Protein reaction device and protein detection system comprising same

Abstract

The present invention provides a protein reaction device comprising: an input part for injecting a reaction solution into a reaction part; and the reaction part for inducing the reaction solution such that a membrane containing a protein reacts with the reaction solution, wherein the reaction part includes: a base including a plurality of flow channels that pass under the membrane; a transparent cover for sealing the flow channels by covering the membrane and the base; and an injection port connected to the input part between the base and the transparent cover, the membrane being disposed between the base and the transparent cover.

Description

Protein reaction device and protein detection system including the same

[0001] The present invention relates to a protein reaction device and a protein detection system including the same, and more particularly, to a protein reaction device based on the HRP sustained reaction method of an antibody-linked single protein and a protein detection system including the same.

[0002] The material presented in this section only provides background information for the present invention and does not constitute prior art.

[0003] When a luminescent solution is added to a membrane with a protein attached, the luminescent solution and the protein antibody HRP react, and using the camera of the protein detection system, the intensity and shape of the luminescence are measured at the membrane protein location, allowing the expression of a specific protein to be identified.

[0004] When the amount of protein is small, the luminescence disappears once the reaction solution is consumed, making signal measurement difficult. In most cases, increasing the measurement time is not possible. This phenomenon occurs very frequently. When the amount of protein is large, the surrounding reaction solution disappears, causing the HRP attached to the protein to change from black to gray or white, making it unusable for measurement data.

[0005] The protein to be measured can be prepared through the following process.

[0006] (1) Protein preparation and electrophoresis

[0007] After extracting proteins from cells or tissues using a buffer, a sample is prepared through protein quantification, and the protein sample to be loaded by electrophoresis is separated according to size as large proteins move slowly through the network structure formed by acrylamide and small proteins move quickly.

[0008] Proteins are placed in a negatively charged SDS buffer and move through a network of acrylamide to the positive electrode.

[0009] When proteins and size markers are placed in wells and voltage is applied to the gel, the proteins migrate at different speeds depending on their size. To separate small proteins, increase the acrylamide concentration, and to separate large proteins, decrease the acrylamide concentration. This separates proteins with large molecular weights.

[0010] The upper part of the electrophoresis is made by first making a gel with stacking buffer so that the proteins start from the same position, and then making a gel with a second running buffer so that they move under the same conditions.

[0011] (2) Transfer of proteins from the gel to the membrane

[0012] Because proteins separated on a gel cannot bind to antibodies, detection using antibodies requires transferring the proteins from the gel to a membrane made of nitrocellulose or PVDF (polyvinylidene difluoride). This transfer is accomplished using running buffer or by applying electricity in a semi-dry manner.

[0013] (3) Blocking process

[0014] After transferring the protein to the membrane, the blocking process fills the empty space of the membrane, allowing only specific proteins to be detected cleanly and reducing nonspecific binding of antibodies to proteins.

[0015] (4) Primary and secondary antibody reactions and detection

[0016] A primary antibody that specifically binds to the protein to be detected is placed on the membrane and reacted with the protein, and then the membrane is reacted with a secondary antibody that has a luminescent function called HRP attached.

[0017] After the secondary antibody reaction, the unbound secondary antibody is washed away with wash buffer, and the protein band is measured with a camera using ECL solution to complete the protein experiment.

[0018] When researching proteins related to diseases such as cancer, dementia, high blood pressure, etc., the method used when extracting and testing proteins is very effective and is used by researchers all over the world.

[0019] Western blot is an experimental method that measures the level of luminescence by attaching HRP to an antibody for a specific protein obtained from cells or tissues. After electrophoresis of the proteins to classify them by size, the proteins in the gel are transferred to a membrane, and then antigen-antibody + luminescent HRP are attached and the amount of light is measured to confirm the level of protein expression.

[0020] In other words, Western blot uses an antibody that reacts with the antigen epitope of the protein to be found to find only the desired protein (antigen) in a sample protein mixture. After separating the proteins by size on a gel using electrophoresis, the proteins are transferred to a membrane such as PVDF or nylon.

[0021] By attaching an antibody with a luminescent probe to a protein on the membrane, the antigen-antibody reaction is used to find the specific protein to be found and measure the position and intensity of the luminescence in a protein experiment.

[0022] The problem to be solved by the present invention is to provide a protein reaction device capable of maintaining membrane activity and a protein detection system including the same.

[0023] The problems to be solved by the present invention are not limited to the problems mentioned above, and other problems not mentioned will be clearly understood by those skilled in the art from the description below.

[0024] When researchers measure proteins on a membrane, if the protein is small or the binding of the luminescent antibody is low, the luminescent reaction is very small and only occurs momentarily, so in most cases, the measurement is not possible and the result disappears.

[0025] Accordingly, we are trying to solve this problem by applying expensive, high-sensitivity cameras, but the reason why measurement is difficult is because the amount of protein and antibody that can be measured sensitively is fundamentally small.

[0026] If a solution is supplied to the membrane in a dark room where light is blocked so that the reaction continues, even if the signal is weak, the reaction continues and weakly reactive proteins can be measured with a camera.

[0027] If the amount of protein is large, it will immediately turn white or off-white due to excessive reaction with the luminescent solution.

[0028] In order to achieve the above object, according to one embodiment of the technical idea of ​​the present invention, a protein reaction device is disclosed, which comprises: an input portion for injecting a reaction solution into a reaction portion; and a reaction portion for inducing the reaction solution so that a membrane containing a protein reacts with the reaction solution, wherein the reaction portion comprises: a base including a plurality of water channels passing under the membrane; a transparent cover covering the membrane and the base to seal the water channels; and an inlet connected to the input portion between the base and the transparent cover, wherein the membrane is arranged between the base and the transparent cover.

[0029] In addition, the protein reaction device is characterized in that the input section injects the reaction solution into the reaction section using pneumatic pressure or hydraulic pressure, either manually or electrically.

[0030] Additionally, the protein reaction device can have an input section that causes the reaction solution to flow in a forward direction away from the inlet using positive pressure, or in a direction approaching the inlet using negative pressure.

[0031] Additionally, the protein reaction device may be configured such that the input portion includes a pump, and the reaction solution injected into the input portion is circulated back to the input portion through the action of the pump.

[0032] Additionally, the protein reaction device may be configured such that the input portion includes a syringe.

[0033] Additionally, the protein reaction device may be configured to further include a buffer section that prevents overflow of the reaction solution by introducing and withdrawing the reaction solution from the opposite side of the side where the inlet is located in the reaction section.

[0034] In addition, the protein reaction device is characterized in that the base is a plate-shaped device having a negative internal space composed of a plurality of channels formed horizontally in parallel so that a reaction solution flows; and a space where a membrane is placed on the channels.

[0035] In addition, the protein reaction device may be configured such that the base and the transparent cover each include a magnet, the base is coupled to the bottom of the imaging chamber using the attractive force of the magnet, and the transparent cover is aligned and coupled to the base using the attractive force of the magnet.

[0036] Additionally, the protein reaction device may be configured to further include handles at both ends of the base and the transparent cover that are used for coupling and separating using the attractive force of the magnet.

[0037] Additionally, the protein reaction device may be configured to further include a sealing portion disposed between the base and the transparent cover to prevent leakage of the reaction solution.

[0038] In addition, the protein reaction device may be configured to further include a connecting channel that functions as a buffer by controlling the flow rate during the inflow and outflow of the reaction solution between the input section and the reaction section.

[0039] In addition, the protein reaction device is characterized by having a reaction section having an S-shape in which a plurality of water channels flow back and forth in a zigzag manner between both ends of the membrane.

[0040] In order to achieve the above purpose, according to one embodiment of the technical idea of ​​the present invention, a protein detection system is disclosed, which comprises a protein reaction device that injects a reaction solution through an inlet, and continuously brings a new reaction solution into contact with a membrane containing a protein while reciprocating or circulating the reaction solution along a channel using air pressure to cause a reaction; an imaging system equipped with a camera that photographs the membrane; and a housing that accommodates the protein reaction device and the imaging system.

[0041] Specific details of other embodiments are included in the “Specific Details for Carrying Out the Invention” and the attached “Drawings.”

[0042] The advantages and / or features of the present invention and the methods for achieving them will become clear with reference to the various embodiments described in detail below together with the accompanying drawings.

[0043] However, the present invention is not limited to the configuration of each embodiment disclosed below, but may be implemented in various different forms, and each embodiment disclosed in this specification is provided only to ensure that the disclosure of the present invention is complete and to fully inform a person having ordinary skill in the art to which the present invention pertains of the scope of the present invention, and it should be understood that the present invention is defined only by the scope of each claim of the claims.

[0044] According to the present invention, when the amount of linked primary and secondary antibodies is small or the reaction occurs immediately and the luminescence disappears due to insufficient reaction solution immediately below the existing membrane protein, the luminescence signal measurement is weak and difficult to measure, or when the amount of protein is too large and the luminescence solution reacts excessively, the immediate surrounding reaction disappears and the signal turns gray or white, the color change can be prevented by continuously causing the reaction.

[0045] In addition, by enabling continuous contact with the luminescent solution, the luminescence occurs continuously, so that by using this patent, in cases where luminescence quickly disappears and measurement is difficult in the past, or even when the luminescent solution disappears due to excessive reaction with a large amount of protein, the signal can be measured with a camera by activating it so that luminescence continues.

[0046] Additionally, when measuring a membrane with a camera, the sensitivity can be increased by increasing the exposure time, which has the advantage of allowing measurement of proteins that could not be measured before.

[0047] The effects that can be obtained by the protein reaction device according to the technical idea of ​​the present invention are not limited to the effects mentioned above, and other effects that are not mentioned can be clearly understood by a person having ordinary skill in the technical field to which the present invention belongs from the description below.

[0048] FIG. 1 is a block diagram of a protein detection system including a protein reaction device according to one embodiment of the present invention.

[0049] Figure 2 is an exemplary diagram of a reaction section of a protein reaction device according to one embodiment of the present invention.

[0050] Figure 3 is an exploded view of the reaction unit of Figure 2.

[0051] Figure 4 is an exploded view of the reaction unit of Figure 2 viewed from a different angle than Figure 3.

[0052] Figure 5 is a plan view of the base constituting the reaction section of Figure 2.

[0053] Figure 6 is a cross-sectional view of the base of Figure 5.

[0054] Figure 7 is an example diagram of the input section of Figure 1.

[0055] Figure 8 is a connection diagram of a syringe among the base and input sections.

[0056] Figure 9 is a connection diagram of the pump among the base and input sections.

[0057] Fig. 10 is a connection diagram of a base and a syringe according to another embodiment.

[0058] Fig. 11 is a connection diagram of a base and a pump according to another embodiment.

[0059] Figure 12 is an example diagram of a reaction section over time.

[0060] Figure 13 is an example of a membrane in which continuous activation is maintained.

[0061] Figure 14 is an example of another membrane.

[0062] Before describing the present invention in detail, it should be understood that the terms or words used in this specification should not be interpreted as being unconditionally limited to their usual or dictionary meanings, and that the inventor of the present invention may appropriately define and use the concepts of various terms in order to explain his or her invention in the best possible manner, and further, that these terms or words should be interpreted as meanings and concepts that are consistent with the technical idea of ​​the present invention.

[0063] That is, it should be noted that the terms used in this specification are only used to describe preferred embodiments of the present invention, and are not intended to specifically limit the contents of the present invention, and that these terms are defined in consideration of various possibilities of the present invention.

[0064] Additionally, it should be noted that in this specification, singular expressions may include plural expressions unless the context clearly indicates a different meaning, and similarly, even if expressed in plural, may include a singular meaning.

[0065] Throughout this specification, whenever a component is described as "including" another component, it may mean that the component may further include any other component, rather than excluding any other component, unless specifically stated otherwise.

[0066] Furthermore, when a component is described as being "inside or connected to" another component, it should be understood that the component may be installed in direct connection with or in contact with the other component, may be installed spaced apart from the other component by a certain distance, and if installed spaced apart from the other component by a certain distance, there may be a third component or means for fixing or connecting the component to the other component, and the description of this third component or means may be omitted.

[0067] On the other hand, if a component is described as being "directly connected" or "directly connected" to another component, it should be understood that no third component or means exists.

[0068] Likewise, other expressions that describe the relationship between components, such as "between" and "directly between", or "adjacent to" and "directly adjacent to", should be interpreted as having the same meaning.

[0069] Additionally, it should be noted that the terms “one side,” “the other side,” “one side,” “the other side,” “first,” “second,” etc. in this specification, if used, are used to clearly distinguish one component from another component, and that the meaning of the component is not limited by such terms.

[0070] In addition, terms related to position, such as “upper,” “lower,” “left,” and “right,” etc., in this specification, if used, should be understood to indicate relative positions of the corresponding components in the corresponding drawings, and unless absolute positions are specified for these positions, these position-related terms should not be understood to refer to absolute positions.

[0071] In addition, in this specification, when specifying the drawing numbers for each component of each drawing, the same component has the same drawing number even if the component is shown in a different drawing, that is, the same reference number indicates the same component throughout the specification.

[0072] In the drawings attached to this specification, the size, position, connection relationship, etc. of each component constituting the present invention may be described with some exaggeration, reduction, or omission in order to sufficiently clearly convey the idea of ​​the present invention or for convenience of explanation, and therefore the proportions or scales may not be strict.

[0073] In addition, in the following description of the present invention, a detailed description of a configuration that is judged to unnecessarily obscure the gist of the present invention, for example, a known technology including a prior art, may be omitted.

[0074] Hereinafter, embodiments of the present invention will be described in detail with reference to the relevant drawings.

[0075] Many protein measurement researchers have found that when measuring proteins on a membrane, if the protein is in small quantities or the binding of luminescent antibodies is low, the luminescent reaction is very small and only occurs momentarily, so in most cases, the measurement is not possible and the result disappears.

[0076] Accordingly, attempts are being made to solve the problem by applying expensive, high-sensitivity cameras, but the fundamental reason for the difficulty in measuring is that the amount of protein and antibody that can be measured sensitively is small.

[0077] If the solution is continuously supplied to the membrane in a dark room where light is blocked so that the reaction continues, even if the signal is weak, the reaction continues and the weakly reacting protein can be measured with a camera.

[0078] If the amount of protein is large, it will immediately turn gray or white due to excessive reaction with the luminescent solution.

[0079] A protein reaction device (100) according to one embodiment of the present invention includes a configuration that causes a luminescence by contacting a luminescent solution (Enhenced Chemiluscence, ECL) with a membrane to which a protein emitting a weak or strong signal depending on the amount of protein is attached, and a configuration that automatically moves the ECL solution back and forth a certain distance to continuously activate the ECL solution on the membrane.

[0080] The reaction solution may include an ECL solution. For example, the reaction solution may be created by mixing luminol and an oxidizing agent (hydrogen peroxide or another oxidizing agent). Luminol is the primary agent in chemiluminescence reactions and reacts with the oxidizing agent to emit light. The oxidizing agent reacts with luminol to induce chemiluminescence.

[0081] There is an advantage in that luminescence can be maintained continuously when the reaction solution is in continuous contact with the protein secondary antibody HRP of the membrane through the reaction section (130).

[0082]

[0083] FIG. 1 is a block diagram of a protein detection system including a protein reaction device according to one embodiment of the present invention.

[0084] Referring to FIG. 1, a protein detection system (10) according to an embodiment of the present invention may be configured to include a protein reaction device (100), an imaging system (200), and a housing (300). The housing (300) is in a chamber form, and an imaging system (200) equipped with a camera (210) is installed inside the housing (300), and when the door is opened, the protein reaction device (100) can be placed on a shelf inside the housing (300).

[0085] The protein reaction device (100) has a function of continuously reacting a membrane containing proteins with a reaction solution until a reaction effect appears. The protein reaction device (100) may be configured to include an input unit (110) and a reaction unit (130).

[0086] The input unit (110) has a function of injecting a reaction solution into the reaction unit (130). In addition, the input unit (110) has a function of applying air pressure to the reaction solution to induce a reaction by continuously bringing the reaction solution into contact with a membrane provided inside the reaction unit (130).

[0087] The reaction unit (130) has a function of inducing the reaction solution to flow in both directions so that the reaction solution frequently comes into contact with the membrane.

[0088] The imaging system (200) has a function of capturing a reaction scene of a membrane and generating an image using a camera (210).

[0089] Hereinafter, a protein reaction device (100) according to one embodiment of the present invention will be described in detail.

[0090] Figure 2 is an exemplary diagram of a reaction section of a protein reaction device according to one embodiment of the present invention.

[0091] Figure 3 is an exploded view of the reaction unit of Figure 2.

[0092] Figure 4 is an exploded view of the reaction unit of Figure 2 viewed from a different angle than Figure 3.

[0093] Referring to FIGS. 2 to 4, the reaction unit (130) may be configured to include a transparent cover (131) and a base (140).

[0094] The input section (110) will be described in detail in Fig. 7.

[0095] The transparent cover (131) has a function of covering the base (140) by being covered with the base (140). In addition, the movement of the reaction solution in the water channel (144) and the presence of proteins detected in the membrane can be observed through the transparent cover (131).

[0096] The transparent cover (131) and the base (140) are coupled to each other, and the reaction solution moves through the water channel (144) formed inside the base (140). That is, since the reaction solution exists between the transparent cover (131) and the base (140), a sealing part (134) can be installed between the transparent cover (131) and the base (140) to prevent the reaction solution from leaking to the outside. The sealing part (134) can be made of rubber in the shape of an O-ring.

[0097] The base (140) includes a plurality of channels passing under the membrane.

[0098] An injection port (141) connected to the input unit (110) may be provided between the base (140) and the transparent cover (131).

[0099] A membrane may be placed between the base (140) and the transparent cover (131).

[0100] The transparent cover (131) must be able to be freely opened and closed with respect to the base (140). To solve this, the transparent cover (131) includes a magnet (136), and the base (140) also includes a magnet (137). The two magnets (136, 137) at corresponding positions can be coupled to each other by the action of attraction. In addition, when the transparent cover (131) and the base (140) are separated, handles (138) can be formed at both ends of the transparent cover (131) for the convenience of separation. The magnet (137) formed on the base (140) can be coupled to a metal stand (135) on the bottom surface of the base (140) by attraction. The stand (135) can be used for transportation.

[0101] Alternatively, the magnet (137) included in the base (140) can be attracted to the bottom of the shelf formed inside the housing (300) of the protein detection system (10).

[0102] Figure 5 is a plan view of the base constituting the reaction section of Figure 2.

[0103] Referring to Fig. 5, the base (140) has a rectangular plate shape. A plurality of channels (144) through which a reaction solution can flow are formed engraved on the base (140). An inlet (141) through which the reaction solution is injected can be formed at one end of the base (140). The inlet (141) is connected to the input unit (110).

[0104] The reaction solution injected into the injection port (141) first encounters the flow control unit (143) and then the connecting water channel (142). The flow control unit (143) is a protrusion formed on the water channel and functions as a buffer by weakening the strong flow rate.

[0105] The connecting channel (142) is a type of storage space located between the input section (110) and the reaction section (130) and has the function of controlling the flow rate so that the reaction solution is evenly distributed to multiple channels (144).

[0106] The channel (144) corresponds to a passage through which the reaction solution flows. Since the reaction solution can flow across the membrane in the forward and backward directions along the channel (144), the reaction solution can continuously change direction and contact the membrane to increase the chance of reaction. The depth of the channel can be determined according to the size of the reaction section (130) and the size of the membrane, and can be designed to have a depth of, for example, 0.3 mm. The width of the channel (144) can be designed to have a width of 1 mm.

[0107] A membrane position (146) is positioned in the center of the water channel (144) where the membrane is positioned. The membrane is in a floating state on the water channel (144), and the reaction solution flows through the upper and lower parts of the membrane.

[0108] A spill storage unit (145) may be placed on the outside of each water channel (144). The spill storage unit (145) is a place to temporarily store a reaction solution that may spill due to a sealing failure.

[0109] Figure 6 is a cross-sectional view of the base of Figure 5.

[0110] Referring to Fig. 6, a cross-section of the base (140) is depicted when cut vertically along the dashed line (A) shown in Fig. 5. The water channel (144) is a passage through which the reaction solution flows. A trench (147) may be formed between the water channels (144). In addition, the space above the water channels (144) and the trench (147) is a floating space (148) where the membrane (M) is positioned. Since the membrane (M) adheres closely to the transparent cover (131) covering the base (140), there is no concern about it moving along with the reaction solution.

[0111] Figure 7 is an example diagram of the input section of Figure 1.

[0112] Referring to Fig. 7, the input unit (110) injects the reaction solution into the reaction unit (130) using air pressure, hydraulic pressure, or a manual or electric method. The input unit (110) may include a syringe, i.e., a syringe (111), or may include a syringe (111) and a driving device (112) that automatically drives the piston of the syringe (111). In addition, the input unit (110) may include a mini pump (114) instead of the syringe (111). Accordingly, the reaction solution may be injected and reciprocated or circulated across the membrane (M) along the water channel by means of air pressure by a syringe (111) operated by a human operator, a syringe (111) operated by a driving device (112), or a mini pump (114). The driving device (112) can be configured to control the linear movement of the syringe (111) piston using the power of an electric motor.

[0113] A syringe (111) having a capacity of 1 ml to 20 ml can be used. When the membrane is placed and the protein reaction device (100) is placed in the housing and an image is measured, if the position of the membrane is misaligned, the image can be adjusted to be positioned horizontally in the correct position through an external program.

[0114] The driving device (112) includes a moving part switch, and when the moving part switch is turned on, the driving device (112) controls the piston of the syringe (111) to reciprocate, thereby allowing the reaction solution to continuously react with the membrane containing the protein.

[0115] Figure 8 is a connection diagram of a syringe among the base and input sections.

[0116] Referring to FIG. 8, the syringe (111) can be connected to the injection port (141) formed in the base (140) through a tube (113).

[0117] Figure 9 is a connection diagram of the pump among the base and input sections.

[0118] Referring to Fig. 9, the mini pump (114) can be connected to the injection port (141) formed in the base (140) through a tube (113). As a difference compared to the syringe (111), the mini pump (114) has the function of circulating the reaction solution.

[0119] Fig. 10 is a connection diagram of a base and a syringe according to another embodiment.

[0120] Referring to Fig. 10, the plurality of water channels (154) engraved on the base (150) are characterized by an S-shape that allows water to flow back and forth in a zigzag manner between both ends of the membrane. That is, compared to the water channels in the same direction on the base (140), the water channels engraved on the base (150) are characterized by a narrower width and a longer length. The position of the buffer section (133) is depicted by a broken line. The syringe (111) is connected to the injection port (151) through the tube (113), and the injection port (151) is connected to the connecting water channel (152) before reaching the water channel (154).

[0121] Fig. 11 is a connection diagram of a base and a mini pump according to another embodiment.

[0122] Referring to Fig. 11, the mini pump (114) can circulate the reaction solution by connecting the inlet (151), which is the starting point of the water channel (154), and the end point of the water channel (154) through a tube (113).

[0123] Figure 12 is an example diagram of a reaction section over time.

[0124] Referring to Fig. 12, a reaction unit (130) is depicted. The process of a reaction solution injected from an inlet (141) (not shown) located on the right side of the reaction unit (130) flowing along a water channel (144) is depicted. The reaction solution slowly permeates along the water channel (144), passes through a membrane (M), and reaches a buffer unit (133). The buffer unit (133) prevents overflow while controlling the height of the reaction solution.

[0125] The buffer section (133) is in the form of a hollow column, the bottom surface of the space inside the column is connected to the water channel (144), and the top surface of the space is in contact with the air, so that when the reaction solution flows into the buffer section (133) through the water channel (144), the height of the reaction solution rises against the atmospheric pressure.

[0126] When positive and negative pressures are alternately transmitted through the input unit (110), the reaction solution can move back and forth around the membrane (M), so that the reaction solution can continuously contact and react with the membrane (M).

[0127] Figure 13 is an example of a membrane in which continuous activation is maintained.

[0128] Referring to Figure 13, the image on the left is an image of a membrane according to a conventional technique, and the image on the right is an image of a membrane obtained using a protein reaction device (100) according to an embodiment of the present invention. Comparing the two images, it can be seen that proteins can be detected more clearly in the present invention, where continuous activation is maintained.

[0129] According to one embodiment of the present invention, a protein reaction device (100) is a method that can continuously cause a reaction to prevent color change in cases where the amount of linked primary and secondary antibodies is small because the luminescence reaction does not occur additionally due to a lack of reaction solution immediately below an existing membrane protein, or the luminescence disappears because the reaction occurs immediately, making it difficult to measure the luminescence signal because it is weak, or in cases where the amount of protein is too large and the luminescence solution reacts excessively, causing the immediate surrounding reaction to disappear and the signal to turn gray or white.

[0130] According to the present invention, since continuous contact with a luminescent solution is enabled, luminescence occurs continuously, so that in cases where measurement is difficult due to luminescence disappearing quickly in the past, or even in cases where the luminescent solution disappears due to excessive reaction with a large amount of protein, the signal can be measured with a camera by activating the luminescence to continue.

[0131] According to the present invention, when measuring a membrane using a camera, the sensitivity can be increased by increasing the exposure time, so there is a great advantage in that it is possible to measure proteins that could not be measured before.

[0132] Figure 14 is an example of another membrane.

[0133] Referring to Fig. 14, images of proteins detected on a membrane are depicted when using vinyl according to a conventional technique and when using a protein reaction device (100) according to an embodiment of the present invention. In cases where sensitivity is high with a weak band, when a very weak signal is detected, when a weak signal that quickly disappears is detected, when detection is made by continued activation of a band, when a situation where it can burn out with a strong band, and even in cases of a very weak signal of chemidoc, protein detection can be made more clearly according to the present invention than in the conventional technique.

[0134] According to one embodiment of the present invention, when the luminescence reaction does not occur additionally due to insufficient reaction solution immediately below the existing membrane protein, or when the amount of linked primary and secondary antibodies is small, or when the reaction occurs immediately and luminescence disappears, or when the amount of protein is too large and the luminescence solution reacts excessively, and the surrounding reaction disappears immediately, the signal turns gray or white, etc., the measurement of the luminescence signal is weak and difficult to measure, and the signal can be continuously caused to occur so that it does not change.

[0135] Above, although some examples have been given and various preferred embodiments of the present invention have been described, the description of the various embodiments described in the “Specific Details for Carrying Out the Invention” section is merely exemplary, and those skilled in the art to which the present invention pertains will readily understand that they can carry out various modifications of the present invention or carry out equivalent implementations of the present invention based on the above description.

[0136] In addition, since the present invention can be implemented in various other forms, the present invention is not limited by the above description, and the above description is provided only to make the disclosure of the present invention complete and to fully inform a person having ordinary skill in the art to which the present invention belongs of the scope of the present invention, and it should be understood that the present invention is defined only by each claim of the claims.

[0137] The present invention can be used in the field of manufacturing a protein detection system.

Claims

1. Input section for injecting the reaction solution into the reaction section; and A membrane containing a protein comprises a reaction unit that induces the reaction solution to react with the reaction solution, The above reaction part is, A base comprising a plurality of channels passing under the membrane; A transparent cover that covers the membrane and the base to seal the water channel; and Including an inlet connected to the input portion between the base and the cover, The membrane is configured to be placed between the base and the transparent cover. Protein reaction device.

2. In claim 1, the input unit, A protein reaction device characterized in that the reaction solution is injected into the reaction section using pneumatic pressure or hydraulic pressure, either manually or by electric means.

3. In claim 1, the input unit, Using positive pressure, the reaction solution is made to flow in a forward direction away from the inlet, or using negative pressure, it is made to flow in a direction approaching the inlet. Protein reaction device.

4. In claim 1, the input unit, A protein reaction device comprising a pump, wherein the reaction solution injected from the input section is configured to circulate back to the input section through the action of the pump.

5. In claim 1, The above input unit is configured to include a syringe, a protein reaction device, 6. In claim 5, A protein reaction device further comprising a buffer section for preventing overflow of the reaction solution by introducing and discharging the reaction solution from the opposite side of the side where the injection port is located in the reaction section.

7. In claim 1, the base, A plurality of water channels formed horizontally and parallel to allow the reaction solution to flow; and A protein reaction device characterized by having a plate-shaped negative internal space formed by a space where the membrane is placed on the water channel.

8. In claim 1, The above base and the above transparent cover each include a magnet, The above base is coupled to the bottom of the shelf within the housing of the protein detection system using the attractive force of the magnet, A protein reaction device in which the above transparent cover is configured to be aligned and combined with the base using the attractive force of the magnet.

9. In claim 1, A protein reaction device, wherein the above base and the above transparent cover are configured to further include handles at both ends that are used for coupling and decoupling using the attractive force of a magnet.

10. In claim 1, A protein reaction device further comprising a sealing portion disposed between the base and the transparent cover to prevent leakage of the reaction solution.

11. In claim 1, It is configured to further include a connecting channel that functions as a buffer by controlling the flow rate when the reaction solution is introduced and discharged between the input unit and the reaction unit. Protein reaction device.

12. In claim 1, the reaction unit comprises: A protein reaction device characterized in that the plurality of water channels have an S-shape that allows the water to flow back and forth in a zigzag manner between both ends of the membrane.

13. A protein reaction device that injects a reaction solution through an inlet and uses air pressure to move or circulate the reaction solution back and forth along a water channel, thereby continuously bringing a membrane containing protein into contact with a new reaction solution to cause a reaction: An imaging system equipped with a camera for photographing the above membrane; and A protein detection system comprising a housing that houses the protein reaction device and the imaging system.

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