Microfluidic chip

Abstract

The micro-fluidic chip comprises a second sheath fluid part, a second sheath fluid adding part, a third sheath fluid channel, a fourth sheath fluid channel and a second waste liquid pool, the second sheath flow part is provided with a second sample liquid inlet, a second sheath liquid inlet, a third auxiliary flow inlet, a fourth auxiliary flow inlet, a second waste liquid outlet, a second gem hole, a second laminar flow groove and a second auxiliary flow groove; the second laminar flow groove and the second auxiliary flow groove are located in the two sides of the second jewel hole and communicate with the second jewel hole, and the second laminar flow groove, the second jewel hole and the second auxiliary flow groove form an hourglass structure. The second sample liquid inlet and the second sheath liquid inlet are communicated with the second laminar flow groove; the third auxiliary flow inlet, the fourth auxiliary flow inlet and the second waste liquid outlet are communicated with the second auxiliary flow groove; the third sheath fluid channel is communicated with the second sheath fluid adding part and the second sheath fluid inlet; the fourth sheath fluid channel is communicated with the second sheath fluid adding part, the third auxiliary flow inlet and the fourth auxiliary flow inlet; the second waste liquid pool is communicated with the second waste liquid outlet.

Description

Technical Field

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

[0002] A complete blood count (CBC) is a common procedure during physical examinations. It involves observing changes in the number and morphological distribution of blood cells in a blood sample to assess the blood condition and further analyze and determine the examinee's health status.

[0003] With the modernization and automation of testing methods, routine blood tests are now generally performed automatically by testing instruments. Because red blood cells and platelets are small, they are difficult to detect accurately using optical methods like white blood cells. The current practice involves diluting the blood sample in the reaction chamber of the testing instrument, then using impedance spectroscopy to count the red blood cells and platelets. A certain amount of the diluted blood sample is then added to a hemolytic reagent to dissolve the red blood cells, followed by impedance spectroscopy to count and classify the white blood cells. Simultaneously, hemoglobin is measured using a colorimetric method. Finally, the mixed sample is discharged from the testing instrument; this constitutes one routine blood test. Furthermore, all paths the blood sample has passed through must be cleaned to ensure cleanliness before the next blood sample can be tested.

[0004] Existing testing instruments suffer from problems such as high overall cost, large size, heavy weight, complex structure, and inconvenience in movement. They can generally only be used in fixed locations in laboratories or testing rooms, which greatly limits their use. Summary of the Invention

[0005] In view of this, the present invention proposes a microfluidic chip.

[0006] The microfluidic chip proposed in this invention includes a second sheath flow section, a second sheath fluid addition section, a third sheath fluid channel, a fourth sheath fluid channel, and a second waste liquid pool; The second sheath flow section is provided with a second sample liquid inlet, a second sheath liquid inlet, a third auxiliary flow inlet, a fourth auxiliary flow inlet, a second waste liquid outlet, a second sapphire hole, a second laminar flow channel, and a second auxiliary flow channel; The second laminar flow channel and the second auxiliary flow channel are located on both sides of the second gem hole and are connected to the second gem hole. The second laminar flow channel, the second gem hole and the second auxiliary flow channel form an hourglass structure. The second sample liquid inlet and the second sheath liquid inlet are connected to the second laminar flow channel, and the third auxiliary flow inlet, the fourth auxiliary flow inlet and the second waste liquid outlet are connected to the second auxiliary flow channel; The second sheath fluid addition section is used to supply sheath fluid to the second sheath flow section; The third sheath fluid channel connects the second sheath fluid addition section and the second sheath fluid inlet; One end of the fourth sheath fluid channel is connected to the second sheath fluid addition section, and the other end of the fourth sheath fluid channel is connected to the third auxiliary flow inlet and the fourth auxiliary flow inlet; The second waste liquid tank is connected to the second waste liquid outlet, and the second waste liquid tank is used to receive the waste liquid discharged from the second sheath flow section.

[0007] As can be seen from the above technical solution, the microfluidic chip proposed in this invention, firstly, integrates an impedance detection structure formed by a second sheath flow section, a second sheath fluid addition section, a third sheath fluid channel, a fourth sheath fluid channel, and a second waste liquid pool on a relatively small microfluidic chip. This enables the microfluidic chip to perform impedance detection of samples. Compared with existing detection instruments, the impedance detection structure integrated on the microfluidic chip is more integrated, miniaturized, more 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, compared with existing sample detection instruments, the microfluidic chip is a disposable consumable that can be directly discarded after sample detection, making it more convenient to use. Furthermore, the waste liquid after impedance detection is retained in the second waste liquid pool, preventing secondary outflow of waste liquid and avoiding pollution problems, eliminating the need for additional processing by the operator. In addition, impedance detection on the microfluidic chip enables accurate and quantitative sample acquisition and processing, and the required sample and reagent volumes are relatively small, reducing sample and reagent waste. Attached Figure Description

[0008] 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.

[0009] Figure 1 This is a schematic diagram of the structure of a microfluidic chip proposed in an embodiment of the present invention; Figure 2 This is an exploded view of a microfluidic chip according to an embodiment of the present invention; Figure 3 This is an exploded view of a microfluidic chip proposed in an embodiment of the present invention from a top perspective; Figure 4 This is an exploded view of the bottom of a microfluidic chip according to an embodiment of the present invention; Figure 5 This is a schematic diagram of the structure of a substrate from a front view according to an embodiment of the present invention; Figure 6This is a schematic diagram of the structure of a substrate from the back side view according to an embodiment of the present invention; Figure 7 This is a schematic diagram of the structure of the cover plate facing away from the substrate according to an embodiment of the present invention; Figure 8 This is a schematic diagram of the structure of the cover plate facing the substrate according to an embodiment of the present invention; Figure 9 This is an exploded view of a partial structure of a microfluidic chip proposed in an embodiment of the present invention; Figure 10 This is an exploded view of a partial structure of a microfluidic chip proposed in an embodiment of the present invention; Figure 11 yes Figure 6 A magnified view of a portion of point G in the middle.

[0010] Furthermore, because 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, therefore... Figure 5 , Figure 6 , Figure 7 and Figure 8 The letters ABCDEF are used for marking to clearly indicate the direction of the passage. Detailed Implementation

[0011] 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.

[0012] like Figures 1 to 6 As shown, an embodiment of the present invention proposes a microfluidic chip, which includes a chip body 100. The chip body 100 is provided with a first sample inlet 10, a second sample inlet 20, a third sample inlet 30, a first detection system 40, a second detection system 50, a third detection system 60, a first driving channel 70, a second driving channel 80, and a third driving channel 90.

[0013] The first detection system 40 is connected to the first injection port 10 and is used to perform optical detection on the sample input through the first injection port 10. The second detection system 50 is connected to the second injection port 20 and is used to perform optical and impedance detection on the sample input through the second injection port 20. The third detection system 60 is connected to the third injection port 30 and is used to perform impedance detection on the sample input through the third injection port 30.

[0014] The first end of the first drive channel 70 is connected to the first detection system 40, and the second end D1 of the first drive channel 70 is used to connect to the first driver. The first driver drives the liquid to run inside the first detection system 40 through the first drive channel 70. The first end of the second drive channel 80 is connected to the second detection system 50, and the second end E1 of the second drive channel 80 is used to connect to the second driver. The second driver drives the liquid to run inside the second detection system 50 through the second drive channel 80. The first end of the third drive channel 90 is connected to the third detection system 60, and the second end F1 of the third drive channel 90 is used to connect to the third driver. The third driver drives the liquid to run inside the third detection system 60 through the third drive channel 90.

[0015] The microfluidic chip proposed in this invention firstly integrates a first detection system 40, a second detection system 50, and a third detection system 60 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, preventing 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 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, requiring relatively small sample and reagent volumes, thus reducing waste of samples and reagents. Furthermore, the first detection system 40, the second detection system 50, and the third detection system 60 are each independent of each other, and the sample detection performed by the three systems is independent and does not interfere with each other. This facilitates the operator's understanding of the different functions performed by each system and allows for corresponding operations. For example, each detection system can be driven and controlled specifically. If the sample mixing effect is poor or the flow rate is slow in a certain detection system, it can be driven separately through the drive channel connected to that detection system to achieve the desired sample mixing effect or flow rate. It should also be noted that the first drive channel 70, the second drive channel 80, and the third drive channel 90 are used to drive the liquid flowing in the first detection system 40, the second detection system 50, and the third detection system 60, respectively, ensuring that the sample can flow normally within these systems for relevant processing.

[0016] 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.

[0017] In some embodiments, the first driver, the second driver, and the third driver are three independently controllable syringes. The syringes have a simple structure and are easy to control.

[0018] In some embodiments, the samples input from the first inlet 10, the second inlet 20, and the third inlet 30 are all blood samples. The first detection system 40 is used to detect the blood sample to obtain its immunoturbidimetric index, the second detection system 50 is used to detect the blood sample to obtain its hemoglobin and white blood cell differential indices, and the third detection system 60 is used to detect the blood sample to obtain its red blood cell and platelet indices. In this embodiment, the proposed microfluidic chip can simultaneously and independently detect the circulating blood sample to obtain immunoturbidimetric, hemoglobin, white blood cell differential, red blood cell, and platelet indices, thereby achieving routine blood count testing. Of course, the first detection system 40, the second detection system 50, and the third detection system 60 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.

[0019] The "immunoturbidimetric indicators" refer to indicators measured using immunoturbidimetry, such as uric acid concentration, C-reactive protein concentration, and serum amyloid protein concentration. The "hemoglobin indicators" include hemoglobin concentration. The "white blood cell differential indicators" include white blood cell classification and quantity; for example, white blood cells include neutrophils, lymphocytes, monocytes, eosinophils, and basophils, and the white blood cell differential indicators include the quantity of these five cell types. The "red blood cell indicators" include the number of red blood cells. The "platelet indicators" include the number of platelets.

[0020] like Figure 1 and Figure 2As shown, in some embodiments, the first injection port 10, the second injection port 20, and the third injection port 30 are disposed on the same side of the chip body 100 and arranged adjacent to each other. 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 injection port 10, the second injection port 20, and the third injection port 30. In this embodiment, by disposing the first injection port 10, the second injection port 20, and the third injection port 30 on the same side of the chip body 100 and arranging them adjacent to each other, sampling by the microfluidic chip is facilitated. Taking the use of microfluidic chips for blood sample detection as an example, in one specific embodiment, the examinee or medical personnel use a lancet to prick the examinee's sampling site. When a blood droplet appears at the sampling site, the first sampling port 10, the second sampling port 20, and the third sampling port 30 are brought into contact with the blood droplet. The blood droplet enters the first detection system 40, the second detection system 50, and the third detection system 60 through the corresponding sampling ports, making sampling extremely convenient.

[0021] Furthermore, by setting the sealing component 200 to block the first inlet 10, the second inlet 20, and the third inlet 30, a closed environment is formed at the beginning of the first detection system 40, the second detection system 50, and the third detection system 60, preventing both gas and liquid from passing through. When gas is introduced through the first drive channel 70, the second drive channel 80, and the third drive channel 90, the gas can only flow along the first detection system 40, the second detection system 50, and the third detection system 60 because the sealing component 200 blocks the first inlet 10, the second inlet 20, and the third inlet 30, facilitating subsequent steps.

[0022] In some embodiments, the sealing member 200 is rotatably mounted on the chip body 100. Rotating the sealing member 200 until it contacts the first injection port 10, the second injection port 20, and the third injection port 30 seals them. Rotating the sealing member 200 until it separates from the first injection port 10, the second injection port 20, and the third injection port 30 opens the sealing member, facilitating operation and preventing the sealing member 200 from separating from the substrate and falling out. Of course, in other embodiments, the sealing member 200 may also be detachably mounted relative to the chip body 100, depending on the actual design requirements.

[0023] In some embodiments, the sealing element 200 may be made of silicone to reduce friction on the first injection port 10, the second injection port 20 and the third injection port 30. At the same time, since silicone has a certain degree of deformability, it can better fit with the first injection port 10, the second injection port 20 and the third injection port 30, thereby improving the sealing effect.

[0024] like Figure 5 and Figure 6As shown, in some embodiments, the second end D1 of the first driving channel 70, the second end E1 of the second driving channel 80, and the second end F1 of the third driving channel 90 are disposed on the same side of the chip body 100 and arranged adjacent to each other. In this embodiment, the first driver, the second driver, and the third driver can be arranged adjacent to each other, thereby facilitating the arrangement of the first driver, the second driver, and the third driver.

[0025] In some embodiments, the chip body 100 includes a substrate 100a, with trenches formed on the surface of the substrate 100a, and a first driving channel 70, a second driving channel 80, and a third driving channel 90 formed by covering the surface of the substrate 100a with a thin film or cover plate. The mixing channel described below can also be formed using this method, and will not be elaborated further.

[0026] like Figures 2 to 6 As shown, in some embodiments, the first detection system 40 includes a first buffer tank 41, a second buffer tank 42, a first mixing channel 43, a first reagent addition unit 44, a first optical detection unit 45, and a second mixing channel 46. The first mixing channel 43 connects to the first sample inlet 10 and the first buffer tank 41. The first reagent addition unit 44 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 45 is connected to the first reagent addition unit 44 and is used to detect the mixture of the sample and the first reagent. The second mixing channel 46 connects to the first optical detection unit 45 and the second buffer tank 42. The first end of the first drive channel 70 is connected to one of the first buffer tank 41 and the second buffer tank 42. The first actuator drives the sample and the first reagent to reciprocate within the first mixing channel 43 and the second mixing channel 46 by inflating or deflating the first drive channel 70.

[0027] Since the mixing of the first reagent and the sample provided by the first reagent addition unit 44 may not be uniform enough, it will affect the accuracy of subsequent optical detection. In this embodiment, by setting a first mixing channel 43 connected to the first sample inlet 10 and a second mixing channel 46 connected to the first optical detection unit 45, before optical detection, the first driver drives the sample and the first reagent to flow back and forth in the first mixing channel 43 and the second mixing channel 46 by inflating or deflating the first driving channel 70, thereby achieving the purpose of mixing the sample and the first reagent.

[0028] In the actual testing process, when the first driver inflates or aspirates the first driving channel 70 a certain number of times to mix the sample and the first reagent to a certain extent, the first driver inflates the first driving channel 70 to drive the mixed sample liquid to the first optical detection unit 45 for optical detection.

[0029] In some embodiments, the first optical detection unit 45 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.

[0030] Taking the detection of CRP (C-reactive protein) in blood cells as an example, during detection, the light source is turned on, and the light penetrates the upper transparent membrane and passes through the mixed sample solution in the first optical detection window. Blood cells in the mixed sample solution absorb the light under chemical reaction. After a certain degree of absorption by the blood cells, the light passes through the lower transparent membrane and is received by the light receiver. The controller detects the change curves of the incident light intensity and the transmitted light intensity, calculates the absorbance of the blood cells in the mixed sample solution, and can then further calculate the CRP index of the blood cells in the mixed sample solution. In some other embodiments, the first detection system 40 can also be used to detect the SAA (serum amyloid A) index of blood cells.

[0031] In some embodiments, after optical detection is completed, the first driver drives the mixed sample liquid to the first buffer pool 41 or the second buffer pool 42 by inflating the first drive channel 70 to collect it, so as to avoid waste liquid flowing out and causing pollution.

[0032] like Figure 5 As shown, in some embodiments, the chip body 100 further includes 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 inlet 10 and is used to quantify the sample input into the first detection system 40 from the first inlet 10. One end of the first sample delivery microchannel 102 is connected to the first sample quantification section 101, and the other end is connected to the first mixing channel 43. One end of the second sample delivery microchannel 103 is connected to the first sample quantification section 101, and the other end is connected to the first reagent addition section 44. 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 40 can be controlled to a certain volume. By controlling the amount of reagent input by the first reagent addition unit 44, the sample entering the first detection system 40 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.

[0033] like Figure 3 , Figure 9 and Figure 10As shown, in some embodiments, the first reagent addition unit 44 includes a first receiving portion 441, a first reagent pool 442, and a first reagent container 443. The first sample inlet 10 and the first optical detection unit 45 are connected to the first reagent pool 442. The first reagent container 443 is housed within the first receiving portion 441 and stores a first reagent. When the first reagent container 443 is pressed, the first reagent is injected into the first reagent pool 442. The first reagent pool 442 is located within the outline of the first receiving portion 441. In this embodiment, by placing the first reagent pool 442 within the outline of the first receiving portion 441, i.e., the first reagent pool 442 and the first receiving portion 441 share a structure, space utilization can be improved, thereby reducing the size of the microfluidic chip.

[0034] like Figure 9 and Figure 10 As shown, in some embodiments, the first receiving portion 441 includes a first sink portion 4411 and a first through-hole portion 4412. The first through-hole portion 4412 is disposed on the bottom surface of the sink portion 4411 and penetrates the chip body 100. The first reagent pool 442 is disposed on the bottom surface of the sink portion 4411 and spaced apart from the first through-hole portion 4412. The first reagent container 443 includes a first cup body 4431 and a first cup rim 4432. The first cup rim 4432 surrounds the opening end of the first cup body 4431 and is embedded in the first sink portion 4411. The first cup rim 4432 is provided with a first reagent delivery microchannel communicating with the first reagent pool 442. The first cup body 4431 is embedded in the first through-hole portion 4412 and communicates with the first reagent delivery microchannel.

[0035] Specifically, when the first reagent container 443 is not pressed, the first reagent in the first reagent container 443 cannot enter the first reagent pool 442 through the first reagent delivery microchannel. Only when the first reagent container 443 is pressed can the first reagent in the first reagent container 443 enter the first reagent pool 442 through the first reagent delivery microchannel.

[0036] like Figure 3 and Figure 4 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 43 and the second mixing channel 46 is disposed on the front side of the substrate 100a, and the other of the first mixing channel 43 and the second mixing channel 46 is disposed on the back side of the substrate 100a. In this embodiment, by disposing of one of the first mixing channel 43 and the second mixing channel 46 on the front side of the substrate 100a and the other of the first mixing channel 43 and the second 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.

[0037] In some embodiments, the first mixing channel 43 and the second 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.

[0038] like Figures 2 to 6 , Figure 11 As shown, in some embodiments, the second detection system 50 includes a first sheath flow section 51, a third buffer tank 52, a second reagent addition section 53, a second optical detection section 54, a third mixing channel 55, a first sheath fluid addition section 56, a first sheath fluid channel 57, a second sheath fluid channel 58, and a first waste liquid tank 59. The first sheath flow section 51 is provided with a first sample liquid inlet 51a, a first sheath fluid inlet 51b, a first auxiliary flow inlet 51c, a second auxiliary flow inlet 51d, and a first waste liquid outlet 51e. The third buffer tank 52 is connected to the second sample inlet 20. The second reagent addition section 53 is connected to the second sample inlet 20, and the first reagent addition section 44 is used to provide a second reagent mixed with the sample. The second optical detection section 54 is connected to the second reagent addition section 53, and the second optical detection section 54 is used to detect the mixture of the sample and the second reagent. The third mixing channel 55 connects the second optical detection section 54 and the first sample liquid inlet 51a. The first sheath fluid addition section 56 is used to provide sheath fluid to the first sheath flow section 51. The first sheath fluid channel 57 connects the first sheath fluid addition section 56 and the first sheath fluid inlet 51b. One end of the second sheath fluid channel 58 connects to the first sheath fluid addition section 56, and the other end connects to the first auxiliary flow inlet 51c and the second auxiliary flow inlet 51d. The first waste liquid tank 59 is connected to the first waste liquid outlet 51e and is used to receive waste liquid discharged from the first sheath flow section 51. The first end of the second drive channel 80 is connected to the third buffer tank 52. The second actuator drives the sample and reagents to reciprocate within the third mixing channel 55 by inflating or deflating the second drive channel 80.

[0039] Since the second reagent added by the second reagent addition unit 53 may not mix the sample and the sample evenly, it may affect the accuracy of optical detection. In this embodiment, by providing a third mixing channel 55 connected to the second optical detection unit 54, before optical detection, the second driver can drive the sample and the second reagent to flow back and forth in the third mixing channel 55 by inflating or deflating the second driving channel 80, thereby achieving the purpose of mixing the sample and the second reagent evenly.

[0040] Taking the second detection system 50 for detecting blood samples to obtain the hemoglobin index and white blood cell classification index of the blood sample as an example, the second reagent is a mixture of hemolysin and hemoglobin reagent, which can dissolve red blood cells and leave white blood cells. When the second driver inflates or inhales air into the second driving channel 80 a certain number of times to mix the sample with the second reagent to a certain extent, the second driver drives the mixed sample liquid into the second optical detection unit 54 through the second driving channel 80 for optical detection to obtain the hemoglobin index of the blood sample.

[0041] In some embodiments, the second optical detection unit 54 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 a 567nm LED light source, 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.

[0042] When detecting hemoglobin levels in blood cells, the light source is turned on. The light penetrates the upper transparent membrane and passes through the mixed sample solution in the second optical detection window. The dissolved blood cells in the mixed sample solution absorb the light under chemical reaction. After the light is absorbed to a certain extent by the dissolved 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 dissolved blood cells in the mixed sample solution. The hemoglobin level of the blood cells in the mixed sample solution can then be further calculated.

[0043] After the optical detection is completed, the second driver drives the mixed sample solution into the first sheath flow section 51 through the second drive channel 80. The remaining white blood cells in the mixed sample solution are then subjected to subsequent impedance detection through the first sheath flow section 51 to obtain the white blood cell classification index of the circulating blood.

[0044] like Figure 5As shown, 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 50 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 second reagent addition section 53. 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 third buffer 52. 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 50 can be controlled to a certain volume. By controlling the amount of reagent input by the second reagent addition unit 53, the sample entering the second detection system 50 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.

[0045] like Figure 3 , Figure 9 and Figure 10 As shown, in some embodiments, the second reagent addition unit 53 includes a second receiving portion 531, a second reagent pool 532, and a second reagent container 533. The second sample inlet 20 and the second optical detection unit 54 are connected to the second reagent pool 532. The second reagent container 533 is housed within the second receiving portion 531 and stores a second reagent. When the second reagent container 533 is pressed, the second reagent is injected into the second reagent pool 532. The second reagent pool 532 is located within the outline of the second receiving portion 531. In this embodiment, by placing the second reagent pool 532 within the outline of the second receiving portion 531, i.e., by having the second reagent pool 532 and the second receiving portion 531 share a structure, space utilization can be improved, thereby reducing the size of the microfluidic chip.

[0046] like Figure 9 and Figure 10As shown, in some embodiments, the second receiving portion 531 includes a second sink portion 5311 and a second through-hole portion 5312. The second through-hole portion 5312 is disposed on the bottom surface of the sink portion 5311 and penetrates the chip body 100. The second reagent pool 532 is disposed on the bottom surface of the sink portion 5311 and spaced apart from the second through-hole portion 5312. The second reagent container 533 includes a second cup body 5331 and a second cup rim 5332. The second cup rim 5332 surrounds the opening end of the second cup body 5331 and is embedded in the second sink portion 5311. The second cup rim 5332 is provided with a second reagent delivery microchannel communicating with the second reagent pool 532. The second cup body 5331 is embedded in the second through-hole portion 5312 and communicates with the second reagent delivery microchannel.

[0047] Specifically, when the second reagent container 533 is not pressed, the second reagent in the second reagent container 533 cannot enter the second reagent pool 532 through the second reagent delivery microchannel. Only when the second reagent container 533 is pressed can the second reagent in the second reagent container 533 enter the second reagent pool 532 through the second reagent delivery microchannel.

[0048] like Figure 5 and Figure 6 As shown, in some embodiments, the chip body 100 includes a substrate 100a, which has a front side and a back side. A third mixing channel 55 is partially disposed on the front side of the substrate 100a and partially disposed on the back side of the substrate 100a. In this embodiment, by partially disposing the third mixing channel 55 on the front side of the substrate 100a and partially disposing it 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.

[0049] In some embodiments, the third mixing channel 55 located on the front side of the substrate 100a and the third mixing channel 55 located on the back side of the substrate 100a are disposed opposite to each other in the thickness direction of the substrate 100a. In this embodiment, the space utilization of the substrate 100a can be improved, and the integration and miniaturization of the microfluidic chip can be realized.

[0050] like Figures 4 to 6 , Figure 11As shown, in some embodiments, the first sheath flow section 51 includes a first gemstone hole 511, a first laminar flow channel 512, and a first auxiliary flow channel 513. The first laminar flow channel 512 and the first auxiliary flow channel 513 are located on both sides of the first gemstone hole 511, and the first laminar flow channel 512, the first gemstone hole 511, and the first auxiliary flow channel 513 form an hourglass structure. The first sample liquid inlet 51a and the first sheath liquid inlet 51b are connected to the first laminar flow channel 512, and the first auxiliary flow inlet 51c, the second auxiliary flow inlet 51d, and the first waste liquid outlet 51e are connected to the first auxiliary flow channel 513.

[0051] like Figures 4 to 6 , Figure 11 As shown, in some embodiments, the first sheath flow section 51 further includes a first guide section 514, a first branch channel 515, and a second branch channel 516. The first guide section 514 is disposed in the middle of the first laminar flow channel 512, and the first guide section 514 is provided with a first guide groove 5141. One end of the first guide groove 5141 is connected to the first sample liquid inlet 51a, and the other end of the first guide groove 5141 extends toward the first gemstone hole 511. The first sheath liquid inlet 51b is disposed on the side of the first sample liquid inlet 51a opposite to the first gemstone hole 511. One end of the first branch channel 515 and one end of the second branch channel 516 are connected to the first sample liquid inlet 51a, and the other ends of the first branch channel 515 and the second branch channel 516 are connected to the first laminar flow channel 512. The first guide section 514 is located between the first branch channel 515 and the second branch channel 516.

[0052] like Figures 4 to 6 , Figure 11 As shown, in some embodiments, the first sheath flow section 51 further includes a third branch channel 517 and a fourth branch channel 518. One end of the third branch channel 517 is connected to the first auxiliary flow inlet 51c, and the other end of the third branch channel 517 is connected to the first auxiliary flow groove 513. One end of the fourth branch channel 518 is connected to the second auxiliary flow inlet 51d, and the other end of the fourth branch channel 518 is connected to the first auxiliary flow groove 513. The first sapphire hole 511 is located between the third branch channel 517 and the fourth branch channel 518.

[0053] In some embodiments, the microfluidic chip further includes a first electrode and a second electrode, the first electrode being disposed in a first laminar flow channel 512 and the second electrode being disposed in a first auxiliary flow channel 513.

[0054] Taking the first sheath flow section 51 as an example, which uses sheath flow technology to detect the impedance of blood cells to determine the white blood cell classification index, the detection process is as follows: The third mixing channel 55 receives a mixed sample solution after the red blood cells have been dissolved, leaving only white blood cells. This mixed sample solution enters the first guide channel 5141 from the first sample solution inlet 51a. Simultaneously, the first sheath fluid addition section 56 is squeezed, injecting the first sheath fluid into the first sheath fluid channel 57 and the second sheath fluid channel 58. The first sheath fluid in the first sheath fluid channel 57 enters the first sheath flow section 51 from the first sheath fluid inlet 51b, and then enters the first branch channel 515 and the second branch channel 516 respectively. The sheath fluid in the first branch channel 515 and the second branch channel 516 encapsulates the white blood cells exiting the first guide channel 5141 and flows together towards the first gem hole 511. According to the impedance counting principle, when white blood cells pass through the first gem hole 511, the conductivity between the first electrode and the second electrode changes, that is, the resistance value changes. Therefore, the impedance detection electrode can statistically count the changed peak value to obtain the white blood cell classification index of the blood flowing in the second detection system 50. The sheath fluid flowing in the first branch channel 515 and the sheath fluid flowing in the second branch channel 516 can serve as the laminar flow source for sheath flow technology, ensuring the normal operation of sheath flow detection. While the first sheath fluid addition section 56 is compressed, it injects the first sheath fluid into the second sheath fluid channel 58. The first sheath fluid in the second sheath fluid channel 58 enters the first sheath flow section 51 from the first auxiliary flow inlet 51c and the second auxiliary flow inlet 51d. The first sheath fluid entering from the first auxiliary flow inlet 51c enters the third branch channel 517, and the first sheath fluid entering from the second auxiliary flow inlet enters the fourth branch channel 518. These two portions of first sheath fluid enter the first auxiliary flow tank 513, maintaining the stability of the flow field within the first auxiliary flow tank 513 and preventing turbulence in the mixture, which could affect the flow of the mixture from the first laminar flow tank 512 to the first auxiliary flow tank 513. After completing the impedance detection, the second driver inputs gas into the second detection system 50 through the second drive channel 80 to drive the waste liquid in the first sheath flow section 51 to the first waste liquid pool 59 for centralized treatment, so as to avoid the waste liquid flowing out and causing pollution.

[0055] In some embodiments, the aperture of the first sapphire aperture 511 is 0.02 mm to 1 mm. By controlling the size of the first sapphire aperture 511 within this range, the manufacturing process difficulty is controlled, while also being compatible with the cell volume of white blood cells, meeting the requirements for white blood cell detection. This ensures that the white blood cells emitted through the first sapphire aperture 511 maintain a relatively ordered crystalline silicon structure, guaranteeing the accuracy of blood cell detection. Preferably, the aperture of the first sapphire aperture 511 is 0.1 mm.

[0056] like Figure 5 and Figure 6As shown, in some embodiments, the chip body 100 includes a substrate 100a, which has a front side and a back side. A first sheath fluid channel 57 and a second sheath fluid channel 58 are disposed on the front side of the substrate 100a, and a first sheath flow portion 51 is disposed on the back side of the substrate 100a. In this embodiment, by disposing the first sheath fluid channel 57 and the second sheath fluid channel 58 on the front side of the substrate 100a and the first sheath flow portion 51 on the back side of the substrate 100a, the space of the substrate 100a is utilized as much as possible, thereby achieving the integration and miniaturization of the microfluidic chip.

[0057] like Figure 3 , Figure 9 and Figure 10 As shown, in some embodiments, the first sheath fluid addition unit 56 includes a first receiving portion 561, a first sheath fluid pool 562, a second sheath fluid pool 563, and a first sheath fluid container 564. A first sheath fluid channel 57 communicates with the first sheath fluid pool 562. A second sheath fluid channel 58 communicates with the second sheath fluid pool 563. The first sheath fluid container 564 is housed within the first receiving portion 561 and stores the first sheath fluid. When the first sheath fluid container 564 is pressed, it injects the first sheath fluid into the first sheath fluid pool 562 and the second sheath fluid pool 563. The first sheath fluid pool 562 and the second sheath fluid pool 563 are located within the outline of the first receiving portion 561. In this embodiment, by placing the first sheath fluid pool 562 and the second sheath fluid pool 563 within the outline of the first receiving portion 561, i.e., sharing a structure with the first receiving portion 561, space can be rationally utilized, achieving the integration and miniaturization of the microfluidic chip.

[0058] like Figure 9 and Figure 10 As shown, in some embodiments, the first receiving portion 561 includes a first recess portion 5611, a first receiving hole portion 5612 and a second receiving hole portion 5613. The first receiving hole portion 5612 and the second receiving hole portion 5613 are disposed on the bottom surface of the first recess portion 5611 and penetrate the chip body 100. The first sheath fluid pool 562 and the second sheath fluid pool 563 are disposed on the bottom surface of the first recess portion 5611. The first sheath fluid container 564 includes a first cavity 5641, a second cavity 5642, and a first cavity edge 5643. The first cavity edge 5643 surrounds the opening ends of the first cavity 5641 and the second cavity 5642. The first cavity edge 5643 is embedded in a first groove portion 5611. The first cavity edge 5643 is provided with a first sheath fluid delivery microchannel communicating with the first sheath fluid pool 562 and a second sheath fluid delivery microchannel communicating with the second sheath fluid pool 563. The first cavity 5641 is embedded in a first receiving hole 5612 and communicates with the first sheath fluid delivery microchannel. The second cavity 5642 is embedded in a second receiving hole portion 5613 and communicates with the second sheath fluid delivery microchannel.

[0059] Specifically, when the first sheath fluid container 564 is not pressed, the first sheath fluid in the first sheath fluid container 564 cannot enter the first sheath fluid pool 562 through the first sheath fluid delivery microchannel, and the first sheath fluid in the first sheath fluid container 564 cannot enter the second sheath fluid pool 563 through the second sheath fluid delivery microchannel. Only when the first sheath fluid container 564 is pressed can the first sheath fluid in the first sheath fluid container 564 enter the first sheath fluid pool 562 through the first sheath fluid delivery microchannel, and the first sheath fluid in the first sheath fluid container 564 enter the second sheath fluid pool 563 through the second sheath fluid delivery microchannel.

[0060] like Figures 2 to 8 , Figure 11 As shown, in some embodiments, the third detection system 60 includes a second sheath flow section 61, a third reagent addition section 62, a fourth mixing channel 63, a fifth mixing channel 64, a second sheath fluid addition section 65, a third sheath fluid channel 66, a fourth sheath fluid channel 67, and a second waste liquid pool 68. The second sheath flow section 61 includes a second sample liquid inlet 61a, a second sheath fluid inlet 61b, a third auxiliary flow inlet 61c, a fourth auxiliary flow inlet 61d, and a second waste liquid outlet 61e. The third reagent addition section 62 is connected to the third sample inlet 30 and is used to provide a third reagent mixed with the sample. The fourth mixing channel 63 is connected to the third reagent addition section 62. The fifth mixing channel 64 is connected to the third sample inlet 30 and the second sample liquid inlet 61a. The second sheath fluid addition section 65 is used to provide sheath fluid to the second sheath flow section 61. The third sheath fluid channel 66 is connected to the second sheath fluid addition section 65 and the second sheath fluid inlet 61b. One end of the fourth sheath fluid channel 67 is connected to the second sheath fluid addition section 65, and the other end of the fourth sheath fluid channel 67 is connected to the third auxiliary flow inlet 61c and the fourth auxiliary flow inlet 61d. The second waste liquid pool 68 is connected to the second waste liquid outlet 61e and is used to receive the waste liquid discharged from the second sheath flow section 61. The first end of the third drive channel 90 is connected to the fourth mixing channel 63. The third actuator drives the sample and reagent to reciprocate within the fourth mixing channel 63 and the fifth mixing channel 64 by inflating or deflating the third drive channel 90.

[0061] Since the mixing of the third reagent and the sample provided by the third reagent addition unit 62 may not be uniform enough, it will affect the accuracy of optical detection. In this embodiment, by setting a fourth mixing channel 63 connected to the third reagent addition unit 62 and a fifth mixing channel 64 connected to the third sample inlet 30, before optical detection, the third driver drives the sample and the third reagent to flow back and forth in the fourth mixing channel and the fifth mixing channel 64 by inflating or deflating the third driving channel 90, thereby achieving the purpose of mixing the sample and the third reagent.

[0062] Taking the third detection system 60 for detecting blood samples to obtain the red blood cell index and platelet index of the blood sample as an example, after the sample and the third reagent are mixed evenly, a mixed sample solution is obtained. The mixed sample solution flows through the fifth mixing channel 64 to the second sheath flow section 61 for impedance detection to obtain the red blood cell index and platelet index.

[0063] like Figure 5 As shown, in some embodiments, the chip body 100 further includes a third sample quantification section 107, a fifth sample delivery microchannel 108, and a sixth sample delivery microchannel 109. The third sample quantification section 107 is connected to the third inlet 30 and is used to quantify the sample input into the third detection system 60 from the third inlet 30. One end of the fifth sample delivery microchannel 108 is connected to the third sample quantification section 107, and the other end is connected to the third reagent addition section 62. One end of the sixth sample delivery microchannel 109 is connected to the third sample quantification section 107, and the other end is connected to the fifth mixing channel 64. Optionally, the fifth sample delivery microchannel 108 and the sixth sample delivery microchannel 109 are capillary structures. In this embodiment, by providing the third sample quantification unit 107, the amount of sample entering the third detection system 60 can be controlled to a certain volume. By controlling the amount of reagent input by the third reagent addition unit 62, the sample entering the third detection system 60 can be diluted to a specified concentration, thereby improving the detection effect. In some embodiments, the volume of the third sample quantification unit 107 is 0.5 μL.

[0064] like Figure 3 , Figure 9 and Figure 10 As shown, in some embodiments, the third reagent addition unit 62 includes a third receiving portion 621, a third reagent pool 622, and a third reagent container 623. The third reagent pool 622 is connected to the third sample inlet 30. The third reagent container 623 is housed within the third receiving portion 621 and stores a third reagent. When the third reagent container 623 is pressed, the third reagent is injected into the third reagent pool 622. The third reagent pool 622 is disposed within the outline of the third receiving portion 621. In this embodiment, by placing the third reagent pool 622 within the outline of the third receiving portion 621, i.e., the third reagent pool 622 and the third receiving portion 621 share a structure, space utilization can be improved, thereby reducing the size of the microfluidic chip.

[0065] like Figure 9 and Figure 10As shown, in some embodiments, the third receiving portion 621 includes a third sink portion 6211 and a third through-hole portion 6212. The third through-hole portion 6212 is disposed on the bottom surface of the third sink portion 6211 and penetrates the chip body 100. The third reagent pool 622 is disposed on the bottom surface of the third sink portion 6211 and spaced apart from the third through-hole portion 6212. The third reagent container 623 includes a third cup body 6231 and a third cup rim 6232. The third cup rim 6232 surrounds the opening end of the third cup body 6231 and is embedded in the third sink portion 6211. The third cup rim 6232 is provided with a third reagent delivery microchannel communicating with the third reagent pool 622. The third cup body 6231 is embedded in the third through-hole portion 6212 and communicates with the third reagent delivery microchannel.

[0066] Specifically, when the third reagent container 623 is not pressed, the third reagent in the third reagent container 623 cannot enter the third reagent pool 622 through the third reagent delivery microchannel. Only when the third reagent container 623 is pressed can the third reagent in the third reagent container 623 enter the third reagent pool 622 through the third reagent delivery microchannel.

[0067] 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. A fourth mixing channel 63 is partially disposed on the front side of the substrate 100a and partially disposed on the back side of the substrate 100a. In this embodiment, by partially disposing the fourth mixing channel 63 on the front side of the substrate 100a and partially disposing it 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.

[0068] In some embodiments, the fourth mixing channel 63 located on the front side of the substrate 100a and the fourth mixing channel 63 located on the back side of the substrate 100a are disposed opposite to each other in the thickness direction of the substrate 100a. In this embodiment, the space utilization of the substrate 100a can be improved, and the integration and miniaturization of the microfluidic chip can be realized.

[0069] like Figure 3 , Figure 4 , Figure 7 and Figure 8As shown, in some embodiments, the chip body 100 further includes a cover plate 100b, which covers the front side of the substrate 100a, and a fifth mixing channel 64 is disposed on the cover plate 100b. In this embodiment, by disposing the fifth mixing channel 64 on the cover plate 100b, the space utilization of the chip body 100 is improved, achieving the integration and miniaturization of the microfluidic chip. Furthermore, the cover plate 100b can prevent external impacts on the microfluidic chip during transportation or before use, thus preventing 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.

[0070] like Figures 4 to 6 , Figure 11 As shown, in some embodiments, the second sheath flow section 61 includes a second sapphire hole 611, a second laminar flow channel 612, and a second auxiliary flow channel 613. The second laminar flow channel 612 and the second auxiliary flow channel 613 are located on both sides of the second sapphire hole 611 and communicate with the second sapphire hole 611. The second laminar flow channel 612, the second sapphire hole 611, and the second auxiliary flow channel 613 form an hourglass structure. The second sample liquid inlet 61a and the second sheath liquid inlet 61b communicate with the second laminar flow channel 612, and the third auxiliary flow inlet 61c, the fourth auxiliary flow inlet 61d, and the second waste liquid outlet 61e communicate with the second auxiliary flow channel 613.

[0071] like Figures 4 to 6 , Figure 11 As shown, in some embodiments, the second sheath flow section 61 further includes a second guide section 614, a fifth branch channel 615, and a sixth branch channel 616. The second guide section 614 is disposed in the middle of the second laminar flow channel 612, and the second guide section 614 is provided with a second guide channel 6141. One end of the second guide channel 6141 is connected to the second sample liquid inlet 61a, and the other end of the second guide channel 6141 extends toward the second gem hole 611. The second sheath liquid inlet 61b is disposed on the side of the second sample liquid inlet 61a opposite to the second gem hole 611. One end of the fifth branch channel 615 and one end of the sixth branch channel 616 are connected to the second sample liquid inlet 61a, and the other ends of the fifth branch channel 615 and the sixth branch channel 616 are connected to the second laminar flow channel 612. The second guide section 614 is located between the fifth branch channel 615 and the sixth branch channel 616.

[0072] like Figures 4 to 6 , Figure 11As shown, in some embodiments, the second sheath flow section 61 further includes a seventh branch channel 617 and an eighth branch channel 618. One end of the seventh branch channel 617 is connected to the third auxiliary flow inlet 61c, and the other end of the seventh branch channel 617 is connected to the second auxiliary flow groove 613. One end of the eighth branch channel 618 is connected to the fourth auxiliary flow inlet 61d, and the other end of the eighth branch channel 618 is connected to the second auxiliary flow groove 613. The second sapphire hole 611 is located between the seventh branch channel 617 and the eighth branch channel 618.

[0073] In some embodiments, the microfluidic chip further includes a third electrode and a fourth electrode, the third electrode being disposed in the second laminar flow channel 612 and the fourth electrode being disposed in the second auxiliary flow channel 613.

[0074] Taking the first sheath flow section 51 as an example, which uses sheath flow technology to detect the impedance of blood cells to determine the red blood cell and platelet indices, the detection process is as follows: The fifth mixing channel 64 receives the mixed sample solution, which enters the second guide channel 6141 from the second sample solution inlet 61a. Simultaneously, the second sheath fluid addition section 65, after being squeezed, injects the second sheath fluid into the third sheath fluid channel 66 and the fourth sheath fluid channel 67. The second sheath fluid in the third sheath fluid channel 66 enters the second sheath flow section 61 from the second sheath fluid inlet 61b, and then enters the fifth branch channel 615 and the sixth branch channel 616 respectively. The sheath fluid in the fifth branch channel 615 and the sixth branch channel 616 encapsulates the red blood cells and platelets exiting from the second guide channel 6141 and flows together towards the second gem hole 611. According to the impedance counting principle, when red blood cells and platelets pass through the second gem hole 611, the conductivity between the third electrode and the fourth electrode will change, that is, the resistance value will change. Therefore, the impedance detection electrode can count and count the peak values ​​of the change, and detect the red blood cell index and platelet index of the blood flowing in the third detection system 60. The second sheath fluid flowing in the fifth branch channel 615 and the sheath fluid flowing in the sixth branch channel 616 can serve as the laminar flow source for sheath flow technology, ensuring the normal operation of sheath flow detection. While the second sheath fluid addition section 65 is compressed, it injects the first sheath fluid into the fourth sheath fluid channel 67. The second sheath fluid in the fourth sheath fluid channel 67 enters the second sheath flow section 61 from the third auxiliary flow inlet 61c and the fourth auxiliary flow inlet 61d. The second sheath fluid entering from the third auxiliary flow inlet 61c enters the seventh branch channel 617, and the second sheath fluid entering from the fourth auxiliary flow inlet enters the eighth branch channel 618. These two sections of second sheath fluid enter the second auxiliary flow channel 613, maintaining the stability of the flow field within the second auxiliary flow channel 613 and preventing turbulence in the mixture, which could affect the flow of the mixture from the second laminar flow channel 612 to the second auxiliary flow channel 613. After completing the impedance detection, the third driver inputs gas into the third detection system 60 through the third drive channel 90 to drive the waste liquid in the second sheath flow section 61 to the second waste liquid pool 68 for centralized treatment, so as to avoid the waste liquid flowing out and causing pollution.

[0075] In some embodiments, the aperture of the second sapphire aperture 611 is 0.02 mm to 1 mm. By controlling the size of the second sapphire aperture 611 within this range, the manufacturing process difficulty is controlled, while also being compatible with the cell volume of red blood cells and platelets, meeting the requirements for detecting red blood cells and platelets. This ensures that the red blood cells and platelets ejected through the second sapphire aperture 611 maintain a relatively ordered crystalline silicon structure, guaranteeing the accuracy of blood cell detection. Preferably, the aperture of the second sapphire aperture 611 is 0.07 mm.

[0076] like Figure 5 and Figure 6As shown, in some embodiments, the chip body 100 includes a substrate 100a, which has a front side and a back side. A third sheath fluid channel 66 and a fourth sheath fluid channel 67 are disposed on the front side of the substrate 100a, and a second sheath flow portion 61 is disposed on the back side of the substrate 100a. In this embodiment, by disposing the third sheath fluid channel 66 and the fourth sheath fluid channel 67 on the front side of the substrate 100a and the second sheath flow portion 61 on the back side of the substrate 100a, the space of the substrate 100a is utilized as much as possible, thereby achieving the integration and miniaturization of the microfluidic chip.

[0077] like Figure 3 , Figure 9 and Figure 10 As shown, in some embodiments, the second sheath fluid adding unit 65 includes a second receiving portion 651, a third sheath fluid pool 652, a fourth sheath fluid pool 653, and a second sheath fluid container 654. A third sheath fluid channel 66 communicates with the third sheath fluid pool 652. A fourth sheath fluid channel 67 communicates with the fourth sheath fluid pool 653. The second sheath fluid container 654 is housed in the second receiving portion 651 and stores second sheath fluid. When the second sheath fluid container 654 is pressed, it injects the second sheath fluid into the third sheath fluid pool 652 and the fourth sheath fluid pool 653. The third sheath fluid pool 652 and the fourth sheath fluid pool 653 are located within the outline of the second receiving portion 651. In this embodiment, by setting the third sheath fluid pool 652 and the fourth sheath fluid pool 653 within the outline of the second accommodating portion 651, that is, by having the third sheath fluid pool 652 and the fourth sheath fluid pool 653 share a structure with the second accommodating portion 651, space can be rationally utilized to achieve the integration and miniaturization of the microfluidic chip.

[0078] like Figure 9 and Figure 10 As shown, in some embodiments, the second receiving portion 651 includes a second recess portion 6511, a third receiving hole portion 6512 and a fourth receiving hole portion 6513. The third receiving hole portion 6512 and the fourth receiving hole portion 6513 are disposed on the bottom surface of the second recess portion 6511 and penetrate the chip body 100. The third sheath fluid pool 652 and the fourth sheath fluid pool 653 are disposed on the bottom surface of the second recess portion 6511. The second sheath fluid container 654 includes a third cavity 6541, a fourth cavity 6542, and a second cavity edge 6543. The second cavity edge 6543 surrounds the opening ends of the third cavity 6541 and the fourth cavity 6542. The second cavity edge 6543 is embedded in the second groove portion 6511. The second cavity edge 6543 is provided with a third sheath fluid delivery microchannel 6544 communicating with the third sheath fluid pool 652 and a fourth sheath fluid delivery microchannel 6545 communicating with the fourth sheath fluid pool 653. The third cavity 6541 is embedded in the third receiving hole portion 6512 and communicates with the third sheath fluid delivery microchannel 6544. The fourth cavity 6542 is embedded in the fourth receiving hole portion 6513 and communicates with the fourth sheath fluid delivery microchannel 6545.

[0079] Specifically, when the second sheath fluid container 654 is not pressed, the second sheath fluid in the second sheath fluid container 654 cannot enter the third sheath fluid pool 652 through the third sheath fluid delivery microchannel 6544, nor can it enter the fourth sheath fluid pool 653 through the fourth sheath fluid delivery microchannel 6545. Only when the second sheath fluid container 654 is pressed can the second sheath fluid in the second sheath fluid container 654 enter the third sheath fluid pool 652 through the third sheath fluid delivery microchannel 6544, and only then can the second sheath fluid in the second sheath fluid container 654 enter the fourth sheath fluid pool 653 through the fourth sheath fluid delivery microchannel 6545.

[0080] 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 in that, It includes a second sheath flow section, a second sheath fluid addition section, a third sheath fluid channel, a fourth sheath fluid channel, and a second waste liquid pool; The second sheath flow section is provided with a second sample liquid inlet, a second sheath liquid inlet, a third auxiliary flow inlet, a fourth auxiliary flow inlet, a second waste liquid outlet, a second sapphire hole, a second laminar flow channel, and a second auxiliary flow channel; The second laminar flow channel and the second auxiliary flow channel are located on both sides of the second gem hole and are connected to the second gem hole. The second laminar flow channel, the second gem hole and the second auxiliary flow channel form an hourglass structure. The second sample liquid inlet and the second sheath liquid inlet are connected to the second laminar flow channel, and the third auxiliary flow inlet, the fourth auxiliary flow inlet and the second waste liquid outlet are connected to the second auxiliary flow channel; The second sheath fluid addition section is used to supply sheath fluid to the second sheath flow section; The third sheath fluid channel connects the second sheath fluid addition section and the second sheath fluid inlet; One end of the fourth sheath fluid channel is connected to the second sheath fluid addition section, and the other end of the fourth sheath fluid channel is connected to the third auxiliary flow inlet and the fourth auxiliary flow inlet; The second waste liquid tank is connected to the second waste liquid outlet, and the second waste liquid tank is used to receive the waste liquid discharged from the second sheath flow section.

2. The microfluidic chip as described in claim 1, characterized in that, The second sheath flow section also includes a second guide section, a fifth branch channel, and a sixth branch channel; The second flow guide is disposed in the middle of the second laminar flow channel. The second flow guide is provided with a second flow channel. One end of the second flow channel is connected to the second sample liquid inlet, and the other end of the second flow channel extends toward the second gemstone hole. The second sheath fluid inlet is located on the side of the second sample fluid inlet opposite to the second gemstone hole. One end of the fifth branch channel and one end of the sixth branch channel are connected to the second sample fluid inlet. The other end of the fifth branch channel and the other end of the sixth branch channel are connected to the second laminar flow channel. The second flow guide is located between the fifth branch channel and the sixth branch channel.

3. The microfluidic chip as described in claim 1, characterized in that, The second sheath flow section further includes a seventh branch channel and an eighth branch channel. One end of the seventh branch channel is connected to the third auxiliary flow inlet, and the other end of the seventh branch channel is connected to the second auxiliary flow groove. One end of the eighth branch channel is connected to the fourth auxiliary flow inlet, and the other end of the eighth branch channel is connected to the second auxiliary flow groove. The second sapphire hole is located between the seventh branch channel and the eighth branch channel.

4. The microfluidic chip as described in claim 1, characterized in that, The microfluidic chip also includes a third electrode and a fourth electrode, the third electrode being disposed in the second laminar flow channel and the fourth electrode being disposed in the second auxiliary flow channel.

5. The microfluidic chip as described in claim 1, characterized in that, The diameter of the second gem hole is 0.02 mm to 1 mm.

6. The microfluidic chip as described in claim 1, characterized in that, The chip body includes a substrate, which has a front side and a back side. The third sheath fluid channel and the fourth sheath fluid channel are disposed on the front side of the substrate, and the second sheath fluid flow portion is disposed on the back side of the substrate.

7. The microfluidic chip as described in claim 1, characterized in that, The second sheath fluid addition section includes a second accommodating section, a third sheath fluid pool, a fourth sheath fluid pool, and a second sheath fluid container; The third sheath fluid channel is connected to the third sheath fluid pool; The fourth sheath fluid channel is connected to the fourth sheath fluid pool; The second sheath fluid container is housed in the second receiving portion, and the second sheath fluid container stores the second sheath fluid. When the second sheath fluid container is pressed, the second sheath fluid is injected into the third sheath fluid pool and the fourth sheath fluid pool; wherein the third sheath fluid pool and the fourth sheath fluid pool are located within the outline of the second receiving portion.

8. The microfluidic chip as described in claim 7, characterized in that, The second receiving portion includes a second recessed portion, a third receiving hole portion, and a fourth receiving hole portion. The third receiving hole portion and the fourth receiving hole portion are disposed on the bottom surface of the second recessed portion and penetrate the chip body. The third sheath fluid pool and the fourth sheath fluid pool are disposed on the bottom surface of the second recessed portion. The second sheath fluid container includes a third cavity, a fourth cavity, and a second cavity edge. The second cavity edge surrounds the opening ends of the third cavity and the fourth cavity. The second cavity edge is embedded in the second groove. The second cavity edge is provided with a third sheath fluid delivery microchannel communicating with the third sheath fluid pool and a fourth sheath fluid delivery microchannel communicating with the fourth sheath fluid pool. The third cavity is embedded in the third receiving hole and communicates with the third sheath fluid delivery microchannel. The fourth cavity is embedded in the fourth receiving hole and communicates with the fourth sheath fluid delivery microchannel.

9. The microfluidic chip as described in claim 1, characterized in that, The microfluidic chip further includes a third reagent addition section, a fourth mixing channel, and a fifth mixing channel; the third reagent addition section is connected to the third sample inlet of the microfluidic chip and is used to provide a third reagent for mixing with the sample; the fourth mixing channel is connected to the third reagent addition section; the fifth mixing channel is connected to the third sample inlet and the second sample liquid inlet.

10. The microfluidic chip as described in claim 9, characterized in that, The chip body is also provided with a third sample quantification section, a fifth sample delivery microchannel and a sixth sample delivery microchannel; The third sample quantification unit is connected to the third sample inlet of the microfluidic chip, and the third sample quantification unit is used to quantify the sample input into the third detection system from the third sample inlet; One end of the fifth sample delivery microchannel is connected to the third sample quantification section, and the other end of the fifth sample delivery microchannel is connected to the third reagent addition section; One end of the sixth sample delivery microchannel is connected to the third sample quantification section, and the other end of the sixth sample delivery microchannel is connected to the fifth mixing channel.

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