Ssepsis instant detection equipment based on microfluidic technology

Abstract

The invention relates to the field of sepsis detection, in particular to sepsis instant detection equipment based on a microfluidic technology, which comprises a base, a chip arranged on the upper end face of the base and a detection assembly arranged on one side, close to an air hole, of a runner groove, the chip comprises an inner core, and a first diaphragm and a second diaphragm covering the upper end face and the lower end face of the inner core, a runner groove penetrating through the two end faces is formed in the surface of the inner core, one end of the runner groove is connected with a feeding pipe, the other end of the runner groove is connected with an air hole, protruding parts are fixed to the surfaces of the sides, facing the inner core, of the first diaphragm and the second diaphragm, and when the second diaphragm and the first diaphragm cover the surface of the inner core, the protruding parts are inserted into the runner groove to form a runner. The detection assembly detects fluid at the tail of the flow channel. According to the invention, a multi-layer embedding mode is adopted to form a flow channel in the micro-fluidic chip in a pressing mode, sealing can be realized only by pressing the membrane I, the inner core and the membrane II, and during disassembly, the membrane I, the inner core and the membrane II can be directly stripped, so that the interior is convenient to clean.

Description

Technical Field

[0001] The present invention relates to the field of sepsis detection, and in particular to a microfluidics-based instant sepsis detection device. Background Art

[0002] Sepsis is a systemic inflammatory response syndrome caused by infection, which is common in patients with severe trauma or infectious diseases. The causes of the disease include infections caused by bacteria, fungi, viruses and parasites, which lead to the body's inflammatory response and immune regulation imbalance.

[0003] Sepsis can be detected in many aspects. The concentration changes of various antibodies are commonly used for detection, such as procalcitonin, C-reactive protein, interleukin-6, etc. The faster the diagnosis result of sepsis, the higher the survival rate of the patient. In order to speed up the detection efficiency of sepsis, microfluidic technology is usually used in the prior art to speed up the detection speed. In order to maintain a good seal, the existing microfluidic chips are mostly one-time bonding designs without disassembly functions. In this case, only liquid can be passed to clean the inside. However, due to the narrow flow channel inside the microfluidic chip, it is easy to hide dirt and blockage, so the inside cannot be cleaned by passing liquid alone, which makes the microfluidic chip unable to be recycled and can only become a disposable product, resulting in a large overall consumption. Summary of the invention

[0004] The present invention aims at the deficiencies in the prior art and provides the following technical solutions: A microfluidics-based instant sepsis detection device comprises a base, a chip arranged on the upper end surface of the base, and a detection component arranged on a side of a flow channel groove close to an air hole.

[0005] Specifically, the chip includes an inner core and diaphragm 1 and diaphragm 2 covering the upper end surface and the lower end surface of the inner core. The surface of the inner core is provided with a flow channel groove penetrating the two end surfaces. One end of the flow channel groove is connected to a feeding pipe, and the other end of the flow channel groove is connected to an air hole. A protrusion is fixed on the surface of diaphragm 1 and diaphragm 2 facing the inner core. When diaphragm 2 and diaphragm 1 cover the surface of the inner core, the protrusion is inserted into the interior of the flow channel groove to form a flow channel, and the detection component detects the fluid at the tail of the flow channel.

[0006] As an improvement of the above technical solution, an edge sealing fence 1 is provided at the edge of the flow channel groove, an edge sealing fence 2 is provided on the outer side of the protrusion, a cavity is separated between the edge sealing fence 2 and the protrusion, and the edge sealing fence 1 is inserted into the cavity and fits the two side walls of the cavity.

[0007] As an improvement of the above technical solution, limited cavities are provided on both end surfaces of the inner core, and limited portions are integrally formed on the end surfaces of diaphragm 1 and diaphragm 2 close to the inner core. Ventilation grooves are provided through the surfaces of diaphragm 1, the inner core and diaphragm 2, and an air pressure regulating device is provided inside the venting grooves. When diaphragm 2 and diaphragm 1 are covered on the surface of the inner core, regulating cavities are separated between diaphragm 2 and the inner core, and between diaphragm 1 and the inner core. The air pressure regulating device reduces the air pressure inside the regulating cavity to drive diaphragm 2 and diaphragm 1 to squeeze the inner core.

[0008] As an improvement of the above technical solution, the air pressure regulating device includes a cannula and an adjusting bolt. The cannula is penetrated and fits the inner wall of the ventilation groove. One end of the cannula is fixedly connected to a sealing plate. The sealing plate closes one side of the ventilation groove of the diaphragm 2. Two positioning rings are fixed to the outside of the cannula. The surface of the positioning ring is provided with a through hole that penetrates into the interior of the cannula. The two positioning rings are respectively arranged inside two regulating chambers. The adjusting bolt is threadedly connected to the inner wall of the cannula. When the adjusting bolt is tightened, the air pressure inside the regulating chamber increases. When the adjusting bolt is loosened, the air pressure inside the regulating chamber decreases.

[0009] As an improvement of the above technical solution, the positioning ring is threadedly connected to the outer wall of the insert tube. When the positioning ring is tightened, the through hole of the positioning ring is connected with the through hole on the side wall of the insert tube. The end of the insert tube away from the sealing plate passes through the outer side of the diaphragm and is threadedly connected with a positioning sleeve. A communicating threaded cavity and a connecting groove are provided inside the positioning sleeve. The adjusting bolt is threadedly arranged inside the threaded cavity. A spring is arranged between the adjusting bolt and the end face of the positioning sleeve, and the connecting groove is connected with the insert tube.

[0010] As an improvement of the above technical solution, the feeding tube includes an insertion part, a liquid storage cylinder and a sealing part. The sealing part is arranged at the outer edge of the liquid inlet of the flow channel groove, and the inner side of the sealing part is integrally formed with an insertion part inserted into the liquid inlet. The liquid storage cylinder is threadedly connected to the inner wall of the sealing part.

[0011] As an improvement of the above technical solution, the base includes a bottom plate and a mounting shell covering the upper end surface of the bottom plate, a limit seat is provided on the end surface of the mounting shell away from the bottom plate, a flip pressure plate is provided on one side of the limit seat, a penetrating focusing groove is provided inside the limit seat, the detection component includes a light source module arranged on the upper end surface of the bottom plate and a photoelectric sensor module arranged on the lower end surface of the pressure plate, the light source module faces the focusing groove, and when a chip is placed inside the limit seat, the pressure plate flips to drive the photoelectric sensor module to cover the surface of the chip.

[0012] As an improvement of the above technical solution, a light shielding frame is arranged on the surface of the pressing plate, and the light shielding frame covers the surface of the light-sensitive side of the photoelectric sensor module.

[0013] As an improvement of the above technical solution, a movable track is provided on the upper end surface of the mounting shell and one side of the base, and a light blocking plate is provided inside the movable track. The light blocking plate covers the pressing plate, the limiting seat and the top of the chip.

[0014] As an improvement of the above technical solution, a display module is arranged on the upper end surface of the base, an overflow groove is opened on the upper end surface of the diaphragm 1, and the air hole is located inside the overflow groove.

[0015] Beneficial effects of the present invention: The flow channel inside the microfluidic chip is formed by pressing in a multi-layer interlocking manner. In subsequent use, it is only necessary to press membrane one, the inner core and membrane two to achieve closure. When disassembly is required, it can be directly peeled off. Therefore, after use, it can be opened for internal cleaning, which can effectively clean the interior and achieve recycling. In addition, in order to strengthen the closure of this modular design, negative pressure is further used to seal the interior. This can ensure that when in use, the liquid circulating inside will not flow out of the gap between the modules, thereby ensuring the closure of the overall structure. BRIEF DESCRIPTION OF THE DRAWINGS

[0016] Figure 1 It is a three-dimensional structural diagram of the present invention; Figure 2 It is the exploded structure diagram of the present invention; Figure 3 It is a three-dimensional structural diagram of the chip of the present invention; Figure 4 for Figure 2 The enlarged structure diagram at A in the middle; Figure 5 for Figure 2 The enlarged structure diagram at B in the middle; Figure 6 for Figure 2 The enlarged structure diagram at C in the middle; Figure 7 for Figure 5 The enlarged structure diagram at b1 in the middle; Figure 8 for Figure 6 The enlarged structure diagram at c1 in the middle; Fig. 9 It is a right side view of the chip of the present invention; Fig.10 for Figure 2 Isometric section view at AA; Fig.11 for Fig.10 The enlarged structure diagram at D in the middle; Fig.12A top view of the chip of the present invention; Fig.13 for Fig.12 Isometric section view at the middle BB; Fig.14 for Fig.13 Enlarged structural diagram at E in the middle.

[0017] Reference numerals: 10, base; 11, bottom plate; 111, light source module; 12, mounting shell; 121, moving track; 122, limiting seat; 123, focusing groove; 13, light blocking plate; 14, pressing plate; 141, photoelectric sensor module; 142, light shielding frame; 20, display module; 30, chip; 31, diaphragm 1; 311, air hole; 312, overflow groove; 32, inner core; 321, limiting cavity; 322, flow channel groove; 3 23. Edge sealing fence one; 33. Diaphragm two; 331. Limiting part; 332. Protruding part; 333. Edge sealing fence two; 34. Insertion tube; 341. Positioning ring; 342. Positioning sleeve; 3421. Threaded cavity; 3422. Connecting groove; 343. Sealing plate; 344. Adjusting cavity; 35. Adjusting plug; 351. Spring; 36. Feeding tube; 361. Sealing part; 362. Liquid storage cylinder; 363. Insertion part; 37. Ventilation groove. DETAILED DESCRIPTION

[0018] In order to make the purpose, technical solution and advantages of the present invention more clearly understood, the present invention is further described in detail below. It should be understood that the specific embodiments described herein are only used to explain the present invention and are not used to limit the present invention.

[0019] Sepsis can be detected in many aspects. The concentration changes of various antibodies are commonly used for detection, such as procalcitonin, C-reactive protein, interleukin-6, etc. The faster the diagnosis result of sepsis, the higher the survival rate of the patient. In order to speed up the detection efficiency of sepsis, microfluidic technology is usually used in the prior art to speed up the detection speed. In order to maintain a good seal, the existing microfluidic chips are mostly one-time bonding designs without disassembly functions. In this case, only liquid can be passed to clean the inside. However, due to the narrow flow channel inside the microfluidic chip, it is easy to hide dirt and blockage, so the inside cannot be cleaned by passing liquid alone, which makes the microfluidic chip unable to be recycled and can only become a disposable product, resulting in a large overall consumption.

[0020] To avoid the above problems, see Figures 1 to 8 , provides a microfluidic technology-based instant sepsis detection device, including: a base 10, a chip 30 arranged on the upper end surface of the base 10, and a detection component arranged on a side of a flow channel 322 close to a pore 311.

[0021] Specifically, the chip 30 includes an inner core 32 and diaphragm 1 31 and diaphragm 2 33 covering the upper end surface and the lower end surface of the inner core 32. The surface of the inner core 32 is provided with a flow channel 322 running through the two end surfaces. One end of the flow channel 322 is connected to a feeding pipe 36, and the other end of the flow channel 322 is connected to an air hole 311. A protrusion 332 is fixed on the surface of the diaphragm 1 31 and the diaphragm 2 33 on one side facing the inner core 32. When the diaphragm 2 33 and the diaphragm 1 31 cover the surface of the inner core 32, the protrusion 332 is inserted into the interior of the flow channel 322 to form a flow channel, and the detection component detects the fluid at the tail of the flow channel.

[0022] The membrane 1 31 and the membrane 2 33 are covered on the surface of the inner core 32, so that a modular embedded structure is formed. When the three are in close contact, the flow channel 322 is squeezed and closed, thereby forming a flow channel with only an inlet and an outlet. The inlet is where the liquid to be tested is injected, and the outlet is where the gas and excess liquid are discharged. When the liquid flows through the flow channel, the detection component will detect the change of the liquid. The change here refers to the change of color and brightness caused by the reaction between the antigen, antibody and marker. For example, when the "double antibody sandwich method" is used for detection: The target is combined with a specific antibody labeled with a luminescent substance to form a sandwich structure. A substrate is added to react with the luminescent substance to generate a chemiluminescent signal. Since the intensity of this signal is proportional to the target content, the content can be detected by only measuring the intensity of the luminescent signal.

[0023] In addition, to facilitate the operator to read, please refer to Figure 1 A display module 20 is disposed on the upper end surface of the base 10 , and the detection result is directly displayed through the display module 20 . The operator can read the result directly and perform touch operation through the display module 20 .

[0024] In the above scheme, only a simple embedded structure is used for connection. This may cause overflow in the gap of the connection position, which will lead to inaccurate final test results. To avoid this problem, please refer to Figures 1 to 8 An edge sealing fence 323 is provided at the edge of the flow channel 322, and an edge sealing fence 333 is provided on the outer side of the protrusion 332. A cavity is separated between the edge sealing fence 333 and the protrusion 332, and the edge sealing fence 323 is inserted into the cavity and fits the two side walls of the cavity.

[0025] By wrapping in the form of a fence, this structure can ensure the sealing effect at the connection, thereby ensuring that the liquid will not overflow from the inside of the flow channel when the liquid is injected, thereby ensuring the sealing of the inside of the flow channel.

[0026] In the above solution, if the pressure inside the flow channel changes greatly, the edge fence 1 323 and the edge fence 2 333 may be squeezed apart by the internal pressure, resulting in a gap at the connection. In this case, liquid leakage may also occur. To further solve this problem, please refer to Figures 1 to 11 , limit cavities 321 are provided at both end surfaces of the inner core 32, and a limit portion 331 is integrally formed on the end surfaces of one side of the diaphragm 1 31 and the diaphragm 2 33 close to the inner core 32. A through ventilation groove 37 is provided on the surfaces of the diaphragm 1 31, the inner core 32 and the diaphragm 2 33, and an air pressure regulating device is arranged inside the ventilation groove 37. When the diaphragm 2 33 and the diaphragm 1 31 are covered on the surface of the inner core 32, a regulating cavity 344 is separated between the diaphragm 2 33 and the inner core 32, and between the diaphragm 1 31 and the inner core 32. The air pressure regulating device reduces the air pressure inside the regulating cavity 344 to drive the diaphragm 2 33 and the diaphragm 1 31 to squeeze the inner core 32.

[0027] Two regulating chambers 344 are formed by separating between diaphragm 1 31, diaphragm 2 33 and inner core 32. When the air pressure regulating device reduces the air pressure inside the regulating chamber 344, the reduction in air pressure will cause diaphragm 1 31 and diaphragm 2 33 to continuously approach inner core 32. When the negative pressure reaches a certain level, the interior becomes sealed. In this case, it is only necessary to perform negative pressure adjustment before injecting liquid to ensure that no leakage occurs during specific testing.

[0028] Based on the records of the above-mentioned scheme, it can be known that in this embodiment, the optimal material for the inner core 32 is a hard material, usually a glass material, and for the diaphragm 1 31 and the diaphragm 2 33, the optimal material is a silicone material. Due to the compactness of the microfluidic chip structure, when silicone is used, while having certain deformation properties, it can ensure the stability of the overall structural morphology of the structure, avoiding the disadvantage of silicone being too soft.

[0029] In order to implement the above gas pressure regulation scheme, please refer to Figures 1 to 11 The air pressure regulating device includes a plug 34 and an adjusting bolt 35. The plug 34 is passed through and fits the inner wall of the ventilation groove 37. One end of the plug 34 is fixedly connected to a sealing plate 343. The sealing plate 343 closes one side of the ventilation groove 37 of the diaphragm 33. Two positioning rings 341 are fixed to the outer side of the plug 34. The surface of the positioning ring 341 is provided with a through hole that penetrates into the inside of the plug 34. The two positioning rings 341 are respectively arranged in the inside of two adjusting chambers 344. The adjusting bolt 35 is threadedly connected to the inner wall of the plug 34. When the adjusting bolt 35 is tightened, the air pressure inside the adjusting chamber 344 increases. When the adjusting bolt 35 is loosened, the air pressure inside the adjusting chamber 344 decreases.

[0030] The height positioning of the adjustment cavity 344 is provided by the positioning ring 341, and the thickness of the positioning ring 341 is the height of the adjustment cavity 344. When the adjustment bolt 35 is screwed inward, the volume in the cavity state is reduced, and the gas does not leak. In this case, the internal air pressure increases. When it is screwed in to a certain extent, the connection between the diaphragm 2 33, the diaphragm 1 31 and the inner core 32 that were originally in a closed state is disconnected. At this time, each component can be cleaned. When the adjustment bolt 35 is screwed outward, the volume in the cavity state is increased, and the gas does not leak. In this case, the internal air pressure decreases, and a negative pressure state is formed. If the inner core 32 is made of hard glass material, the diaphragm 1 31 and the diaphragm 2 33 will be squeezed toward the inner core 32. When it is screwed out to a certain extent, the connection between the diaphragm 1 31, the diaphragm 2 33 and the inner core 32 is completely closed, and liquid can be injected for detection.

[0031] Although the above solution can realize the connection of the structure, the overall solution is not easy to disassemble. If the elastic deformation of the diaphragm 1 31 and the diaphragm 2 33 of the silicone material is relied on, the sealing performance may become weaker and weaker. In order to avoid this situation, please refer to Figures 1 to 11 The positioning ring 341 is threadedly connected to the outer wall of the insert tube 34. When the positioning ring 341 is tightened, the through hole of the positioning ring 341 is connected to the through hole on the side wall of the insert tube 34. The end of the insert tube 34 away from the sealing plate 343 penetrates to the outer side of the diaphragm 31 and is threadedly connected to the positioning sleeve 342. The interior of the positioning sleeve 342 is provided with a connected threaded cavity 3421 and a connecting groove 3422. The adjusting bolt 35 is threadedly arranged inside the threaded cavity 3421. A spring 351 is arranged between the adjusting bolt 35 and the end face of the positioning sleeve 342. The connecting groove 3422 is connected to the insert tube 34.

[0032] That is, the positioning ring 341 and the positioning sleeve 342 are fixed by threads. When installing, first insert the diaphragm 2 33 into the insertion tube 34, and then screw in the first positioning ring 341 until it is completely tightened and the positioning ring 341 is connected to the through hole on the surface of the insertion tube 34. Then, insert the inner core 32 into the insertion tube 34 and align the corresponding edge sealing fence 1 323, edge sealing fence 2 333 and protrusion 332. Then screw in the second positioning ring 341, and also screw it until it is completely tightened and the positioning ring 341 is connected to the through hole on the surface of the insertion tube 34. , and then install the diaphragm 31, and finally tighten the positioning sleeve 342 on the outside. In the initial state, the adjusting bolt 35 needs to be completely screwed into the inside of the threaded cavity 3421, so that it can be ensured that when negative pressure is required, it can be achieved directly by loosening it outward. The spring 351 is provided to provide a rebound force of elastic deformation during the adjustment process. When loosened, this rebound force can pull the adjusting bolt 35 inward, thereby strengthening the tightness between the threads. In addition, a sealing rubber ring can be installed at the connection to strengthen the sealing.

[0033] In one embodiment, see Figure 12 to Figure 14 The feeding tube 36 includes an insertion portion 363, a liquid storage cylinder 362 and a sealing portion 361. The sealing portion 361 is arranged at the outer edge of the liquid inlet of the flow channel groove 322. The inner side of the sealing portion 361 is integrally formed with an insertion portion 363 inserted into the liquid inlet. The liquid storage cylinder 362 is threadedly connected to the inner wall of the sealing portion 361.

[0034] The insertion portion 363 is used to provide an insertion connection, and the sealing portion 361 is used to strengthen the sealing of the liquid inlet. The liquid to be tested can be directly placed in the liquid storage cylinder 362, and a pressure pump can be installed outside the liquid storage cylinder 362. In this way, the liquid will be injected into the interior of the flow channel under the action of external force, thereby completing the injection of the liquid.

[0035] In addition, Figure 6 As shown, the square-shaped slot can be used to place test papers, markers marked with luminous substances, and other related test pieces for testing, and the circular slot at the head end is the entrance of the flow channel 322, and the outlet of the flow channel 322 is the air hole 311, which is located at the end of the square-shaped slot.

[0036] Since some tests are conducted by "immunoturbidimetry" and some are conducted by "double antibody sandwich method" or other optical testing methods, in order to ensure that this embodiment supports these color and brightness change test schemes simultaneously, please refer to Figures 1 to 4 Specifically, the base 10 includes a bottom plate 11 and a mounting shell 12 covering the upper end surface of the bottom plate 11, a limit seat 122 is provided on the end surface of the mounting shell 12 away from the bottom plate 11, a flip press plate 14 is provided on one side of the limit seat 122, a penetrating light focusing groove 123 is provided inside the limit seat 122, the detection component includes a light source module 111 arranged on the upper end surface of the bottom plate 11 and a photoelectric sensor module 141 arranged on the lower end surface of the press plate 14, the light source module 111 faces the light focusing groove 123, when the chip 30 is placed inside the limit seat 122, the press plate 14 flips to drive the photoelectric sensor module 141 to cover the surface of the chip 30.

[0037] That is, a photoelectric sensor module 141 is arranged on the top, and a light source module 111 is arranged on the bottom. The design is completely through-through, and the chip 30 is placed at the center of the limit seat 122. For tests that require light from the light source module 111, the light source module 111 can be started to emit corresponding light. For tests that do not require light from the light source module 111, the light source module 111 can be turned off. During the entire test process, the pressure plate 14 covers the surface of the chip 30. In this case, the light will not be affected by external light, thereby ensuring the accuracy of the test results.

[0038] In the above scheme, the influence of external light is avoided. In order to further enhance the accuracy of the test results, please refer to Figures 1 to 4 A light shielding frame 142 is disposed on the surface of the pressing plate 14 , and the light shielding frame 142 covers the surface of the light-sensitive side of the photoelectric sensor module 141 .

[0039] The light shielding frame 142 is used to further shield the light, thereby reducing the influence of the light generated by the test operation at different positions on the adjacent positions, and further enhancing the accuracy of the test results.

[0040] Since the detection of microfluidic technology requires the penetration of light, the materials through which the light passes are usually highly transparent. This may cause light to be transmitted when high-brightness light is irradiated. In order to prevent the structural parts from being transmitted by high-brightness light, please refer to Figure 1 and Figure 2 A movable track 121 is provided between the upper end surface of the mounting shell 12 and one side of the base 10 , and a light blocking plate 13 is provided inside the movable track 121 . The light blocking plate 13 covers the pressing plate 14 , the limiting seat 122 and the top of the chip 30 .

[0041] A movable light blocking plate 13 is provided at the top to directly block external light. When operation is required, the light blocking plate 13 is moved to the other side, and then the chip 30 is operated. After the pressing plate 14 presses the chip 30, the light blocking plate 13 is moved above the pressing plate 14 and the chip 30 to block, thereby reducing the impact of high-brightness light.

[0042] In the above solution, both the surface of the pressing plate 14 and the light blocking plate 13 need to be provided with slots corresponding to the air holes 311 to ensure the normal flow of the internal airflow.

[0043] In the above solution, only the air hole 311 is used for exhaust. In this case, if there is too much liquid inside, the liquid may flow out of the air hole 311. In order to avoid the outflowing liquid from polluting the surrounding environment, please refer to Figures 1 to 4 An overflow groove 312 is formed on the upper end surface of the diaphragm 31 , and the air hole 311 is located inside the overflow groove 312 .

[0044] The overflow tank 312 is used to provide an external temporary storage tank, and excess liquid can be temporarily stored inside the overflow tank 312.

[0045] The above embodiments are only used to illustrate the technical solutions of the present invention, rather than to limit them.

Claims

1. A microfluidics-based instant sepsis detection device, characterized in that: include: Base (10); A chip (30) is arranged on the upper end surface of the base (10), the chip (30) comprising an inner core (32) and a diaphragm sheet 1 (31) and a diaphragm sheet 2 (33) covering the upper end surface and the lower end surface of the inner core (32); a flow channel (322) penetrating the two end surfaces is provided on the surface of the inner core (32); one end of the flow channel (322) is connected to a feeding pipe (36), and the other end of the flow channel (322) is connected to an air hole (311); and a protrusion (332) is fixed on the surface of the diaphragm sheet 1 (31) and the diaphragm sheet 2 (33) on one side facing the inner core (32); A detection component disposed on a side of the flow channel groove (322) close to the air hole (311); When the second diaphragm (33) and the first diaphragm (31) are covered on the surface of the inner core (32), the protrusion (332) is inserted into the flow channel groove (322) to form a flow channel, and the detection component detects the fluid at the tail of the flow channel; The two end surfaces of the inner core (32) are provided with limited cavities (321); the end surfaces of the diaphragm 1 (31) and the diaphragm 2 (33) close to the inner core (32) are integrally formed with limited portions (331); the surfaces of the diaphragm 1 (31), the inner core (32) and the diaphragm 2 (33) are provided with penetrating ventilation grooves (37); and the ventilation grooves (37) are provided with air pressure regulating devices inside. When the diaphragm 2 (33) and the diaphragm 1 (31) are covered on the surface of the inner core (32), an adjustment cavity (344) is separated between the diaphragm 2 (33) and the inner core (32), and between the diaphragm 1 (31) and the inner core (32), and the air pressure adjustment device reduces the air pressure inside the adjustment cavity (344) to drive the diaphragm 2 (33) and the diaphragm 1 (31) to squeeze the inner core (32); The air pressure regulating device comprises a cannula (34) and a regulating plug (35); The insert tube (34) is passed through and fits the inner wall of the ventilation groove (37); one end of the insert tube (34) is fixedly connected to a sealing plate (343); the sealing plate (343) closes one side of the ventilation groove (37) of the second diaphragm (33); two positioning rings (341) are fixed to the outer side of the insert tube (34); a through hole is formed on the surface of the positioning ring (341) and penetrates to the inside of the insert tube (34); the two positioning rings (341) are respectively arranged inside two adjustment chambers (344); the adjustment bolt (35) is threadedly connected to the inner wall of the insert tube (34); When the adjusting bolt (35) is tightened, the air pressure inside the adjusting chamber (344) increases, and when the adjusting bolt (35) is loosened, the air pressure inside the adjusting chamber (344) decreases; The positioning ring (341) is threadedly connected to the outer wall of the insert tube (34). When the positioning ring (341) is tightened, the through hole of the positioning ring (341) is communicated with the through hole on the side wall of the insert tube (34). One end of the insert tube (34) away from the sealing plate (343) passes through the outer side of the diaphragm (31) and is threadedly connected to a positioning sleeve (342). The interior of the positioning sleeve (342) is provided with a communicating threaded cavity (3421) and a connecting groove (3422). The adjusting bolt (35) is threadedly arranged inside the threaded cavity (3421). A spring (351) is arranged between the end surface of the adjusting bolt (35) and the positioning sleeve (342). The connecting groove (3422) is communicated with the insert tube (34).

2. According to claim 1, a microfluidics-based instant sepsis detection device is characterized by: An edge sealing fence 1 (323) is provided at the edge of the flow channel groove (322), and an edge sealing fence 2 (333) is provided on the outer side of the protrusion (332). A cavity is separated between the edge sealing fence 2 (333) and the protrusion (332), and the edge sealing fence 1 (323) is inserted into the cavity and fits against two side walls of the cavity.

3. The microfluidics-based instant sepsis detection device according to claim 1, characterized in that: The feeding tube (36) comprises an inserting portion (363), a liquid storage cylinder (362) and a sealing portion (361); The sealing portion (361) is arranged at the outer edge of the liquid inlet of the flow channel groove (322), and an insertion portion (363) inserted into the liquid inlet is integrally formed on the inner side of the sealing portion (361), and the liquid storage cylinder (362) is threadedly connected to the inner wall of the sealing portion (361).

4. The microfluidics-based instant sepsis detection device according to claim 1, characterized in that: The base (10) comprises a bottom plate (11) and a mounting shell (12) covering the upper end surface of the bottom plate (11); a limit seat (122) is provided on the end surface of the mounting shell (12) away from the bottom plate (11); a reversible pressing plate (14) is provided on one side of the limit seat (122); and a penetrating light focusing groove (123) is provided inside the limit seat (122); The detection assembly comprises a light source module (111) arranged on the upper end surface of the bottom plate (11) and a photoelectric sensor module (141) arranged on the lower end surface of the pressing plate (14), wherein the light source module (111) faces the focusing groove (123); When the chip (30) is placed inside the limiting seat (122), the pressing plate (14) is turned over to drive the photoelectric sensor module (141) to cover the surface of the chip (30).

5. The microfluidics-based instant sepsis detection device according to claim 4, characterized in that: A light shielding frame (142) is provided on the surface of the pressing plate (14), and the light shielding frame (142) covers the surface of the light-sensitive side of the photoelectric sensor module (141).

6. The microfluidics-based instant sepsis detection device according to claim 5, characterized in that: A movable track (121) is provided between the upper end surface of the mounting shell (12) and one side of the base (10), a light blocking plate (13) is provided inside the movable track (121), and the light blocking plate (13) covers the pressing plate (14), the limiting seat (122) and the top of the chip (30).

7. A microfluidics-based instant sepsis detection device according to any one of claims 1 to 6, characterized in that: The upper end surface of the base (10) is provided with a display module (20), the upper end surface of the diaphragm 1 (31) is provided with an overflow groove (312), and the air hole (311) is located inside the overflow groove (312).

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