCR reaction is completed and held at a constant temperature for a certain time.
That is, each process shown in FIG. 6 does not necessarily mean that each process is performed independently and in the order shown in FIG. 6, and includes a case where a plurality of processes are performed in chronological order. .
In the case described above, the time until the end of the PCR reaction and the typing reaction is separately measured for each measurement target and input to the control unit 22 in advance.
In the determination step, the fluorescence intensity value acquired by the measurement unit 10 is determined by the determination unit 23 based on a determination algorithm adapted to the measurement target SNP. A determination result indicating whether the SNP site is homo-type or hetero-type is displayed on the display unit 3 of the personal computer 2. At this time, if necessary, the above-mentioned related information can be searched from the database inside and outside the determination apparatus 1 and displayed on the display unit 3 together with the determination result.
After the determination step, the moving table 7 returns on the rail 12 toward the sample loading door 5, moves to the position where the moving table 7 was installed in step S1, and stops. Thus, a series of steps is completed.
According to the determination apparatus 1 of the present embodiment, the reaction vessel 102 of the reaction vessel 100 is plastically deformed by the reaction vessel dividing unit 8, and the DNA amplification reaction and the typing reaction are performed in each divided reaction chamber 105, and then continuously. Measurement is performed. Accordingly, since it is not necessary to transfer the sample by a nozzle or the like, it is possible to eliminate the risk of occurrence of contamination accompanying the sample transfer. Further, since it is not necessary to provide a mechanism for dispensing or the like, the apparatus can be miniaturized.
In addition, the reaction vessel 100 is installed and fixed on the moving table 7 with the bottom surface of each reaction vessel 102 exposed, and moves across the rail 12, so that the reaction vessel dividing unit 8 and the temperature adjusting unit 9 are connected to the reaction vessel 100. Each process can be performed by approaching from below. Therefore, the operation space of the reaction vessel dividing unit 8 and the temperature adjusting unit 9 can be saved, and the apparatus configuration can be further simplified.
Furthermore, since the temperature control unit 9 performs two types of temperature control, that is, temperature cycle control for PCR and heat retention for typing reaction, the determination device 1 can be configured only by providing a temperature control mechanism in one place. . Therefore, the determination apparatus 1 can be further downsized.
In addition, in the case of a configuration in which the determination unit 23 displays the safety information of the drug related to the SNP on the display unit 3 together with the determination result, the determination result can be immediately used for daily clinical practice. It is possible to contribute to providing medical care more suitable for the patient.
For example, in the above-described embodiment, the measurement unit may not be provided and the measurement may be performed by an external measurement device.
Further, for example, in the above-described embodiment, the example in which the reaction tank dividing unit 8 plastically deforms the reaction tank 102 by pressure to divide the reaction tank 102 into a plurality of reaction chambers 105 has been described, but the determination apparatus of the present invention is limited to this. Not. The reaction vessel 102 may be deformed by heating or the like, or may be deformed by being chemically cured by a temperature change, light rays such as visible light, ultraviolet light, or the like. Moreover, these methods may be combined as appropriate.
Further, when the reaction tank 102 is configured to be deformed by heating, the reaction tank dividing unit 8 and the temperature adjusting unit 9 are integrated with each other by providing a cooling mechanism to the pressing block 16 of the reaction tank dividing unit 8. It is good also as a structure. If it does in this way, after dividing | segmenting a reaction tank into several reaction chambers, it can transfer to an amplification reaction process, without moving a reaction container, and can further promote size reduction and speeding-up of an apparatus.
In the case of such a configuration, amplification and measurement can be performed while maintaining the divided shape of the reaction chamber with the pressing block 16. For this reason, the reaction vessel 100 that does not undergo plastic deformation can be used.
In the above-described embodiment, an example in which the rail 12 is linear has been described. However, the rail 12 may be appropriately bent or meandered according to the arrangement of each mechanism. However, it is preferable to form it in a straight line because the distance of the rail 12 can be made the shortest and the apparatus can be configured simply and compactly.
Furthermore, instead of using a rail to configure the track, the track may be configured as follows.
For example, a driving means (for example, a motor and wheels) is provided on the moving table 7 to be self-propelled, a guide rail is installed along the side surface of the moving table 7 instead of the rail, and a stopper such as a claw type is appropriately provided at a necessary place And the movable table 7 may be configured to be locked at a necessary place.
Further, in addition to the track of the present embodiment, an auxiliary track may be installed above (in the air) the track, and the moving table 7 may be held at two points, the track and the auxiliary track in the air.
Furthermore, instead of the track of the present embodiment, the auxiliary track is used as a main track, and a driving unit is provided separately from the moving table 7, and the moving table 7 is suspended and suspended from the driving unit to perform various processes (temperature adjustment, The reaction vessel may be moved to a place where the reaction tank division or the like is performed and the processing may be performed.
Further, in the above-described embodiment, the example in which the reaction vessel is arranged horizontally and the reaction vessel dividing unit 8 and the temperature adjusting unit 9 approach from the lower side of the reaction vessel has been described. It is not limited to. For example, the reaction vessel is arranged such that the upper and lower surfaces of the reaction vessel are positioned in the left-right direction of the determination device 1, and the reaction vessel dividing unit 8 and the temperature adjusting unit 9 are configured to approach the reaction vessel from the left-right direction of the determination device 1. May be. In this case, the reaction vessel temperature adjusting unit 9 performs heating and cooling from either one or both of the upper surface side and the lower surface side of the reaction vessel.
Furthermore, in the above-described embodiment, an example in which the temperature adjusting unit 9 performs heating and cooling for amplification and heat insulation for typing reaction has been described. Instead, the temperature adjusting unit performs the heating and cooling described above. The determination device may be configured so that the temperature control mechanism is provided in the measurement unit and the typing reaction and measurement are performed by the measurement unit. In this case, if only an object that can be measured without using the PCR method is set as a measurement object, it is not necessary to install the temperature adjusting unit 9, and the number of parts can be reduced, thereby further simplifying the apparatus.
Furthermore, in the above-described embodiment, the example in which the light emission detection unit 20 is configured by the excitation light optical fiber and the detection optical fiber has been described, but instead, photoelectric conversion such as excitation LED, photodiode, or the like. An optical system such as an element may be incorporated to configure a light emission detection unit in a box shape, and measurement may be performed with a reaction container accommodated in the light emission detection unit. In this case, it is not necessary to route an optical fiber or the like, and the apparatus can be miniaturized.
Furthermore, in the above-described embodiment, the example in which the installation part 13 of the movable table 7 is a frame shape has been described. A configuration in which the periphery of the reaction vessel is sandwiched and held from above and below can also be employed.
In addition, in the above-described embodiment, an example in which a reaction vessel having a reaction vessel is used has been described. In addition, a reaction vessel having a shape in which individual reaction chambers (wells) are connected by a flow path is used. Also good. In this case, it is possible to make the wells individually independent by deforming the flow path portion via the reaction tank dividing section, and to perform necessary reactions therein.
In addition, the temperature control part 9 mentioned above can also take the structure of the following incubators in addition to the structure of the said description, or it replaces with the structure of the said description. This incubator will be described with reference to the drawings.
FIG. 10 is a diagram illustrating a configuration of the incubator according to the second embodiment.
As shown in FIG. 10, the incubator of the second embodiment stores a reaction sample in a DNA chip (container) 210 and places the DNA chip 210 on a heat transfer block 220 to heat and cool the DNA chip 210. Do. As the DNA chip, in addition to the known DNA chip, each form of the reaction container of the first embodiment can be used. The heat transfer block 220 transfers heat to the DNA chip 210 and is made of a plate-like metal having good heat conductivity. As a metal, silver, copper, gold | metal | money, aluminum, an alloy containing any of these, etc. are preferable. The heat transfer block 220 is supported by the chip base 270. The chip base 270 has an opening 270A that is slightly smaller than the heat transfer block 220, and a thin concave portion 270B that is slightly larger than the heat transfer block 220 is provided around the opening 270A. The heat transfer block 220 is housed and supported in the recess 270 </ b> B of the chip base 270. The chip table 270 is supported by support columns 274 fixed to the top of the frame 272. On the DNA chip 210, a presser 212 for placing the DNA chip 210 on the heat transfer block 220 is placed. The presser 212 is made of a heat insulating material to prevent heat dissipation from the DNA chip 210.
A plate-like heater 230 penetrating the opening 270A of the chip base 270 is provided in close contact with the lower surface of the heat transfer block 220. The heater 230 heats the heat transfer block 220. The heater 230 is preferably capable of rapid heating and rapid cooling, and is composed of, for example, a ceramic heater having high thermal conductivity. As the ceramic material, aluminum nitride, aluminum oxide, silicon carbide, silicon nitride and the like are preferable.
A cooling device 240 is provided below the heater 230. The cooling device 240 is provided so as to be movable between a contact position in contact with the heater 230 and a separated position away from the heater 230, and cools the heat transfer block 220 by contacting the heater 230 at the contact position. Below the cooling device 240, there is provided a moving device 260 that is provided on the stand 272 and supports the cooling device 240 and moves the cooling device 240 to the contact position and the separation position. The cooling device 240 has a contact surface 240A that comes into contact with the lower surface of the heater 230, and a heat conductive sheet 241 is attached to the contact surface 240A. Thereby, contact thermal resistance can be made small.
According to the second embodiment, when the reaction sample is heated, the heat transfer block 220 that holds the DNA chip 210 that stores the reaction sample is rapidly moved by the heater 230 provided in close contact with the heat transfer block 220. Heated. On the other hand, when cooling the reaction sample, the cooling device 240 contacts the heater 230, and the heat transfer block 220 is immediately cooled by the cooling device 240 via the heater 230. Since the heater 230 is made of a ceramic heater having high thermal conductivity, it quickly cools when the cooling device 240 comes into contact. Therefore, the reaction sample can be heated or cooled rapidly, and the temperature of the reaction sample can be controlled at high speed.
Note that the set temperature of the heater 230 is not necessarily set to the target temperature. For example, if the temperature is initially set higher than the target temperature and gradually lowered to the target temperature, further rapid heating can be realized. The same applies to the cooling device.
Further, only the moving device 260 that moves the cooling device 240 to the contact position and the separation position is movable. Therefore, the apparatus configuration can be simplified and the apparatus can be easily downsized.
A heater 230, a cooling device 240, and a moving device 260 are provided below the heat transfer block 220 that holds the DNA chip 210. For this reason, since there is room in the space above the DNA chip 210, it is easy to set the DNA chip 210, measure fluorescence, and the like. Therefore, an apparatus with good operability can be provided.
FIG. 11 is a diagram illustrating a configuration of the incubator according to the third embodiment.
As shown in FIG. 11, the incubator of the third embodiment uses a heat sink 242 as the cooling device 240 of the second embodiment and an air cylinder 262 as the moving device 260 of the second embodiment. The heat sink 242 is fixed to a fixing plate 264 of the air cylinder 262 via a spacer 266. A heat conductive sheet 241 is attached to the upper surface of the heat sink 242. When the reaction sample is cooled, the heat sink 242 comes into contact with the heater 230 and heat is released from the heater 230. The heat sink is made of a metal selected from aluminum, an aluminum alloy, and copper.
The other parts have the same configuration as that of the incubator of the second embodiment, and are given the same reference numerals and explanations thereof are omitted.
According to the third embodiment, since the cooling device 240 is configured by the heat sink 242, the device configuration is the simplest. Further, since the moving device 260 is constituted by the air cylinder 262, the device configuration is simplified.
In the following embodiments, an example in which the air cylinder 262 is used will be described. However, the moving device 260 is not limited to the air cylinder 262. For example, an electromagnetic actuator (solenoid), a combination of a spring and a motor, a combination of a motor and a screw screw, or the like may be used.
FIG. 12 is a diagram illustrating a configuration of the incubator according to the fourth embodiment.
As shown in FIG. 12, the incubator of the fourth embodiment is provided with a cooling fan 244 for cooling the heat sink 242 below the heat sink 242 of the incubator of the third embodiment. The heat sink 242 and the cooling fan 244 are fixed to the fixing plate 264 of the air cylinder 262 via the spacer 266.
In addition, the other part is the structure similar to the incubator of 3rd Embodiment, attaches | subjects the same code | symbol and abbreviate | omits the description.
Since the heat sink 242 simply radiates heat, if the heat sink 242 is used alone as in the third embodiment, the temperature of the heat sink 242 rises due to repeated heating and cooling, and the cooling rate becomes slow. There is.
In contrast, according to the third embodiment, since the cooling fan 244 for cooling the heat sink 242 is provided, the temperature of the heat sink 242 can be kept constant even when heating and cooling are repeated. Therefore, high-speed cooling is possible until the PCR reaction is completed.
FIG. 13 is a diagram illustrating a configuration of an incubator according to the fifth embodiment.
As shown in FIG. 13, the incubator of the fifth embodiment includes a heat sink 246 fixed to a fixing plate 264 of the air cylinder 262 via a spacer 266. The heat sink 246 is provided with a conduit (not shown) through which fluid flows, and cooling water is circulated through the conduit to cool the heat sink 246. The heat sink 246 is provided with a water supply port 246A for supplying cooling water and a drain port 246B for discharging cooling water. A heat conductive sheet 241 is attached to the upper surface of the heat sink 246.
According to the fifth embodiment, since the heat sink 246 is cooled by the circulating cooling water, the temperature of the heat sink 246 can be kept constant even if heating and cooling are repeated. Therefore, high-speed cooling is possible until the PCR reaction is completed.
Further, since the thickness of the heat sink 246 in the vertical direction can be reduced as compared with the heat sink 242 of the third embodiment, the apparatus can be downsized.
FIG. 14 is a diagram illustrating a configuration of the incubator according to the sixth embodiment.
As shown in FIG. 14, the incubator of the sixth embodiment includes a heat sink 248 fixed to a fixing plate 264 of the air cylinder 262 via a spacer 266. The heat sink 248 is provided with a pipe (not shown) through which a fluid flows. A refrigerant having a boiling point lower than the target cooling temperature circulates in the pipe and the heat sink 248 is cooled by the heat of vaporization. The heat sink 248 is provided with a supply port 248A for supplying the refrigerant and an exhaust port 248B for discharging the refrigerant. A heat conductive sheet 241 is attached to the upper surface of the heat sink 248. Examples of the refrigerant include ethyl alcohol, diethyl ether, benzene, ammonia, acetylene, liquid nitrogen and the like.
According to the sixth embodiment, since the heat sink 248 is cooled by the circulating refrigerant, the temperature of the heat sink 248 can be kept constant even if heating and cooling are repeated. Therefore, high-speed cooling is possible until the PCR reaction is completed.
Further, since the thickness of the heat sink 248 in the vertical direction can be reduced as compared with the heat sink 242 of the third embodiment, the apparatus can be downsized.
FIG. 15 is a diagram illustrating a configuration of an incubator according to the seventh embodiment.
As shown in FIG. 15, the incubator of the seventh embodiment includes a metal block 250 that cools the heater 230, and a Peltier element 252 that is provided in close contact with the metal block 250 on the lower surface of the metal block 250.
The metal block 250 is made of a metal having good thermal conductivity, and is made of silver, copper, gold, aluminum, or the like. A heat conductive sheet 241 is attached to the upper surface of the metal block 250.
The Peltier element 252 cools the heater 230 at an arbitrary temperature via the metal block 250. The Peltier element 252 has a heat absorption surface 252A and a heat dissipation surface 252B, absorbs (cools) heat from the heat absorption surface 252A, and releases heat from the heat dissipation surface 252B. An endothermic surface 252 </ b> A is in close contact with the lower surface of the metal block 250.
A heat sink 242 for cooling heat dissipation from the heat dissipation surface 252B of the Peltier element 252 is provided in close contact with the heat dissipation surface 252B of the Peltier element 252, and a cooling fan 244 for cooling the heat sink 242 is provided below the heat sink 242. Is provided.
The heat sink 242 and the cooling fan 244 are fixed to the fixing plate 264 of the air cylinder 262 via the spacer 266.
According to the seventh embodiment, since the cooling temperature can be arbitrarily set by the Peltier element 252, the cooling rate can be controlled with higher accuracy. For example, since the cooling temperature can be lowered to room temperature or less by the Peltier element 252, a higher cooling rate can be realized.
In the eighth embodiment, the following incubator is provided instead of the temperature adjustment unit 9 of the determination apparatus 1 of the first embodiment.
FIG. 16 is a diagram illustrating a configuration of the determination device 1 according to the eighth embodiment.
The incubator of the eighth embodiment includes a Peltier element 252. An incubator peltier element 252 is disposed below the movable table (container installation portion) 7.
The Peltier element 252 has a heat absorption surface 252A and a heat dissipation surface 252B, absorbs (cools) heat from the heat absorption surface 252A, and releases heat from the heat dissipation surface 252B.
Since the Peltier element 252 can switch the functions of the heat absorbing surface 252A and the heat radiating surface 252B, heating and cooling can be performed with one Peltier element 252.
A heat sink 242 for cooling heat dissipation from the heat dissipation surface 252B of the Peltier element 252 is closely attached to the heat dissipation surface 252B of the Peltier element 252, and a cooling fan 244 for cooling the heat sink 242 is provided below the heat sink 242. Is provided. A heat conductive sheet 241 is attached to the upper surface of the Peltier element 252.
In addition, the structure of the spacer 266, the air cylinder 262, and the fixed plate 264 is the same structure as the incubator of 3rd Embodiment, attaches | subjects the same code | symbol and abbreviate | omits the description.
According to the eighth embodiment, since the cooling temperature can be arbitrarily set by the Peltier element 252, the cooling rate can be controlled with higher accuracy. For example, since the cooling temperature can be lowered to room temperature or less by the Peltier element 252, a higher cooling rate can be realized.
In addition, according to the eighth embodiment, the reaction tank is deformed and divided into a plurality of reaction chambers, and high-speed and accurate heating and cooling are performed by the incubator, so that most of the detection determination work can be mechanized. For this reason, human error can be prevented and a large number of samples can be processed efficiently.
Further, according to the eighth embodiment, it is possible to shorten the time required for performing gene detection / determination and to provide a small apparatus.
That is, it is possible to reduce the size of the apparatus by placing a heating / cooling and detection mechanism around a moving table that runs on the rail. By adopting the configuration of the present invention for a heating / cooling mechanism that tends to be large, it is possible to achieve high-speed heating / cooling and downsizing at the same time.
According to the incubator of the present invention, downsizing is easy with a simple configuration, and the PCR reaction time can be shortened by controlling the temperature of the reaction sample at high speed.
1 Gene detection and judgment device 7 Moving table (container installation part)
8 Reaction tank division unit 9 Temperature control unit (heating / cooling unit)
DESCRIPTION OF SYMBOLS 10 Measurement part 11 Movement mechanism 12 Rail 23 Judgment part 24 Reading part 100 Reaction container 102 Reaction tank 105 Reaction chamber
210 DNA chip 212 Presser 220 Heat transfer block 230 Heater 240 Cooling device 260 Moving device 270 Chip base
A container containing a reaction sample;
A heat transfer block on which the container is placed and holds the container;
A heater that is in close contact with the heat transfer block and heats the heat transfer block;
A cooling device provided so as to be movable between a contact position in contact with the heater and a separated position away from the heater, and cooling the heat transfer block by contacting the heater at the contact position;
A moving device for moving the cooling device to the contact position and the separation position;
A chip base in which a recess capable of accommodating the container is formed;
Said heat transfer block disposed in the chip base of said recess,
The recess is formed with an opening opened toward the cooling device,
The heater is a plate shape penetrating the opening.
The heater is in close contact with the lower surface of the heat transfer block,
The cooling device contacts the lower surface of the heater at the contact position;
The incubator according to claim 1, wherein the moving device supports the cooling device from at least one of a lower side and a horizontal direction.
The incubator according to claim 1, wherein the moving device includes either an air cylinder or an electromagnetic actuator .
The incubator according to claim 1, wherein the heat transfer block includes a heat conductive material.
The incubator according to claim 1, wherein the heater includes a ceramic material having high thermal conductivity.
The incubator of claim 5 , wherein the ceramic material comprises aluminum nitride, aluminum oxide, silicon carbide, or silicon nitride.
The incubator according to claim 1, wherein the cooling device has a contact surface that contacts the heater, and a heat conductive sheet is attached to the contact surface.
The incubator according to claim 1, wherein the cooling device includes a heat sink.
9. The incubator according to claim 8 , wherein the heat sink has a conduit through which a fluid flows, and the heat sink is cooled by cooling water flowing through the conduit and circulating.
9. The incubator according to claim 8 , wherein the heat sink has a conduit through which a fluid flows, and the heat sink is cooled by a refrigerant having a boiling point lower than a predetermined cooling temperature that circulates through the conduit.
The incubator according to claim 1, wherein the cooling device includes a heat sink and a fan that cools the heat sink.
The cooling device is:
A metal block that conducts heat to the heater;
A Peltier element having a heat absorbing surface for absorbing heat and a heat radiating surface for radiating heat, wherein the heat absorbing surface contacts the metal block;
A heat sink in close contact with the heat dissipation surface of the Peltier element;
The incubator according to claim 1, further comprising: a fan that cools the heat sink.
The incubator according to claim 12, wherein the metal block includes a heat conductive material.
A Peltier element having an endothermic surface that absorbs heat and a heat radiating surface that dissipates heat;
A container having a reaction vessel and containing a reaction sample;
A heat sink provided movably between a contact position where the Peltier element and the container are in contact with each other via a thermally conductive sheet, and a spaced position where the Peltier element is separated from the container;
A moving device for moving the heat sink to the contact position and the separation position;
A container installation part in which the container is installed;
A pair of rails having a gap in which the container can be stored and holding the container setting portion;
The container installation part is
A frame-shaped installation part on which the container is installed;
A transporter disposed on the rail;
The installation part has a holding part that extends horizontally in a frame in the installation part in a frame shape and holds the outer peripheral part of the container,
The container installation unit moves along the rails by moving a transport mechanism that moves the container installation unit along the rails in a state of straddling the rails, and the pair of rails An incubator for holding the container toward the Peltier element in the gap.
An incubator according to claim 15;
A moving mechanism for moving the container installation portion along the rail;
A reaction vessel dividing section for deforming the reaction vessel and dividing it into a plurality of reaction chambers;
A measurement unit that is provided so as to be movable in parallel with the upper surface of the container installed in the container installation unit above the container installation unit and measures a reaction in each of the reaction chambers;
A gene detection and determination apparatus comprising:
JP2012082488A 2007-06-29 2012-03-30 Incubator and gene detection / judgment device Expired - Fee Related JP5553367B2 (en)
JP2007171867 2007-06-29
JP2007189627 2007-07-20
JP2012082488A JP5553367B2 (en) 2007-06-29 2012-03-30 Incubator and gene detection / judgment device
JP2009521610 Division 2008-06-27
JP2012125262A JP2012125262A (en) 2012-07-05
JP5553367B2 true JP5553367B2 (en) 2014-07-16
ID=40226047
JP2009521610A Expired - Fee Related JP4969650B2 (en) 2007-06-29 2008-06-27 Gene detection determination apparatus, gene detection determination method, and gene reaction apparatus
JP2012082488A Expired - Fee Related JP5553367B2 (en) 2007-06-29 2012-03-30 Incubator and gene detection / judgment device
US (1) US8828712B2 (en)
JP (2) JP4969650B2 (en)
TW (1) TW200916587A (en)
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2008-06-27 WO PCT/JP2008/061725 patent/WO2009005001A1/en active Application Filing
2008-06-27 TW TW97124006A patent/TW200916587A/en unknown
2008-06-27 JP JP2009521610A patent/JP4969650B2/en not_active Expired - Fee Related
2012-03-30 JP JP2012082488A patent/JP5553367B2/en not_active Expired - Fee Related
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JPWO2009005001A1 (en) 2010-08-26
US20100227383A1 (en) 2010-09-09
US8828712B2 (en) 2014-09-09
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