JP2015053893A - High-speed gene amplification detection device - Google Patents

Abstract

PROBLEM TO BE SOLVED: To provide a reaction control device that can perform accurate temperature control and temperature measurement and rapid raising or lowering of temperature.SOLUTION: There is provided a high-speed gene amplification detection device including: an additional mechanism capable of further stable temperature control; a pretreatment mechanism including an introduction of a reverse transcription reaction process before a PCR reaction enabling RNA detection; a melting curve analysis function; and an optical measuring function of an optimum chip technology for droplet holding and optical measurement, and of the PCR reaction.

Description

  The present invention relates to a genetic analysis apparatus using a reaction vessel suitable for conducting rapid research and clinical analysis of a very small amount of genes in basic life science, basic medical research, and medical practice, for example, animals such as humans The present invention relates to gene analysis that handles a reaction apparatus for detecting a specific base sequence at high speed from nucleic acid base sequences such as genomic DNA of plants and messenger RNA.

  Polymerase chain reaction (hereinafter abbreviated as PCR) is a method for amplifying a specific base sequence from a mixture of various types of nucleic acids. DNA templates such as complementary DNA reverse transcribed from genomic DNA or messenger RNA in the mixture, two or more primers and thermostable enzyme, salts such as magnesium, and four deoxyribonucleoside triphosphates (dATP, dCTP, dGTP, dTTP) and separating the nucleic acid, the step of binding the primer, and the step of hybridization using the nucleic acid to which the primer is bound by a thermostable enzyme as a template, are repeated at least once. The sequence can be amplified. Thermal cycling is performed by raising and lowering the temperature of the reaction vessel used for the DNA amplification reaction. There are various mechanisms for changing the temperature, but the temperature of the reaction vessel containing the sample is changed by a heater or Peltier element, heat exchange using hot air, and the reaction vessel is switched to a heater block or liquid bath at different temperatures. There is a mechanism for changing the temperature by bringing the sample into contact with each other, and a method for changing the temperature by flowing a sample in a flow path having regions of different temperatures. As the fastest commercially available device, for example, Light Cycler (Roche Cycler), for example, introduces a sample, a DNA polymerase, a DNA piece serving as a primer, and a fluorescent labeling dye for measurement into each of a plurality of glass capillary tubes. The temperature of the minute droplet in the capillary tube is changed by blowing hot air having the same temperature as the temperature of the droplet to be changed, for example, two temperatures of 55 ° C. and 95 ° C., and at the same time, the glass capillary tube It has a mechanism for irradiating the fluorescent light with excitation light of a fluorescent dye and measuring the obtained fluorescence intensity. By these methods, it is possible to repeatedly change the temperature of the sample.

  In addition, a fluid collision thermal cycler device that controls the sample temperature by causing a fluid jet to collide with the outer wall of the sample-containing region has been reported (Japanese Patent Publication No. 2001-519224 (Patent Document 1)). Therefore, in order to perform PCR at a higher speed up to now, the present inventors have used a technology for converting the temperature of a minute water droplet at a high speed by irradiating infrared light having a wavelength specifically absorbed in water, and circulating water. Have developed ultra-high-speed PCR devices that can perform temperature cycling at high speed by heat exchange with circulating water (JP 2008-278791, JP 2009-118798, WO 2010/113990, WO 2011/105507 (Patent Documents 2 to 5)). ).

Special table 2001-519224 JP 2008-278791 A JP 2009-118798 A WO2010 / 113990 WO2011 / 105507

  As described above, in the conventional technique, when a cycle between a plurality of temperatures is repeated with a rapid temperature change, 1) strict temperature control, 2) stable temperature maintenance, and 3) to a target temperature. It is difficult to achieve no overshoot when moving. For example, the rate of change of temperature in a heater or Peltier element is as slow as several degrees C per second, and in the process of reaching the target temperature due to the relationship between heat generation and heat conduction, there is no overshoot in order to reach the target temperature at high speed. It is difficult to change the temperature. Moreover, basically, when heat conduction in a solid is utilized, a thermal gradient is formed between the heat source and the surface, and thus strict control is impossible. Further, heat is taken away at the moment when the sample touches the heater or Peltier element, and a delay occurs until the surface temperature returns to the predetermined temperature. Further, when the reaction tank is brought into contact with a different heater or liquid bath, the moving mechanism is complicated, and it is difficult to control the temperature of the heater or liquid bath. Furthermore, in the method in which the sample is caused to flow through the flow paths having different temperature regions, there is a problem that the surface temperature of the flow path itself changes with the movement of the sample, making temperature control difficult. In addition, when changing the temperature by blowing warm air, it is necessary to blow a large amount of air because the heat capacity of air is small. It is difficult to strictly control the typical blowing temperature in units of 1 ° C.

  In the past, the present inventors have been able to constantly supply energy to the target using constant infrared light irradiation or hot water that is refluxed at high speed in order to continuously supply a constant amount of heat. Has developed a unique reaction control device that can perform temperature control, temperature measurement and quick temperature rise and fall. Furthermore, by combining this with a fluorescence detection system, we have developed a high-speed PCR detector that incorporates a fluorescence detection method that detects the amplification reaction in real time using a fluorescent dye whose fluorescence intensity increases with the amplification of DNA by PCR reaction. (Patent Documents 2 to 5).

  An object of the present invention is to provide a nucleic acid reaction control apparatus that can further improve these previous inventions and can perform more accurate temperature control, temperature measurement, and quick temperature increase / decrease. .

  In view of the above problems, the present invention provides a high-speed reaction control device (eg, high-speed PCR device) having an additional mechanism that enables more stable temperature control and a gene analysis or gene amplification method using the same.

That is, the present invention provides the following apparatus and method.
[1] a reaction vessel having one or more wells for containing a sample solution containing nucleic acid;
A heat sink or heat exchange chamber;
A temperature controller for the heat sink or the heat exchange bath configured to maintain the heat sink or the heat exchange bath at a first temperature;
A thermoelectric element that is disposed between the heat sink or the heat exchange tank and the reaction tank and mediates heat transfer between the heat sink or the heat exchange tank and the reaction tank;
A thermoelectric element controller that changes the temperature of the reaction vessel between the first temperature and the second temperature by controlling the operation of the thermoelectric element;
An apparatus for gene analysis or gene amplification configured such that the temperature of the reaction vessel becomes the first temperature when the operation of the thermoelectric element is off.
[2] The first temperature is a nucleic acid elongation reaction temperature,
The apparatus according to [1] above, wherein the second temperature is (i) a nucleic acid denaturation temperature, or (ii) a nucleic acid denaturation temperature or a nucleic acid annealing temperature.
[3] The temperature control device is
(I) temperature sensor,
(Ii) a thermal wire for heating the heat sink, and (iii) a feedback control mechanism for controlling power supply to the thermal wire based on temperature information of the heat sink from the temperature sensor. ] Or the apparatus according to [2].
[4] The temperature control device recirculates the liquid at the predetermined temperature between the liquid reservoir holding the liquid at the predetermined temperature and fluidly connected to the heat exchange tank through the tubular flow path and the heat exchange tank. The apparatus according to [1] or [2], wherein the apparatus is a liquid reflux type temperature control device that controls the temperature of the heat exchange tank.
[5] The thermoelectric element control device is
The apparatus according to any one of [1] to [4], further comprising: a temperature sensor; and a computer that controls the operation of the thermoelectric element based on temperature information of the reaction vessel from the temperature sensor.
[6] The apparatus according to any one of [1] to [5], wherein the thermoelectric element is a Peltier element.
[7] The above [1] to [1], further comprising a thin plate for heat conduction disposed between the thermoelectric element and the reaction tank in order to increase heat transfer efficiency between the thermoelectric element and the reaction tank. 6] The apparatus according to any one of the above.
[8] The bottom surface and wall surface of the reaction vessel are formed of metal or silicon selected from the group consisting of aluminum, nickel, magnesium, titanium, platinum, gold, silver, and copper having a thickness of 1 to 100 microns. The apparatus according to any one of [1] to [7].
[9] The device according to any one of [1] to [8], wherein the amount of the sample solution is several tens of μL or less per well.
[10] When a fluorescent dye is contained in the sample solution, the fluorescence emitted from the fluorescent dye in the well is detected in conjunction with the switching of the temperature of the reaction vessel, and the time change of the fluorescence intensity is measured. The apparatus in any one of said [1]-[9] further provided with the fluorescence detection apparatus for.
[11] The above [1] to [10], further comprising a reaction vessel frame that hermetically covers and covers the reaction vessel to prevent evaporation of the sample droplets disposed in the wells, and further includes a heat retaining member to prevent condensation. The apparatus in any one of.
[12] The reaction vessel frame further includes a hole or an optical window that facilitates measurement of an optical signal from the sample in the reaction vessel frame, and the optical window includes an optically transparent heating element. The apparatus according to [11].
[13] A column (pillar) is disposed at a sample arrangement position of each well of the reaction tank, and a sealant for preventing sample liquid evaporation is placed on the well so as to be supported by the pillar. The apparatus according to any one of [1] to [9] above, wherein the sample liquid being measured is prevented from adhering to the sealing agent for preventing evaporation by a pillar.
[14] The method according to any one of [1] to [13], further including means for measuring a change in fluorescence intensity of a sample solution containing nucleic acids in one or more wells provided in the reaction vessel. Equipment.
[15] As a means for measuring changes in fluorescence intensity,
An optical system including one or more fluorescent light sources for irradiating the sample liquid, an optical fiber that conducts light of each wavelength, and a condensing lens that focuses the light on the observation target at the irradiation site;
An optical fiber corresponding to each of one or more fluorescent wavelengths, a bandpass filter that passes a specific fluorescent wavelength disposed downstream of the optical fiber, and a fluorescence detector that conducts fluorescence for detecting the fluorescence intensity of the sample solution A detection system for simultaneously acquiring the fluorescence intensity of the fluorescent labeling substance bound to the cells consisting of
The apparatus according to [14] above.
[16] As one or more fluorescent light sources for irradiating the sample liquid, an LED light source to which an intensity variable adjustment function is added;
When two or more fluorescent light sources are used, each wavelength varies depending on the function of aligning the light intensities of the respective fluorescent light sources, the difference in fluorescence sensitivity to the excitation light of each monochromatic light wavelength, or the difference in fluorescence intensity. A function to adjust the intensity balance for each monochromatic light unit so as to have the same level of detection sensitivity, and a function to variably adjust the irradiation time from continuous light to pulse light of 10 ms or less, and to perform continuous processing The apparatus according to any one of [14] to [15] above, comprising a fluorescence detection control unit.
[17] In the temperature controller of the heat sink or the heat exchange tank, the temperature of the Peltier element or the like controlled and set at a target temperature on the heat exchange surface with respect to a heat exchange medium such as water circulating at high speed The apparatus according to any one of [1] to [16] above, further comprising a heat exchanging portion that contacts the controllable heat generation source over a wide area.
[18] The apparatus according to [17], wherein the heat exchanging unit includes a heat exchanging container having a height within 5 mm from a contact surface with a temperature-controllable heat source such as a Peltier element.
[19] One or more pillar-type heat exchange pillars that do not hinder the circulation of the high-speed liquid in the heat exchange region in order to increase the contact area with a heat-controllable heat source such as a Peltier element in the heat exchange unit The apparatus according to any one of [17] to [18], further including a heat exchange container disposed in the container.
[20] In a reaction vessel provided with one or a plurality of wells for containing a sample solution containing the nucleic acid, hydrophilic treatment is performed so that the sample solution can be brought into contact with the well surface with a wider surface area. The apparatus according to any one of [1] to [19] above, wherein
[21] In a reaction vessel having one or a plurality of wells for containing a sample solution containing the nucleic acid, a hydrophobic treatment is applied to the surface outside the well in order to prevent the sample solution from leaking out of the well. The apparatus according to any one of [1] to [20] above, wherein the apparatus is applied.
[22] A method for performing PCR using the apparatus according to any one of [1] to [21],
(A) placing a sample solution containing nucleic acid in a well;
(B) Switching the reaction vessel temperature from the nucleic acid elongation reaction temperature as the first temperature to (i) the nucleic acid denaturation temperature or (ii) the nucleic acid denaturation temperature or the nucleic acid annealing temperature as the second temperature. The process of performing,
(C) the step of subsequently switching the temperature of the reaction vessel from the second temperature to the first temperature, and (d) repeating step (b) and step (c) a predetermined number of times at predetermined time intervals Process,
Including
Switching the temperature of the reaction vessel from the second temperature to the first temperature by turning off the operation of the thermoelectric element.
[23] In step (d), when steps (b) (ii) and (c) are repeated a predetermined number of times,
Switching the temperature of the reaction vessel from the nucleic acid elongation reaction temperature as the first temperature to the nucleic acid denaturation temperature as the second temperature in (b) (ii) and subsequently from the nucleic acid denaturation temperature to the above Switching the temperature of the reaction vessel to a first temperature;
Switching of the reaction vessel temperature from the nucleic acid elongation reaction temperature as the first temperature to the nucleic acid annealing temperature as the second temperature in (b) (ii) above, and subsequently from the nucleic acid annealing temperature to the above The method according to [22] above, comprising alternately performing switching of the temperature of the reaction vessel to the first temperature at predetermined time intervals.
[24] A method for measuring a melting curve using the apparatus according to any one of [1] to [21],
(A) placing a sample solution containing nucleic acid in a well;
(B) Switching the reaction vessel temperature from the nucleic acid elongation reaction temperature as the first temperature to (i) the nucleic acid denaturation temperature or (ii) the nucleic acid denaturation temperature or the nucleic acid annealing temperature as the second temperature. The process of performing,
(C) the step of subsequently switching the temperature of the reaction vessel from the second temperature to the first temperature, and (d) repeating step (b) and step (c) a predetermined number of times at predetermined time intervals Process,
(E) The PCR product after the reaction is heat-treated and dissociated by a thermal change at a constant rate of 5 ° C./min or less between 60 ° C. and 90 ° C., for example, and the change in fluorescence intensity and the sample solution at that time The process of monitoring the temperature of the product (multiple peaks occur when non-specific products are included, so the specificity of the product can be confirmed)
Including
Switching the temperature of the reaction vessel from the second temperature to the first temperature by turning off the operation of the thermoelectric element.

  In relation to the above “addition mechanism that enables more stable temperature control”, the reaction temperature control device of the present invention is, for example, three temperatures used in a normal PCR reaction, that is, a denaturation temperature (hereinafter referred to as a high temperature). ), Annealing temperature (hereinafter referred to as low temperature), and extension reaction temperature (hereinafter referred to as medium temperature) can be realized in a short time, and in particular, the reaction time can be increased depending on the length of the DNA strand to be reacted. And a means for stably providing the extension reaction temperature which requires adjustment at a high speed. That is, for example, in one embodiment of the present invention, (1) a heat sink with a large heat capacity controlled to be stable at a medium temperature, and (2) an electric power supply that supplies heat so as to keep the temperature of the heat sink constant. Means for high-speed circulation of a medium-temperature liquid at a hot wire or at a constant temperature; (3) a DNA reaction chip on which a sample for carrying out a DNA extension reaction is placed; and (4) a temperature of the upper surface of the chip containing the DNA reaction chip. A container having an observation window that is optically transparent with respect to the wavelength of the fluorescence observation region for maintaining the temperature at 75 ° C. or higher, and (5) actively moving the heat disposed between the DNA reaction chip and the heat sink. There is provided a high-speed gene amplification device having a heat transfer means such as a Peltier element, and (6) a means for detecting a change in fluorescence intensity of a liquid on a DNA reaction chip. When using a heat sink with a material with a large heat capacity and a heat source such as a heating wire, the heat sink material has a large heat capacity and a metal with high heat conductivity (eg, aluminum, duralumin, gold, silver, tungsten, Nepalese brass, It is desirable to use magnesium, molybdenum, beryllium, and alloys using these elements. Moreover, you may use the heat exchange tank using the high-speed circulation liquid set to medium temperature as what is used equivalent to a heat sink. In that case, not only a high-speed liquid reflux type reaction control apparatus having only one reservoir, but also a high-speed liquid reflux type reaction control having two or three reservoirs capable of supporting two- or three-temperature PCR by itself. Only one reservoir set at a medium temperature in the apparatus may be used. For the DNA reaction chip on which the sample is placed, the configuration of the reaction vessel of the high-speed liquid reflux PCR apparatus (WO2010 / 113990) previously filed by the inventors can be used as it is.

  Advantages of the present invention in that the temperature of the reaction vessel is controlled using a medium temperature heat sink or heat exchange vessel are as follows: 1) strict temperature control is possible for medium temperature, and 2) stable temperature maintenance for medium temperature. 3) No overshoot when moving to medium temperature. Regarding the ability to solve the temperature overshoot problem, the temperature of the heat sink or heat exchanger with a large heat capacity is almost constant, so the temperature of the reaction vessel surface and the temperature of the heat sink or heat exchanger are almost instantaneous. Can be equilibrated. In the present invention, the heat capacity of the reaction vessel and the sample is insignificant compared to the heat sink or heat exchange vessel, and the temperature of the heat sink or heat exchange vessel is stable with respect to the operation of the thermoelectric element (eg, Peltier element). In addition, since the temperature of the stable point (medium temperature) is located between the high temperature and the low temperature, it is higher than the conventional Peltier element control type gene amplification device operated from room temperature. As long as the amount of heat transferred when moving to a low or low temperature is minimized and the temperature of the heat sink or heat exchanger is stable, the amount of current required to operate the temperature change to a high or low temperature is reduced. Easy to estimate. Further, even if heat is locally deprived from the heat sink or heat exchange tank by the operation of the Peltier element, a heat gradient is basically not generated because the heat capacity of the heat sink or heat exchange tank is sufficiently large. Of course, the temperature of the reaction tank when the thermoelectric element such as a Peltier element is OFF does not exceed the temperature of the heat sink or the heat exchange tank. According to the present invention, it is possible to change the temperature by 30 ° C. or more within 0.5 seconds. Therefore, according to the present invention, since the time required for temperature change can be extremely shortened, for example, the total time for performing the PCR reaction can be remarkably shortened compared with the conventional apparatus.

  In addition, by using a plurality of optical fibers, it is possible to continuously measure changes in the fluorescence intensity at a low cost and at a plurality of small fluorescence wavelengths.

  Further, as an advantage of adopting a module that can cope with a high temperature change in the heat sink, it is easier to measure a melting curve that makes a constant temperature change stably.

  Further, by dropping the sample liquid onto a hydrophilically treated plate for heat exchange, the sample liquid extends over a larger area, and heat exchange can be efficiently performed with a wider surface area.

  According to the present invention, the liquid from each liquid reservoir having different two or three temperatures, which is necessary in the conventional liquid reflux reaction control apparatus for performing the two-temperature or three-temperature PCR, is alternately supplied to the heat exchange tank. An advantage is provided that a switching operating part such as a valve for circulation is not required. Alternatively, when the present invention is implemented using a liquid reflux type reaction control device having a plurality of reservoirs capable of corresponding to two or three temperatures, a medium temperature is set to a plurality of different temperatures using a switching mechanism such as a valve. The advantage is that it can be easily realized.

It is a schematic diagram which shows the whole structure of the reaction control apparatus (example: PCR apparatus) of a high-speed liquid reflux type. It is the schematic of the heat exchange tank used for the reaction control apparatus of a high-speed liquid reflux type. It is a schematic diagram which shows the form of the reaction tank used for the apparatus of this invention, and the dissolution method of a freeze-drying reagent. It is a schematic diagram which shows the attachment method to the cylindrical reaction frame and heat exchange tank which are used for the apparatus of this invention. It is a schematic diagram which shows the switching sequence of the valve | bulb used for a high-speed liquid reflux type reaction control apparatus. It is a figure which shows the result of (A) the data regarding a temperature change and (B) PCR reaction which were performed using the high-speed liquid reflux type reaction control apparatus. It is a schematic diagram which shows the attachment method to the slide glass type | mold reaction frame used for the apparatus of this invention, and a heat exchange tank. It is a schematic diagram which shows the drive mechanism of the slide type piston valve used for the reaction control apparatus of a high-speed liquid recirculation | reflux type | mold. It is a schematic diagram which shows the drive mechanism of the slide type piston valve used for the reaction control apparatus of a high-speed liquid recirculation | reflux type | mold. It is a schematic diagram which shows the drive mechanism of the rotary valve | bulb used for a high-speed liquid reflux type reaction control apparatus. It is a schematic diagram which shows the temperature change mechanism by the membrane used for the high-speed liquid reflux type reaction control apparatus. It is a schematic diagram which shows the drive mechanism of the temperature setting type | mold valve used for the reaction control apparatus of a high-speed liquid recirculation | reflux type | mold. It is a schematic diagram showing an example of the arrangement of a DNA reaction chip, temperature control of the upper surface, and fluorescence detection method using an example of the configuration of a high-speed liquid reflux type reaction control device. It is a schematic diagram showing an example of a method of arrangement of a DNA reaction chip, temperature control of an upper surface, and fluorescence detection using an example of a configuration of a reaction tank of a high-speed liquid reflux type reaction control device. An example of a method for arranging a DNA reaction chip, controlling the temperature of the upper surface, and detecting fluorescence using an example of a reaction tank chip transport system and a reverse transcription reaction in a reaction tank of a high-speed liquid reflux reaction control apparatus It is a schematic diagram which shows. It is a schematic diagram which shows an example of a structure of the fluorescence detection method of the sample in the reaction tank of this invention. It is a schematic diagram which shows an example of a structure of the fluorescence detection method of the sample in the reaction tank of this invention. It is a schematic diagram which shows an example of the structure of the reaction tank of this invention. It is a schematic diagram which shows an example of the structure of the reaction tank of this invention, and an example of a detection method. It is a schematic diagram which shows an example of the structure of the reaction tank of this invention. It is a schematic diagram which shows an example of a structure of a high-speed liquid reflux type reaction control apparatus. It is a schematic diagram which shows an example of a structure of a light heating type reaction control apparatus. It is a schematic diagram which shows the angle dependence of the transmittance | permeability of ND filter in an example of a structure of a light heating type reaction control apparatus. It is a schematic diagram which shows an example of a structure of this invention. It is a graph which shows typically the temperature change of the DNA sample of this invention, and operation | movement of a Peltier device. Schematic example of an apparatus configuration for simultaneously irradiating sample liquid with multiple wavelengths of fluorescence excitation light using an optical fiber array, simultaneously acquiring the emitted fluorescence amounts of multiple wavelengths, and simultaneously acquiring fluorescent images of multiple wavelengths FIG. It is the spectrum figure which showed typically the example which selected the wavelength set of the some fluorescence excitation light for irradiating a sample liquid, and the some fluorescence to detect. It is the figure which showed typically an example of the irradiation measurement timing of the some fluorescence excitation light irradiated to a sample liquid, and the some fluorescence detected. A heat sink having a heat exchanging portion in contact with a heat-controllable heat source such as a Peltier element that is controlled and set at a target temperature on a heat exchanging surface such as water that circulates at high speed, or a large area, or the heat exchanging It is the figure which showed typically an example about the temperature controller (temperature controller) of a tank. A heat sink having a heat exchanging portion in contact with a heat-controllable heat source such as a Peltier element that is controlled and set at a target temperature on a heat exchanging surface such as water that circulates at high speed, or a large area, or the heat exchanging It is the figure which showed typically an example about the temperature controller (temperature controller) of a tank. A heat sink having a heat exchanging portion in contact with a heat-controllable heat source such as a Peltier element that is controlled and set at a target temperature on a heat exchanging surface such as water that circulates at high speed, or a large area It is the figure which showed typically an example about the PCR apparatus using the temperature controller (temperature controller) of a tank. A reaction vessel equipped with one or more wells for containing a sample solution containing nucleic acid is subjected to hydrophilic treatment so that the sample solution can be brought into contact with the well surface with a larger surface area, and the surroundings. It is the figure which showed typically an example about the structure of the well which processed hydrophobicity, and the shape of a sample liquid.

  Hereinafter, embodiments of the present invention will be described with reference to the drawings. However, these embodiments are examples, and the scope of the present invention is not limited thereto.

  FIG. 1 is a schematic diagram showing the overall configuration of an embodiment of a high-speed liquid reflux type reaction control device. This reaction control apparatus typically includes a reaction vessel 1, a reaction vessel frame 2, a heat exchange chamber 3, a liquid reservoir tank 4, a heat source 5, and a stirring mechanism 6. , A pump 7, a switching valve 8, a bypass flow path 9, and an auxiliary temperature control mechanism 10. Preferably, it further includes a fluorescence detector 201, a control analysis unit 202 for sending a control signal 203, and an optical window (or hole) 204.

  In a preferred embodiment, the plurality of liquid reservoir tanks 4 have a minute amount so that there is no difference in the height of the liquid in each tank during the high-speed circulation of the liquid and this does not cause a pressure difference due to the difference in water level height. The liquid is connected by a thin connecting tube 15 that can move between tanks. Further, in order to realize heat exchange in a short time, as shown in FIG. 1, the liquid is circulated from each reservoir tank 4 by the pump 7 at all times and is not guided to the heat exchange tank 3. The liquid is guided to the bypass channel 9 by the valve 8 and constantly circulated. In addition, the circulating liquid is piped so as to be recirculated by fine adjustment by the auxiliary temperature control mechanism 10 so as to be the same as the temperature of the liquid in the reservoir tank 4 before returning to the reservoir tank 4. Here, the auxiliary temperature control mechanism 10 incorporates a heating mechanism and a cooling mechanism, and can realize both heating and cooling by a Peltier element or the like, or a heating system by an resistance heating mechanism and an air cooling fin type. It is also possible to use a cooling mechanism. A liquid temperature sensor 16 is disposed in each reservoir tank 4 and each auxiliary temperature control mechanism 10, and the heat source 5 and the auxiliary temperature are controlled so that the liquid temperature can be controlled to a desired temperature from the temperature information from these sensors. The control mechanism 10 can be controlled. Here, as the liquid temperature sensor, it is desirable to use a thermistor made of a material that does not corrode even if it is in direct contact with the liquid, or a thermocouple with a corrosion protection coating.

  Further, in a preferred embodiment, each reservoir tank prevents the tank from being destroyed when there is an increase in pressure in the reservoir tank due to gas such as water vapor generated by heat supply from a heat source. In order to prevent the generation of the liquid level through the connecting tube due to the difference, a pressure leak valve 2003 that effectively discharges the generated gas to the outside of the tank is disposed.

  The reaction vessel 1 is typically composed of a thin plate of aluminum, nickel, or gold having a plurality of depressions (wells). The thickness of the thin plate in the indented region is preferably configured to be thinner than the surroundings in order to enhance thermal conductivity, and is typically about 10 to 30 microns thick, but is not limited thereto. The area between adjacent depressions is preferably thicker to ensure overall strength, and typically has a thickness in the range of 100 microns to 500 microns, but is not so limited. The reaction tank 1 is typically formed integrally with the bottom of the reaction tank frame 2 having a shape such as a square or a circle. The reaction tank 1 and the reaction tank frame 2 are typically configured to be detachable from the heat exchange tank 3 (see FIG. 4).

  The temperature of the liquid introduced into the heat exchange tank 3 is controlled by a heat source 5 disposed inside the liquid reservoir tank 4. Preferably, a stirring mechanism 6 is provided in order to quickly remove heat from the surface of the heat source 5 and make the temperature inside the liquid reservoir tank 4 uniform. The liquid in the liquid reservoir tank 4 is guided into the flow path by the pump 7. By the switching valve 8, the liquid is guided to the heat exchange tank 3 or is guided to the bypass flow path 9 and returns directly to the liquid reservoir tank 4 without passing through the heat exchange tank 3. If necessary, the auxiliary temperature control mechanism 10 finely controls the temperature of the liquid changed during the circulation so as to be discharged after being corrected to the same temperature as the set temperature in the tank 4. Suppresses temperature fluctuations.

  The liquid introduced into the heat exchange tank 3 may be water, but is not limited to this, and any liquid may be used as long as it has a large heat capacity and low viscosity (eg, liquid ammonia). it can. However, it is desirable to use a non-toxic and non-flammable liquid from the viewpoint of safety. In addition, for example, by using a liquid having a boiling point higher than that of water, the sample liquid can be surely brought to 100 ° C. It is also possible to reliably change the temperature up to the freezing point of water.

  Preferably, as shown in FIG. 1, the reaction vessel frame 2 is provided with a change in the fluorescence intensity of the fluorescent dye in the sample solution that changes due to the reaction of the sample solution in the reaction vessel 1, in one or more reaction vessels. An optical window 204 that transmits the excitation light of the fluorescent dye as well as the fluorescence is disposed so that each of the optical windows can be measured. Moreover, the time change of the fluorescence intensity of each measured reaction tank 1 can be measured by arrange | positioning the fluorescence detector 201. FIG. In the embodiment of FIG. 1, an excitation light irradiation mechanism and a fluorescence detection mechanism are provided in each of the plurality of fluorescence detectors 201. For example, when performing a PCR reaction, different primers or different samples The different PCR amplification information of each of the plurality of reaction vessels 1 to which the liquid has been dropped can be independently measured. The fluorescence intensity data acquired by the fluorescence detector 201 is recorded by the control analysis unit 202 and has a function of estimating the amount of DNA or mRNA in the sample solution obtained by the PCR reaction. Further, the control analysis unit 202 obtains switching information of the switching valve 8 to estimate whether or not the temperature change of the sample liquid after the valve switching has reached a target temperature from the change in fluorescence intensity over time, and It also has a mechanism for controlling valve switching based on the result. This is due to the fact that the fluorescence quenching based on the movement of water molecules universally possessed by fluorescent dyes depends on the liquid temperature, so that the amount of change in fluorescence intensity per unit time becomes small or zero. This is an estimate, and is particularly effective in confirming the achievement of a high temperature state in which DNA is denatured.

  In the embodiment shown in FIG. 1, a configuration is shown in which one detector is arranged in each reaction tank 1, but a plurality of light sources for fluorescence excitation such as a fluorescence excitation light source and a cooled CCD camera can be combined. You may measure the fluorescence intensity change of the reaction tank 1. FIG. Alternatively, when fewer detectors than the number of reaction vessels 1 are used, the fluorescence intensity of all reaction vessels 1 can be increased by combining a mechanical drive mechanism that can move at high speed on the XY plane with the detectors. You may measure.

  The volume of the sample solution can be in the range of 0.1 μL to 100 μL per well, but is not limited thereto. A preferable volume of the sample solution is 0.1 to several tens (e.g., 90, 80, 70, 60, 50, 40, 30, 20, 10) μL per well. For example, it is also suitable to use 0.5 μL to 10 μL per well, 1 μL to 5 μL per well, 1 μL to 2 μL per well, and the like. In addition to the sample solution, the well may contain mineral oil or the like for preventing evaporation of the sample solution. The volume of the mineral oil is preferably about several μL (eg, 3 to 4 μL), but is not limited to this, and it will be apparent to those skilled in the art that it can be appropriately changed depending on the size of the well and the sample amount.

  FIG. 2 is a schematic view of the heat exchange tank 3 used in the high-speed liquid reflux type reaction control device. The heat exchange tank 3 includes an inlet A (11) and an inlet B (12) for introducing liquids having different temperatures as a basic configuration. Further, the heat exchange tank 3 includes a plurality of outlets, outlet A (13) and outlet B (14) for returning the liquid in the heat exchange tank 3 to the liquid reservoir tank 4. FIG. 2A shows a state in which liquid at a certain temperature from the liquid reservoir tank 4 is introduced from the inlet A (11) and discharged from the outlet A (13), and FIG. Are schematically shown in the figure from the inlet B (12) and discharged from the outlet B (14). The number of inlets is not limited to two, and a plurality of inlets corresponding to a plurality of temperatures for which the temperature of the sample liquid is desired to be changed can be prepared. For example, when a three-temperature system is desired, the number of inlets is three. The number of outlets is not limited to 2 as in the case of the inlets. Note that the arrows in FIG. 2 roughly indicate the direction in which the liquid introduced into or discharged from the heat exchange tank 3 flows.

  The total volume of the liquid circulated between the heat exchange tank 3 and the liquid reservoir tank 4 is, for example, the temperature change of the reaction tank 3 in consideration of the flow rate of the liquid used for the circulation, the heat capacity of the liquid, and the stability of the temperature When the flow rate is 10 mL or more per second to achieve high speed and temperature stability, the total volume is usually several tens of mL or more, preferably 100 mL or more, more preferably 200 mL or more, and most preferably , 300 mL or more. The upper limit of the volume can be appropriately set in consideration of the portability of the apparatus.

  The capacity of the heat exchange tank 3 is preferably about 10 times or more the sample amount per well, more preferably about 100 times or more, and most preferably about 1000 times or more. Typically, the capacity of the heat exchange bath is about 0.01 mL to 10 mL per well, more preferably about 0.05 mL to a few mL (eg, 9, 8, 7, 6, 5, 4, 3, 2, 1 mL), and most preferably from about 0.1 mL to 2 mL.

  FIG. 3 is a schematic diagram showing the form of a reaction vessel that can be used in the apparatus of the present invention and a method for dissolving a lyophilized reagent. Various shapes of reaction tanks or wells can be used, and FIG. 3A shows, as an example, a reaction tank A (21) in which the surface in contact with the liquid of the heat exchange tank is a hemispherical reaction tank B. (22) Triangular pyramid shaped reaction vessel C (23), spherical reaction vessel D (24), holding a stable position of a droplet having a conical structure in a spherical recess and contact surface area The reaction tank C '(231) which enabled the expansion | swelling of each is shown. In view of the efficiency of heat conduction, those skilled in the art can easily understand that the larger the area of the surface in contact with the liquid in the heat exchange tank, the better the efficiency.

  It is convenient to freeze and dry the reagents necessary for the reaction. As shown in FIG. 3B, it is possible to prepare a freeze-dried reagent 25 at the bottom of the reaction vessel 26. In addition, if a plug-like freeze-dried reagent 25 is formed inside a dispensing tip 27 used when dispensing a sample, the reagent can be dissolved in the sample by moving the sample liquid 28 up and down. Is possible. Alternatively, the freeze-dried reagent 25 can be dissolved by forming the freeze-dried reagent 25 on the surface of the fiber ball 29 in which nylon fibers or the like are bundled and inserting the sample into the sample 28 inside the reaction vessel 26 and stirring. It is.

FIG. 4 is a schematic view showing a cylindrical reaction vessel frame 32 that can be used in the apparatus of the present invention and a method for attaching it to the heat exchange vessel 37. Since it is inconvenient to directly handle a reaction tank composed of a thin film, it is convenient to fix the reaction tank 31 to a reaction tank frame 32 as shown in FIG. 4A. The reaction vessel frame 32 is preferably formed of a heat insulating material such as polystyrene, polycarbonate, PEEK, acrylic or the like. In addition, it is desirable for rapid and highly accurate temperature increase / decrease of the reaction tank 31 to suppress the coupling area with the reaction tank 31 as small as possible (for example, 5 mm ² or less).

  FIG. 4B shows an embodiment in which the reaction tank 31 is attached to the heat exchange tank 37. A thread 34 is formed on the surface of the reaction tank frame 32. The method of screwing is shown. As shown in FIG. 4B, it is desirable to attach a seal 35 to the opening in order to maintain watertightness. FIG. 4C shows yet another mounting method. As shown in FIG. 4C, it is also possible to employ a tapered reaction vessel frame 36 and attach it to the heat exchange vessel 38 only by pressure.

  FIG. 5 shows a specific example of a valve switching mechanism used in a high-speed liquid reflux type reaction control device. An inlet valve A (41) and an inlet valve B (43) for introducing a liquid into the reaction tank, an outlet valve A (42) and an outlet valve B (44) for introducing the liquid to the outside are shown. The liquid guided from the inlet valve A (41) returns from the outlet valve A (42) to the liquid reservoir tank 4, and the liquid guided from the inlet valve A (43) flows from the outlet bawl B (44) to another liquid reservoir tank 4. Return. By alternately repeating these two states, the sample in the reaction vessel can be reacted. As a more preferable valve switching method, in addition to the above two states, the inlet valve B (43) and the outlet valve A (42) or the inlet valve A (41) and the outlet valve B (44) are simultaneously opened for a moment. By doing so, it is possible to suppress the mixing of liquids having different temperatures, and the temperature control of the liquid reservoir tanks of the respective systems becomes easy.

  The circulation rate of the liquid is not particularly limited, but is usually about 1 mL / second to 100 mL / second, more preferably 5 mL / second to 50 mL / second, and most preferably 7 mL / second to 15 mL / second. . In order to circulate to the heat exchange tank 3 without lowering the temperature of the liquid in the reservoir tank, it is desirable that the liquid is always circulated from the reservoir tank at a high speed of 10 mL / s or more by the pump 7.

  FIG. 6A shows a graph obtained from data relating to temperature control realized by using the above-described mechanism. As shown in FIG. 6A, the temperature can be raised from 60 ° C. to 92 ° C. and returned to 60 ° C. in a short time such as 1.5 seconds. FIG. 6B is a graph showing the results of real-time PCR. The solution conditions for performing PCR are as follows. Reaction buffer 1.0 μL, 2 mM dNTP (dATP, dCTP, dGTP, dTTP) 1 μL, 25 mM magnesium sulfate 1.2 μL, 10% fetal calf serum 0.125 μL, SYBR Green I 0.5 μL, 2 types of each primer 0.6 μL, sterile water 3.725 μL , KOD plus polymerase 0.25 μL, genomic DNA 1.0 μL. As temperature conditions, first, 95 ° C. for 10 seconds, and then, temperature change at 95 ° C. for 1 second and 60 ° C. for 3 seconds was performed for 40 cycles. The circulation rate of the liquid was about 10 mL / second.

  FIG. 7 shows a variation relating to a method for detaching the reaction tank 59 and the reaction tank frame 51 from the heat exchange tank that can be used in the apparatus of the present invention. The reaction tank 59 is stretched and attached to the slide glass type reaction tank frame 51 (FIG. 7A). When the slide glass type reaction vessel frame 51 is attached to the heat exchange vessel, the reaction vessel frame 51 can be slid sideways along the guide rail 53 and pressed against the seal 54 to be fixed (FIG. 7B). Alternatively, it is possible to insert the slide glass reaction frame 51 into the slide receiving port 55 and press it against the seal 57 using the hinge 56 (FIG. 7C).

  FIG. 8 is a schematic diagram showing a variation of the valve switching mechanism used in the high-speed liquid reflux type reaction control device, and shows a slide-type piston valve drive mechanism different from that shown in FIG. A piston 65 that can slide to the left and right is used as a valve mechanism that changes the temperature of the reaction vessel 66. On the left side of the piston 65, liquid is introduced from the inlet A (61) into the heat exchange tank 67, and is led to the outside from the outlet A (62). On the right side of the piston 65, liquid is introduced from the inlet B (63) into the heat exchange tank 67, and is guided to the outside from the outlet B (64). When the piston 65 slides to the right with respect to the reaction tank 66, the reaction tank 66 reaches equilibrium with the temperature of the liquid introduced from the inlet A (61). Conversely, when the piston 65 slides to the left, the reaction tank 66 is introduced from the inlet B (63). It reaches equilibrium with the temperature of the liquid. Moreover, when the piston 65 is located directly under the reaction tank 66, the reaction tank 66 can be removed without liquid leaking. It is desirable that the piston 65 is made of a material excellent in heat insulation, or is hollow and filled with gas, or is in a vacuum state. Note that the arrows in FIG. 8 roughly indicate the direction of liquid flow.

  FIG. 9 shows several variations of the piston drive mechanism of the piston valve used in the high-speed liquid reflux type reaction control device. As one method, the piston 71 is integrated with the piston rod 72 and is directly moved from the outside (FIG. 9A). As another method, the piston 73 is made of a ferromagnetic material such as iron or nickel, or a magnet 74 is incorporated in a piston made of another material. An electromagnetic coil 75 is installed outside and the current is controlled to slide the piston 73 left and right (FIG. 9B). As a further method, by controlling the pressure on the inlet side or the fluid resistance of the outlet, it is possible to slide the piston 76 to the left and right by utilizing the pressure difference between both sides of the piston 76 (FIG. 9C). The white arrow in FIG. 9 indicates the direction in which the piston moves, the black arrow indicates the flow of the fluid, the direction of flow of the fluid is indicated by the direction of the arrow, and the flow rate is roughly indicated by the thickness of the arrow.

  FIG. 10 shows another form of the valve switching mechanism used in the high-speed liquid reflux type reaction control device. A rotary valve 81 made of an inclined elliptical plate to which a rod 82 as a rotary shaft is coupled is inserted into a heat exchange tank 83 having a circular cross section. The rotary valve 81 divides the heat exchange tank 83 into left and right, and the liquid introduced from the right or left of the heat exchange tank can be guided to the reaction tank 84 by turning the rotary shaft 82. The shape of the rotary valve 81 in FIG. 10 is an inclined flat plate, but other shapes such as a spiral screw are also possible, and any shape that produces a similar effect by rotating the rotating shaft may be used. In addition, the black arrow in FIG. 10 shows the rotation direction of the rotating shaft 82, and the outline arrow roughly shows a mode that the liquid flows.

  FIG. 11 shows a structure in which the liquid is replaced by a structure other than the valve. The heat exchange tank 98 is partitioned by a membrane A (95) and a membrane B (96). The liquid introduced from the inlet A (91) is led to the outside by the outlet A (92). Since the membrane exists, it is not derived from the inlet B (93) or the outlet B (94) (FIG. 11A). When the pressure of the liquid introduced from the inlet A (91) exceeds the pressure of the liquid introduced from the inlet B (93), by pushing the membrane A (95) and the membrane B (96) to the left side, The heat of the liquid introduced from the inlet A (91) is transmitted to the reaction tank 97 (FIG. 11B). When the relationship between the pressures of the liquids introduced from the inlet A (91) and the inlet B (93) is reversed, the temperature of the reaction tank 97 reaches an equilibrium state with the temperature of the liquid introduced from the inlet B (93). (FIG. 11C). The membrane is desirably made of a thin film having excellent heat resistance such as heat resistant rubber. Note that the arrows in FIG. 11 roughly indicate the direction of liquid flow.

  FIG. 12 is a schematic diagram showing still another drive mechanism of the temperature setting type valve used in the high-speed liquid reflux type reaction control device. Here, the temperature which can be set is not limited to two. FIG. 12 shows a structure in which three or more reaction vessel temperatures can be set. A rotary valve 101 having a groove 102 formed on the side surface is inserted into the heat exchange tank 103. An inlet and an outlet are provided on both sides of the rotary valve 101. For example, the liquid introduced from the inlet A (104) flows into the groove 102 through the flow path 108 and transfers heat to the reaction tank 109 before the outlet A. Guided out from (105). On the other hand, the liquid introduced from the inlet B (106) is led out from the outlet B (107) without contacting the reaction tank 109. However, by rotating the rotary valve 101, the liquid introduced from an arbitrary inlet can be brought into contact with the reaction tank (FIG. 12C). By rotating the rotary valve 101 with the elapsed time 111, the temperature 110 can be changed as shown in the graph of FIG. 12C. The rotary valve 101 is preferably made of a heat insulating material.

  FIG. 13 is a schematic diagram showing an overall configuration of an embodiment of a temperature control mechanism in which a description of a control system portion of a three-temperature system of a high-speed liquid reflux type reaction control device is omitted. The reaction control unit for causing a high-speed PCR reaction typically has a reaction vessel 1 for exchanging heat between the liquid circulating at high speed and the PCR reaction droplet, and the PCR reaction on the reaction tank. Reaction vessel frame 2 to prevent external contamination and droplet evaporation to droplets, heat exchange chamber 3 to which high-speed circulating liquid for heat exchange is introduced, liquid at three temperatures Liquid reservoir tanks 4 that hold the liquid at respective temperatures, and a heat source 5, a stirring mechanism 6, a pump 7, a switching valve 8, a bypass flow path 9, and an auxiliary temperature control mechanism for each reservoir tank 10 is provided. In order to realize high-speed PCR, the liquid from each reservoir tank circulates in the direction of the arrow of the liquid flow direction 18, and the flow path is joined from each reservoir tank via each switching valve 8 at the joint 90. The liquid flowing out from the heat exchange tank 3 is also branched into the reflux flow path to each reservoir tank by the joint 90 on the downstream side. In order to circulate any one of the high-temperature, medium-temperature, and low-temperature reservoir tanks 4 by simultaneously linking the switching valves 8 in both the branch flow paths on the upstream side and the downstream side of the heat exchange tank 3. By switching to, the high-speed circulating liquid that is instantaneously introduced into the heat exchange tank 3 can be switched to one of high temperature, medium temperature, and low temperature. Here, in FIG. 13, the configuration of the apparatus and the arrangement of the piping are schematically shown for easy understanding, so the length of the piping between the parts is not shown in the same way as the actual length, The length of the pipe connecting between 90 and each switching valve 8 is preferably such that the switching valve 8 is arranged adjacent to the joint 90 so that there is little residual high-speed liquid. Further, in order to minimize the temperature drop of the high-speed circulating liquid supplied from each reservoir tank 4 to the heat exchange tank 3, the flow path length from each reservoir tank 4 to the heat exchange tank 3 is minimized. The parts incorporated between each reservoir tank 4 and the heat exchange tank 3 may be configured to incorporate a minimum number of parts, in which only two parts (mechanisms) of the pump 7 and the switching valve 8 are incorporated. preferable. On the other hand, even if the length of the flow path returning from the heat exchange tank 3 to each reservoir tank 4 is slightly longer, there is no problem because the temperature is corrected by the downstream auxiliary temperature control mechanism 10 and then returned to the reservoir tank 4. Further, the position of the pump 7 is to maintain the flow rate reliably in the heat exchange tank 3 to supply the high-speed circulating liquid, and when not supplied to the heat exchange tank 3, it is instantly and surely supported by the switching valve. In order to recirculate to each reservoir tank via the temperature control mechanism 10, a pump 7 is arranged between each reservoir tank 4 and the upstream side switching valve 8 that supplies the heat exchange tank 4, and the high-speed recirculation liquid is always supplied to the reservoir tank 4. It is preferably arranged so that it is configured to “push out” directly from. Further, in order to minimize the temperature drop of the high-speed circulating liquid supplied from each reservoir tank 4 to the heat exchange tank 3, the inner diameters of these channels are desirably 2 mm or more.

  As described in the example of FIG. 1, each reservoir and each auxiliary temperature control mechanism is provided with a liquid temperature sensor 16 for measuring the temperature of the liquid, and each reservoir tank 4 based on each information of the sensor 16. The temperature control by the heat source 5 and the temperature of the liquid passing through each auxiliary temperature control mechanism 10 can be finely adjusted to the same temperature as the temperature of the reservoir tank 4. In addition, since the temperature buffering function of the reservoir tank 4 can be minimized by introducing the auxiliary temperature control mechanism 10, the capacity of the reservoir tank 4, that is, the amount of circulated liquid can be kept to a minimum. . In addition, in this example, the three-temperature PCR reaction corresponding to each of the three states of denaturation, annealing, and extension is realized with respect to the two-temperature PCR reaction of the example of FIG. Here, regarding the control of the three temperatures of high temperature, medium temperature, and low temperature, the temperature of the reservoir is also a heating system in order to maintain a high temperature of 95 ° C. or higher for the high temperature (the central reservoir tank 4 in FIG. 13). However, for intermediate and low temperature reservoirs, it may be necessary to fine tune the reaction temperature, ie, reservoir temperature, depending on the type of enzyme used. Here, raising the temperature of the liquid in each reservoir tank 4 can be easily realized by supplying heat from a heat source. However, when the temperature is lowered, for example, an auxiliary liquid heat radiation mechanism added to the reservoir tank 4 is used. The liquid temperature can be lowered by 17. The auxiliary liquid radiating mechanism 17 is operated only when it is desired to lower the temperature of the liquid in the reservoir tank 4, and the liquid in the reservoir is sucked at a high speed by a pump system incorporated in the mechanism. The heat of the liquid is radiated in the process of passing through the flow path incorporating the cooling mechanism, and the liquid is finally confirmed until the liquid temperature set by the liquid temperature sensor 16 installed in the reservoir tank 4 is reached. Can be cooled.

  Therefore, as described in the description of FIGS. 1 to 6, the liquid in each reservoir tank 4 supplies heat from the heat source 5 to the reservoir tank 4, and the temperature of each reservoir is increased by the feedback control of the temperature sensor 16. Denaturation temperature), medium temperature (extension reaction temperature), and low temperature (annealing reaction temperature). In addition, since the temperature of the heat source is controlled at a temperature higher than room temperature, it is desirable to arrange the heat source on the bottom surface of the reservoir tank 4 for effective heat convection. In order to make the temperature uniform not only by heat convection, but also at a higher speed, a mechanism for making the temperature distribution of the liquid uniform, such as the stirring mechanism 6, operates to make it uniform. When the liquid is discharged from each reservoir tank 4 at all times by, for example, the pump 6 at a flow rate of 10 mL / second, and when the liquid is not guided to the heat exchange tank 3 by the switching valve 8 arranged at the subsequent stage of the pump. Then, the liquid is returned to the auxiliary temperature control mechanism 10 through the bypass channel 9 and finely adjusted to the set temperature of the reservoir tank 4 and then returned to the reservoir tank 4. That is, the preparation system is prepared by circulating the reservoir tank 4 → the pump 7 → the switching valve 8 → the auxiliary temperature control mechanism 10 → the reservoir tank 4. On the other hand, when it is desired to change the temperature of the reaction tank 1 to the temperature of this liquid, the switching valve 8 at the rear stage of the pump 7 is switched to the direction of the heat exchange tank 3 and the flow direction of the liquid discharged from the heat exchange tank 3 is changed. The switching valve 8 to be controlled is also switched, and the temperature of the reaction tank 1 is set to a predetermined value as a circulation of the reservoir tank 4 → the pump 7 → the switching valve 8 → the heat exchange tank 3 → the switching valve 8 → the auxiliary temperature control mechanism 10 → the reservoir tank 4. The temperature of the liquid in the reservoir tank 4 is changed to the same temperature.

  In addition, in the three reservoir tanks 4, a slight amount of deviation occurs in the reflux of the liquid in this switching process. Therefore, when the three reservoir tanks are operated independently, the liquid process is repeated as the reaction process is repeated. There may be a difference in the height of the surface, overflowing of the liquid from the tank and a difference in the liquid feeding speed from the three tanks may occur. In order to cope with it, the connecting tube 15 may be disposed as a mechanism for aligning the liquid level. The connection tube 15 is intended to make the liquid surface height uniform, and is not intended to actively move liquids having different temperatures, so it is desirable that the connection tube 15 be a sufficiently thin tube. Further, the position of the arrangement is preferably near the bottom surface of each reservoir 4.

  In the case of performing the PCR reaction using the three-temperature reservoir tank 4, the operation of the apparatus system will be described using a typical example, similarly to the PCR reaction in the case of two temperatures in FIG. 6B. Here, the three-temperature PCR reaction is performed in the following steps. First, as an initial reaction, a high-temperature liquid is refluxed for 10 seconds or more from a high-temperature reservoir tank 4 set at 95 ° C. or 96 ° C. so that the temperature becomes 94 ° C. or higher in order to thermally denature the double-stranded DNA to be reacted. Then, the temperature of the reaction vessel 1 is set to 94 ° C. or more for 10 seconds or more. Here, the temperature when the heat denaturation is performed is such that the temperature at the lowest temperature is 94 ° C. or higher even when there is a difference in the temperature distribution of the entire reaction tank 1. To set the temperature. As a result, a single-stranded DNA is produced and, depending on the enzymes, the enzymes necessary for the PCR reaction are activated. Next, an annealing process for specifically binding the primer and DNA is performed by refluxing the liquid from the low-temperature reservoir tank 4 in which the liquid temperature is set to 60 ° C. so that the temperature of the reaction tank is about 60 ° C. Circulating the temperature of 1 to 60 ° C. for 1 second, and finally, the temperature of the medium temperature reservoir tank 4 is set so that the reaction vessel 1 becomes approximately 72 ° C. in the extension reaction of the complementary DNA strand by the heat-resistant DNA polymerase. The medium temperature reservoir tank 4 was circulated for 3 seconds under the conditions set to be 72 ° C., and when the expansion was completed, the heat denaturation step was performed again with the 95 ° C. liquid from the high temperature reservoir tank 4. Reactor 1 temperature is advanced to a temperature of 94 ° C. or higher in 1 second of circulation, and then, similarly, about 40 cycles, with a reaction of low temperature 60 ° C. for 1 second and medium temperature 72 ° C. for 3 seconds as one cycle. By repeating the response, it is possible to perform the amplification of DNA sequence region targeting. Here, in order to send the liquid to the heat exchange tank 3 so that the temperature does not actually drop from the temperature of the reservoir tank 4, it is necessary to recirculate the liquid at a sufficiently high speed. In this example, the liquid circulation rate was about 10 mL / second, and it was possible to change the temperature in a manner that prevented a temperature drop. Further, in the above embodiment, since the annealing temperature varies depending on the primer to be designed and the optimum primer binding temperature, the optimum annealing temperature is calculated using the melting curve analysis described later, and the low temperature reservoir tank is calculated. It is desirable to set a temperature of 4. Further, in the above example, the extension reaction time is set to 3 seconds, but is not limited to this, and the set time can be appropriately determined by calculating from the relationship between the extension rate of the DNA polymerase enzyme and the target sequence size. it can. For example, a typical Taq polymerase has a DNA extension rate of about 60 nucleotides / second at 70 ° C. Therefore, in the case of this enzyme, a target region having a length of about 150 to 180 bases can be obtained by an extension reaction of 3 seconds. Can be amplified. Therefore, in order to effectively realize the high-speed PCR reaction in this apparatus system, it is necessary to narrow down the target region to several hundred bases in length and to select the optimal DNA polymerase enzyme according to the purpose. However, it is desirable to use a polymerase that can react as fast as possible.

  Further, when performing the cycle at the above three temperatures, it is possible to combine at least two measurement methods of endpoint type measurement and real-time (real-time) amplification measurement. As shown in FIG. 1, the high-speed gene amplification apparatus of the present invention can incorporate an optical detection system for optically monitoring the amplification of the target gene product. In measurement using a fluorescent dye, the fluorescence intensity of which changes greatly when incorporated into the hydrogen-bonded region of double-stranded DNA, generally called intercalator type, the amount of product is determined by the fact that the target DNA product is double-stranded. This is important for quantitative measurement. Therefore, in the endpoint type, since the measurement is performed after the reaction is completed, the measurement is performed after the reaction is completed in a temperature range where measurement in the double-stranded DNA state is possible, or the last amplification cycle is performed. Immediately after the completion, it is desirable to estimate the amount of amplification of the fluorescence intensity by the double-stranded DNA by measuring the fluorescence intensity and performing a comparative analysis with the fluorescence intensity before the start of the amplification reaction. It is important to note that fluorescent dyes have a thermofluorescence quenching phenomenon in which the fluorescence intensity in the solution changes depending on the solution temperature, so it is important that the measurement temperature be the same. It is.

  On the other hand, in real-time measurement, the amount of amplification for each amplification cycle is estimated, so measurement in each cycle is necessary. The measurement timing in each cycle is desirably measured just before the thermal denaturation starts, when the extension reaction ends. Again, in order to eliminate the influence of thermofluorescence quenching, it is desirable that the solution temperature during measurement in each cycle be the same temperature. In addition, measurement using a DNA polymerase having a 5'-3 'exonuclease function and a probe DNA fragment incorporating a donor fluorescent dye and an acceptor fluorescent dye to cope with fluorescence energy transfer, generally called the Taqman probe method. In some cases, the 5'-3 'exonuclease reaction proceeds during the extension reaction of the DNA polymerase, so the endpoint type measures the fluorescence intensity at the respective fluorescence wavelengths of the donor fluorescent dye and acceptor fluorescent dye before the start of measurement. After the gene amplification reaction is completed, the fluorescence intensity at the respective fluorescence wavelengths of the donor fluorescent dye and the acceptor fluorescent dye is measured to quantitatively determine how much the probe DNA was actually degraded by the enzyme. By detecting, the presence or absence of the target base sequence can be analyzed. Here again, it is desirable that the solution temperature during measurement be the same temperature in order to eliminate the influence of thermofluorescence quenching. On the other hand, in the real-time measurement, the degradation reaction of the probe DNA fragment proceeds during the extension reaction of the polymerase. Therefore, the wavelength of the donor fluorescent dye and the acceptor at the end of the extension reaction of each amplification cycle, heat denaturation, or annealing. The fluorescence intensity may be measured at the wavelength of the warning dye. However, as a point to be noted here, in order to eliminate the influence of thermofluorescence quenching, it is desirable that the solution temperature at the time of measurement in each cycle be the same temperature.

  Moreover, since the reaction tank 1 used for the high-speed PCR reaction of the present invention can be a disposable chip, when exchanging, discharge the liquid filling the heat exchange tank 3, It is necessary to take the procedure of removing the reaction vessel frame 2 after removing the liquid and then removing the reaction vessel 1. Therefore, in the embodiment shown in FIG. 13, the air inflow pipe 2001 is arranged so as to be connected to the heat exchange tank 3 with the valve (switching valve) 8 interposed therebetween, and the liquid in the heat exchange tank 3 is arranged. Similarly, the discharge pipe 2002 is arranged so as to be connected to the circulation path to one auxiliary temperature control mechanism 10 of the reservoir tank 4 through the valve (switching valve) 8 and the liquid discharge pump 6. Actually, when performing a gene amplification reaction or the like using the liquid in the reservoir tank 4 at three temperatures, the two valves 8 attached to the tubes 2001 and 2002 are closed, and the liquid reflux from the three reservoir tanks 4 is closed. Will not be affected. At the stage where the gene amplification reaction is finished, the six switching valves 8 coupled to the three reservoir tanks 4 are switched so as not to exchange liquids with the heat exchange tank 3, and then the tubes 2001, The valve 8 connected to each of 2002 is connected, and the liquid in the heat exchange tank 3 is sent to the auxiliary temperature control mechanism 10 of the low temperature reservoir tank 4 by using the pump 7, for example, and the heat exchange tank 3. The interior can be filled with air. After that, when the reaction tank 1 is replaced and another reaction tank 1 is newly set, the switching valve 8 connected to the pipes 2001 and 2002 is closed, and the liquid is sent from the reflux system from the reservoir tank 4. When started, the heat exchange tank 3 is filled with a liquid, and a normal gene amplification reaction can be resumed.

  Furthermore, in the apparatus of the present invention, it is possible to measure the melting curve by utilizing a mechanism for controlling the temperature of the liquid. In the case of performing a melting curve analysis, for example, a temperature change at a ramp rate of 0.11 ° C./sec is continuously applied from 65 to 95 ° C. to the reaction solution in the reaction vessel 1 and the temperature is set in the reaction vessel 1. While monitoring the temperature of the reaction tank 1 with the liquid temperature sensor, the change in the intensity of the intercalator fluorescent dye in the PCR reaction liquid in the reaction tank 1 at that time is measured using an optical measurement module as shown in FIG. It is possible to measure the melting curve analysis of the correlation between temperature and fluorescence intensity. At this time, for example, using the reservoir tank in which the auxiliary liquid heat radiation mechanism 17 is incorporated among the three reservoir tanks 4 in FIG. 13, first, the liquid in the reservoir tank is reached until the start temperature reaches a predetermined low temperature side. Reduce the temperature. Next, heat is gradually added to the heat source in the reservoir tank, and heat supply is performed while measuring with the temperature sensor 16 so that the temperature rises to about 0.11 ° C./sec. Supply reservoir tank fluid. The liquid returned from the heat exchange tank 3 is adjusted by the auxiliary temperature control mechanism 10 so as to have the same temperature as that of the reservoir tank, and is returned to the reservoir tank. Finally, when the final temperature reaches, for example, 95 ° C., the liquid temperature in the reservoir tank may be lowered, and the liquid temperature may be lowered to the initially set temperature again by the auxiliary liquid heat dissipation mechanism 17.

  As described with reference to FIG. 1, the reaction vessel 1 is kept in a sealed state by the reaction vessel frame 2. In a preferred embodiment, the reaction vessel frame 2 is always kept at 75 ° C. or higher by a heater incorporated in the reaction vessel frame 2 based on temperature data measured by the temperature sensor 16. Heating by this heater prevents the water vapor in the frame from condensing on the inner surface of the frame, thereby keeping the water vapor pressure in the frame constant. Even if the liquid droplets are arranged in a state of being exposed without adding such as, it is possible to change the temperature in the range of 50 to 97 ° C. without evaporation.

  Similarly, a temperature control method for melting curve analysis can be used to maintain a constant temperature at a temperature different from the PCR reaction. Accordingly, reverse transcription reaction can be performed on the PCR reaction solution in the reaction vessel. For example, after transferring the RNA to DNA by refluxing the liquid at a liquid temperature of 50 ° C. for 10 minutes or more, the temperature of this reservoir tank is adjusted to the temperature at which the normal PCR reaction is performed, and continuously reversed. It is possible to proceed from the photoreaction to the PCR reaction.

  The gene amplification reaction process that follows the specific reverse transcription reaction includes one-step operation (reverse transcription and amplification are performed continuously in one tube) or two-step operation (reverse transcription and amplification are performed in separate tubes). Here, an example of the operation procedure is shown by taking a one-step operation as an example. For example, when Tth DNA Polymerase (Roche) is used as a one-step RT-PCR reverse transcriptase for short targets, the optimal reaction temperature for this reaction is 55-70 ° C. (1) Low temperature reservoir tank Is set to 50-60 ° C., which is lower than the normal annealing temperature, and the liquid in the low temperature reservoir tank 4 is refluxed to the heat exchange tank 3 for about 30 minutes to perform the reverse transcription reaction, and then (2) the high temperature reservoir tank From step 4, the liquid having a temperature of 94 ° C. or higher is refluxed to the heat exchange tank 3 for about 2 minutes to perform initial heat denaturation. A thermal denaturation process, followed by an annealing process with a liquid at 45-66 ° C. corresponding to the primer properties from the low temperature reservoir tank 4 which was temperature adjusted for annealing, , It is possible to carry out an amplification reaction of the target RNA by performing cycle of extension reaction for 3 seconds by 68 to 70 ° C. a liquid that matches the enzymatic properties of the medium-temperature reservoir tank 4. In this embodiment, after adjusting the temperature of one of the three different reservoir tanks 4 to the optimum temperature for the reverse transcription reaction and performing the reverse transcription reaction, the temperature is again set to the optimum temperature for the PCR reaction. Although the three-temperature gene amplification reaction is performed in this manner, the above-described process may be performed by adding the fourth reservoir tank 4 having the optimum temperature for the reverse transcription reaction in the same manner.

  FIG. 14 illustrates one example of another method for providing the reaction vessel 1 with a measurement function for the melting curve analysis. In this embodiment, the Peltier temperature control mechanism 19 is disposed on the bottom surface of the heat exchange tank 3, and the Peltier temperature control mechanism 19 is pierced with a liquid flow pipe 20 that is circulated for the PCR reaction. Therefore, the liquid circulation for the high-speed PCR reaction described in FIG. 13 can be performed in the same manner. However, when the measurement of the melting curve analysis is further performed, the liquid flow 18 in the liquid channel tube 20 is stopped, The melting curve analysis is performed by controlling the temperature of the stationary liquid filled in the heat exchange tank 3 by the Peltier temperature control mechanism 19 and the temperature sensor 16 in the heat exchange tank 3. This mechanism can also be used in reverse transcription reactions. In that case, the optimum temperature and time for the reverse transcription reaction are provided by the Peltier temperature control mechanism 19, and when the reverse transcription reaction is completed, the configuration of the two-temperature gene amplification apparatus as shown in FIG. High-speed gene amplification can be continuously performed continuously using the configuration of the three-temperature gene amplification apparatus as shown.

  FIG. 15 is a schematic diagram showing an example of an embodiment of a method for using a continuous disposable reaction tank 1 in the present invention and an example of an embodiment of a reaction tank unit including a reaction tank 1 capable of performing a reverse transcription reaction. is there. The reaction tank 1 of the present invention can be used as a disposable chip as described in the explanation of FIG. In this case, as shown in the AA cross-sectional view of FIG. 15, for example, the reaction tank unit 1015 for performing high-speed gene amplification reaction typically has a reaction tank 1 for performing PCR and an O for fixing the reaction tank 1. A guide rail 1011 is provided by providing a reaction tank frame 2 and a heat exchange tank 3 for sandwiching the upper and lower sides of the reaction tank 1 with spacers such as a ring 1010 that guarantees heat insulation and sealing properties, and a guide rail 1011 for transporting the reaction tank. A plurality of reaction tanks 1 can be transferred to the reaction tank section 1015. When the reaction tank 1 is used in the reaction, the reaction tank 1 can be fixed by the O-ring 1010 by being sandwiched between the reaction tank frame 2 and the heat exchange tank 3, and the liquid can be introduced from the liquid reservoir tank 4. On the other hand, when transporting, by separating the reaction vessel frame 2 and the heat exchange vessel 3 from the reaction vessel 1 and loosening the O-ring 1010, the tip of the reaction vessel 1 can be moved along the guide rail 1011 and exchanged. . As can be seen from the AA cross-sectional view of FIG. 15, the reaction vessel frame 2 can take an optically transparent configuration for observing and measuring the reaction solution optically disposed on the reaction vessel 1. . In this case, a transparent electrode 1014 that effectively generates heat due to resistance such as ITO is sandwiched between two thin glass plates 1013, and the temperature of the reaction vessel frame 2 is controlled without hindering optical observation. can do. In particular, the temperature sensor 16 is installed on the inner surface of the inner glass plate 1013 and the temperature is adjusted to 75 ° C. or higher to prevent condensation on the inner surface of the reaction tank frame 2 and to prevent changes in vapor pressure. The evaporation of the reaction solution disposed on the tank 1 can be prevented.

  In addition, by placing a reverse transcription reaction tank unit 1016 in front of the reaction tank unit 1015 on the guide rail 1011, the RNA sample is reverse transcribed into cDNA, and high-speed gene amplification is performed in the subsequent reaction tank unit 1015. Can do. In the reverse transcription reaction tank unit 1016, as can be seen from the BB cross-sectional view of FIG. 15, the frame having the same configuration as the reaction tank frame 2 optically observes and measures the reaction solution disposed on the reaction tank 1. To achieve this, an optically transparent configuration can be taken. In this case, a transparent electrode 1014 that effectively generates heat due to resistance such as ITO is sandwiched between two thin glass plates 1013, and the temperature inside the frame is controlled without hindering optical observation. Can do. In particular, by installing the temperature sensor 16 on the inner surface of the inner glass plate 1013 and adjusting it to a temperature of about 75 ° C. or higher, condensation on the inner surface of the reaction vessel frame 2 can be prevented, and the change in vapor pressure can be prevented. It is possible to prevent evaporation of the reaction solution disposed on the reaction tank 1. A reverse transcription reaction temperature plate 1012 is disposed on the lower surface of the reaction tank 1, and the PCR solution is brought into close contact with the reaction tank 1 in a state set to, for example, 50 ° C. as an optimum temperature for reverse transcription. When reverse transcription is completed by reacting the temperature of the plate in the reaction vessel 1 at about 50 ° C. for about 30 minutes, the PCR can be started by sliding the guide rail to the reaction vessel unit 1015.

  FIG. 16 is a schematic diagram showing an example of an embodiment of a real-time detection method in a multi-sample gene amplification reaction of the present invention. The reaction detection apparatus of the present invention typically includes a multiwell reaction vessel 1101, a plurality of reaction wells 1102 arranged in an array, and a detection apparatus 1201. A function of measuring the fluorescence intensity in all the samples with fewer detectors than the number of reaction wells by detecting the fluorescence intensity of the PCR sample on the reaction well 1102 by scanning the detection device 1201 in, for example, the direction 1202 during the PCR reaction. Is provided. Here, as described in the explanation of FIG. 13, in the case of performing fluorescence detection by the intercalator method, the state of the double-stranded DNA before the start of thermal denaturation is maintained at the end of the PCR extension reaction. It is desirable to measure during the time. In addition, in the case of fluorescence detection of the amount of a fluorescent probe that causes a quantitative change during the PCR extension reaction of a fluorescent probe, such as the Taqman probe method, the thermal denaturation or annealing stage is performed from the timing after the PCR extension reaction is completed. Can be measured. However, in any case, it is desirable that the temperature of the reaction solution containing the fluorescent dye be the same in order to compare and measure the fluorescence intensity. This is to prevent the fluorescence intensity from being different due to different temperatures, even with the amount of fluorescent dye in the same reaction solution, due to temperature-dependent fluorescence quenching.

  FIG. 17 is a schematic diagram showing an example of an embodiment of a real-time detection method in a multi-sample gene amplification reaction of the present invention. The reaction detection apparatus of the present invention typically includes a multi-well reaction tank 1101, a plurality of reaction wells 1102 arranged in an array, and a detection probe 1203. As shown in FIG. 16, an array of detection probes 1203 having the same amount as the number of reaction wells 1102 on 1101 is prepared and a continuous time change without a break is measured by observing the fluorescence intensity of the PCR sample at a fixed point. Unlike the scanning type, it is possible to detect a continuous fluorescence intensity change.

  FIG. 18 shows that as a means for preventing the reaction solution on the reaction vessel 1 from drying during the PCR reaction, a seal 1302 that is sealed to prevent evaporation of the sample placed on the reaction well 1102 is attached to the reaction vessel 1101. An example of embodiment is shown typically. Here, since the seal 1302 is not in contact with the sample solution 1303 in the reaction well 1102, and in order to suppress movement of the sample reaction solution in the well during the PCR measurement during the drop of the reaction droplet, during transport, the center of each reaction well 1 schematically shows an example of a structure in which a pillar 1301 is formed. The pillar 1301 may be a structure made by stamping or adding a metal such as aluminum having high thermal conductivity, or may be glass or plastic having optical transparency.

  This prevents 5-10 μL of the PCR solution from moving during the PCR reaction and coming into contact with the sealant. Also, the droplets can be spread over a wider surface area by the pillar, and as a result, the reaction liquid can be spread out with a wider surface area than when the droplets of the reaction liquid are simply dropped on the surface of the reaction tank 1101. The temperature of the reaction solution can be exchanged with the heat exchange tank more effectively. In addition, when the pillar 1301 is an optically transparent plastic or a polymer structure material such as PDMS, the fluorescence intensity of PCR is increased by incorporating a substance that emits fluorescence different from the wavelength detected during real-time PCR measurement. It can be used as a reference for calibration.

  FIG. 19 shows a DNA probe 1306 or a DNA probe 1306 or a DNA probe 1306 that can be hybridized in the vicinity on the surface of a pillar 1301 made of a material such as optical fiber glass or plastic having optical conductivity installed in a reaction well 1102. It is the schematic diagram which showed an example of embodiment which combined the primer. As a result, when amplification of the PCR reaction product is performed effectively, the DNA amplification product binds effectively near the pillar surface, and the fluorescence is detected with higher detection sensitivity than usual by utilizing the optical fiber characteristics of the pillar. Real-time PCR reaction can be detected. As a means for emitting fluorescence, as shown in FIG. 19A, a means using an intercalator 1304 such as SYBR Green that emits fluorescence by intercalating in the case of a DNA double strand, or as shown in FIG. 19B When the PCR reaction product 1302 is hybridized with the DNA, the probe structure using the fluorescence resonance energy transfer (FRET) method in which the fluorescent substance 1305 bound to the DNA probe end emits fluorescence due to the collapse of the three-dimensional structure of the DNA is used. be able to. Alternatively, when the target DNA is effectively amplified by introducing a fluorescent acceptor fluorescent dye into the surface of the pillar 1301 or into the pillar 1301 and using an intercalator as a donor fluorescent dye, a probe bound to the pillar surface It is also possible to measure the acceptor fluorescence from the fluorescence emission of the column by binding the DNA and the amplification product DNA and effectively generating intercalator fluorescence on the pillar surface. The advantage of this is that from the observation of target DNA with the index of change in fluorescence intensity of the conventional intercalator, the fluorescence energy transfer is used to observe fluorescence with a wavelength different from that of another interocalator fluorescent dye, which is emission information of acceptor fluorescence. In other words, it is possible to measure quantitatively, and it is possible to perform measurement with lower noise and high quantitativeness.

  FIG. 20 effectively controls the volume of the reaction liquid, and realizes a spatial arrangement of the reaction liquid in the reaction tank 1101 that can be in contact with the heat exchange tank with a larger surface area, which cannot be realized only by dropping conventional droplets. Therefore, an example of an embodiment in which a reaction liquid introduction path and a reaction region are configured in a reaction tank by a microfabrication technique is schematically shown. A micro-channel type reaction vessel 1401 shown in this example is formed on a reaction vessel 1404 such as an aluminum thin plate having excellent thermal conductivity used in the examples shown in FIGS. PDMS) or the like, and a flow path forming polymer 1403 made of a material having optical transparency and elasticity is bonded. This chip has a sample inlet 1405, a microchannel 1402 through which a reaction liquid is introduced from the sample inlet by capillary action, a reaction liquid reservoir 1407 filled with the reaction liquid, and a reaction liquid is collected. By pushing this, an air reservoir 1406 used for collecting the reaction solution from the sample inlet 1405 by air pressure is arranged. In this embodiment, after introducing the reaction solution into the inlet 1405 and performing gene amplification with the high-speed gene amplification apparatus shown in FIG. 1 or FIG. 13, the sample recovery air reservoir 1406 is pushed to It can be collected from the sample inlet 1405. For example, it is appropriate that the reaction solution to be poured is 5 μL or less, and it is desirable to keep the volume from the inlet 1405 to the reaction solution reservoir 1407 within 5 μL. In the above embodiment, the air reservoir is used. However, the position of the air reservoir may be the sample discharge port 1408 as shown in the cross-sectional view of FIG. In this case, in the case of recovering the reaction liquid after the reaction, it can be recovered from the sample outlet 1408 by blowing air from the sample inlet 1405. In the embodiment of FIG. 20, the height of the reaction liquid reservoir 1407 is set higher than that of the micro flow path 1402, but in order to perform heat exchange more effectively, the height of the reaction liquid reservoir 1407 is made as low as possible. By expanding the area, a more efficient PCR reaction can be performed.

  FIG. 21 schematically shows an example of the embodiment in the case where the syringe pump 1411 is used as a means for sending a temperature control liquid with respect to the embodiment shown in FIG. A heat source 5 is disposed on the surface of a syringe pump 1411 capable of automatic liquid feeding and automatic suction at a flow rate of 10 mL or more per second, and a temperature sensor 16 is disposed in the syringe pump, and a liquid for temperature control is used as a heat exchange tank. 3, the switching valve 8 of the syringe pump 1411 having a temperature to be fed is switched, and the liquid is introduced from each syringe pump into the heat exchange tank 3 through the joint 90. The liquid returning from the heat exchange tank 3 is stored in the auxiliary temperature control mechanism 10 via the joint 90 and the switching valve 8, and after returning the liquid to the same temperature as set in the syringe pump 1411, the syringe pump It has a function of refluxing. When the liquid feeding from the syringe pump is finished and the liquid feeding of another temperature from another syringe pump 1411 is started, the switching valve 8 is connected to the syringe pump 1411 and the auxiliary temperature control mechanism 10. The liquid is collected in the syringe pump 1411 by switching.

  FIG. 22 shows an example of an embodiment in which infrared rays with strong absorption of water in the reaction solution are irradiated to control the temperature of the reaction solution and a temperature change due to the absorption is used. The inventors have already described in Japanese Patent Application Laid-Open No. 2008-278791 the technology of high-speed PCR using absorption of focused infrared light. In this example of FIG. 22, the temperature control of the reaction solution is controlled by the infrared laser 1510. Rather than intensity control, a gradation ND filter 1515 whose transmittance continuously changes in a circular fashion and a motor 1513 such as a stepping motor that precisely controls the angle of the ND filter 1515 via a shaft 1514 are used. The light intensity is changed at high speed by changing the angle at high speed. As a result, not only a rapid temperature change, but also various constant rotation speeds, the temperature gradient per unit time of the reaction solution can be accurately and precisely performed, and the temperature change can be freely programmed. You can also

The apparatus configuration of this embodiment shown in FIG. 22 condenses visible light from an illumination light source (such as a halogen lamp) 1501 with a condenser lens 1502, and each reaction solution on the reaction well plate 1507 on the automatic XY stage 1503. The image can be observed with an image observation camera (cooled CCD or the like) 1522 while being focused through the objective lens 1508 so that the state can be optically observed. The automatic XY stage 1503 can be observed by a well of arbitrary coordinates by being driven by an X-axis motor 1504 and a Y-axis motor 1505. In addition, the temperature of the reaction well plate 1507 can be controlled by the stage heater 1506 to a temperature that becomes the lowest temperature in the PCR reaction such as an annealing temperature, for example. On the other hand, the infrared laser 1510 passes through the beam expander 1511, the laser shutter 1512, and the gradation ND filter 1515, and can be introduced into the microscope optical system by the infrared laser dichroic mirror 1509. Further, the gradation ND filter 1515 has a central shaft 1514 connected to a motor 1513 such as a stepping motor, whereby the infrared laser transmittance by the gradation ND filter 1515 can be freely adjusted. Here, as for the ND gradation pattern on the surface of the gradation ND filter, normally, as shown in FIG. 23A, ND = ND _MAX · (θ / θ _MAX ) linearly according to the angle θ. What changes according to the relationship may be used. Alternatively, by writing a gradation pattern in advance depending on the angle θ, it is possible to irradiate the water droplet with infrared light having a predetermined transmitted light intensity while rotating at a constant angular velocity. FIG. 23B is an example in which gradation is configured so that the process for performing the normal three-temperature PCR reaction is one cycle for one rotation. First, it is increased from 0% transmitted light to 100% transmitted at once, and the nucleic acid is thermally denatured by raising the water droplet temperature to a temperature of 95 ° C. or higher, and then the transmitted light is returned to 0%. The temperature of the water droplet is lowered to the annealing temperature by setting the temperature to 55 to 60 degrees in advance, and the transmitted light is transmitted by, for example, about 30% by rotating the ND filter disk. It can be changed to 70 degrees, and the PCR extension reaction proceeds. At this time, when the disk is rotated at a constant angular velocity, the ratio of the irradiation time of each transmitted light can be realized by reflecting the spatial arrangement of the gradation pattern. In order to perform fluorescence observation in order to quantitatively measure the PCR reaction in the reaction well, this optical system receives excitation light from a fluorescence excitation light source (such as a mercury lamp) 1517 as a fluorescence excitation light source shutter 1518, Excitation light can be introduced by the fluorescence excitation light dichroic mirror 1516 via the fluorescence excitation light projection lens 1519, and the light of the wavelength of the infrared laser for heating and the excitation light are not introduced. The fluorescence intensity can be quantitatively measured by the image observation camera 1522 such as a cooled CCD via the camera dichroic mirror 1520 and the imaging lens 1521 adjusted as described above. The optical heating method described in FIG. 22 can be used flexibly in combination with the method described in FIGS.

For example, by adding the optical heating method of FIG. 22 to the embodiment of FIGS. 1 to 21 described above, the melting curve analysis function can be easily incorporated without changing the temperature of the reservoir tank 4. . Specifically, the function of the target nucleic acid molecule and the intercalator is performed before the liquid having the lowest temperature in the flow of the high-speed circulating liquid from the reservoir tank 4 is circulated in advance or before the introduction of the high-speed circulating liquid is started. An infrared laser for heating is continuously irradiated onto water droplets containing a fluorescent dye having a gradation, and at this time, the gradation ND filter 1515 configured so that the degree of gradation of dimming decreases linearly (linearly) as a linear function. , The temperature of the water droplet can be increased or decreased linearly by rotating it at a constant angular velocity such that the temperature of the water droplet follows sufficiently stably. Here, ascending can be realized when rotating in a direction in which the magnitude of ND decreases, and descending can be realized when rotating in a direction in which the magnitude of ND increases. By recording the angle information and changes in fluorescence intensity at a slow rotation of 0.1 radians or less per second, the droplet temperature and fluorescence intensity results can be obtained using the droplet temperature estimation method from the angle θ described below. Can be obtained and a melting curve analysis can be performed. Here, the temperature is estimated by setting the transmitted light 0% to θ = 0 radians, the transmitted light 100% to θ = 2π radians, and irradiating so that the temperature of the water droplet is 95 ° C. or higher when the transmitted light 100% is irradiated. By adjusting the infrared intensity of the light source and rotating the gradation ND filter while maintaining the adjusted fluorescence intensity, the angle is _{expressed by} the relational expression (θ / 2π) · (T _MAX -T _MIN ). A means for estimating the temperature of the water droplet from the measurement of θ can be used. Here, T _MAX is the temperature of the water droplet at the time of irradiation with transmitted light 100%, and T _MIN is the temperature of the water droplet at the transmitted light 0% before irradiation.

  Alternatively, as shown in FIG. 23 (b), on the disk of the gradation ND filter, the ratio of transmitted light is rotated at a constant speed so that one or several PCR reactions are completed once in one rotation. If this configuration is combined with one system of a high-speed reflux system for refluxing a high-speed liquid having the lowest temperature as a target for stabilizing the minimum temperature of the droplets by arranging it in a θ-dependent manner, A high-speed PCR reaction can be easily realized by optical photothermal conversion. Here, since there is only one high-speed recirculation system, it is not necessary to incorporate the complicated switching valve and the switching program described in FIGS. 1 to 21, and only one reservoir tank is sufficient. It can be greatly simplified.

  The present invention also provides a device for gene analysis or gene amplification, which device comprises a reaction vessel, heat sink, or heat sink with one or more wells for containing a sample solution containing nucleic acid. ) Or heat exchange chamber, heat sink or heat exchanger temperature controller configured to maintain the heat sink or heat exchange chamber at a first temperature (eg, nucleic acid elongation reaction temperature) (Example: temperature sensor, heat wire, liquid reflux type temperature controller), mediating heat transfer between heat sink or heat exchange tank and reaction tank, placed between heat sink or heat exchange tank and reaction tank By controlling the operation of the thermoelectric element (eg, Peltier element) and thermoelectric element, the temperature of the reaction vessel is set to the first temperature and the second temperature (eg, nucleus). Thermoelectric element controller (example: temperature sensor, computer (example: PC)) that changes between the temperature of the thermoelectric element and the temperature of the thermoelectric element is off. The temperature of the reaction vessel is configured to be the first temperature.

  FIG. 24 is a schematic diagram showing a non-limiting example of the configuration of such an apparatus for gene analysis or gene amplification of the present invention. The embodiment of the present invention shown in FIG. 24 has a DNA reaction chip container 2401 for holding a sample containing DNA, a Peltier element 2403, and heat for increasing the heat conduction efficiency between the Peltier element 2403 and the reaction chip container 2401. Conductive thin plate 2402, heat sink 2404, heat wire 2405 for heating heat sink 2404, temperature sensor 2406 for monitoring the temperature of reaction chip container 2401, temperature sensor 2407 for monitoring the temperature of heat sink 2404, reaction chip container 2401 An observation window 2408 for observing the sample, and a fluorescence detection module 2409 for observing the state of the sample in the sample liquid via the observation window 2408.

  As the DNA reaction chip container 2401, the structure of the reaction container used in the liquid reflux type or light absorption heating type reaction control apparatus described above and the optical fluorescence intensity detection system can be used as they are. As a heat source, a heat sink 2404 controlled to a DNA extension reaction temperature (medium temperature) is used as a stable heat source, and a thin plate for heat conduction 2402 (aluminum, duralumin, gold, Heat is supplied to the DNA reaction chip via a metal having high thermal conductivity or an alloy including silver, tungsten, Nepal brass, magnesium, molybdenum, beryllium, and alloys using these elements). Thus, the DNA can be moved at high speed to the DNA denaturation temperature (high temperature) or the annealing temperature (low temperature) by depriving of heat. The temperature sensor 2406 is arranged on the upper surface of the heat conducting thin plate 2402 arranged immediately below the reaction chip, and can monitor the temperature of the reaction chip on the upper surface of the heat conducting plate in real time. The Peltier element 2403 can be driven so that the written temperature change profile becomes the same temperature. A heat sink is a metal or other material that has sufficient heat capacity and thermal conductivity to be stable and at medium temperature (eg, aluminum, duralumin, gold, silver, tungsten, Nepal brass, magnesium, molybdenum, beryllium, and their elements. The temperature sensor 2407 disposed in the heat sink is monitored from a module that can supply heat stably, such as a heating wire 2405, and the information from the sensor 2407 Temperature control module (example: feedback control mechanism) (this is the control of the amount of current and polarity for current-driven heat sources such as heating wires, and the water heating / cooling module for liquid reflux temperature control devices. It has a function to send an ON / OFF control signal) and constantly supplies necessary heat to the heat sink. It is kept. The most significant feature of the present invention is that the heat sink is set to an intermediate temperature (Note: Strictly speaking, the temperature of the heat sink in order to set the reaction vessel or the reaction vessel to an intermediate temperature, the temperature of the reaction vessel is set in consideration of the loss of heat conduction. Medium temperature DNA elongation reaction for the purpose of the temperature of the DNA reaction chip without autonomous high-speed overshooting when the Peltier element is turned off. The temperature can be achieved as an equilibrium temperature. In general, a method of maintaining a constant temperature by continuously supplying heat using a feedback control element such as a Peltier element is likely to cause overshoot and temperature oscillations derived from feedback control, and power consumption becomes very large. There are problems such as shortening of device life due to continuous operation of Peltier devices. On the other hand, in the present invention, which can be realized by turning off the Peltier element in this way, the Peltier element can be turned off at the time of the PCR extension reaction that spends the most time in the PCR reaction, and the annealing is performed particularly on the low temperature side. It can be achieved in such a manner that the elongation reaction temperature approaches the equilibrium point without taking the risk of detaching the double-stranded DNA bound by the above by overshoot due to temperature rise. In addition, the DNA denaturation temperature on the high temperature side and the annealing temperature on the low temperature side are Peltier element operations (denaturation reaction and annealing reaction) in a short time of about 1 second, and a slight overshoot is allowed. There is no need to control the temperature, and since the heat source that contacts the Peltier element that puts heat in and out of the DNA reaction chip is stable at medium temperature, the amount of current applied to reach the target temperature is roughly It is possible to estimate the value of. The DNA reaction chip has an observation window 2408 in which an exothermic transparent electrode such as ITO is arranged on the upper surface of the DNA reaction chip container 2401 as shown in the example of the liquid reflux type apparatus. Heat is supplied so that the temperature is 75 ° C. or higher. This prevents evaporation from the bottom surface of the reagent in the chip and condensation on the top surface of the container, and even a small amount of reagent reaction solution is evaporated. The PCR reaction can be detected by the fluorescence detection module 2409 without any problem.

  FIG. 25 schematically shows the reaction temperature (a) of the reagent in the DNA reaction chip and an example (b) of current application to the Peltier element. As can be seen from the figure, the operation time of the Peltier element is limited to a short time operation to make the temperature high and low, and the temperature change from the heat sink to the DNA reaction chip changes from the heat sink to the medium temperature. This is brought about by the heat balance of heat conduction.

  According to the present invention, it is possible to control the temperature so as to change the temperature at high speed. Therefore, in standard PCR, for example, when the denaturation temperature (high temperature) is set to 94 ° C., the extension temperature (medium temperature) is set to 72 ° C., and the annealing temperature (low temperature) is set to 55 ° C. The time required for each temperature change from medium temperature, medium temperature to low temperature, and low temperature to medium temperature is, for example, 2 seconds, 1 second, 0.9 seconds, 0.8 seconds, 0.7 seconds, 0.6 seconds, 0.5 seconds, 0.4 seconds, or 0.3 seconds or It is possible to set a shorter time.

  In the present embodiment, the case of the three-temperature PCR is illustrated, but similarly, the two-temperature PCR including only the high temperature and the medium temperature can be realized by only turning on / off the Peltier element to the high temperature. The melting curve analysis and RT-PCR process can also be realized by slowly changing the heat sink temperature, or slowly while feeding back heat to the DNA reaction chip by the Peltier element using a temperature sensor. This can be realized by changing the temperature.

  In the present embodiment, the heat sink and the heating wire are used as the medium temperature heat source. However, in the high-speed liquid reflux type reaction control device having one medium temperature liquid reservoir, or described in FIG. 1, FIG. 13, and FIG. In such a high-speed liquid reflux type reaction control apparatus that can cope with two or three temperatures, one liquid reservoir set to an intermediate temperature and the heat exchange tank 3 may be used instead of the heat sink. In addition, the liquid reflux reaction control apparatus including a plurality of reservoirs that can handle two or three temperatures has an advantage that the intermediate temperature itself can have different temperature variations.

  FIG. 26 shows an apparatus configuration for simultaneously irradiating a sample liquid with fluorescence excitation light of a plurality of wavelengths using an optical fiber array, simultaneously acquiring the emitted fluorescence amounts of the plurality of wavelengths, and simultaneously acquiring the fluorescence images of the plurality of wavelengths. It is the figure which showed typically an example. FIG. 27 is a spectrum diagram schematically showing an example in which a plurality of fluorescence excitation lights for irradiating the sample liquid and a plurality of fluorescence wavelength sets to be detected are selected. FIG. 28 is a diagram schematically showing an example of irradiation measurement timings of a plurality of fluorescence excitation lights to be irradiated to a sample liquid and a plurality of fluorescence to be detected. These figures show one or more for irradiating the sample solution as a means of measuring the fluorescence intensity change of the sample solution containing nucleic acids in one or more wells provided in a reaction vessel. A fluorescent light source, an optical fiber that conducts light of each wavelength, and an optical system that includes a condensing lens that focuses the light on the observation target at the irradiation site, and conducts fluorescence for detecting the fluorescence intensity of the sample liquid. The fluorescence intensity of the fluorescence-labeled substance bound to the cells, which is composed of an optical fiber corresponding to each of one or more fluorescence wavelengths, a band-pass filter arranged after the optical fiber and passing a specific fluorescence wavelength, and a fluorescence detector, is simultaneously An apparatus having a detection system for acquisition is described.

  The apparatus of the embodiment of FIG. 26 includes an excitation light source unit (3801-3805) including a fluorescence excitation light source that generates six different monochromatic excitation lights and one light source for bright field microscopic images. Each excitation light source is connected to a controller 3806-3810 that can individually control the light emission timing, light emission time, and light emission intensity. As the excitation light source, in the case of continuous irradiation, a light source combining a filter with an ordinary broadband light source such as a xenon lamp or a mercury lamp, or a laser light source such as a semiconductor excited solid laser or a He-Ne laser One of the most suitable is small, and the output wavelength is narrow and the intensity is stable and can be controlled quantitatively at the same time. Filters can be applied to ordinary broadband light sources such as xenon lamps and mercury lamps. This LED light source has the function of adjusting the light intensity at each monochromatic light wavelength, which is difficult with a combined light source, to the same extent, and can easily control pulse emission in less than milliseconds. The controller 3806-3810 connected to the excitation light source can control the intensity and output time of the excitation light source, thereby freely controlling the balance of the intensity of each monochromatic light, and from continuous light to pulsed light. It is possible to irradiate light. One example of the pulse exposure method using a pulse light source is also described in FIG. 28, for example, at a plurality of timings near the end of the extension reaction in each PCR reaction cycle in the PCR process. A measuring method can be used.

  A lens 3816 for condensing the excitation light of the respective light sources 3801 to 3805 to the optical fiber is disposed at the excitation light exit of each LED excitation light source, and each excitation light generated by each excitation light source is focused as an optical fiber bundle. Then, the end face of each optical fiber 3818 is irradiated for each excitation light, and the excitation light is introduced into each independent optical fiber 3818 in the optical fiber bundle. These optical fibers are bundled, irradiated from the opposite end surface, and irradiated to the sample liquid sample in the well on the heat exchange tank 3 through the condensing microlens 3820. The diameter of the optical fiber is typically 100 microns, and the width of the microchannel through which the sample cells in the microchip pass is typically 10 to 100 microns. Therefore, a microlens 3820 for condensing excitation light is disposed immediately above the sample solution well. By adjusting the focal position of the microlens 3820, it is possible to irradiate only a very narrow region of about 1 micron diameter of the sample liquid with excitation light, and the irradiation region diameter is about 100 microns. Irradiation over a wide area is also possible.

  When the focused excitation light is irradiated to the sample liquid sample, fluorescence of a specific wavelength is emitted from the sample in a spherical wave shape as the PCR reaction proceeds. The fluorescence emitted in one hemispherical direction (in the embodiment of FIG. 26 in the direction of the upper surface of the well) is guided by the microlens 3820 to the end face where the optical fibers 3819 prepared for the number of fluorescence wavelength bands to be measured are bundled. Further, the light is guided to a fluorescence intensity detection unit that performs fluorescence intensity detection via an optical fiber.

  In this embodiment, for example, a fluorescence intensity detection unit comprising fluorescence detectors 3811 to 3815 for detecting fluorescence intensities in six different fluorescence wavelength regions is mounted in this embodiment, and is emitted from the end face of each optical fiber 3819. Fluorescence can be measured by first guiding the fluorescence to the lens 3816 disposed at the end point of each optical fiber, and then guiding the fluorescence to the filter 3817 and fluorescence detectors 3811 to 3815 for each fluorescence wavelength to be measured. . As a fluorescence detector, it is suitable to use a photomultiplier tube that can detect weak light and easily quantify the amount of received light. However, both the excitation light source and the fluorescence detector are suitable for the measurement target. It is desirable to select an appropriate device such as a semiconductor element having a photoelectric conversion function such as an aparancia photodiode. In addition, a fluorescent filter 3817 that can be exchanged according to measurement conditions can be mounted on the detection port of the fluorescence detector.

  The detected fluorescence amount is analyzed by the fluorescence detection control unit 3822. Here, particularly when the amount of fluorescence detected is weak, the control unit provides feedback control to the control controller 3806-3810 so as to increase the intensity of the LED light source serving as the fluorescence light source. It also has a function to increase sensitivity.

  FIG. 27 shows an example of six types of fluorescence excitation light sources mounted on the apparatus of FIG. 26 and wavelength set selection of fluorescence to be detected. Here, an example of 6 wavelengths of fluorescence excitation and 6 wavelengths of fluorescence detection is shown, but the number can be easily increased by increasing the number of light sources, detectors, and optical fibers. In particular, it is possible to simultaneously use fluorescent dyes that react to different excitation lights with overlapping fluorescence wavelengths that were difficult with conventional continuous light irradiation by using pulsed light from an LED light source by shifting the timing of pulse light irradiation. Is possible. In FIG. 27, the excitation light source center wavelengths are 370, 440, 465, 498, 533, 618 nm, and the fluorescence center wavelengths are 488, 510, 580, 610, 640, 660 nm as examples.

  The feature of the device system configuration of this embodiment is to solve the intensity unevenness with the wavelength dependence of the wavelength spectrum of the conventional excitation light source, and more positively adjust the excitation light intensity for the fluorescence wavelength with less sensitivity In addition, it is possible to measure weak signals more accurately and quantitatively. In addition, more fluorescent dyes can be combined by combining short pulsed light of less than ms, which was difficult to achieve with conventional xenon lamps. Realizes simultaneous measurement.

  FIG. 29 shows a heat sink having a heat exchange part that contacts a heat-controllable heat source such as a Peltier element that is controlled and set at a target temperature on a heat exchange surface with respect to a heat exchange medium such as water that circulates at high speed in a wide area. Or it is the figure which showed typically an example about the temperature control apparatus (temperature controller) of this heat exchange tank. Here, a reservoir 2801 that exchanges heat with a heat exchange medium such as water that circulates at high speed, a heat source 2802 that can be temperature controlled such as a Peltier element connected thereto, and a heat exchange medium such as water in the reservoir 2801. An inlet 2803 to be introduced and an outlet 2804 for discharging a heat exchange medium such as water whose temperature is controlled from the reservoir 2801 are included. Here, the heat source 2802 can not only perform heating by lowering the temperature of the heat source, but also can lower the liquid temperature by cooling the heat exchange medium.

FIG. 30 shows a heat sink having a heat exchanging portion that contacts a heat-controllable heat source such as a Peltier element that is controlled and set to a target temperature on a heat exchanging surface with respect to a heat exchanging medium such as water circulating at high speed. Or it is the figure which showed typically an example about the temperature control apparatus (temperature controller) of this heat exchange tank. In order to more efficiently exchange heat from the heat source, the contact area with the heat source with respect to the capacity is maximized. For example, the capacity of the heat exchange region is V, and the contact with the heat source When the area of the surface is S,
V = S x less than 5 mm (height: h)
Thus, it is desirable that the height h is less than 5 mm. In order to further increase the contact area, it is also desirable to arrange a plurality of pillars 2901 in the heat exchange region as described in FIG. Here, it is desirable to use, for example, a columnar column having a diameter of 3 mm or less so that the pillar has a small flow resistance of a heat exchange medium such as water circulating at high speed. In addition, it is desirable to use a spindle shape or a thin plate.

  FIG. 31 shows a heat sink having a heat exchange section that contacts a heat-controllable heat source such as a Peltier element that is controlled and set at a target temperature on the heat exchange surface with respect to a heat exchange medium such as water that circulates at high speed in a wide area. Or it is the figure which showed typically an example about the PCR apparatus using the temperature controller (temperature controller) of this heat exchange tank. In the present embodiment, by utilizing the high-speed temperature control function of the heat sink 2800, a liquid such as water serving as a heat exchange medium whose temperature is controlled by the pump 7 is placed in the heat exchange tank 3 in which a sample solution for performing a PCR reaction is installed. Circulating and performing temperature changes at high speed enables melting curve analysis in addition to high-speed PCR reactions.

For example, a method of performing PCR using an apparatus,
(A) placing a sample solution containing nucleic acid in a well;
(B) Switching the reaction vessel temperature from the nucleic acid elongation reaction temperature as the first temperature to (i) the nucleic acid denaturation temperature or (ii) the nucleic acid denaturation temperature or the nucleic acid annealing temperature as the second temperature. The process of performing,
(C) the step of subsequently switching the temperature of the reaction vessel from the second temperature to the first temperature, and (d) repeating step (b) and step (c) a predetermined number of times at predetermined time intervals Process,
Including
A method can be realized in which the temperature of the reaction vessel is switched from the second temperature to the first temperature by turning off the operation of the thermoelectric element.

In step (d), when steps (b) (ii) and (c) are repeated a predetermined number of times,
Switching the temperature of the reaction vessel from the nucleic acid elongation reaction temperature as the first temperature to the nucleic acid denaturation temperature as the second temperature in (b) (ii) and subsequently from the nucleic acid denaturation temperature to the above Switching the temperature of the reaction vessel to a first temperature;
Switching of the reaction vessel temperature from the nucleic acid elongation reaction temperature as the first temperature to the nucleic acid annealing temperature as the second temperature in (b) (ii) above, and subsequently from the nucleic acid annealing temperature to the above It is also possible to repeat switching the temperature of the reaction vessel to the first temperature alternately at a predetermined time interval.

Furthermore, a method for measuring a melting curve using this apparatus,
(A) placing a sample solution containing nucleic acid in a well;
(B) Switching the reaction vessel temperature from the nucleic acid elongation reaction temperature as the first temperature to (i) the nucleic acid denaturation temperature or (ii) the nucleic acid denaturation temperature or the nucleic acid annealing temperature as the second temperature. The process of performing,
(C) the step of subsequently switching the temperature of the reaction vessel from the second temperature to the first temperature, and (d) repeating step (b) and step (c) a predetermined number of times at predetermined time intervals Process,
(E) The PCR product after the reaction is heat-treated and dissociated by a thermal change at a constant rate of 5 ° C./min or less between 60 ° C. and 90 ° C., for example, and the change in fluorescence intensity and the sample solution at that time The process of monitoring the temperature of the product (multiple peaks occur when non-specific products are included, so the specificity of the product can be confirmed)
Including
A method is also possible in which switching of the temperature of the reaction vessel from the second temperature to the first temperature is performed by turning off the operation of the thermoelectric element.

  FIG. 32 shows a reaction vessel having one or a plurality of wells for containing a sample solution containing nucleic acid so that the sample solution can be brought into contact with the well surface with a larger surface area. It is the figure which showed typically an example about the structure of a well and the shape of the sample liquid which performed the periphery and performed the hydrophobic process. FIG. 32A shows some examples of various shapes of the reaction vessel in which the sample liquid is also arranged as shown in FIG. 3A. However, hydrophobic treatment such as Teflon coating is applied to the portion 311 where the sample liquid is not placed. As shown in FIG. 32B, the sample solution is sampled as shown in FIG. 32B by creating a hydrophobic region and performing hydrophilic treatment by coating the surface (inner surface) 312 of the portion where the sample solution is placed, for example, with a hydroxyl group or the like. The surface (inner surface) 312 of the portion on which the liquid is disposed can be extended as widely as possible, and the sample liquid can be more efficiently transferred by increasing the contact area with the surface (inner surface) 312 of the portion on which the heat exchange is performed. Heat exchange can proceed. On the other hand, it is possible to prevent the sample liquid from leaking from the well by performing a hydrophobic treatment such as Teflon coating on the portion 311 where the sample liquid is not placed.

  The present invention is useful as a reaction apparatus for carrying out a reaction required to strictly control the temperature of a sample. The present invention is also useful as a reaction apparatus for carrying out a reaction required to rapidly change the temperature of a sample.

  The present invention is particularly useful as a PCR apparatus capable of performing PCR reactions with high speed, high accuracy, and high amplification rate. Since the apparatus of the present invention can be miniaturized, it is useful as a portable PCR apparatus.

DESCRIPTION OF SYMBOLS 1 Reaction tank 2 Reaction tank frame 3 Heat exchange tank 4 Liquid reservoir tank 5 Heat source 6 Stirring mechanism 7 Pump 8 Switching valve 9 Bypass flow path 90 Joint 10 Auxiliary temperature control mechanism 11 Inlet A
12 Inlet B
13 Outlet A
14 Outlet B
15 Connecting Tube 16 Temperature Sensor 17 Auxiliary Liquid Heat Dissipating Mechanism 18 Liquid Flow Direction 19 Peltier Temperature Control Mechanism 20 Liquid Channel Pipe 2001 Air Inflow Pipe 2002 Liquid Discharge Pipe 2003 in Heat Exchange Tank Pressure Leak Valves 21, 22 23, 24, 26, 231 Reaction tank 25 Lyophilized reagent 27 Dispensing tip 28 Sample 29 Fiber ball 31 Reaction tank 32 Reaction tank frame 33 Reaction tank receiving port 34 Thread 35 Seal 36 Tapered reaction tank frame 37, 38 Heat exchange tank 41 Inlet valve A
42 Outlet valve A
43 Inlet valve B
44 Outlet valve B
51 Slide Glass Type Reaction Tank Frames 52, 58 Reaction Tank Receiving Port 53 of Heat Exchange Tank 53 Guide Rail 54 Seal 55 Slide Receiving Port 56 Hinge 59 Reaction Tank 61 Inlet A
62 Outlet A
63 Inlet B
64 Outlet B
65 Piston 66 Reaction tank 67 Heat exchange tank 71 Piston 72 Piston rod 73 Piston 74 Magnet 75 Electromagnetic coil 76 Piston 81 Rotary valve 82 Rotating shaft 83 Heat exchange tank 84 Reaction tank 91 Inlet A
92 Outlet A
93 Inlet B
94 Outlet B
95 Membrane A
96 Membrane B
97 Reaction tank 98 Heat exchange tank 101 Rotary valve 102 Groove 103 Heat exchange tank 104 Inlet A
105 Outlet A
106 Inlet B
107 Outlet B
108 Flow path 109 Reaction tank 110 Temperature 111 Elapsed time 201 Fluorescence detector 202 Control analysis section 203 Control signal 204 Optical window 1010 O-ring 1011 Guide rail 1012 Reverse transfer reaction temperature plate 1013 Glass plate 1014 Transparent electrode 1015 Reaction tank section 1016 Reverse rotation Copy reaction tank section 1101 Reaction tank 1102 Reaction well 1201 Fluorescence detection probe 1202 Fluorescence detection probe scanning direction 1203 Arrayed fluorescence detection probe 1301 Pillar 1302 Evaporation prevention seal 1303 PCR solution 1304 Intercalator 1305 Fluorescence probe 1306 DNA probe 1401 Micro flow Road type reaction tank 1402 Micro flow path 1403 Flow path forming polymer 1404 Reaction tank 1405 Sample inlet 1406 Sample collection air reservoir 1407 Reaction liquid reservoir Bas 1408 sample outlet 1411 syringe pump 1501 ... illumination light source (such as a halogen lamp)
1502 ... Condenser lens 1503 ... Automatic XY stage 1504 ... X-axis motor 1505 ... Y-axis motor 1506 ... Stage heater 1507 ... Reaction well plate 1508 ... Objective lens 1509 ... Infrared laser dichroic mirror 1510 ... Infrared laser 1511 ... Beam Expander 1512 ... Laser shutter 1513 ... Motor (stepping motor, etc.)
1514 ... Shaft 1515 ... Gradation ND filter 1516 ... Dichroic mirror 1517 for fluorescence excitation light ... Light source for fluorescence excitation (mercury lamp, etc.)
1518 ... Fluorescence excitation light source shutter 1519 ... Fluorescence excitation light projection lens 1520 ... Camera dichroic mirror 1521 ... Imaging lens 1522 ... Image observation camera (cooling CCD, etc.)
2401 ... DNA reaction chip container 2402 ... heat conduction thin plate 2403 ... Peltier element 2404 ... heat sink 2405 ... heating wire 2406, 2407 ... temperature sensor 2408 ... observation window 2409 ... fluorescence detection module 2800 ... heat sink 2801 ... heat of water circulating at high speed Reservoir 2802 for exchanging heat to the exchange medium. Temperature controllable heat source 2803 such as a Peltier element. Inlet 2804 for introducing a heat exchange medium such as water into the reservoir 2801. Heat of water or the like whose temperature is controlled from the reservoir 2801. Outlet 2901 for discharging the exchange medium ... pillar 311 ... part 312 on which the sample liquid is not placed ... surface (inner surface) of the part on which the sample liquid is placed
313: Sample liquid 3801-3805 ... LED (or laser) light source 3806-3810 ... Light source controller 3811-3815 ... Fluorescence detector 3816 ... Lens 3817 ... Fluorescence filter 3818, 3819 ... Optical fiber 3820 ... Condensing microlens 3821 ... Collision Meter lens or condenser lens 3822 ... Fluorescence detection control unit 3823 ... Sample thermometer

Claims (10)

A reaction vessel with one or more wells for containing a sample solution containing nucleic acid;
A heat sink or heat exchange bath,
A temperature control device for the heat sink or the heat exchange bath configured to maintain the heat sink or the heat exchange bath at a first temperature;
A thermoelectric element that mediates heat transfer between the heat sink or the heat exchange tank and the reaction tank, disposed between the heat sink or the heat exchange tank and the reaction tank;
A thermoelectric control device that changes the temperature of the reaction vessel between the first temperature and the second temperature by controlling the operation of the thermoelectric element;
Means for measuring a change in fluorescence intensity of the sample solution containing the nucleic acid in one or more of the wells provided in the reaction vessel,
An apparatus for gene analysis or gene amplification configured such that the temperature of the reaction vessel becomes the first temperature when the operation of the thermoelectric element is off. As a means of measuring changes in fluorescence intensity,
An optical system including one or more fluorescent light sources for irradiating the sample liquid, an optical fiber that conducts light of each wavelength, and a condensing lens that focuses the light on the observation target at the irradiation site;
An optical fiber corresponding to each of one or more fluorescent wavelengths, a bandpass filter that passes a specific fluorescent wavelength disposed downstream of the optical fiber, and a fluorescence detector that conducts fluorescence for detecting the fluorescence intensity of the sample liquid The detection apparatus which acquires simultaneously the fluorescence intensity of the fluorescence label | marker substance couple | bonded with the said cell which consists of these. As one or more fluorescent light sources for irradiating the sample liquid, an LED light source with an intensity variable adjustment function,
When two or more fluorescent light sources are used, each wavelength varies depending on the function of aligning the light intensities of the respective fluorescent light sources, the difference in fluorescence sensitivity to the excitation light of each monochromatic light wavelength, or the difference in fluorescence intensity. A function to adjust the intensity balance for each monochromatic light unit so as to have the same level of detection sensitivity, and a function to variably adjust the irradiation time from continuous light to pulse light of 10 ms or less, and to perform continuous processing The apparatus according to claim 1, further comprising a fluorescence detection control unit.   In the temperature controller of the heat sink or the heat exchange tank, the temperature of a Peltier element or the like that is controlled and set to a target temperature on a heat exchange surface with respect to a heat exchange medium such as water circulating at high speed can be controlled. The apparatus in any one of Claims 1-3 provided with the heat exchange part which contacts a heat-generation source with a large area.   The apparatus of Claim 4 provided with the container for heat exchange which has the height within 5 mm from the contact surface with the heat-controllable heat sources, such as a Peltier element, in the said heat exchange part.   In the heat exchanging unit, in order to increase a contact area with a heat source capable of controlling temperature such as a Peltier element, one or more pillar type heat exchanging pillars that do not hinder circulation of high-speed liquid in the heat exchanging region are provided in the container. The apparatus of Claim 4 or 5 provided with the container for heat exchange arrange | positioned in.   In the reaction vessel provided with one or a plurality of wells for containing the sample solution containing the nucleic acid, hydrophilic treatment is performed so that the sample solution can be brought into contact with the surface of the well with a wider surface area. The apparatus according to any one of claims 1 to 6.   In the reaction vessel having one or a plurality of wells for containing the sample solution containing the nucleic acid, the surface outside the well is subjected to hydrophobic treatment in order to prevent the sample solution from leaking out of the well. The apparatus according to claim 1. The first temperature is a nucleic acid elongation reaction temperature;
The apparatus according to any one of claims 1 to 8, wherein the second temperature is (i) a nucleic acid denaturation temperature, or (ii) a nucleic acid denaturation temperature or a nucleic acid annealing temperature. A method for measuring a melting curve using the apparatus according to any one of claims 1 to 9,
(A) placing a sample solution containing nucleic acid in a well;
(B) Switching the reaction vessel temperature from the nucleic acid elongation reaction temperature as the first temperature to (i) the nucleic acid denaturation temperature or (ii) the nucleic acid denaturation temperature or the nucleic acid annealing temperature as the second temperature. The process of performing,
(C) a step of subsequently switching the temperature of the reaction vessel from the second temperature to the first temperature, and (d) repeating step (b) and step (c) a predetermined number of times at predetermined time intervals Process,
(E) The PCR product after the reaction is heat-treated and dissociated by a thermal change at a constant rate of 5 ° C./min or less between 60 ° C. and 90 ° C., for example, and the change in fluorescence intensity and the sample solution at that time The process of monitoring the temperature of the product (multiple peaks occur when non-specific products are included, so the specificity of the product can be confirmed)
Including
The method wherein switching the temperature of the reaction vessel from the second temperature to the first temperature is performed by turning off the operation of the thermoelectric element.