Home detection micro-fluidic chip and micro-fluidic detection device

Abstract

The utility model discloses a household detection micro-fluidic chip and a micro-fluidic detection device, which belong to the field of micro-fluidic chips and comprise a chip body and M detection modules arranged on the chip body, in the detection module, the bottom end of a quantitative chamber is communicated with a first reaction chamber through a first connecting channel, and the connecting point of the first connecting channel and the first reaction chamber is lower than the bottom end of the quantitative chamber; the second reaction chamber is provided with a flow guide structure which is concave inwards and is in a sharp mouth shape; the tail end of the upper surface of the second reaction chamber is lower than the bottom end of the first reaction chamber; one end of the second connecting channel is communicated with the bottom end of the first reaction chamber, and the other end is communicated with the second reaction chamber at the tail end of the upper surface of the flow guide structure; impedance of the second connecting channel is greater than that of the first connecting channel; the top end of the second reaction chamber is connected with the top end of the test strip through a third connecting channel, and the top end of the test strip is higher than that of the second reaction chamber. According to the utility model, more efficient, convenient and accurate home nucleic acid detection can be realized.

Description

Home-based microfluidic chips and microfluidic detection devices Technical Field

[0001] This utility model belongs to the field of microfluidic chips, and more specifically, relates to a home-based detection microfluidic chip and a microfluidic detection device. Background Technology

[0002] In daily life, the demand for virus testing persists. While home antigen tests can quickly provide preliminary results, their sensitivity is poor, and false negatives occur frequently, failing to meet the need for accurate testing. In contrast, nucleic acid testing, with its high sensitivity and specificity, has become the gold standard for virus detection. However, traditional quantitative polymerase chain reaction (qPCR) technology relies on expensive laboratory equipment, such as thermal cyclers and quantitative fluorescence detectors, and requires operation by professional technicians, demanding specific experimental environments, making it unsuitable for widespread use in home settings. For example, in remote areas or resource-scarce communities, the availability of such specialized equipment is difficult, hindering the implementation of qPCR testing.

[0003] On the other hand, testing for specific viruses such as human papillomavirus (HPV) using traditional hospital testing methods not only incurs time and financial costs for patients, but also raises concerns about privacy, as some patients may avoid testing due to fear or social pressure, increasing the risk of disease transmission. Therefore, developing a reliable, convenient, and low-cost home-based nucleic acid testing method is urgently needed.

[0004] The CRISPR / Cas system offers a new approach to nucleic acid detection, utilizing the specific recognition of targets by crRNA and the trans-cleavage activity of Cas proteins. To improve detection sensitivity, it is often combined with isothermal amplification techniques such as recombinase polymerase amplification (RPA). RPA can rapidly amplify nucleic acids under isothermal conditions and is highly compatible with the CRISPR-Cas system. However, current CRISPR / Cas-based home nucleic acid detection technologies still face several bottlenecks, including the following:

[0005] (1) Nucleic acid extraction is a complex and cumbersome process. Existing magnetic bead-based extraction methods require multiple reagent washing and elution operations, which demand high technical skills from operators and are prone to contamination. Although the proteinase K method simplifies some procedures, it requires precise control of multiple temperature stages to regulate proteinase K activity and avoid interference with subsequent reactions, which is almost impossible to achieve precisely in a home environment.

[0006] (2) Low integration. Most detection methods require multiple manual transfers of samples or products during extraction, amplification, and detection, increasing the risk of cross-contamination and making operation inconvenient. Although some "one-pot" methods have attempted to address this issue, the compatibility problem between isothermal amplification and the CRISPR system remains unresolved. Cas protein activation can damage the nucleic acid amplification template, reducing amplification efficiency and detection sensitivity. While some studies have addressed this through methods such as spatial isolation of reaction reagents, screening for specific PAM sites, or using light-controlled nucleotides, these methods suffer from cumbersome preliminary work and high costs.

[0007] (3) Insufficient multiplex detection capability. In actual testing, it is often necessary to detect multiple pathogens or multiple subtypes of the same pathogen at the same time, and existing detection technologies are difficult to meet this requirement.

[0008] Microfluidics technology offers a potential solution to these problems. It integrates multiple steps, such as sample processing, reaction, and detection, onto a microchip, enabling automated and miniaturized detection. However, most existing microfluidic chip platforms rely on active pump systems, such as pneumatic pumps and syringe pumps, to drive fluid flow. These active pumps not only increase equipment cost and size but also require external power, limiting their application in environments without stable power supplies, such as homes. Furthermore, while fluorescence-based microfluidic chips offer high sensitivity, they require specialized fluorescence detection equipment to read the results, making them unsuitable for home testing. Passive micropumps, while eliminating dependence on external power, require complex valve control structures and manufacturing processes based on passive microvalves, and variations in manual operation can lead to unstable fluid control accuracy. A portable microfluidic chip was designed in patent application number 2024119465786, but when applied to nucleic acid detection, it suffers from problems such as non-specific amplification due to a shared quantitative chamber and complex multiple primer design.

[0009] In summary, existing technologies have many shortcomings in the field of home-based nucleic acid testing, and there is an urgent need for an innovative microfluidic chip technology to meet practical needs. Summary of the Invention

[0010] In response to the shortcomings and improvement needs of existing technologies, this utility model provides a home testing microfluidic chip and a microfluidic detection device, with the aim of achieving more efficient, convenient and accurate home nucleic acid testing.

[0011] To achieve the above objectives, according to one aspect of the present invention, a home detection microfluidic chip is provided, comprising: a chip body, and M detection modules disposed on the chip body;

[0012] The detection module includes: a quantitative chamber, a first connecting channel, a first reaction chamber, a second connecting channel, a second reaction chamber, a third connecting channel, and a test strip;

[0013] The first reaction chamber contains a first reactant; the bottom of the metering chamber is connected to the first reaction chamber via a first connecting channel, and the connection point between the first connecting channel and the first reaction chamber is lower than the bottom of the metering chamber.

[0014] The second reaction chamber is pre-embedded with a second reactant; a concave and pointed flow guide structure is provided in the middle of the second reaction chamber, and the end of the upper surface of the flow guide structure is lower than the bottom of the first reaction chamber; one end of the second connecting channel is connected to the bottom of the first reaction chamber, and the other end is connected to the second reaction chamber at the end of the upper surface of the flow guide structure; the impedance of the second connecting channel is greater than the impedance of the first connecting channel.

[0015] The top of the second reaction chamber is connected to the top of the test strip via a third connecting channel, and the top of the test strip is higher than the top of the second reaction chamber.

[0016] Where M is a positive integer.

[0017] Furthermore, the lower surface of the flow guiding structure is an arc surface.

[0018] Furthermore, the chip body includes multiple chip layers, and the first reaction chamber, the second connection channel, and the second reaction chamber are located on the same chip layer.

[0019] In some alternative embodiments, the connection point between the first connection channel and the first reaction chamber is higher than the bottom of the first reaction chamber;

[0020] Furthermore, the first connection channel and the first reaction chamber are located on different chip layers.

[0021] In some optional embodiments, the connection point between the first connection channel and the first reaction chamber is located at the bottom end of the first reaction chamber;

[0022] Furthermore, the first connection channel and the first reaction chamber are located on the same chip layer.

[0023] Furthermore, the quantitative chamber is V-shaped, and the apex of the V-shape is the bottom of the quantitative chamber.

[0024] Furthermore, the detection module also includes: a detection chamber for pre-embedding test strips; and absorbent materials are provided at both ends of the detection chamber.

[0025] According to another aspect of the present invention, a microfluidic detection device is provided, comprising: a base and K microfluidic chips;

[0026] The base has K slots, and K microfluidic chips are fixed in the K slots respectively;

[0027] Among them, the microfluidic chip is the home detection microfluidic chip provided by this utility model.

[0028] In summary, the above-described technical solutions conceived by this utility model can achieve the following beneficial effects:

[0029] This utility model provides a home-use microfluidic chip for testing, which integrates one or more detection modules. Each detection module includes two reaction chambers, and the flow channels, the relative flow resistance between channels, the chambers, and the relative positions between the chambers are all specially designed. Specifically, the bottom of the quantitative chamber is connected to the first reaction chamber through a first connecting channel, and the connection point between the first connecting channel and the first reaction chamber is lower than the bottom of the quantitative chamber. The bottom of the first reaction chamber is connected to the second reaction chamber through a second connecting channel, and the connection point between the second connecting channel and the second reaction chamber is lower than the bottom of the first reaction chamber. The impedance of the second connecting channel is greater than the impedance of the first connecting channel. The top of the second reaction chamber is connected to the top of the test strip through a third connecting channel, and the top of the test strip is higher than the top of the second reaction chamber. Based on this structural design, after sample quantification via the quantitative chamber, applying a suitable positive force transfers the sample to the first reaction chamber for the first reaction step, while preventing the sample from entering the second reaction chamber. After the first reaction, applying another suitable positive force transfers the reaction products from the first reaction chamber to the second reaction chamber for the second reaction step. After the second reaction, applying a reverse force transfers the reaction products from the second reaction chamber to the test strip, allowing the nucleic acid detection result to be read. Simultaneously, the flow-guiding effect on the lower surface of the flow-guiding structure prevents the reaction products from returning to the first reaction chamber via the second connecting channel when transferred to the test strip, ensuring the accuracy and sensitivity of the final detection result. This structural design allows for simple manipulation of the fluid during nucleic acid detection by applying force to the chip, completing the two-step reaction process. It effectively avoids the non-specific amplification problems that may occur with traditional shared quantitative chambers and simplifies multiplex primer design. Attached Figure Description

[0030] Figure 1 is a schematic diagram of the home detection chip provided in Embodiment 1 of this utility model;

[0031] Figure 2 is a partially enlarged view of the structural schematic diagram of the home detection chip provided in Embodiment 1 of this utility model;

[0032] Figure 3 is a schematic diagram of the layered structure of the home detection chip provided in Embodiment 1 of this utility model, wherein the second connection channel is a siphon tube;

[0033] Figure 4 is a schematic diagram of the layered structure of the home detection chip provided in Embodiment 2 of this utility model, wherein the second connection channel is designed with a pre-embedded soluble film.

[0034] In all the accompanying drawings, the same reference numerals are used to denote the same elements or structures, wherein:

[0035] 1-Chip body; 2-Detection module; 21-Quantitative chamber; 22-First connection channel; 23-First reaction chamber; 24-Second connection channel; 25-Second reaction chamber; 26-Third connection channel; 27-Flow guiding structure; 271-Upper surface of flow guiding structure; 272-Lower surface of flow guiding structure. Detailed Implementation

[0036] To make the objectives, technical solutions, and advantages of this utility model clearer, the present utility model will be further described in detail below with reference to the accompanying drawings and embodiments. It should be understood that the specific embodiments described herein are merely illustrative of the present utility model and are not intended to limit the present utility model. Furthermore, the technical features involved in the various embodiments of the present utility model described below can be combined with each other as long as they do not conflict with each other.

[0037] Those skilled in the art should understand that these embodiments are merely used to explain the technical principles of this utility model and are not intended to limit the scope of protection of this utility model. It should be noted that in the description of this utility model, terms such as "upper," "lower," "left," "right," "inner," and "outer," indicating directions or positional relationships, are based on the directions or positional relationships shown in the accompanying drawings. This is merely for ease of description and does not indicate or imply that the device or element must have a specific orientation, or be constructed and operated in a specific orientation; therefore, it should not be construed as a limitation of this utility model. Furthermore, it should be noted that in the description of this utility model, unless otherwise explicitly specified and limited, the terms "installed," "connected," and "linked" should be interpreted broadly. For example, they can refer to a fixed connection, a detachable connection, or an integral connection; a mechanical connection or an electrical connection; a direct connection or an indirect connection through an intermediate medium; or a connection within two components. Those skilled in the art can understand the specific meaning of the above terms in this utility model according to the specific circumstances. Furthermore, in this utility model, the terms "first," "second," etc. (if present), in this utility model and its accompanying drawings, are used to distinguish similar objects and are not necessarily used to describe a specific order or sequence.

[0038] To effectively address the issues of nonspecific amplification and complex multiple primer design caused by shared quantitative chambers, while reducing the difficulty and complexity of fluid manipulation and improving the portability of microfluidic chips, this invention provides a home-use microfluidic chip and microfluidic detection device. The structure of the microfluidic chip has been improved, specifically including the special design of the flow channels, the relative flow resistance between the channels, the chambers, and the relative positions between the chambers. This allows for simple manipulation of the chip's placement orientation to control the fluid during the detection process.

[0039] It is easy to understand that in this utility model, descriptions such as "top," "bottom," "high," and "low" are all relative to the chip when it is placed upright. When the chip is placed upright, the highest point of each structure is the top of the corresponding structure, and the lowest point of each structure is the bottom of the corresponding structure. "Forward force" and "reverse force" are relative to the top and bottom of the chip. The force from the top of the chip to the bottom of the chip is the forward force, and conversely, the force from the bottom of the chip to the top of the chip is the reverse force.

[0040] The following is an example.

[0041] Example 1:

[0042] A home-based detection microfluidic chip, as shown in Figures 1-3, includes: a chip body 1, and five detection modules 2 disposed on the chip body 1.

[0043] As shown in Figures 1 and 2, the detection module 2 includes: a quantitative chamber 21, a first connecting channel 22, a first reaction chamber 23, a second connecting channel 24, a second reaction chamber 25, a third connecting channel 26, and a test strip;

[0044] The first reaction chamber 23 is pre-embedded with the first reactant; the bottom end of the metering chamber 21 is connected to the first reaction chamber 23 through the first connecting channel 22, and the connection point between the first connecting channel 22 and the first reaction chamber 23 is lower than the bottom end of the metering chamber 21.

[0045] The second reaction chamber 25 is pre-embedded with a second reactant; a concave and pointed flow guide structure 27 is provided in the middle of the second reaction chamber 25, and the end of the upper surface 271 of the flow guide structure is lower than the bottom of the first reaction chamber 23; one end of the second connecting channel 24 is connected to the bottom of the first reaction chamber 23, and the other end is connected to the second reaction chamber 25 at the end of the upper surface 271 of the flow guide structure; the impedance of the second connecting channel 24 is greater than the impedance of the first connecting channel 22.

[0046] The top of the second reaction chamber 25 is connected to the top of the test strip via the third connecting channel 26, and the top of the test strip is higher than the top of the second reaction chamber 26.

[0047] Based on the home testing microfluidic chip designed in this embodiment, after sample quantification is achieved through the quantitative chamber 21, the sample can be transferred to the first reaction chamber 23 for the first step reaction by applying an appropriate positive force through methods such as placing the chip body upright or shaking it by hand, while the sample does not enter the second reaction chamber 25. After the first step reaction is completed, the reaction product in the first reaction chamber 23 can be transferred to the second reaction chamber 25 for the second step reaction by applying an appropriate positive force through methods such as shaking it by hand. After the second step reaction is completed, the reaction product in the second reaction chamber 25 can be transferred to the test strip by applying a reverse force through methods such as placing the chip body upside down or shaking it by hand, and the nucleic acid detection result can be read through the test strip. Under the guiding effect of the lower surface 272 of the guiding structure, when the reaction product in the second reaction chamber 25 is transferred to the test strip, it will not return to the first reaction chamber 23 through the second connecting channel 24, ensuring the accuracy and sensitivity of the final detection result. The above structural design allows for the manipulation of fluids during nucleic acid detection by simply applying force to the chip, completing the two-step reaction of nucleic acid detection. It effectively avoids the non-specific amplification problem that may be caused by traditional shared quantitative chambers, and also makes the design of multiple primers simpler and clearer.

[0048] It is easy to understand that, in order to facilitate the transfer of liquid between chambers, corresponding vents are also provided in the chip to connect each chamber (quantitative chamber, first reaction chamber, second reaction chamber) to the atmosphere, so as to balance the pressure between the chambers.

[0049] As a preferred embodiment, as shown in Figure 2, in this embodiment, the lower surface 272 of the flow guiding structure is an arc surface, which can better guide the reaction products to the third connection channel 26 while ensuring that the reaction products do not enter the second connection channel 24, thereby improving the detection efficiency.

[0050] The chip body includes multiple chip layers, as shown in Figure 3. As a further preferred embodiment, in this embodiment, the first reaction chamber 23, the second connection channel 24, and the second reaction chamber 25 are located on the same chip layer. Due to the presence of the flow guiding structure 27, placing the first reaction chamber 23, the second connection channel 24, and the second reaction chamber 25 on the same chip layer can simplify the layered structure design of the chip and reduce the chip cost without affecting the detection results.

[0051] In practical applications, the impedance of the second connection channel can be increased by strategies such as pre-embedding a soluble membrane, using a siphon channel, or performing hydrophobic modification. This effectively prevents the sample from entering the second reaction chamber before the first reaction is completed, ensuring that the first reaction proceeds fully in the first reaction chamber. Optionally, as shown in Figures 1-3, in this embodiment, the second connection channel is a siphon channel. After the first reaction is completed, by forward-swinging the chip body, the reaction products in the first reaction chamber can overcome the resistance of the siphon channel and transfer to the second reaction chamber.

[0052] To facilitate the transfer of samples from the quantitative chamber to the first reaction chamber, as an optional implementation, as shown in Figure 1, in this embodiment, the connection point between the first connecting channel and the first reaction chamber is higher than the bottom of the first reaction chamber.

[0053] Furthermore, the first connection channel and the first reaction chamber are located on different chip layers.

[0054] As further shown in Figure 1, in this embodiment, the quantitative chamber is V-shaped, with the apex of the V being the bottom of the quantitative chamber. This shape facilitates rapid and uniform quantification of the sample after it is added to the quantitative chamber, based on its own gravity, providing a stable and accurate sample volume for subsequent reactions. It is easy to understand that the size of the quantitative chamber needs to be designed according to the required sample volume. For example, for general nucleic acid detection, its volume can be designed to be 10-50 μL, which meets the required sample volume for the reaction without causing sample waste or incomplete reaction due to an excessively large chamber.

[0055] To further improve the efficiency of the transfer of reaction products to the test strip, thereby improving the detection efficiency, as a preferred embodiment, the detection module further includes: a detection chamber for pre-embedding the test strip; absorbent materials (absorbent paper, absorbent sponge, etc.) are respectively provided at both ends of the detection chamber, and the absorbent materials also serve to fix the strip.

[0056] In this embodiment, the chip body serves as the carrier of the entire microfluidic chip and can be made of materials such as polymethyl methacrylate (PMMA) and polystyrene (PS). These materials possess excellent optical properties, chemical stability, and processing performance, facilitating observation of the internal reactions of the chip and subsequent processing. One or more detection modules are rationally arranged on the chip body according to actual detection needs. It is easy to understand that the number of detection modules within the same chip body can be flexibly set according to actual detection requirements. For example, in scenarios involving the combined detection of multiple pathogens, the number of detection modules can be appropriately increased to achieve simultaneous detection of different items on multiple samples.

[0057] The first and second reaction chambers are used for different stages of the reaction, such as RPA amplification and CRISPR recognition-cutting reaction. The reaction chambers can also be made of the same material as the chip body and manufactured using microfabrication processes. Their internal space design must consider the amount of reactants and the space required for the reaction; generally, the volume of each reaction chamber is between 10-30 μL to ensure that the reactants can be fully mixed and reacted, while avoiding a decrease in reaction efficiency due to excessive space.

[0058] The materials of the first, second, and third connecting channels are consistent with the chip body, and their inner diameter design is crucial, requiring precise calculation based on fluid dynamics principles and the required flow rate and volume. For example, the inner diameter of the first connecting channel can be designed to be 0.2-0.5 mm to ensure that the sample can smoothly enter the first reaction chamber when a positive force is applied, without the channel being too wide causing sample residue in the quantitative chamber or too narrow obstructing flow. The inner diameter of the second connecting channel, considering the functional requirements of preventing liquid from flowing into the second reaction chamber initially and transferring liquid later, can be designed to be 0.1-0.3 mm, and combined with strategies such as pre-embedded soluble membranes, siphon channels, or hydrophobic modifications, precise fluid control can be achieved. The inner diameter of the third connecting channel can be appropriately increased to 0.3-0.6 mm to ensure that the reaction products can quickly flow to the test strip after the chip is inverted.

[0059] As the display medium for test results, test strips can be commercially available, high-quality immunochromatographic test strips. The appropriate strip should be selected based on the specific test being performed. It's easy to understand that when setting up the detection chamber, its dimensions must precisely match the test strip to ensure it is securely fixed within the chamber without affecting its performance.

[0060] The following explanation uses a specific testing example to illustrate how to use the home testing microfluidic chip provided in this embodiment.

[0061] Sample addition and quantification: Place the portable microfluidic chip upright on a stable surface. Using a pipette or dropper, slowly add the sample to be tested into the quantification chamber of each detection module. Due to the "V"-shaped structure of the quantification chamber, the sample will quickly converge to the bottom, achieving quantification. During sample addition, care should be taken to avoid generating air bubbles to ensure accurate sample addition.

[0062] First reaction: After adding the sample, apply positive force to the chip by hand and gently shaking it, or by using a small centrifuge, to allow the sample in each quantitative chamber to break through the first connection channel and quickly transfer to the first reaction chamber. The first reaction chamber contains the corresponding reactants, such as primers, templates, and enzymes, for RPA amplification. The sample and reactants are thoroughly mixed in the first reaction chamber and reacted at a suitable temperature. The reaction time depends on the specific reaction type, but generally RPA amplification takes 15-30 minutes.

[0063] Second reaction: After the first reaction, a positive force is applied to the chip again, such as by shaking the chip again or performing a short centrifugation, causing the solution in each of the first reaction chambers to break through the second connection channel and transfer to the second reaction chamber. If a pre-embedded soluble membrane strategy is used, the soluble membrane dissolves under liquid pressure or specific conditions. If a siphon channel or hydrophobic modification strategy is used, the liquid transfer is achieved by overcoming the corresponding resistance with the applied positive force. The second reaction chamber also contains pre-embedded reactants, such as Cas protein and crRNA required for the CRISPR reaction. The solution reacts with these reactants in a second reaction to generate the final reaction product. The reaction time is generally 10-20 minutes.

[0064] Result Reading: After the reaction in the second reaction chamber is complete, carefully invert the chip so that the reaction product flows through the third connection channel to the test strip under gravity. After a preset time (usually 5-10 minutes), observe the color development of the test line and control line on the test strip and read the result. If both the test line and control line develop color, the result is negative; if only the control line develops color and the test line does not, the result is positive; if the control line does not develop color, it indicates a possible problem in the testing process, and the result is invalid.

[0065] The above testing process is simple to operate. It can complete the complex testing process by simply adjusting the placement orientation of the chip and applying a simple external force (such as positive force, inversion, etc.). No professional operating skills or complicated instruments and equipment are required, which greatly improves the feasibility and convenience of home testing.

[0066] Example 2:

[0067] A home-use microfluidic chip for monitoring. This embodiment is similar to Embodiment 1 above, except that, as shown in Figure 4, in this embodiment, the impedance of the second connection channel is increased by pre-embedding a soluble film. When a suitable positive force is applied to the chip body, the soluble film dissolves, and the liquid in the first reaction chamber can be smoothly transferred to the second reaction chamber, achieving precise fluid control.

[0068] Example 3:

[0069] A home-based detection microfluidic chip. This embodiment is similar to Embodiment 1 above, except that in this embodiment, the connection point between the first connecting channel and the first reaction chamber is located at the bottom end of the first reaction chamber;

[0070] Furthermore, the first connection channel and the first reaction chamber are located on the same chip layer.

[0071] This structural design allows the first connection channel and the first reaction chamber to be located on the same chip layer while achieving fluid control, simplifying the layered structure design of the chip.

[0072] Example 4:

[0073] A microfluidic detection device includes: a base and K microfluidic chips;

[0074] The base has K slots, and K microfluidic chips are fixed in the K slots respectively;

[0075] The microfluidic chip is the home detection microfluidic chip provided in any of the above embodiments.

[0076] This embodiment integrates multiple home-based testing microfluidic chips into a single microfluidic testing device, enabling simultaneous multi-detection and increasing throughput. For example, it allows for the simultaneous testing of multiple samples for different parameters, saving testing time and costs. In practical applications, the number of home-based testing microfluidic chips in the device can be flexibly adjusted according to testing needs.

[0077] The base can be made of plastic or metal. The key feature is that the slot on the base is sized to fit snugly against the chip, ensuring the chip is securely placed and preventing it from shifting during operation and affecting test results. The base can also be designed with auxiliary structures such as anti-slip pads and marking areas to facilitate user operation and identification of chips for different testing items.

[0078] Those skilled in the art will readily understand that the above description is merely a preferred embodiment of the present utility model and is not intended to limit the present utility model. Any modifications, equivalent substitutions, and improvements made within the spirit and principles of the present utility model should be included within the protection scope of the present utility model.

Claims

1. A home-based detection microfluidic chip, characterized in that, include: The chip body, and M detection modules disposed on the chip body; The detection module includes: a quantitative chamber, a first connecting channel, a first reaction chamber, a second connecting channel, a second reaction chamber, a third connecting channel, and a test strip; the first reaction chamber contains a first reactant; the bottom of the quantitative chamber is connected to the first reaction chamber via the first connecting channel, and the connection point between the first connecting channel and the first reaction chamber is lower than the bottom of the quantitative chamber; the second reaction chamber contains a second reactant; the middle of the second reaction chamber has an inwardly recessed, pointed flow guide structure, the end of the upper surface of the flow guide structure is lower than the bottom of the first reaction chamber; one end of the second connecting channel is connected to the bottom of the first reaction chamber, and the other end is connected to the second reaction chamber via the end of the upper surface of the flow guide structure; the impedance of the second connecting channel is greater than the impedance of the first connecting channel; the top of the second reaction chamber is connected to the top of the test strip via the third connecting channel, and the top of the test strip is higher than the top of the second reaction chamber; where M is a positive integer.

2. The home monitoring microfluidic chip as described in claim 1, characterized in that, The lower surface of the flow guiding structure is an arc surface.

3. The home monitoring microfluidic chip as described in claim 1 or 2, characterized in that, The chip body includes multiple chip layers, and the first reaction chamber, the second connection channel, and the second reaction chamber are located on the same chip layer.

4. The home monitoring microfluidic chip as described in claim 3, characterized in that, The connection point between the first connection channel and the first reaction chamber is higher than the bottom of the first reaction chamber; and the first connection channel and the first reaction chamber are located on different chip layers.

5. The home monitoring microfluidic chip as described in claim 3, characterized in that, The connection point between the first connection channel and the first reaction chamber is located at the bottom end of the first reaction chamber; and the first connection channel and the first reaction chamber are located on the same chip layer.

6. The home monitoring microfluidic chip as described in claim 1 or 2, characterized in that, The quantitative chamber is V-shaped, and the apex of the V-shape is the bottom of the quantitative chamber.

7. The home monitoring microfluidic chip as described in claim 1 or 2, characterized in that, The detection module further includes: a detection chamber for pre-embedding the test strip; and absorbent materials are respectively provided at both ends of the detection chamber.

8. A microfluidic detection device, characterized in that, include: A base and K microfluidic chips; the base is provided with K slots, and the K microfluidic chips are respectively fixed in the K slots; wherein, the microfluidic chips are the home detection microfluidic chips according to any one of claims 1 to 7.

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