Microfluidic chip

Abstract

A microfluidic chip, comprising a chip body. The chip body is provided with a first sample inlet, a second sample inlet, a first detection system and a second detection system, wherein the first detection system is in communication with the first sample inlet, and is used for performing optical detection on a sample input from the first sample inlet; and the second detection system is in communication with the second sample inlet, and is used for performing optical detection on a sample input from the second sample inlet. The proposed microfluidic chip has the following advantages: higher integration, miniaturization, better portability, lower cost and enhanced ease of use are achieved, no contamination is caused, the waste of samples and reagents can be reduced, and a first detection system and a second detection system are independent of each other and free from mutual interference, thereby enabling an operator to know about different functions realized by the two systems and perform corresponding operations.

Description

microfluidic chip Technical Field

[0001] This invention relates to the field of medical devices, and more particularly to a microfluidic chip. Background Technology

[0002] CRP, also known as C-reactive protein, is a protein that rises sharply in blood plasma when the body is infected or tissues are damaged. It primarily reflects the degree of inflammatory response or tissue damage and is widely used in acute phase reactions, cardiovascular disease risk assessment, monitoring inflammatory diseases, predicting postoperative complications, and tumor surveillance.

[0003] SAA, also known as serum amyloid A, is a precursor to tissue amyloid protein A. It is an acute-phase protein that increases in levels during tissue injury and inflammatory responses, affecting cell adhesion, migration, proliferation, and aggregation. It is commonly seen in tissue infections, such as acute and chronic inflammatory diseases like purulent infections, severe trauma, myocardial infarction, rheumatoid arthritis, systemic vasculitis, and polymyalgia rheumatica.

[0004] The combined use of CRP and SAA is often used for the rapid diagnosis of bacterial and viral infections. It can serve as a sensitive indicator reflecting infection and inflammation control and is widely used in the auxiliary diagnosis of infectious diseases, prediction of coronary heart disease risk, dynamic monitoring of efficacy and prognosis in cancer patients, monitoring of transplant rejection, and monitoring of the improvement of rheumatoid arthritis. It is particularly significant in the early diagnosis of pediatric infectious diseases and neonatal sepsis, and in the early differentiation of bacterial and viral infections in infants and young children than either test alone.

[0005] With the modernization and automation of testing methods, CRP and SAA tests are now generally completed automatically by testing instruments. The current common practice is to add blood samples and reagents to the reaction chamber of the testing instrument for dilution, allowing the blood samples and reagents to react fully, and then use transmission turbidimetry or scattering turbidimetry to measure the absorbance of the solution after the reaction, and finally calculate its concentration.

[0006] However, since all the components used in the above-mentioned detection steps, such as sampling devices, reaction tanks, quantitative devices, and fluid pipelines, are located inside the detection instrument, especially the components involving fluids and liquid chemical reagents, are connected to the detection instrument, the existing detection instruments have problems such as high overall cost, large size, heavy weight, complex structure, and inconvenience in moving. They can generally only be used in a fixed location in the laboratory or testing room, which has great limitations.

[0007] Furthermore, the above steps, such as sampling, sample separation, mixing, measurement, and cleaning, are all completed automatically by the testing instrument. Any problem in any step will affect the accuracy of CRP and SAA test results. When a problem occurs, the testing instrument needs to be shut down and a comprehensive investigation needs to be conducted to confirm the cause of the problem, which will affect the testing efficiency. Summary of the Invention

[0008] In view of this, the present invention proposes a microfluidic chip.

[0009] The microfluidic chip proposed in this invention includes a chip body, wherein the chip body is provided with:

[0010] First injection port;

[0011] Second injection port;

[0012] A first detection system is connected to the first sample inlet and is used to perform optical detection on the sample input from the first sample inlet.

[0013] The second detection system is connected to the second sample inlet and is used to perform optical detection on the sample input from the second sample inlet.

[0014] As can be seen from the above technical solution, the microfluidic chip proposed in this invention, firstly, integrates a first detection system and a second detection system on a small microfluidic chip. Compared with existing sample detection instruments, the microfluidic chip is more integrated, miniaturized, portable, and lower in cost. Operators can use the microfluidic chip for sample detection in any suitable environment without being subject to too many usage restrictions. Secondly, the microfluidic chip is a disposable consumable, which can be directly discarded after sample detection, making it more convenient to use. The waste liquid after sample detection remains in the microfluidic chip, eliminating the problem of secondary leakage and pollution. Operators do not need to perform additional processing. Even if adverse factors occur during sample detection, a new microfluidic chip can be directly replaced for detection, reducing the impact on detection efficiency. Furthermore, the microfluidic chip used for sample detection can accurately and quantitatively acquire and process samples, and the required sample and reagent volumes are relatively small, reducing waste of samples and reagents. In addition, the first and second detection systems are independent of each other, and the sample detection performed by the two systems is independent and does not interfere with each other, making it easy for operators to understand the different functions performed by the two systems and take corresponding actions. For example, individual detection systems can be driven and controlled in a targeted manner. If the sample mixing effect is poor or the flow rate is slow in a certain detection system, the detection system can be driven separately to achieve the desired effect of sample mixing or flow rate. Attached Figure Description

[0015] To more clearly illustrate the technical solutions of the embodiments of the present invention, the drawings used in the following description of the embodiments will be briefly introduced. Obviously, the drawings described below are some embodiments of the present invention. For those skilled in the art, other drawings can be obtained from these drawings without creative effort.

[0016] Figure 1 is a schematic diagram of the structure of a microfluidic chip proposed in an embodiment of the present invention;

[0017] Figure 2 is an exploded view of a microfluidic chip proposed in an embodiment of the present invention;

[0018] Figure 3 is an exploded view of the microfluidic chip proposed in an embodiment of the present invention from the top perspective;

[0019] Figure 4 is an exploded view of the bottom of a microfluidic chip according to an embodiment of the present invention.

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

[0021] Figure 6 is a schematic diagram of the structure of a substrate from the back side view according to an embodiment of the present invention;

[0022] Figure 7 is an exploded view of a partial structure of a microfluidic chip proposed in an embodiment of the present invention.

[0023] Furthermore, since the channels of the proposed microfluidic chip are partially located on the front side of the substrate, partially on the back side of the substrate, and partially on the cover plate, the letters AB are used to mark them in Figures 5 and 6 to clearly indicate the direction of the channels. Detailed Implementation

[0024] The technical solutions of the embodiments of the present invention will be clearly and completely described below with reference to the accompanying drawings. Obviously, the described embodiments are only some, not all, of the embodiments of the present invention. Other embodiments obtained by those skilled in the art based on the embodiments of the present invention without creative effort are all within the scope of protection of the present invention.

[0025] As shown in Figures 1 to 4, an embodiment of the present invention proposes a microfluidic chip. The microfluidic chip includes a chip body 100, which is provided with a first sample inlet 10, a second sample inlet 20, a first detection system 30, and a second detection system 40. The first detection system 30 is connected to the first sample inlet 10 and is used to perform optical detection on the sample input from the first sample inlet 10. The second detection system 40 is connected to the second sample inlet 20 and is used to perform optical detection on the sample input from the second sample inlet 20.

[0026] The microfluidic chip proposed in this invention firstly integrates a first detection system 30 and a second detection system 40 on a relatively small microfluidic chip. Compared to existing sample detection instruments, the microfluidic chip is more integrated, miniaturized, portable, and lower in cost. Operators can use the microfluidic chip for sample detection in any suitable environment without being subject to many usage restrictions. Secondly, the microfluidic chip is a disposable consumable that can be discarded directly after sample detection, making it more convenient to use. Waste liquid after sample detection remains in the microfluidic chip, eliminating the problem of secondary leakage and contamination. Operators do not need to perform additional processing. Even if adverse factors occur during sample detection, a new microfluidic chip can be directly replaced for re-detection, reducing the impact on detection efficiency. Furthermore, the microfluidic chip, used for sample detection, can accurately and quantitatively acquire and process samples, while requiring relatively small sample and reagent volumes, reducing waste of samples and reagents. Furthermore, the first detection system 30 and the second detection system 40 are independent of each other, and the sample detection performed by the two systems is independent and does not interfere with each other. This makes it easy for the operator to understand the different functions performed by each system and to take corresponding actions. For example, each detection system can be driven and controlled in a targeted manner. If the sample mixing effect or flow rate of a certain detection system is not good or the flow rate is slow, then the detection system can be driven separately to achieve the desired effect of sample mixing or flow rate.

[0027] In some embodiments, the components of the microfluidic chip are manufactured using a one-piece precision injection molding method, which can improve the overall integrity of the microfluidic chip and also ensure the accuracy of steps such as sampling, adding reagents, 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] As shown in Figures 1 to 3, in some embodiments, the first sampling port 10 and the second sampling port 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 sampling port 10 and the second sampling port 20. In this embodiment, by arranging the first sampling port 10 and the second sampling port 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 sampling port 10 and the second sampling port 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 sampling ports, 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] As shown in Figures 3 to 6, 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 to 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] As shown in Figure 3, 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] As shown in Figure 5, 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] As shown in Figures 3 and 7, 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] As shown in Figure 7, 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] As shown in Figures 3 to 6, 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 of 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, achieving the integration and miniaturization of the microfluidic chip.

[0045] In some embodiments, the first mixing channel 33 and the second mixing channel 36 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.

[0046] As shown in Figures 3 to 6, in some embodiments, the first detection system 30 further includes a first waste liquid tank 37, which is connected to the first buffer tank 31. In this embodiment, by providing the first waste liquid tank 37, after the first optical detection unit 35 completes optical detection, the mixture of the sample and the first reagent can be driven into the first waste liquid tank 37 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 first waste liquid tank 37. After the first optical detection unit 35 completes optical detection, the mixture of the sample and the first reagent can be driven into the first buffer tank 31 for storage, or directly retained in the first mixing channel 33 and the second mixing channel 36.

[0047] As shown in Figures 3 to 6, in some embodiments, the second detection system 40 includes a third buffer tank 41, a fourth buffer tank 42, a third mixing channel 43, a second reagent addition unit 44, a second optical detection unit 45, and a fourth mixing channel 46. The third mixing channel 43 connects to the second sample inlet 20 and the third buffer tank 41. The second reagent addition unit 44 is connected to the second sample inlet 20 and is used to provide a second reagent mixed with the sample. The second optical detection unit 45 is connected to the second reagent addition unit 44 and is used to detect the mixture of the sample and the second reagent. The fourth mixing channel 46 connects to the second optical detection unit 45 and the fourth buffer tank 42.

[0048] Since the second reagent added by the second reagent addition unit 44 may not mix the sample and the sample evenly, it may affect the accuracy of subsequent optical detection. In this embodiment, by providing a third mixing channel 43 connected to the second sample inlet 20 and a fourth mixing channel 46 connected to the second optical detection unit 45 to mix the sample and the second reagent, the accuracy of subsequent optical detection can be improved.

[0049] In some embodiments, the second optical detection unit 45 has a second optical detection window, through which the mixed sample liquid can flow and remain. The upper and lower surfaces of the second 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.

[0050] When the second detection system 40 is used, the light source is turned on. The light penetrates the upper light-transmitting membrane and passes through the mixed sample liquid in the second optical detection 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 light-transmitting 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. Then, the SAA index of the blood cells in the mixed sample liquid can be further calculated.

[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 also includes 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 pressing the third film can drive the sample and the second reagent to flow back and forth in the third mixing channel 43 and the fourth mixing channel 46. In this embodiment, 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 can effectively reduce costs. Of course, driving 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-described method. For example, in some other embodiments, a second driving channel can be connected to the second detection system 40, and a syringe can be connected to the second driving channel. The syringe injects 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 quantification section 104, a third sample delivery microchannel 105, and a fourth sample delivery microchannel 106. The second sample quantification section 104 is connected to the second injection port 20 and is used to quantify the sample input into the second detection system 40 from the second injection port 20. One end of the third sample delivery microchannel 105 is connected to the second sample quantification section 104, and the other end of the third sample delivery microchannel 105 is connected to the third mixing channel 43. One end of the fourth sample delivery microchannel 106 is connected to the second sample quantification section 104, and the other end of the fourth sample delivery microchannel 106 is connected to the second reagent addition section 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] As shown in Figures 3 and 7, 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] As shown in Figure 7, 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 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] As shown in Figures 3 to 6, 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] As shown in Figures 3 to 6, 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] As shown in Figures 3 and 4, 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 the present invention, but the scope of protection of the present invention 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 the present invention, and these modifications or substitutions should all be covered within the scope of protection of the present invention. Therefore, the scope of protection of the present invention should be determined by the scope of the claims.

Claims

1. A microfluidic chip, characterized by, Includes a chip body, wherein the chip body is provided with: First injection port; Second injection port; A first detection system is connected to the first sample inlet and is used to perform optical detection on the sample input from the first sample inlet. The second detection system is connected to the second sample inlet and is used to perform optical detection on the sample input from the second sample inlet.

2. The microfluidic chip of claim 1, wherein, The samples input from both the first and second injection ports are blood samples; The first detection system is used to detect the blood sample to obtain the C-reactive protein (CRP) level of the blood sample, and the second detection system is used to detect the blood sample to obtain the serum amyloid A (SAA) level of the blood sample.

3. The microfluidic chip of claim 1, wherein, The first sample inlet and the second sample inlet are located on the same side of the chip body and are arranged side by side adjacent to each other; The microfluidic chip also includes a sealing component, which is closable to the chip body and is used to block the first injection port and the second injection port.

4. The microfluidic chip of claim 1, wherein, The first detection system includes a first buffer tank, a second buffer tank, a first mixing channel, a first reagent addition unit, a first optical detection unit, and a second mixing channel; The first mixing channel connects the first sample inlet and the first buffer tank; The first reagent addition section is connected to the first injection port, and the first reagent addition section is used to provide a first reagent mixed with the sample; The first optical detection unit is connected to the first reagent addition unit, and the first optical detection unit is used for detecting the mixture of the sample and the first reagent; The second mixing channel connects the first optical detection unit and the second buffer pool.

5. The microfluidic chip of claim 4, wherein, The first buffer pool has a first opening, and the second buffer pool has a second opening; The microfluidic chip also includes a first film and a second film. The first film covers the first opening, and the second film covers the second opening. The first film is an elastic film. By pressing the first film, the sample and the first reagent can be driven to flow back and forth in the first mixing channel and the second mixing channel.

6. The microfluidic chip of claim 4, wherein, The chip body is also provided with a first sample quantification section, a first sample delivery microchannel, and a second sample delivery microchannel; The first sample quantification unit is connected to the first injection port, and the first sample quantification unit is used to quantify the sample input into the first detection system from the first injection port; One end of the first sample delivery microchannel is connected to the first sample quantitative section, and the other end of the first sample delivery microchannel is connected to the first mixing channel. One end of the second sample delivery microchannel is connected to the first sample quantification section, and the other end of the second sample delivery microchannel is connected to the first reagent addition section.

7. The microfluidic chip of claim 4, wherein, The first reagent addition section includes a first receiving section, a first reagent pool, and a first reagent container; The first sample inlet and the first optical detection unit are connected to the first reagent cell; The first reagent container is housed in the first receiving part, and the first reagent container stores the first reagent. When the first reagent container is pressed, the first reagent is injected into the first reagent pool. The first reagent pool is located within the outline of the first receiving part.

8. The microfluidic chip of claim 6, wherein, The first receiving portion includes a first sink portion and a first through-hole portion. The first through-hole portion is disposed on the bottom surface of the first sink portion and penetrates the chip body. The first reagent pool is disposed on the bottom surface of the first sink portion and is spaced apart from the first through-hole portion. The first reagent container includes a first cup body and a first cup rim. The first cup rim surrounds the opening end of the first cup body and is embedded in the first settling groove. The first cup rim is provided with a first reagent delivery microchannel communicating with the first reagent pool. The first cup body is embedded in the first through hole and communicates with the first reagent delivery microchannel.

9. The microfluidic chip of claim 4, wherein, The chip body includes a substrate, which has a front side and a back side. One of the first mixing channel and the second mixing channel is disposed on the front side of the substrate, and the other of the first mixing channel and the second mixing channel is disposed on the back side of the substrate.

10. The microfluidic chip of claim 9, wherein, The first mixing channel and the second mixing channel are disposed opposite to each other in the thickness direction of the substrate.

11. The microfluidic chip of claim 4, wherein, The first detection system also includes a first waste liquid tank, which is connected to the first buffer tank.

12. The microfluidic chip of claim 1, wherein, The second detection system includes a third buffer tank, a fourth buffer tank, a third mixing channel, a second reagent addition unit, a second optical detection unit, and a fourth mixing channel; The third mixing channel is connected to the second sample inlet and the third buffer tank; The second reagent addition section is connected to the second injection port, and the second reagent addition section is used to provide a second reagent mixed with the sample; The second optical detection unit is connected to the second reagent addition unit, and the second optical detection unit is used for detecting the mixture of the sample and the second reagent; The fourth mixing channel connects the second optical detection unit and the fourth buffer pool.

13. The microfluidic chip of claim 12, wherein, The third buffer pool has a third opening, and the fourth buffer pool has a fourth opening; The microfluidic chip also includes a third film and a fourth film. The third film covers the third opening, and the fourth film covers the fourth opening. The third film is an elastic film. By pressing the third film, the sample and the second reagent can be driven to flow back and forth in the third mixing channel and the fourth mixing channel.

14. The microfluidic chip of claim 12, wherein, The chip body is also provided with a second sample quantification section, a third sample delivery microchannel and a fourth sample delivery microchannel; The second sample quantification unit is connected to the second injection port, and the second sample quantification unit is used to quantify the sample input into the second detection system from the second injection port; One end of the third sample delivery microchannel is connected to the second sample quantification section, and the other end of the third sample delivery microchannel is connected to the third mixing channel; One end of the fourth sample delivery microchannel is connected to the second sample quantification section, and the other end of the fourth sample delivery microchannel is connected to the second reagent addition section.

15. The microfluidic chip of claim 12, wherein, The second reagent addition section includes a second containment section, a second reagent pool, and a second reagent container; The second sample inlet and the second optical detection unit are connected to the second reagent cell; The second reagent container is housed in the second receiving part, and the second reagent is stored in the second reagent container. When the second reagent container is pressed, the second reagent is injected into the second reagent pool. The second reagent pool is located within the outline of the second receiving part.

16. The microfluidic chip of claim 15, wherein, The second receiving portion includes a second sink portion and a second through-hole portion. The second through-hole portion is disposed on the bottom surface of the second sink portion and penetrates the chip body. The second reagent pool is disposed on the bottom surface of the second sink portion and is spaced apart from the second through-hole portion. The second reagent container includes a second cup body and a second cup rim. The second cup rim surrounds the opening end of the second cup body and is embedded in the second settling groove. The second cup rim is provided with a second reagent delivery microchannel that communicates with the second reagent pool. The second cup body is embedded in the second through hole and communicates with the second reagent delivery microchannel.

17. The microfluidic chip of claim 12, wherein, The chip body includes a substrate, the substrate includes a front side and a back side, one of the third mixing channel and the fourth mixing channel is disposed on the front side of the substrate, and the other of the third mixing channel and the fourth mixing channel is disposed on the back side of the substrate.

18. The microfluidic chip of claim 17, wherein, The third mixing channel and the fourth mixing channel are arranged opposite to each other in the thickness direction of the substrate.

19. The microfluidic chip of claim 12, wherein, The second detection system also includes a second waste liquid tank, which is connected to the third buffer tank.

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