JP2007292527A - Microchip and system for detecting chemical reaction - Google Patents
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Abstract
Description
本発明は、有機化合物、生体試料などの微量試料を混合、反応、合成、抽出、分離する事を目的としたマイクロチップであってそれら操作結果を検出する事が可能な化学反応検出システムに関する。 The present invention relates to a chemical reaction detection system that is a microchip intended to mix, react, synthesize, extract, and separate a trace amount sample such as an organic compound and a biological sample and detect the operation results.
有機化学、生化学分野において混合、反応、合成、抽出、分離、分析について高速化、微少試料、微小空間での操作が注目されており、その技術を確立するためにマイクロチップの研究が精力的に進められている。
一般的にマイクロチップ は、微細な流路をもったガラス基板と試料を導入及び排出する孔をもったガラス基板の2枚が接合されたものである。
In the fields of organic chemistry and biochemistry, mixing, reaction, synthesis, extraction, separation, and analysis have been attracting attention for high-speed operation, small samples, and operation in microspaces, and research on microchips has been vigorous to establish that technology. It is advanced to.
In general, a microchip is formed by bonding a glass substrate having a fine channel and a glass substrate having holes for introducing and discharging a sample.
マイクロチップ内で前述した混合、反応、合成、抽出、分離(以後、これら5工程を反応と略す)が行われた後、それらによって得られた生成物について該マイクロチップ内で分析・検出(以後、これら2工程を検出と略す)を行う。 前述の反応・検出を行う際、一般的に反応に必要な試薬を順に送液する。マイクロチップ外に試薬を貯蔵するリザーバーを設け試薬をポンプを用いて送液する。試薬を別の試薬へ変更する度にポンプの入れ替えや流路の洗浄工程が必要になる。また、操作の際に気泡や不純物が混入しやすく反応結果のばらつきの原因となる。
この課題の対策としてリザーバーを1枚のマイクロチップ内に封入する方法があるが、試薬を入れ替える際に流路の分岐の部分に先に送液した試薬が残留し反応結果のばらつきの原因となる。
After the above-described mixing, reaction, synthesis, extraction, and separation (hereinafter, these five steps are abbreviated as reactions) are performed in the microchip, the products obtained by these are analyzed and detected in the microchip (hereinafter referred to as “reactions”). These two steps are abbreviated as detection). When performing the above-described reaction / detection, reagents necessary for the reaction are generally sent in order. A reservoir for storing the reagent is provided outside the microchip, and the reagent is fed using a pump. Each time the reagent is changed to another reagent, a pump replacement and a flow path cleaning step are required. In addition, bubbles and impurities are likely to be mixed during the operation, causing variations in reaction results.
As a countermeasure to this problem, there is a method of enclosing a reservoir in one microchip. However, when the reagent is replaced, the reagent that has been sent first remains in the branch of the flow path, causing variations in reaction results. .
本発明の目的は、操作の際に気泡や不純物の混入を防ぎ、反応結果のばらつきを軽減する事ができるマイクロチップ及び化学反応検出システムを提供することである。 An object of the present invention is to provide a microchip and a chemical reaction detection system capable of preventing bubbles and impurities from being mixed during operation and reducing variations in reaction results.
本発明は、以下の通りである。
(1)幅が1μm〜1cmの流路、前記流路に流体を導入可能な導入孔、及び前記流路から流体を排出可能な排出孔とを有するマイクロチップであって、更に化学反応又は生化学反応に使用する試薬を蓄えるためのリザーバー部を同一チップ内に有し、かつ前記流路によって導通していることを特徴とするマイクロチップ。
(2)化学反応又は生化学反応を目的とした反応部、幅が1μm〜1cmの流路、前記流路に流体を導入可能な導入孔、及び前記流路から流体を排出可能な排出孔を有するマイクロチップであって、更に前記反応に使用する試薬を蓄えるためのリザーバー部を同一チップ内に有し、導入孔、リザーバー部、反応部がこの順に配置され、かつ前記流路によって導通していることを特徴とするマイクロチップ。
(3)前記リザーバー部と前記反応部との間に更に流体の流量の調節又は流体の送液/停止を切り替えることができるバルブを有する(2)記載のマイクロチップ。
(4)前記流路が分岐部がないものであり、前記流路内にリザーバー部及び反応部が形成されている(2)又は(3)記載のマイクロチップ。
(5)(1)記載のマイクロチップと、化学反応又は生化学反応を目的とした反応部、幅が1μm〜1cmの流路、前記流路に流体を導入可能な導入孔、及び前記流路から流体を排出可能な排出孔を有する第2のマイクロチップとを導通手段により連結して構成される化学反応検出システム。
(6)(1)〜(4)いずれか記載のマイクロチップに化学反応又は生化学反応に使用する試薬を導入し、使用するまでは凍結保存し、使用直前に解凍する事によって化学反応又は生化学反応を行う事を特徴とする化学反応検出方法。
The present invention is as follows.
(1) A microchip having a flow path having a width of 1 μm to 1 cm, an introduction hole through which fluid can be introduced into the flow path, and a discharge hole through which fluid can be discharged from the flow path. A microchip having a reservoir part for storing a reagent used for a chemical reaction in the same chip and being connected by the flow path.
(2) a reaction section for the purpose of chemical reaction or biochemical reaction, a flow path having a width of 1 μm to 1 cm, an introduction hole capable of introducing a fluid into the flow path, and a discharge hole capable of discharging the fluid from the flow path The microchip further includes a reservoir part for storing the reagent used for the reaction in the same chip, and the introduction hole, the reservoir part, and the reaction part are arranged in this order, and are conducted by the flow path. A microchip characterized by
(3) The microchip as set forth in (2), further comprising a valve capable of switching the flow rate of the fluid or switching the liquid feeding / stopping between the reservoir unit and the reaction unit.
(4) The microchip according to (2) or (3), wherein the flow path has no branch part, and a reservoir part and a reaction part are formed in the flow path.
(5) The microchip according to (1), a reaction part intended for chemical reaction or biochemical reaction, a channel having a width of 1 μm to 1 cm, an introduction hole through which fluid can be introduced into the channel, and the channel A chemical reaction detection system configured by connecting a second microchip having a discharge hole capable of discharging a fluid from a liquid by a conduction means.
(6) The reagent used for the chemical reaction or biochemical reaction is introduced into the microchip according to any one of (1) to (4), stored frozen until use, and thawed immediately before use. A chemical reaction detection method characterized by performing a chemical reaction.
本発明に従うと、前述の反応・検出を行う際、試薬を別の試薬へ変更する度にポンプの入れ替えや流路の洗浄工程が不要になる為、操作の際に気泡や不純物の混入を防ぐことができ反応結果のばらつきを軽減する事ができる。
また、導入孔、流路、リザーバー部、流路、反応部が順に並んでおり流路の分岐がない為、分岐点における試薬の残留を防ぐ事ができ、反応結果のばらつきを軽減する事ができる。
According to the present invention, when performing the above-described reaction / detection, it is not necessary to replace the pump or clean the flow path every time the reagent is changed to another reagent, thereby preventing air bubbles and impurities from being mixed during operation. Variation of reaction results can be reduced.
In addition, since the introduction hole, flow path, reservoir section, flow path, and reaction section are arranged in order and there is no branch of the flow path, it is possible to prevent the reagent from remaining at the branch point and reduce the variation in the reaction results. it can.
本発明のマイクロチップの一実施態様を図1に示す。図1は、導入孔2、リザーバー部3、5、7、バルブ41、42、43、反応部8が順に形成され、微細な流路により分岐部がなく導通されているマイクロチップである。 One embodiment of the microchip of the present invention is shown in FIG. FIG. 1 shows a microchip in which an introduction hole 2, reservoir portions 3, 5, 7, valves 41, 42, 43, and a reaction portion 8 are formed in this order and are connected by a fine flow path without a branching portion.
本発明のマイクロチップに使用する素材はガラス又はプラスチックが好ましい。 The material used for the microchip of the present invention is preferably glass or plastic.
本発明のリザーバー部は、化学反応又は生化学反応に使用する試薬を蓄えるためのチップ内に形成される部位である。リザーバー部の形状は流路同様に溝形状でも構わないし円柱状、半球上でも差し支えない。抗原抗体反応に使用する場合の試薬は、標識抗体溶液、抗原溶液、及び洗浄剤等である。 The reservoir portion of the present invention is a site formed in a chip for storing a reagent used for a chemical reaction or a biochemical reaction. The shape of the reservoir portion may be a groove shape as in the flow path, or may be a cylindrical shape or a hemisphere. Reagents for use in the antigen-antibody reaction include a labeled antibody solution, an antigen solution, and a cleaning agent.
リザーバー部と反応部が同一チップ内に形成されている場合、リザーバー部と反応部との間に更に流体の流量の調節又は流体の送液/停止を切り替えることができるバルブを有することが好ましい。 When the reservoir portion and the reaction portion are formed in the same chip, it is preferable to further include a valve capable of switching the flow rate of the fluid or switching the fluid supply / stop between the reservoir portion and the reaction portion.
バルブは小型化を考慮するとダイヤフラム式バルブ、電磁バルブ、又は手動式回転バルブが好ましい。特に簡便なものとして、シリコンゴム等の素材で形成された3方弁を有する3方弁バルブが挙げられる。 In view of miniaturization, the valve is preferably a diaphragm valve, an electromagnetic valve, or a manual rotary valve. A particularly simple one is a three-way valve valve having a three-way valve formed of a material such as silicon rubber.
反応部の一例としては、図2に示すように、流路の底面11から流路の上面10に向かって突起部からなるダム部9を形成し、抗体が固定化されたマイクロビーズ8を流路内に固定化したものが挙げられる。 As an example of the reaction part, as shown in FIG. 2, a dam part 9 made of a protrusion is formed from the bottom face 11 of the flow path toward the upper face 10 of the flow path, and the microbeads 8 on which the antibody is immobilized are allowed to flow. The thing fixed in the road is mentioned.
本発明のマイクロチップの他の実施態様としては、図1に示すマイクロチップにおいて、導入孔2、リザーバー部3、5、7、バルブ41、42、43が順に形成され、微細な流路により分岐部がなく導通されているマイクロチップで、反応部がない形態である。
この第1のマイクロチップと、反応部を有する第2のマイクロチップとを導通手段により連結して化学反応検出システムが得られる。
As another embodiment of the microchip of the present invention, in the microchip shown in FIG. 1, an introduction hole 2, reservoir portions 3, 5, and 7, valves 41, 42, and 43 are formed in this order, and branched by a fine flow path. This is a microchip that is conductive without a part and has no reaction part.
A chemical reaction detection system is obtained by connecting the first microchip and the second microchip having the reaction part by a conduction means.
本発明のマイクロチップの導入孔からポンプを用いて送液する際に使用するチューブ、あるいはマイクロチップを連結するのに使用するチューブやジョイントの素材は、反応物の付着が少ないテフロン(登録商標)、ポリプロピレン、PEEK(=ポリエーテルエーテルケトン)などが好ましい。 Teflon (registered trademark) is a tube used when liquid is fed from the introduction hole of the microchip of the present invention by using a pump, or a tube or joint material used to connect the microchip is less attached to the reactant. , Polypropylene, PEEK (= polyetheretherketone) and the like are preferable.
本発明において、化学反応を検出する検出部を、反応部を有するマイクロチップと同じチップ上に設けても良い。又は反応部を有するマイクロチップと、検出部を有する別の検出用マイクロチップとを連結する方法もある。検出機としては熱レンズ検出器(以下、TLMと略す。)のような流体を正確に測定できるようなものが好ましい。 In the present invention, the detection unit for detecting a chemical reaction may be provided on the same chip as the microchip having the reaction unit. Alternatively, there is a method of connecting a microchip having a reaction part and another detection microchip having a detection part. A detector that can accurately measure a fluid such as a thermal lens detector (hereinafter abbreviated as TLM) is preferable.
本発明の化学検出方法について、抗原抗体反応の場合の例を以下に示す。図1に示すマイクロチップのリザーバー部に標識抗体溶液、抗原溶液、及び洗浄剤充填し、各バルブを解放する事により反応を開始させる。又は、図1に示すマイクロチップのリザーバー部に標識抗体溶液、及び洗浄剤充填し、この状態でマイクロチップを凍結保存する。こうすることによって、リザーバー内の試薬の蒸発や流路内への気泡の混入を防止することができる。使用時に、マイクロチップを解凍し、抗原リザーバー部に抗原溶液を充填し各バルブを解放する事により反応を開始させる。 Regarding the chemical detection method of the present invention, an example in the case of an antigen-antibody reaction is shown below. The reservoir of the microchip shown in FIG. 1 is filled with a labeled antibody solution, an antigen solution, and a cleaning agent, and the reaction is started by opening each valve. Alternatively, the reservoir portion of the microchip shown in FIG. 1 is filled with a labeled antibody solution and a cleaning agent, and the microchip is stored frozen in this state. By doing so, it is possible to prevent evaporation of the reagent in the reservoir and mixing of bubbles into the flow path. At the time of use, the reaction is started by thawing the microchip, filling the antigen reservoir with the antigen solution, and releasing each valve.
《実施例》
図1のように導入孔2、標識抗体溶液リザーバー3、バルブ41、洗浄剤リザーバー5、バルブ42、抗原溶液リザーバー7、バルブ43、反応部8がこの順に並んだ微細な流路を有し且つ、流路内にダム9を有するマイクロチップ1を用意した。マイクロチップの素材は、環状オレフィン樹脂であり、寸法は70mm×30mm×0.75mmである。流路の幅は0.5mm、深さは0.5mmである。バルブはシリコンゴム製の3方弁を用いた。
次いで、抗CEA(=CARCINOEMBRYONIC ANTIGEN) 抗体をポリスチレン製のマイクロビーズに固相化し、1%ウシ血清アルブミンを含むリン酸緩衝液で抗CEA抗体により被覆されていないマイクロビーズ表面を被覆した。該マイクロビーズをマイクロチップに導入し流路内の反応部8に固定した。所定のリザーバーにCEA抗原溶液、洗浄剤(リン酸緩衝液)、ペルオキシダーゼ標識抗体溶液を封入した。その後、導入孔2より洗浄剤を2μL/分の速度で導入して、マイクロビーズに固相化された抗CEA抗体を、CEA抗原、ペルオキシダーゼ標識抗CEA抗体と順に反応させた。
最後に3,3',5,5'-TetramethylbenzidineとH2O2の混合溶液を基質として導入し酵素反応を実施した。該酵素反応により発色した基質を検出用マイクロチップ上でTLM(励起波長=650nm)を用いて発色量を計測した。各抗原濃度につきn=5で測定しそれらの平均値及びばらつきを示す指標であるCV値(=標準偏差/平均値×100)を計算した。
"Example"
As shown in FIG. 1, the introduction hole 2, the labeled antibody solution reservoir 3, the valve 41, the cleaning agent reservoir 5, the valve 42, the antigen solution reservoir 7, the valve 43, and the reaction part 8 have fine channels arranged in this order, and A microchip 1 having a dam 9 in the flow path was prepared. The material of the microchip is a cyclic olefin resin, and the dimensions are 70 mm × 30 mm × 0.75 mm. The width of the channel is 0.5 mm and the depth is 0.5 mm. A three-way valve made of silicon rubber was used as the valve.
Next, an anti-CEA (= CARCINOEMBRYONIC ANTIGEN) antibody was immobilized on polystyrene microbeads, and a microbead surface not coated with an anti-CEA antibody was coated with a phosphate buffer containing 1% bovine serum albumin. The microbead was introduced into the microchip and fixed to the reaction section 8 in the flow path. A CEA antigen solution, a detergent (phosphate buffer), and a peroxidase-labeled antibody solution were sealed in a predetermined reservoir. Thereafter, a detergent was introduced from the introduction hole 2 at a rate of 2 μL / min, and the anti-CEA antibody immobilized on the microbeads was reacted with CEA antigen and peroxidase-labeled anti-CEA antibody in this order.
Finally, a mixed solution of 3,3 ′, 5,5′-Tetramethylbenzidine and H 2 O 2 was introduced as a substrate to carry out an enzyme reaction. The color development amount of the substrate colored by the enzyme reaction was measured on a detection microchip using TLM (excitation wavelength = 650 nm). The CV value (= standard deviation / average value × 100), which is an index showing the average value and variation of each antigen concentration measured at n = 5, was calculated.
《比較例》
図3のように導入孔2、反応部8、排出孔6が順に並んだ微細な流路を有し且つ、流路内にダム9を有するマイクロチップ1を用意した。マイクロチップの素材は、環状オレフィン樹脂であり、寸法は70mm×30mm×0.75mmである。流路の幅は0.5mm、深さは0.5mmである。
次いで、抗CEA(=CARCINOEMBRYONIC ANTIGEN) 抗体をポリスチレン製のマイクロビーズに固相化し、1%ウシ血清アルブミンを含むリン酸緩衝液で抗CEA抗体により被覆されていないマイクロビーズ表面を被覆した。該マイクロビーズをマイクロチップに導入し流路内の反応部8に固定した。
CEA抗原、洗浄剤(リン酸緩衝液)、ペルオキシダーゼ標識抗体の各試薬を別々のマイクロシリンジに入れそれぞれ順に導入孔2よりマイクロチップへ導入し、実施例と同様の反応を行った。
最後に3,3',5,5'-TetramethylbenzidineとH2O2の混合溶液を基質として導入し酵素反応を実施した。該酵素反応により発色した基質を検出用マイクロチップ上でTLM(励起波長=650nm)を用いて発色量を計測した。各抗原濃度につきn=5で測定しそれらの平均値及びばらつきを示す指標であるCV値(=標準偏差/平均値×100)を計算した。
《Comparative example》
As shown in FIG. 3, a microchip 1 having a fine flow path in which an introduction hole 2, a reaction portion 8, and a discharge hole 6 are arranged in this order and having a dam 9 in the flow path was prepared. The material of the microchip is a cyclic olefin resin, and the dimensions are 70 mm × 30 mm × 0.75 mm. The width of the channel is 0.5 mm and the depth is 0.5 mm.
Next, an anti-CEA (= CARCINOEMBRYONIC ANTIGEN) antibody was immobilized on polystyrene microbeads, and a microbead surface not coated with an anti-CEA antibody was coated with a phosphate buffer containing 1% bovine serum albumin. The microbead was introduced into the microchip and fixed to the reaction section 8 in the flow path.
Each reagent of CEA antigen, detergent (phosphate buffer) and peroxidase-labeled antibody was put in a separate microsyringe and introduced into the microchip through the introduction hole 2 in order, and the same reaction as in the example was performed.
Finally, a mixed solution of 3,3 ′, 5,5′-Tetramethylbenzidine and H 2 O 2 was introduced as a substrate to carry out an enzyme reaction. The color development amount of the substrate colored by the enzyme reaction was measured on a detection microchip using TLM (excitation wavelength = 650 nm). The CV value (= standard deviation / average value × 100), which is an index showing the average value and variation of each antigen concentration measured at n = 5, was calculated.
実施例及び比較例の抗原濃度に応じた発色量(=TLMシグナル)を計測した結果を表1に示した。実施例、比較例ともにほぼ同等なTLMシグナル(平均値)を示したがCV値は実施例の方が1/3に低減した。 Table 1 shows the results of measuring the color development amount (= TLM signal) according to the antigen concentrations of the examples and comparative examples. The TLM signal (average value) was almost the same in both Examples and Comparative Examples, but the CV value was reduced to 1/3 in the Examples.
1 マイクロチップ
2 導入孔
3.標識抗体溶液のリザーバー
41、42、43 流路切換バルブ
5 洗浄剤リザーバー
6 排出孔
7 抗原溶液リザーバー
8 反応部(抗体が固定化されたマイクロビーズ)
9 ダム
1 Microchip 2 Introduction hole 3. Reservoir 41, 42, 43 of labeled antibody solution Channel switching valve 5 Cleaning agent reservoir 6 Discharge hole 7 Antigen solution reservoir 8 Reaction part (microbead on which antibody is immobilized)
9 Dam
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JP2013106595A (en) * | 2011-11-24 | 2013-06-06 | Institute Of Microchemical Technology | Micro device and bioassay system |
JP2015142893A (en) * | 2014-01-31 | 2015-08-06 | 株式会社日立製作所 | System and method for providing drugs |
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JP2013106595A (en) * | 2011-11-24 | 2013-06-06 | Institute Of Microchemical Technology | Micro device and bioassay system |
JP2015142893A (en) * | 2014-01-31 | 2015-08-06 | 株式会社日立製作所 | System and method for providing drugs |
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