Microfluidic chip

Abstract

The micro-fluidic chip comprises a chip main body, the chip main body is provided with a first sample inlet, a second sample inlet, a first detection system and a second detection system, the first detection system is communicated with the first sample inlet, the first detection system is used for carrying out optical detection on a sample input from the first sample inlet, the second detection system is communicated with the second sample inlet, and the second detection system is used for carrying out optical detection on a sample input from the second sample inlet. And the second detection system is used for performing optical detection on the sample input from the second sample inlet. The provided micro-fluidic chip is more integrated, miniaturized, more portable, lower in cost, more convenient to use and free of pollution, waste of samples and reagents can be reduced, the first detection system and the second detection system are mutually independent and do not interfere with each other, and the detection accuracy is improved. And an operator can conveniently know different functions realized by the two functions and carry out corresponding operation.

Description

TECHNICAL FIELD

[0001] The utility model relates to the field of medical apparatus and instruments, especially to a microfluidic chip. BACKGROUND

[0002] CRP is also called C-reactive protein, which is a protein sharply rising in plasma when the body is infected or damaged. It mainly reflects the degree of inflammatory reaction or tissue damage, and is used for acute phase reaction, cardiovascular disease risk assessment, monitoring of inflammatory diseases, prediction of postoperative complications, tumor monitoring, etc.

[0003] SAA is also called serum amyloid A, which is a precursor substance of tissue amyloid A and belongs to acute phase protein. It rises in tissue damage and inflammatory reaction, and affects cell adhesion, migration, proliferation and aggregation. It is commonly seen in tissue infection, such as acute and chronic inflammatory diseases, such as suppurative infection, severe trauma, myocardial infarction, rheumatoid arthritis, systemic vasculitis, rheumatic polymyalgia, etc.

[0004] CRP and SAA are commonly used for rapid diagnosis of bacterial infection and viral infection, and can be used as sensitive indicators reflecting infection and inflammation control. They are widely used in the auxiliary diagnosis of infectious diseases, the risk prediction of coronary heart disease, the dynamic monitoring of the efficacy and prognosis of tumor patients, the monitoring of transplant rejection, and the monitoring of rheumatoid arthritis disease improvement. In particular, they have greater significance than single tests in the early diagnosis of pediatric infectious diseases, neonatal sepsis, and the early differentiation of bacterial and viral infections in infants and young children.

[0005] With the development of modernization and automation of detection methods, the current CRP and SAA tests are generally automatically completed by detection instruments. The common method at present is to add blood samples and reagents into the reaction pool of the detection instrument for dilution, so that the blood samples and reagents can fully react, and then the transmittance turbidimetry or scattering turbidimetry is used to measure the absorbance of the reacted solution, and finally the concentration is calculated.

[0006] However, since the sampling device, reaction pool, quantitative device and fluid pipeline used in the above detection steps are all arranged inside the detection instrument, especially the components involving fluid and liquid chemical reagents are connected to the detection instrument, the existing detection instrument has the problems of high overall cost, large size, large weight, complex structure and inconvenience for moving, etc. It can only be used in a fixed position in the laboratory or detection room, which has a large use limitation.

[0007] In addition, the above sampling, sampling, mixing, measuring and cleaning steps are automatically completed by the detection instrument, and any problem in any step will affect the accuracy of the CRP and SAA detection results. When a problem occurs, the detection instrument needs to be shut down and a comprehensive investigation needs to be conducted to confirm the problem cause, which affects the detection efficiency. Utility model content

[0008] Therefore, the utility model provides a micro fluidic chip.

[0009] The micro fluidic chip provided by the utility model, including chip main part, the chip main part is provided with:

[0010] First sample inlet;

[0011] Second sample inlet;

[0012] First detection system, the first detection system with first sample inlet intercommunication, the first detection system is used to the sample of input from the optical detection of first sample inlet;

[0013] Second detection system, the second detection system with second sample inlet intercommunication, the second detection system is used to the sample of input from the optical detection of second sample inlet.

[0014] From the above technical scheme can see, the micro fluidic chip provided by the utility model, first, by the integration design first detection system and second detection system on the small volume micro fluidic chip, compared with the sample detection instrument of prior art, micro fluidic chip is more integrated, miniaturization, more portable, cost is lower, operator can use micro fluidic chip in any suitable environment and carry out sample detection, will not be too many use restrictions.Second, micro fluidic chip is disposable consumable, after sample detection, directly discard can, use more convenient.Sample detection after waste liquid remains in micro fluidic chip, will not exist waste liquid secondary flow and cause pollution problem, operator need not additional processing, even if in sample detection process appeared adverse factor influence, directly replace a micro fluidic chip and detect again, reduce the influence on detection efficiency.Furthermore, micro fluidic chip is used for sample detection, can accurately, quantitatively realize the acquisition and processing of sample, and the required sample amount and reagent amount are relatively less, reduce the waste of sample and reagent.In addition, first detection system and second detection system are independent, and the sample detection between the two is independent and does not interfere with each other, facilitating the operator to understand the different functions realized by the two and to make corresponding operation. For example, each detection system can be driven and controlled, such as the sample mixing effect in a certain detection system is not good or the flow speed is slow, the detection system can be driven alone to make the sample mixing effect or flow speed reach the effect desired by the operator. BRIEF DESCRIPTION OF DRAWINGS

[0015] In order to more clearly illustrate the technical solutions of the embodiments of the present application, the drawings needed to be used in the embodiment description will be briefly introduced as follows. Obviously, the drawings described in the following embodiment are some embodiments of the present application, and for those skilled in the art, other drawings can be obtained without creative labor on the basis of these drawings.

[0016] Figure 1 is a structural schematic diagram of a microfluidic chip according to an embodiment of the present application;

[0017] Figure 2 is an exploded schematic diagram of a microfluidic chip according to an embodiment of the present application;

[0018] Figure 3 is an exploded schematic diagram of a top view of a microfluidic chip according to an embodiment of the present application;

[0019] Figure 4 is an exploded schematic diagram of a bottom view of a microfluidic chip according to an embodiment of the present application;

[0020] Figure 5 is a structural schematic diagram of a front view of a substrate according to an embodiment of the present application;

[0021] Figure 6 is a structural schematic diagram of a back view of a substrate according to an embodiment of the present application;

[0022] Figure 7 is an exploded schematic diagram of a partial structure of a microfluidic chip according to an embodiment of the present application.

[0023] In addition, since the channels of the proposed microfluidic chip are partially arranged on the front surface of the substrate, partially arranged on the back surface of the substrate, and partially arranged on the cover plate, the channels can be clearly identified in Figure 5 and Figure 6 are marked with the letter AB. DETAILED DESCRIPTION

[0024] The technical solutions in the embodiments of the present application will be described clearly and completely below with reference to the drawings in the embodiments of the present application. Obviously, the described embodiments are some embodiments of the present application, rather than all the embodiments. Based on the embodiments in the present application, other embodiments obtained by those skilled in the art without creative labor fall within the scope of protection of the present application.

[0025] For example, Figures 1 to 4The utility model discloses an embodiment proposes a micro -fluidic chip, micro -fluidic chip includes chip main part 100, and chip main part 100 is provided with first sample inlet 10, second sample inlet 20, first detection system 30 and second detection system 40, and first detection system 30 communicates with first sample inlet 10, and first detection system 30 is used for carrying out optical detection to the sample of input from first sample inlet 10, and second detection system 40 communicates with second sample inlet 20, and second detection system 40 is used for carrying out optical detection to the sample of input from second sample inlet 20.

[0026] The micro -fluidic chip provided by the utility model embodiment, first, by the integration design first detection system 30 and second detection system 40 on the small volume micro -fluidic chip, compared with the sample detection instrument of prior art, micro -fluidic chip is more integrated, miniaturization, more portable, cost is lower, and the operator can use micro -fluidic chip to carry out sample detection in any suitable environment, and will not be subjected to too many use restrictions. Secondly, micro -fluidic chip is disposable consumable, and after sample detection, directly discarding can, and use is more convenient. The waste liquid after sample detection remains in the micro -fluidic chip, and there is no problem of pollution caused by the secondary flow of waste liquid, and the operator does not need to carry out additional processing, even if there is an adverse factor influence in the sample detection process, directly replaces a micro -fluidic chip and carries out detection again, reduces the influence on detection efficiency. Furthermore, micro -fluidic chip is used for sample detection, can accurately, quantitatively realize the acquisition and processing of sample, and the required sample amount and reagent amount are relatively less, reduce the waste of sample and reagent. In addition, first detection system 30 and second detection system 40 are independent of each other, and the sample detection between the two is independent of each other and does not interfere with each other, facilitating the operator to understand the different functions realized by the two and making corresponding operation. For example, each detection system can be driven and controlled, for example, the sample mixing effect in a certain detection system is not good or the flow speed is slow, then the detection system can be driven alone, so that the mixing effect or flow speed of the sample reaches the effect desired by the operator.

[0027] In some embodiments, the components of the micro -fluidic chip are made by one-piece precision injection molding, which can improve the integrity of the micro -fluidic chip and also ensure its accuracy during sampling, reagent addition and dilution.

[0028] In some embodiments, the samples input from the first inlet 10 and the second inlet 20 are both blood samples. The first detection system 30 is used to detect the blood sample to obtain the C-reactive protein (CRP) level, and the second detection system 40 is used to detect the blood sample to obtain the serum amyloid A (SAA) level. In this embodiment, the proposed microfluidic chip can simultaneously and independently detect the CRP and SAA levels in the flowing blood sample. Of course, the first detection system 30 and the second detection system 40 can also be used to detect other indicators in the blood sample, depending on the actual design requirements. It should also be noted that the proposed microfluidic chip is not limited to the detection of blood samples; it can also be used to detect other samples, depending on the actual design requirements.

[0029] The "C-reactive protein index" includes C-reactive protein concentration. The "serum amyloid A index" includes serum amyloid A concentration.

[0030] like Figures 1 to 3 As shown, in some embodiments, the first inlet 10 and the second inlet 20 are located on the same side of the chip body 100 and arranged adjacently side by side. The microfluidic chip also includes a sealing member 200, which is closable and connected to the chip body 100. The sealing member 200 is used to block the first inlet 10 and the second inlet 20. In this embodiment, by arranging the first inlet 10 and the second inlet 20 on the same side of the chip body 100 and arranged adjacently side by side, the sampling of the microfluidic chip is facilitated. Taking the microfluidic chip for blood sample detection as an example, in a specific embodiment, the examinee or medical personnel prick the examinee's sampling site with a lancet. When a blood droplet appears at the sampling site, the first inlet 10 and the second inlet 20 are brought into contact with the blood droplet. The blood droplet enters the first detection system 30 and the second detection system 40 through the corresponding inlet, respectively, making sampling extremely convenient.

[0031] Furthermore, by setting the sealing component 200 to block the first injection port 10 and the second injection port 20, a closed environment is formed at the beginning of the first detection system 30 and the second detection system 40, which facilitates subsequent steps.

[0032] In some embodiments, the sealing member 200 is rotatably disposed on the chip body 100. Rotating the sealing member 200 to contact the first sample inlet 10 and the second sample inlet 20 will seal both of them, and rotating the sealing member 200 to separate it from the first sample inlet 10 and the second sample inlet 20 will open it. This facilitates operation and also prevents the sealing member 200 from separating from the substrate and falling off and being lost. Of course, in some other embodiments, the sealing member 200 may also be configured to be detachable from the chip body 100, depending on the actual design requirements.

[0033] In some embodiments, the sealing element 200 may be made of silicone to reduce friction on the first injection port 10 and the second injection port 20. At the same time, since silicone has a certain degree of deformability, it can better fit with the first injection port 10 and the second injection port 20, thereby improving the sealing effect.

[0034] like Figures 3 to 6 As shown, in some embodiments, the first detection system 30 includes a first buffer tank 31, a second buffer tank 32, a first mixing channel 33, a first reagent addition unit 34, a first optical detection unit 35, and a second mixing channel 36. The first mixing channel 33 connects to the first sample inlet 10 and the first buffer tank 31. The first reagent addition unit 34 is connected to the first sample inlet 10 and is used to provide a first reagent mixed with the sample. The first optical detection unit 35 is connected to the first reagent addition unit 34 and is used to detect the mixture of the sample and the first reagent. The second mixing channel 36 connects the first optical detection unit 35 and the second buffer tank 32.

[0035] Since the mixing of the first reagent and the sample provided by the first reagent addition unit 34 may not be uniform enough, it will affect the accuracy of subsequent optical detection. In this embodiment, by setting a first mixing channel 33 connected to the first sample inlet 10 and a second mixing channel 36 connected to the first optical detection unit 35 to mix the sample and the first reagent, the accuracy of subsequent optical detection can be improved.

[0036] In some embodiments, the first optical detection unit 35 has a first optical detection window, through which the mixed sample liquid can flow and remain. The upper and lower surfaces of the first optical detection window are respectively provided with an upper light-transmitting film and a lower light-transmitting film. A light source, such as an LED light source with a wavelength of 567nm, is provided above the upper light-transmitting film, and a light receiver is provided below the lower light-transmitting film. A processor is connected to the light source and the light receiver.

[0037] When the first detection system 30 is activated, the light source is turned on. The light penetrates the upper transparent membrane and passes through the mixed sample liquid in the first optical window. The blood cells in the mixed sample liquid absorb the light under the chemical reaction. After the light is absorbed to a certain extent by the blood cells, it passes through the lower transparent membrane and is received by the light receiver. The controller detects the change curve of the incident light intensity and the transmitted light intensity, and calculates the absorbance of the blood cells in the mixed sample liquid. The CRP index of the blood cells in the mixed sample liquid can then be further calculated.

[0038] like Figure 3As shown, in some embodiments, the first buffer pool 31 has a first opening 311, and the second buffer pool 32 has a second opening 321. The microfluidic chip also includes a first film and a second film. The first film covers the first opening 311, and the second film covers the second opening 321. The first film is an elastic film, and pressing the first film can drive the sample and the first reagent to flow back and forth in the first mixing channel 33 and the second mixing channel 36. In this embodiment, the structure for driving the sample and the first reagent to flow in the first mixing channel 33 and the second mixing channel 36 is simple and can effectively reduce costs. Of course, driving the sample and the first reagent to flow in the first mixing channel 33 and the second mixing channel 36 is not limited to the above-described method. For example, in some other embodiments, the first detection system 30 can be connected to a first driving channel, and the first driving channel can be connected to a syringe. The syringe injects or extracts air into the first detection system 30 through the first driving channel to drive the sample and the first reagent to flow back and forth in the first mixing channel 33 and the second mixing channel 36.

[0039] like Figure 5 As shown, in some embodiments, the chip body 100 is further provided with a first sample quantification section 101, a first sample delivery microchannel 102, and a second sample delivery microchannel 103. The first sample quantification section 101 is connected to the first injection port 10 and is used to quantify the sample input into the first detection system 30 from the first injection port 10. One end of the first sample delivery microchannel 102 is connected to the first sample quantification section 101, and the other end of the first sample delivery microchannel 102 is connected to the first mixing channel 33. One end of the second sample delivery microchannel 103 is connected to the first sample quantification section 101, and the other end of the second sample delivery microchannel 103 is connected to the first reagent addition section 34.

[0040] Optionally, the first sample delivery microchannel 102 and the second sample delivery microchannel 103 are capillary structures. In this embodiment, by providing the first sample quantification unit 101, the amount of sample entering the first detection system 30 can be controlled to a certain volume. By controlling the amount of reagent input by the first reagent addition unit 34, the sample entering the first detection system 30 can be diluted to a specified concentration, thereby improving the detection effect. In some embodiments, the volume of the first sample quantification unit 101 is 0.8 μL.

[0041] like Figure 3 and Figure 7As shown, in some embodiments, the first reagent addition unit 34 includes a first receiving portion 341, a first reagent pool 342, and a first reagent container 343. The first sample inlet 10 and the first optical detection unit 35 are connected to the first reagent pool 342. The first reagent container 343 is housed within the first receiving portion 341 and stores a first reagent. When the first reagent container 343 is pressed, the first reagent is injected into the first reagent pool 342. The first reagent pool 342 is located within the outline of the first receiving portion 341. In this embodiment, by placing the first reagent pool 342 within the outline of the first receiving portion 341, i.e., the first reagent pool 342 and the first receiving portion 341 share a structure, space utilization can be improved, thereby reducing the size of the microfluidic chip.

[0042] like Figure 7 As shown, in some embodiments, the first receiving portion 341 includes a first sink portion 3411 and a first through-hole portion 3412. The first through-hole portion 3412 is disposed on the bottom surface of the sink portion 3411 and penetrates the chip body 100. The first reagent pool 342 is disposed on the bottom surface of the sink portion 3411 and spaced apart from the first through-hole portion 3412. The first reagent container 343 includes a first cup body 3431 and a first cup rim 3432. The first cup rim 3432 surrounds the opening end of the first cup body 3431 and is embedded in the first sink portion 3411. The first cup rim 3432 is provided with a first reagent delivery microchannel communicating with the first reagent pool 342. The first cup body 3431 is embedded in the first through-hole portion 3412 and communicates with the first reagent delivery microchannel.

[0043] Specifically, when the first reagent container 343 is not pressed, the first reagent in the first reagent container 343 cannot enter the first reagent pool 342 through the first reagent delivery microchannel. Only when the first reagent container 343 is pressed can the first reagent in the first reagent container 343 enter the first reagent pool 342 through the first reagent delivery microchannel.

[0044] like Figures 3 to 6 As shown, in some embodiments, the chip body 100 includes a substrate 100a, which has a front side and a back side. One of the first mixing channel 33 and the second mixing channel 36 is disposed on the front side of the substrate 100a, and the other of the first mixing channel 33 and the second mixing channel 36 is disposed on the back side of the substrate 100a. In this embodiment, by disposing one of the first mixing channel 33 and the second mixing channel 36 on the front side of the substrate 100a and the other of the first mixing channel 33 and the second mixing channel 36 on the back side of the substrate 100a, the space utilization of the substrate 100a is improved, and the integration and miniaturization of the microfluidic chip are achieved.

[0045] In some embodiments, the first mixing channel 33 and the second mixing channel 36 are arranged opposite to each other in the thickness direction of the substrate 100a. With this arrangement, the space utilization of the substrate 100a can be improved, and the integration and miniaturization of the microfluidic chip can be achieved.

[0046] As shown in FIG. 1, in some embodiments, the first detection system 30 further includes a first waste pool 37, which is in communication with the first buffer pool 31. With this arrangement, after the optical detection in the first optical detection unit 35 is completed, the mixture of the sample and the first reagent can be driven into the first waste pool 37 for collection, so as to avoid pollution caused by the mixture flowing out. It should be noted that, in some embodiments, the chip body 100 can also not be provided with the first waste pool 37, and after the optical detection in the first optical detection unit 35 is completed, the mixture of the sample and the first reagent can be stored in the first buffer pool 31 or directly retained in the first mixing channel 33 and the second mixing channel 36. Figures 3 to 6 As shown in FIG. 1, in some embodiments, the second detection system 40 includes a third buffer pool 41, a fourth buffer pool 42, a third mixing channel 43, a second reagent adding unit 44, a second optical detection unit 45, and a fourth mixing channel 46. The third mixing channel 43 is in communication with the second sample inlet 20 and the third buffer pool 41. The second reagent adding unit 44 is in communication with the second sample inlet 20, and is used to provide a second reagent mixed with the sample. The second optical detection unit 45 is in communication with the second reagent adding unit 44, and is used to detect the mixture of the sample and the second reagent. The fourth mixing channel 46 is in communication with the second optical detection unit 45 and the fourth buffer pool 42.

[0047] Figures 3 to 6 Since the second reagent adding unit 44 provides the second reagent mixed with the sample, the mixture between the sample and the second reagent can not be uniform enough, which can affect the accuracy of subsequent optical detection. In this embodiment, the third mixing channel 43 in communication with the second sample inlet 20 and the fourth mixing channel 46 in communication with the second optical detection unit 45 are arranged to mix the sample and the second reagent, so as to improve the accuracy of subsequent optical detection.

[0048] In some embodiments, the second optical detection unit 45 has a second optical detection window, and the mixed sample liquid can stay in the second optical detection window after being mixed. The upper surface and the lower surface of the second optical detection window are respectively provided with an upper light-transmitting film and a lower light-transmitting film. An upper side of the upper light-transmitting film is provided with a light source, such as an LED light source with a wavelength of 567 nm. A lower side of the lower light-transmitting film is provided with a light receiver. The light source and the light receiver are connected with a processor.

[0049] In some embodiments, the second optical detection unit 45 has a second optical detection window, and the mixed sample liquid can stay in the second optical detection window after being mixed. The upper surface and the lower surface of the second optical detection window are respectively provided with an upper light-transmitting film and a lower light-transmitting film. An upper side of the upper light-transmitting film is provided with a light source, such as an LED light source with a wavelength of 567 nm. A lower side of the lower light-transmitting film is provided with a light receiver. The light source and the light receiver are connected with a processor.

[0050] ​When the second detection system 40 is in detection, the light source is turned on, the light penetrates the upper light-transmitting film and passes through the mixed sample liquid in the second optical detection window, the blood cells in the mixed sample liquid absorb light under the chemical reaction, and the light is received by the light receiver after being absorbed by the blood cells to a certain extent through the lower light-transmitting film. The controller detects the change curve of the incident light intensity and the transmitted light intensity, calculates the absorbance of the blood cells in the mixed sample liquid, and further calculates the SAA index of the blood cells in the mixed sample liquid.

[0051] As shown in Figure 3 In some embodiments, the third buffer pool 41 has a third opening 411, and the fourth buffer pool 42 has a fourth opening 421. The microfluidic chip further comprises a third film and a fourth film, the third film covers the third opening 411, and the fourth film covers the fourth opening 421. The third film is an elastic film, and by pressing the third film, the sample and the second reagent can be driven to flow back and forth in the third mixing channel 43 and the fourth mixing channel 46. In this implementation, the structure for driving the sample and the second reagent to flow in the third mixing channel 43 and the fourth mixing channel 46 is simple, and the cost can be effectively reduced. Of course, the driving of the sample and the second reagent to flow in the third mixing channel 43 and the fourth mixing channel 46 is not limited to the above-mentioned manner. For example, in some other embodiments, a second driving channel can be connected to the second detection system 40, the second driving channel is connected to a syringe, and the syringe injects air or extracts air into the second detection system 40 through the second driving channel to drive the sample and the second reagent to flow back and forth in the third mixing channel 43 and the fourth mixing channel 46.

[0052] As shown in Figure 5 In some embodiments, the chip body 100 is further provided with a second sample quantifying part 104, a third sample conveying microchannel 105, and a fourth sample conveying microchannel 106. The second sample quantifying part 104 is in communication with the second sample inlet 20, and the second sample quantifying part 104 is used for quantifying the sample input into the second detection system 40 from the second sample inlet 20. One end of the third sample conveying microchannel 105 is in communication with the second sample quantifying part 104, and the other end of the third sample conveying microchannel 105 is in communication with the third mixing channel 43. One end of the fourth sample conveying microchannel 106 is in communication with the second sample quantifying part 104, and the other end of the fourth sample conveying microchannel 106 is in communication with the second reagent adding part 44.

[0053] Optionally, the third sample delivery microchannel 105 and the fourth sample delivery microchannel 106 are capillary structures. In this embodiment, by providing the second sample quantification unit 104, the amount of sample entering the second detection system 40 can be controlled to a certain volume, and by controlling the amount of reagent input by the second reagent addition unit 44, the sample entering the second detection system 40 can be diluted to a specified concentration, thereby improving the detection effect. In some embodiments, the volume of the second sample quantification unit 104 is 0.8 μL.

[0054] like Figure 3 and Figure 7 As shown, in some embodiments, the second reagent addition unit 44 includes a second receiving portion 441, a second reagent pool 442, and a second reagent container 443. The second sample inlet 20 and the second optical detection unit 45 are connected to the second reagent pool 442. The second reagent container 443 is housed within the second receiving portion 441 and stores a second reagent. When the second reagent container 443 is pressed, the second reagent is injected into the second reagent pool 442. The second reagent pool 442 is located within the outline of the second receiving portion 441. In this embodiment, by placing the second reagent pool 442 within the outline of the second receiving portion 441, i.e., the second reagent pool 442 and the second receiving portion 441 share a common structure, space utilization can be improved, thereby reducing the size of the microfluidic chip.

[0055] like Figure 7 As shown, in some embodiments, the second receiving portion 441 includes a second sink portion 4411 and a second through-hole portion 4412. The second through-hole portion 4412 is disposed on the bottom surface of the sink portion 4411 and penetrates the chip body 100. The second reagent pool 442 is disposed on the bottom surface of the sink portion 4411 and spaced apart from the second through-hole portion 4412. The second reagent container 443 includes a second cup body 4431 and a second cup rim 4432. The second cup rim 4432 surrounds the opening end of the second cup body 4431 and is embedded in the second sink portion 4411. The second cup rim 4432 is provided with a second reagent delivery microchannel communicating with the second reagent pool 442. The second cup body 4431 is embedded in the second through-hole portion 4412 and communicates with the second reagent delivery microchannel.

[0056] Specifically, when the second reagent container 443 is not pressed, the second reagent in the second reagent container 443 cannot enter the second reagent pool 442 through the second reagent delivery microchannel. Only when the second reagent container 443 is pressed can the second reagent in the second reagent container 443 enter the second reagent pool 442 through the second reagent delivery microchannel.

[0057] like Figures 3 to 6As shown, in some embodiments, the chip body 100 includes a substrate 100a, which has a front side and a back side. One of the third mixing channel 43 and the fourth mixing channel 46 is disposed on the front side of the substrate 100a, and the other of the third mixing channel 43 and the fourth mixing channel 46 is disposed on the back side of the substrate 100a. In this embodiment, by disposing one of the third mixing channel 43 and the fourth mixing channel 46 on the front side of the substrate 100a and the other of the third mixing channel 43 and the fourth mixing channel 46 on the back side of the substrate 100a, the space utilization of the substrate 100a is improved, and the integration and miniaturization of the microfluidic chip are achieved.

[0058] In some embodiments, the third mixing channel 43 and the fourth mixing channel 46 are disposed opposite to each other in the thickness direction of the substrate 100a. This embodiment can improve the space utilization of the substrate 100a, enabling the integration and miniaturization of the microfluidic chip.

[0059] like Figures 3 to 6 As shown, in some embodiments, the second detection system 40 further includes a second waste liquid tank 47, which is connected to the third buffer tank 41. In this embodiment, by providing the second waste liquid tank 47, after the second optical detection unit 45 completes optical detection, the mixture of the sample and the second reagent can be driven into the second waste liquid tank 47 for collection, preventing the mixture from flowing out and causing contamination. It should be noted that in some embodiments, the chip body 100 may not have a second waste liquid tank 47. After the second optical detection unit 45 completes optical detection, the mixture of the sample and the second reagent can be driven into the second buffer tank 32 for storage, or directly retained in the third mixing channel 43 and the fourth mixing channel 46.

[0060] like Figure 3 and Figure 4 As shown, in some embodiments, the chip body 100 further includes a cover plate 100b, which covers the front side of the substrate 100a. In this embodiment, the cover plate 100b can prevent external impacts on the microfluidic chip during transportation or before use, thus avoiding damage to certain structures or reagent containers and improving the safety of the microfluidic chip. Simultaneously, the cover plate 100b can also prevent external moisture, debris, etc., from affecting the microfluidic chip before detection, ensuring the accuracy of the detection.

[0061] The above description is merely a specific embodiment of this utility model, but the protection scope of this utility model is not limited thereto. Any person skilled in the art can easily conceive of various equivalent modifications or substitutions within the technical scope disclosed in this utility model, and these modifications or substitutions should all be covered within the protection scope of this utility model. Therefore, the protection scope of this utility model should be determined by the scope of the claims.

Claims

1. A microfluidic chip, characterized by, The chip comprises a chip body, a first sample inlet, a second sample inlet, a first detection system, and a second detection system. The first detection system is used for optical detection of a sample input from the first sample inlet. The second detection system is used for optical detection of a sample input from the second sample inlet. The first detection system is used for detection of a blood sample to obtain a C-reactive protein (CRP) index of the blood sample. The second detection system is used for detection of the blood sample to obtain a serum amyloid A (SAA) index of the blood sample.

2. The microfluidic chip of claim 1, wherein, The first sample inlet and the second sample inlet are arranged on the same side of the chip body and adjacent to each other. The first detection system comprises a first buffer pool, a second buffer pool, a first mixing channel, a first reagent adding part, a first optical detection part, and a second mixing channel. The first mixing channel is in communication with the first sample inlet and the first buffer pool.

3. The microfluidic chip of claim 2, wherein, The first reagent adding part is in communication with the first sample inlet and is used to provide a first reagent mixed with a sample. The first optical detection part is in communication with the first reagent adding part and is used for detection of a mixture of the sample and the first reagent. The first buffer pool has a first opening, and the second buffer pool has a second opening. The microfluidic chip further comprises a first film and a second film. The first film is an elastic film, and the sample and the first reagent can be driven to flow back and forth in the first mixing channel and the second mixing channel by pressing the first film. The chip body further comprises a first sample quantifying part, a first sample conveying microchannel, and a second sample conveying microchannel. The first sample quantifying part is in communication with the first sample inlet and is used to quantify a sample input from the first sample inlet to the first detection system. The first sample conveying microchannel has one end in communication with the first sample quantifying part and the other end in communication with the first mixing channel. The second sample conveying microchannel has one end in communication with the first sample quantifying part and the other end in communication with the first reagent adding part. And / or, the first reagent adding part comprises a first accommodating part, a first reagent pool and a first reagent container, the first sample inlet and the first optical detection part communicate with the first reagent pool, the first reagent container is accommodated in the first accommodating part, the first reagent container stores the first reagent, and the first reagent container injects the first reagent into the first reagent pool when being pressed, wherein the first reagent pool is arranged within the profile range of the first accommodating part; And / or, the chip body comprises a substrate, the substrate comprises a front surface and a back surface, one of the first mixing channel and the second mixing channel is arranged on the front surface of the substrate, and the other of the first mixing channel and the second mixing channel is arranged on the back surface of the substrate; And / or, the first detection system further comprises a first waste liquid pool, and the first waste liquid pool communicates with the first buffer pool.

4. The microfluidic chip of claim 3, wherein, The first accommodating part comprises a first sink part and a first through-hole part, the first through-hole part is arranged on the groove bottom surface of the first sink part and penetrates through the chip body, and the first reagent pool is arranged on the groove bottom surface of the first sink part and is arranged in a spaced manner with the first through-hole part. The first reagent container comprises a first cup body and a first cup flange, the first cup flange surrounds the periphery of the opening end of the first cup body, the first cup flange is embedded in the first sink part, the first cup flange is provided with a first reagent delivery micro-channel which communicates with the first reagent pool, and the first cup body is embedded in the first through-hole part and communicates with the first reagent delivery micro-channel.

5. The microfluidic chip of claim 3, wherein, The first mixing channel and the second mixing channel are arranged in a relative manner in the thickness direction of the substrate.

6. The microfluidic chip of claim 1, wherein, The second detection system comprises a third buffer pool, a fourth buffer pool, a third mixing channel, a second reagent adding part, a second optical detection part and a fourth mixing channel; The third mixing channel communicates the second sample inlet and the third buffer pool; The second reagent adding part communicates with the second sample inlet, and the second reagent adding part is used for providing a second reagent mixed with a sample; The second optical detection part communicates with the second reagent adding part, and the second optical detection part is used for detecting a mixed solution of the sample and the second reagent; The fourth mixing channel communicates the second optical detection part and the fourth buffer pool.

7. The microfluidic chip of claim 6, wherein, The third buffer pool has a third opening, the fourth buffer pool has a fourth opening, the micro-fluidic chip further comprises a third film and a fourth film, the third film covers the third opening, the fourth film covers the fourth opening, the third film is an elastic film, and the sample and the second reagent can be driven to flow back and forth in the third mixing channel and the fourth mixing channel by pressing the third film; And / or, the chip body is further provided with a second sample quantifying part, a third sample conveying micro-channel and a fourth sample conveying micro-channel, the second sample quantifying part is in communication with the second sample inlet, the second sample quantifying part is used for quantifying the sample input from the second sample inlet into the second detection system, one end of the third sample conveying micro-channel is in communication with the second sample quantifying part, the other end of the third sample conveying micro-channel is in communication with the third mixing channel, one end of the fourth sample conveying micro-channel is in communication with the second sample quantifying part, the other end of the fourth sample conveying micro-channel is in communication with the second reagent adding part; And / or, the chip body comprises a substrate, the substrate comprises a front surface and a back surface, one of the third mixing channel and the fourth mixing channel is arranged on the front surface of the substrate, and the other of the third mixing channel and the fourth mixing channel is arranged on the back surface of the substrate; And / or, the second detection system further comprises a second waste liquid pool, the second waste liquid pool is in communication with the third buffer pool.

8. The microfluidic chip of claim 6, wherein, The second reagent adding part comprises a second containing part, a second reagent pool and a second reagent container; The second sample inlet and the second optical detection part are in communication with the second reagent pool; The second reagent container is contained in the second containing part, the second reagent container stores a second reagent, and the second reagent container injects the second reagent into the second reagent pool when being pressed; The second reagent pool is arranged within the profile range of the second containing part.

9. The microfluidic chip of claim 8, wherein, The second containing part comprises a second sink part and a second through-hole part, the second through-hole part is arranged on the groove bottom surface of the second sink part and penetrates through the chip body, and the second reagent pool is arranged on the groove bottom surface of the second sink part and is arranged in a spaced manner with the second through-hole part; The second reagent container comprises a second cup body and a second cup rim, the second cup rim surrounds the periphery of the open end of the second cup body, the second cup rim is embedded in the second sink part, the second cup rim is provided with a second reagent conveying micro-channel in communication with the second reagent pool, and the second cup body is embedded in the second through-hole part and is in communication with the second reagent conveying micro-channel.

10. The microfluidic chip of claim 7, wherein, The third mixing channel and the fourth mixing channel are arranged in a relative manner in the thickness direction of the substrate.

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