TWI821757B - Biological chip detection device and detection method thereof - Google Patents

Abstract

The invention provides a biological chip detection device and a detection method. The detection device includes a conductive layer, which is stacked with a base material to form a body. The base material has a reaction area in a so-called counter electrode, and the reaction area is coated with The receptor that can be used to detect the binding of the target; the flow guide layer has an opening co-located with the reaction zone, the receptor is exposed to the body at the opening, and there is a microfluidic channel between the flow guide layer and the substrate; the detection method includes droplet The steps of sampling, cleaning and detection are to drop the sample liquid directly from the opening into the reaction area to react with the receptor. After the reaction time, the cleaning liquid is added to the reaction area and added to the sample liquid, and then penetrates into the microfluidic through capillary action. Channels are discharged side by side, and then the detection liquid is dripped into the reaction area for sample detection. The sample detection can be completed without external force driving, and the detection efficiency is effectively improved.

Description

Biological chip detection device and detection method thereof

The invention provides a detection device, particularly a biological chip detection device and a detection method thereof.

A conventional biological chip detection device has a reaction area coated with a receptor that can be combined with a detection target. The reaction area is set in the detection device and is not exposed. During detection, the operator collects samples from biological body fluids (such as Take an appropriate amount of sample from the blood and drop it at the entrance of the reaction zone, and then use an external power device to push the sample to the reaction zone through, for example, gas pressure, allowing the sample liquid to contact the receptor and pass through the reaction for detection, and then Get analysis results. However, by pressurizing the sample through an external power device, the sample is easily damaged under pressure, resulting in inaccurate analysis results.

Another conventional biochip detection device also drops the sample liquid at the entrance of the reaction area, drains the sample liquid into the reaction area through capillary action, and performs detection after contacting the receptor to obtain The analysis results. However, the process of draining the sample liquid to the reaction area takes time. The reaction does not start until the sample liquid is drained to the reaction area. This will cause a delay in the detection time and make it difficult to effectively improve the detection efficiency.

The inventor then devoted his mind to research and developed a biochip detection device and a detection method, in order to efficiently complete sample detection without the need for external driving force.

In order to achieve the above object, the present invention provides a biological chip detection device, which includes a body that includes a base material and a conductive layer. The base material is provided with a pair of electrodes, and the base material is provided with a pair of electrodes. There is a local reaction zone, and the reaction zone is coated with a receptor for detecting the binding of the target; the flow guide layer is stacked on the substrate, and the flow guide layer has an opening co-located with the reaction zone, and the receptor The opening is exposed to the body, allowing a sample liquid to be dropped directly on the reaction zone to react with the receptor, and there is a microfluidic channel connecting the reaction zone between the flow guide layer and the substrate, After the reaction, a cleaning solution is added to the sample liquid and then penetrated into the microfluidic channel and discharged.

Preferably, the flow-guiding layer includes a hydrophilic layer with capillary action and a hydrophobic layer that does not absorb water. The hydrophobic layer is located between the substrate and the hydrophilic layer, and the opening penetrates the hydrophilic layer and the hydrophobic layer. Directly leading to the reaction zone, the hydrophobic layer has bare space to form the microfluidic channel between the substrate and the hydrophilic layer.

Preferably, the opening is hexagonal and has a reaction section of equal width and a tapered buffer section. The buffer section has a wide end and a narrow end, and the wide end continues from the reaction section. One end, and the narrow end communicates with the bare space of the hydrophobic layer and communicates with the microfluidic channel.

Preferably, the method further includes an adsorption member, the hydrophilic layer has a drainage outlet at an end of the microfluidic channel away from the reaction zone, and the adsorption member is disposed on the hydrophilic layer at the drainage outlet.

Preferably, it further includes a shell, the body and the adsorption member are covered and positioned by the shell, the shell has a viewing window directly connected to the reaction zone above the receptor through the opening, and the shell There is an air hole on one side of the drain port, and the drain port communicates with the air hole in the shell.

In order to achieve the above object, the present invention provides a detection method for a biological chip detection device, which includes the steps of dropping a sample, cleaning and detecting. In the step of dropping a sample, the sample liquid is dropped directly from the opening into the reaction area. , and react with the receptor for a reaction time; in the cleaning step, after the reaction time, the cleaning solution is dripped into the sample liquid in the reaction zone and is larger than the capacity of the reaction zone. volume, allowing the sample liquid and cleaning liquid to penetrate into the microfluidic channel through capillary action and be discharged; in the detection step: after the cleaning step, a detection liquid is dripped into the reaction area to perform sample detection.

Preferably, in the step of dropping the sample, the sample liquid is reacted in the reaction zone with a volume of 10 to 15 microliters, and the reaction time is 1 to 5 minutes.

Preferably, in the cleaning step, a first drop of cleaning liquid is first dropped into the reaction zone to clean the sample liquid, and the sample liquid and cleaning liquid are allowed to penetrate into the microfluidic channel to perform the first cleaning. Then drop a second drop of cleaning solution in the reaction area to clean the sample solution, and allow the sample solution and cleaning solution to penetrate into the microfluidic channel for a second cleaning.

Preferably, in the detection step, a first drop of detection solution is first dropped in the reaction area, and after the residual cleaning solution and detection solution are allowed to penetrate into the microfluidic channel through capillary action, a second drop of detection solution is then dropped in the reaction area. In the reaction area, the second drop of detection liquid stays in the reaction area to perform the sample detection.

In order to achieve the above object, the present invention provides another detection method of a biological chip detection device, which includes the steps of dropping a sample, cleaning and detecting. In the step of dropping a sample, the sample liquid is directly dropped from the opening to the reaction. area, and react with the receptor for a reaction time; in the cleaning step, after the reaction time, the cleaning solution is dripped into the sample liquid in the reaction area and is larger than the capacity of the reaction area. The holding volume allows the sample liquid and cleaning liquid to penetrate into the microfluidic channel through capillary action and be discharged; in the detection step: after the cleaning step, a detection liquid is dropped into the reaction zone to perform sample detection; wherein , the sample liquid and cleaning liquid or the detection liquid flowing through the microfluidic channel are quickly absorbed by the adsorption member and discharged from the microfluidic channel.

In order to achieve the above object, the present invention provides another detection method of a biological chip detection device, which includes the steps of dropping a sample, cleaning and detecting. In the step of dropping a sample, the sample liquid is directly dropped from the opening to the reaction. area, and react with the receptor for a reaction time; in the cleaning step, after the reaction time, the cleaning solution is dripped into the sample liquid in the reaction area and is larger than the capacity of the reaction area. accommodate the volume, allowing the sample liquid and cleaning liquid to penetrate into the microfluidic channel through capillary action and be discharged; during detection In the step of: after the cleaning step, a detection liquid is dropped into the reaction area to perform sample detection; wherein the pore size is adjusted to control the sample liquid and cleaning liquid or the detection liquid to be discharged from the The flow rate of the microchannel.

Therefore, the biochip detection device and the detection method of the present invention allow the sample liquid to be dropped directly into the reaction area to react with the receptor first. After the reaction, the sample liquid and the cleaning liquid or the detection liquid are then It penetrates into the microfluidic channel and is discharged. In addition to completing the detection without external force, it can also directly react with the receptor when the sample liquid is dripped into the reaction area, which can relatively shorten the detection time, thereby effectively improving the detection The efficacy of efficiency.

100:Biological chip detection device

10:Ontology

11: Microfluidic channel

20:Substrate

21:Electrode

22:Reaction zone

23: Receptor

30: diversion layer

31:Opening

311: Reaction section

312: Buffer segment

312a: wide end

312b: Narrow end

32: Hydrophilic layer

321: First piercing

322: Drainage outlet

33:Hydrophobic layer

331: Second piercing

332:Third piercing

40: Adsorption parts

50: Shell parts

51:Window

52: pores

53: Fixed part

54:Slot

55: Ribs

56:Half shell part

S: sample solution

W: cleaning fluid

T: test solution

200:Detection method

201: Drop sample

202:Cleaning

203:Detection

Figure 1 is a schematic three-dimensional view of a biochip detection device according to an embodiment of the present invention.

Figure 2 is a schematic three-dimensional view of the main body of the embodiment of the present invention.

Figure 3 is an exploded schematic diagram of the main body of the embodiment of the present invention.

Figure 4 is a top exploded schematic diagram of the body of the embodiment of the present invention.

Figure 5 is an exploded schematic view of the shell according to the embodiment of the present invention.

FIG. 6 is a partial cross-sectional schematic diagram of a biological chip detection device according to an embodiment of the present invention.

Figure 7 is a flow block diagram of a detection method according to an embodiment of the present invention.

Figure 8A is a schematic diagram of the biochip detection device according to the embodiment of the present invention, in which sample liquid is directly dropped into the reaction area.

Figure 8B is a schematic diagram that continues Figure 8A and after the reaction time, the cleaning solution is dripped into the reaction zone until it penetrates into the microfluidic channel and is discharged.

Figure 8C is a schematic diagram of continuing Figure 8B and after the cleaning step, the detection solution is dropped into the reaction area for the second time to perform sample detection.

8D is a schematic diagram of the biological chip detection device according to the embodiment of the present invention adjusting the shell to reduce the pores.

In order to fully understand the purpose, characteristics and effects of the present invention, the present invention is described in detail through the following specific embodiments and the accompanying drawings, as follows:

Referring to FIGS. 1 to 8D , the present invention provides a biological chip detection device 100 and a detection method 200 thereof. The biowafer detection device 100, as shown in Figures 1 to 6, includes a body 10 including a substrate 20 and a flow guide layer 30, and in one embodiment further includes an adsorption member 40 and a shell. 50, of which:

The substrate 20 is provided with a pair of electrodes 21, and has a reaction zone 22 in a part of the pair of electrodes 21. The reaction zone 22 is coated with a receptor 23 that can be combined with a detection target. The detection target of the receptor 23 It can be an antibody, antigen, nucleic acid or small molecule, but is not limited to this.

The flow guide layer 30 is stacked with the base material 20 to form the body 10 . The flow guide layer 30 has an opening 31. The opening 31 is hollow and directly connected to the reaction zone 22. There is no object in the opening 31. The opening 31 and the reaction zone 22 are arranged on-site. The receptor 23 The opening 31 is exposed to the body 10 so that a sample liquid S can be directly dropped on the reaction area 22 to react with the receptor 23 (as shown in FIG. 8A ). There is a micro-channel 11 between the flow-guiding layer 30 and the substrate 20, and the micro-channel 11 is connected to the reaction zone 22. The sample liquid S is, for example, blood, but the present invention is not limited thereto.

As shown in Figures 2 to 4, the flow guide layer 30 of this embodiment includes a hydrophilic layer 32 and a hydrophobic layer 33. The hydrophobic layer 33 is located between the base material 20 and the hydrophilic layer 32. The hydrophilic layer 32 has capillary action. And can be smoked Water, the hydrophobic layer 33 does not absorb water, the openings 31 penetrate the hydrophilic layer 32 and the hydrophobic layer 33 and directly lead to the reaction zone 22, while the hydrophobic layer 33 has bare space to form a micro-channel 11 between the substrate 20 and the hydrophilic layer 32 .

As shown in FIG. 3 , the hydrophilic layer 32 of this embodiment has a first perforation 321 , and the hydrophilic layer 32 has a drainage outlet 322 at an end of the microchannel 11 away from the reaction zone 22 , and the hydrophobic layer 33 has a second perforation. 331, the opening 31 is formed by overlapping the first perforation 321 and the second perforation 331; in addition, the hydrophobic layer 33 has a third perforation 332 to form the bare void, and the second perforation 331 and the drainage port 322 are connected to both sides of the third perforation 332. end.

As shown in Figure 4, the opening 31 is hexagonal and has a reaction section 311 and a buffer section 312. The reaction section 311 is of equal width, while the buffer section 312 is tapered. The buffer section 312 has a wide end 312a and a narrow end 312b. The wide end 312a continues from one end of the reaction section 311, and the narrow end 312b is connected to the third through hole 332 of the hydrophobic layer 33 and connected to the microchannel 11. The receptor 23 in this embodiment is located in the reaction section 311, and the buffer section 312 is provided to have the functions of buffering and flow rate adjustment. The hexagonal shape of the opening 31 is only an embodiment, and the invention is not limited thereto. Since the opening 31 is hexagonal and directly connected to the reaction zone 22, the hydrophilic layer 32 does not produce capillary action in the opening 31, and the sample liquid S is blocked by the hexagonal structure of the opening 31, so that the sample liquid S When the cleaning liquid W or the detection liquid T is dropped in the reaction zone 22, it will not overflow.

As shown in FIGS. 5 and 6 , the body 10 and the adsorption member 40 are covered and positioned by the shell 50 . The shell 50 has a viewing window 51 passing through the opening 31 directly above the receptor 23 to the reaction zone 22 , and the shell 50 There is an air hole 52 on one side of the drain port 322 , and the drain port 322 communicates with the air hole 52 in the shell 50 . Preferably, the adsorbent member 40 is disposed on the hydrophilic layer 32 at the drainage outlet 322 .

As shown in FIGS. 5 and 6 , the shell 50 has a fixing part 53 corresponding to the adsorbing part 40 . The fixing part 53 presses the adsorbing part 40 on the drain outlet 322 so that the adsorbing part 40 is positioned without any displacement. In this embodiment, the fixing part 53 is two ribs protruding from the shell 50. However, the fixing part 53 in the present invention is not limited to the above embodiment of ribs. For example, the fixing part 53 can also be one or three. More than one rib, the shape of the rib includes but Not limited to linear shapes, such as dots or sheets. In other words, anything that can achieve the function of pressing the adsorption member 40 on the drain outlet 322 belongs to the scope of protection of the fixing part 53 of the present invention; in addition, the shell 50 has a slot 54 corresponding to the main body 10 for the main body. 10 is inserted so that the reaction area 22 is located in the window 51, and the shell 50 has a rib 55 in the slot 54, and the body 10 in the slot 54 is pressed and positioned by the rib 55. In addition, the shell member 50 in this embodiment is composed of two half shell parts 56 joined together.

As shown in Figure 7, the detection method 200 includes the steps of dropping a sample 201, cleaning 202 and detecting 203, wherein:

In the step of dropping the sample 201, the sample liquid S is dropped directly from the opening 31 onto the reaction area 22 (as shown in FIG. 8A), and reacts with the receptor 23 for a reaction time. Preferably, the sample liquid S is reacted in the reaction zone 22 with a volume of 10 to 15 microliters, and the reaction time is 1 to 5 minutes. The receptor 23 of the present invention may include but is not limited to immunoglobulins, nucleic acid probes, chemical molecules or functional proteins; the sample liquid of the present invention contains a detection target that can bind to the receptor. In one embodiment, the receptor 23 is an IgG antibody or an IgM antibody, and the detection target contained in the sample liquid S is a type of virus or microorganism that can specifically bind to the IgG antibody or IgM antibody.

In one embodiment, the receptor 23 is an immunoglobulin, which further refers to an antibody against the novel coronavirus receptor binding domain protein (anti-COVID-19 RBD antibody), and its concentration is 1-10ug/mL (microgram/mL). ml); and the detection target contained in the sample liquid S is, in this embodiment, the novel coronavirus receptor binding domain protein (COVID-19 RBD) contained in saliva or nasal mucus, and its detectable range is 1~1000pg/ mL (pg/ml).

In the step of cleaning 202, after the reaction time, the cleaning solution W is dripped into the reaction zone 22 and the sample solution S is larger than the accommodated volume of the reaction zone 22, allowing the sample solution S and the cleaning solution W to penetrate through capillary action. The microfluidic channel 11 is discharged, and the capillary action is provided by the hydrophilic layer 32 in this embodiment. Preferably, In this embodiment, during the cleaning step 202 (as shown in FIG. 8B ), a first drop of 35 microliters of cleaning solution W is first dropped to clean the sample liquid S in the reaction zone 22 to remove the remaining sample liquid S. in the substance that does not specifically bind to the receptor 23, and allow the sample solution S and the cleaning solution W to penetrate into the microfluidic channel 11 to complete the first cleaning, and then drop a second drop of 35 microliters of the cleaning solution in the reaction area 22 The sample liquid S is then washed, and the substances remaining in the sample liquid S that are not specifically bound to the receptor 23 are removed again, and the sample liquid S and the cleaning liquid W are allowed to penetrate into the microfluidic channel 11 to complete the second process. Cleaning, so that the reaction zone 22 will not affect the detection results due to non-specific binding substances remaining in the sample solution S.

In the detection step 203, after the cleaning step 202, a detection liquid T is dropped into the reaction area 22 to perform sample detection. Preferably, in the step of detection 203 in this embodiment, the first drop of 35 microliters of detection liquid T is first dropped in the reaction area 22, and the detection liquid T is allowed to penetrate into the microfluidic channel 11 through capillary action (as shown in Figure 8B (as shown in Figure 8C), then drop a second drop of detection liquid in the reaction area 22, and the second drop of detection liquid T stays in the reaction area 22 (as shown in Figure 8C), so as to perform the electrochemical reaction on the reacted receptor 23. Sample testing.

The above-mentioned sample liquid S and cleaning liquid W penetrate into the microchannel 11 through capillary action in the step of cleaning 202, and the detection liquid T penetrates into the microchannel 11 through capillary action in the step of detecting 203. In this embodiment, both are filled The microfluidic channel 11 is quickly absorbed by the adsorbent 40 when discharged from the drain port 322, so that the sample liquid S and the cleaning liquid W in the step of cleaning 202, or the detection liquid T in the step of detecting 203, can be accelerated. Exhaust the microfluidic channel 11. The arrangement of the adsorption member 40 is only a preferred embodiment, and the present invention is not limited thereto. It means that the sample liquid S and the cleaning liquid W or the detection liquid T flowing through the microchannel 11 will fill the microchannel 11 It can also be naturally discharged from the drain port 322. The difference is that the sample liquid S, the cleaning liquid W or the detection liquid T can be quickly absorbed and discharged from the microfluidic channel 11 in the presence of the adsorbent 40.

In one embodiment, the size of the pores 52 is adjusted to control the flow rate of the sample liquid S and the cleaning liquid W or the detection liquid T out of the microfluidic channel 11 . As shown in FIGS. 8A to 8C , when the air holes 52 of the housing 50 are relatively When it is large, because the exhaust volume that can be provided is larger, the sample liquid S, the cleaning liquid W or the detection liquid T are discharged from the microfluidic channel 11 faster; as shown in Figure 8D, when the pores 52 of the housing 50 are relatively large, When the time is small, the exhaust volume that can be provided is less, so the sample liquid S and the cleaning liquid W or the detection liquid T are discharged from the microfluidic channel 11 at a slower speed. The size of the pores 52 is controlled according to the speed requirements of the sample liquid S and the cleaning liquid W or the detection liquid T discharged from the microfluidic channel 11. In this embodiment, the pores 52 have a fixed diameter in the housing 50. The housing 50 can be replaced to adjust the diameter of the air hole 52, but the invention is not limited thereto. For example, a flow valve (not shown in the figure) is provided on the housing 50, and the air hole 52 is formed in the flow valve, and the hole diameter is The size can be adjusted by the flow valve, and the flow rate of the sample liquid S and the cleaning liquid W or the detection liquid T discharged from the microfluidic channel 11 can also be controlled.

From the above description, it is easy to find that the characteristics of the present invention are:

1. The biochip detection device 100 and its detection method 200 of the present invention are that the sample liquid S can be directly dropped in the reaction area 22, and the sample liquid S and the receptor 23 are allowed to react first, and then the sample liquid S and the cleaning liquid W are reacted. It penetrates into the microfluidic channel 11 and is discharged. Compared with the conventional detection device, which uses capillary action to first guide the sample liquid to the reaction area and then performs the reaction, the present invention can not only complete the sample detection without external force driving, but also can pass through When the sample liquid S is dripped into the reaction area 22, it directly reacts with the receptor 23 first, so as to avoid the delay of the detection time caused by the sample liquid having to be drained to the reaction area, so that the detection time is relatively shortened, thereby effectively improving the detection efficiency.

2. Since the opening 31 is in a hexagonal shape, and the opening 31 is directly connected to the reaction zone 22, the hydrophilic layer 32 does not produce capillary action in the opening 31, and the opening 31 with a hexagonal structure can form a capillary action on the sample liquid S. The blocking effect prevents the sample liquid S, the cleaning liquid W or the detection liquid T from overflowing when they are dropped in the reaction area 22, thereby smoothing the detection process and helping to further improve the detection efficiency.

3. Through the arrangement of the adsorption member 40, when the sample liquid S, cleaning liquid W or detection liquid T are discharged from the microfluidic channel 11, they are quickly absorbed by the adsorption member 40. Compared with natural discharge, the effect of acceleration can be achieved, and there is Helps further improve detection efficiency.

The present invention has been disclosed above with preferred embodiments. However, those skilled in the art should understand that the embodiments are only used to illustrate the present invention and should not be interpreted as limiting the scope of the present invention. It should be noted that any changes and substitutions that are equivalent to this embodiment should be considered to be within the scope of the present invention. Therefore, the protection scope of the present invention shall be subject to the scope of the patent application.

100:Biological chip detection device

10:Ontology

23: Receptor

31:Opening

50: Shell parts

51:Window

52: pores

Claims (18)

A biological chip detection device, which includes a body, which includes: a base material, which is provided with a pair of electrodes, and has a reaction area in a part of the pair of electrodes, and the reaction area is coated with a receptor that can be combined with a detection target ; And a flow guide layer, which is stacked with the base material. The flow guide layer has an opening co-located with the reaction zone. The opening is hollow and has no objects living in it and directly leads to the reaction zone. The receptor The opening is exposed to the body, allowing a sample liquid to be directly dropped on the pair of electrodes in the reaction zone to react with the receptor, and there is a gap between the conductive layer and the substrate that communicates with the reaction zone. Microfluidic channel, the sample liquid after reaction is added with a cleaning solution and then penetrates into the microfluidic channel and is discharged. The biological chip detection device according to claim 1, wherein the flow guide layer includes a hydrophilic layer with capillary action and a hydrophobic layer that does not absorb water. The hydrophobic layer is located between the substrate and the hydrophilic layer. The hole penetrates the hydrophilic layer and the hydrophobic layer and directly leads to the reaction zone. The hydrophobic layer has bare space to form the micro-channel between the substrate and the hydrophilic layer. The biological chip detection device of claim 2, wherein the opening is hexagonal and has a reaction section of equal width and a tapered buffer section, and the buffer section has a wide end and a narrow end. , the wide end continues from one end of the reaction section, and the narrow end communicates with the bare space of the hydrophobic layer and communicates with the microfluidic channel. The biological chip detection device according to claim 2, further comprising an adsorbent member, the hydrophilic layer has a drain outlet at an end of the microfluidic channel away from the reaction zone, and the adsorbent member is disposed on the hydrophilic layer at the drain outlet. superior. The biological chip detection device according to claim 4, further comprising a shell, the body and the adsorption member are covered and positioned by the shell, the shell has a viewing window directly above the receptor through the opening The reaction zone, and the shell member has an air hole on one side of the drain port, and the drain port communicates with the air hole in the shell member. The biochip detection device according to claim 1, wherein the receptor is selected from immunoglobulins, nucleic acid probes, chemical molecules or functional proteins. A detection method for the biochip detection device as described in any one of claims 1 to 3, which includes the following steps: drop sample: drop the sample liquid directly from the opening onto the counter electrode in the reaction area, And react with the receptor for a reaction time; cleaning: after the reaction time, the cleaning solution is dripped into the sample liquid in the reaction zone and is larger than the accommodated volume of the reaction zone, so that the sample The liquid and cleaning liquid penetrate into the microfluidic channel through capillary action and are discharged; and detection: after the cleaning step, a detection liquid is dropped into the reaction zone to perform sample detection. The detection method as described in claim 7, wherein in the step of dropping the sample, the sample liquid is reacted in the reaction zone with a volume of 10 to 15 microliters, and the reaction time is 1 to 5 minutes. The detection method as described in claim 8, wherein in the cleaning step, the first drop of the cleaning solution is first dropped into the reaction zone to clean the sample solution, and the sample solution and the cleaning solution are allowed to penetrate into the reaction zone. Microfluidic channel to complete the first cleaning, then drop the second drop as described The cleaning liquid then cleans the sample liquid in the reaction zone, and the sample liquid and the cleaning liquid are allowed to penetrate into the microfluidic channel to complete the second cleaning. The detection method as described in claim 8, wherein in the detection step, the first drop of the detection solution is first dropped into the reaction zone, and the residual cleaning solution and detection solution are allowed to penetrate into the microfluidic through capillary action. After the passage, a second drop of the detection liquid is dropped in the reaction area, and the second drop of the detection liquid stays in the reaction area to perform the sample detection. A detection method for a biochip detection device as described in claim 4, which includes the following steps: Dropping: drop the sample liquid directly from the opening onto the counter electrode in the reaction area, and perform contact with the receptor. Reaction of a reaction time; cleaning: after the reaction time, the cleaning solution is dripped into the sample solution in the reaction zone and is larger than the accommodated volume of the reaction zone, allowing the sample solution and cleaning solution to penetrate into the reaction zone. Microfluidic channel; and detection: after the cleaning step, a detection liquid is dropped into the reaction zone to perform sample detection; wherein the sample liquid and cleaning liquid or the detection liquid flowing through the microfluidic channel are The adsorption member quickly absorbs and discharges the microfluidic channel. The detection method as described in claim 11, wherein in the step of dropping the sample, the sample liquid is reacted in the reaction zone with a volume of 10 to 15 microliters, and the reaction time is 1 to 5 minutes. The detection method as described in claim 12, wherein in the cleaning step, the first drop of the cleaning solution is first dropped into the reaction zone to clean the sample liquid, and the sample liquid is allowed to The liquid and the cleaning liquid penetrate into the microfluidic channel to complete the first cleaning, and then drop a second drop of the cleaning liquid in the reaction zone to clean the sample liquid, and allow the sample liquid and the cleaning liquid to penetrate into the microfluidic channel again. runner to complete the second cleaning. The detection method as described in claim 12, wherein in the detection step, the first drop of the detection solution is first dropped into the reaction zone, and the residual cleaning solution and detection solution are allowed to penetrate into the microfluidic through capillary action. After the passage, a second drop of the detection liquid is dropped in the reaction area, and the second drop of the detection liquid stays in the reaction area to perform the sample detection. A detection method for a biochip detection device as described in claim 5, which includes the following steps: Dropping: drop the sample liquid directly from the opening onto the counter electrode in the reaction area, and perform contact with the receptor. Reaction of a reaction time; cleaning: after the reaction time, the cleaning solution is dripped into the sample solution in the reaction zone and is larger than the accommodated volume of the reaction zone, allowing the sample solution and cleaning solution to penetrate into the reaction zone. Microfluidic channel; and detection: after the cleaning step, a detection liquid is dropped into the reaction zone to perform sample detection; wherein the pore size is adjusted to control the sample liquid and cleaning liquid or the detection The flow rate of liquid exiting the microfluidic channel. The detection method as described in claim 15, wherein in the step of dropping the sample, the sample liquid is reacted in the reaction zone with a volume of 10 to 15 microliters, and the reaction time is 1 to 5 minutes. The detection method as described in claim 16, wherein in the cleaning step, the first drop of the cleaning solution is first dropped into the reaction zone to clean the sample solution, and the sample solution and the cleaning solution are allowed to penetrate into the reaction zone. The microfluidic channel is used to complete the first cleaning, and then a second drop of the cleaning solution is dropped in the reaction zone to clean the sample liquid, and the sample liquid and cleaning liquid are allowed to penetrate into the microfluidic channel to complete the second time. Clean. The detection method as described in claim 16, wherein in the detection step, the first drop of the detection solution is first dropped into the reaction zone, and the residual cleaning solution and detection solution are allowed to penetrate into the microfluidic through capillary action. After the passage, a second drop of the detection liquid is dropped in the reaction area, and the second drop of the detection liquid stays in the reaction area to perform the sample detection.

Images