WO2019237742A1 - 一种多通道快速检测微流体检测芯片 - Google Patents

一种多通道快速检测微流体检测芯片 Download PDF

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Publication number
WO2019237742A1
WO2019237742A1 PCT/CN2019/073042 CN2019073042W WO2019237742A1 WO 2019237742 A1 WO2019237742 A1 WO 2019237742A1 CN 2019073042 W CN2019073042 W CN 2019073042W WO 2019237742 A1 WO2019237742 A1 WO 2019237742A1
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Prior art keywords
detection
channel
microfluidic
layer
chip
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PCT/CN2019/073042
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English (en)
French (fr)
Inventor
许行尚
陈杰弗瑞
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Nanjing Lanyu Biological Technology Co Ltd
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Nanjing Lanyu Biological Technology Co Ltd
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Priority to US16/770,955 priority Critical patent/US11440006B2/en
Priority to SG11202100097VA priority patent/SG11202100097VA/en
Priority to EP19819952.3A priority patent/EP3698872B1/en
Publication of WO2019237742A1 publication Critical patent/WO2019237742A1/zh
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    • B—PERFORMING OPERATIONS; TRANSPORTING
    • B01—PHYSICAL OR CHEMICAL PROCESSES OR APPARATUS IN GENERAL
    • B01L—CHEMICAL OR PHYSICAL LABORATORY APPARATUS FOR GENERAL USE
    • B01L3/00—Containers or dishes for laboratory use, e.g. laboratory glassware; Droppers
    • B01L3/50—Containers for the purpose of retaining a material to be analysed, e.g. test tubes
    • B01L3/502—Containers for the purpose of retaining a material to be analysed, e.g. test tubes with fluid transport, e.g. in multi-compartment structures
    • B01L3/5027—Containers for the purpose of retaining a material to be analysed, e.g. test tubes with fluid transport, e.g. in multi-compartment structures by integrated microfluidic structures, i.e. dimensions of channels and chambers are such that surface tension forces are important, e.g. lab-on-a-chip
    • B01L3/502715—Containers for the purpose of retaining a material to be analysed, e.g. test tubes with fluid transport, e.g. in multi-compartment structures by integrated microfluidic structures, i.e. dimensions of channels and chambers are such that surface tension forces are important, e.g. lab-on-a-chip characterised by interfacing components, e.g. fluidic, electrical, optical or mechanical interfaces
    • B—PERFORMING OPERATIONS; TRANSPORTING
    • B01—PHYSICAL OR CHEMICAL PROCESSES OR APPARATUS IN GENERAL
    • B01L—CHEMICAL OR PHYSICAL LABORATORY APPARATUS FOR GENERAL USE
    • B01L3/00—Containers or dishes for laboratory use, e.g. laboratory glassware; Droppers
    • B01L3/50—Containers for the purpose of retaining a material to be analysed, e.g. test tubes
    • B01L3/502—Containers for the purpose of retaining a material to be analysed, e.g. test tubes with fluid transport, e.g. in multi-compartment structures
    • B01L3/5027—Containers for the purpose of retaining a material to be analysed, e.g. test tubes with fluid transport, e.g. in multi-compartment structures by integrated microfluidic structures, i.e. dimensions of channels and chambers are such that surface tension forces are important, e.g. lab-on-a-chip
    • B—PERFORMING OPERATIONS; TRANSPORTING
    • B01—PHYSICAL OR CHEMICAL PROCESSES OR APPARATUS IN GENERAL
    • B01L—CHEMICAL OR PHYSICAL LABORATORY APPARATUS FOR GENERAL USE
    • B01L2200/00—Solutions for specific problems relating to chemical or physical laboratory apparatus
    • B01L2200/10—Integrating sample preparation and analysis in single entity, e.g. lab-on-a-chip concept
    • B—PERFORMING OPERATIONS; TRANSPORTING
    • B01—PHYSICAL OR CHEMICAL PROCESSES OR APPARATUS IN GENERAL
    • B01L—CHEMICAL OR PHYSICAL LABORATORY APPARATUS FOR GENERAL USE
    • B01L2300/00—Additional constructional details
    • B01L2300/06—Auxiliary integrated devices, integrated components
    • B01L2300/0627—Sensor or part of a sensor is integrated
    • B01L2300/0645—Electrodes
    • B—PERFORMING OPERATIONS; TRANSPORTING
    • B01—PHYSICAL OR CHEMICAL PROCESSES OR APPARATUS IN GENERAL
    • B01L—CHEMICAL OR PHYSICAL LABORATORY APPARATUS FOR GENERAL USE
    • B01L2300/00—Additional constructional details
    • B01L2300/08—Geometry, shape and general structure
    • B01L2300/0809—Geometry, shape and general structure rectangular shaped
    • B01L2300/0816—Cards, e.g. flat sample carriers usually with flow in two horizontal directions
    • B—PERFORMING OPERATIONS; TRANSPORTING
    • B01—PHYSICAL OR CHEMICAL PROCESSES OR APPARATUS IN GENERAL
    • B01L—CHEMICAL OR PHYSICAL LABORATORY APPARATUS FOR GENERAL USE
    • B01L2300/00—Additional constructional details
    • B01L2300/08—Geometry, shape and general structure
    • B01L2300/0861—Configuration of multiple channels and/or chambers in a single devices
    • B01L2300/0864—Configuration of multiple channels and/or chambers in a single devices comprising only one inlet and multiple receiving wells, e.g. for separation, splitting
    • B—PERFORMING OPERATIONS; TRANSPORTING
    • B01—PHYSICAL OR CHEMICAL PROCESSES OR APPARATUS IN GENERAL
    • B01L—CHEMICAL OR PHYSICAL LABORATORY APPARATUS FOR GENERAL USE
    • B01L2300/00—Additional constructional details
    • B01L2300/08—Geometry, shape and general structure
    • B01L2300/0887—Laminated structure
    • B—PERFORMING OPERATIONS; TRANSPORTING
    • B01—PHYSICAL OR CHEMICAL PROCESSES OR APPARATUS IN GENERAL
    • B01L—CHEMICAL OR PHYSICAL LABORATORY APPARATUS FOR GENERAL USE
    • B01L2300/00—Additional constructional details
    • B01L2300/16—Surface properties and coatings
    • B01L2300/161—Control and use of surface tension forces, e.g. hydrophobic, hydrophilic
    • B—PERFORMING OPERATIONS; TRANSPORTING
    • B01—PHYSICAL OR CHEMICAL PROCESSES OR APPARATUS IN GENERAL
    • B01L—CHEMICAL OR PHYSICAL LABORATORY APPARATUS FOR GENERAL USE
    • B01L3/00—Containers or dishes for laboratory use, e.g. laboratory glassware; Droppers
    • B01L3/50—Containers for the purpose of retaining a material to be analysed, e.g. test tubes
    • B01L3/502—Containers for the purpose of retaining a material to be analysed, e.g. test tubes with fluid transport, e.g. in multi-compartment structures
    • B01L3/5027—Containers for the purpose of retaining a material to be analysed, e.g. test tubes with fluid transport, e.g. in multi-compartment structures by integrated microfluidic structures, i.e. dimensions of channels and chambers are such that surface tension forces are important, e.g. lab-on-a-chip
    • B01L3/502723—Containers for the purpose of retaining a material to be analysed, e.g. test tubes with fluid transport, e.g. in multi-compartment structures by integrated microfluidic structures, i.e. dimensions of channels and chambers are such that surface tension forces are important, e.g. lab-on-a-chip characterised by venting arrangements

Definitions

  • the invention belongs to the technical field of medical equipment, and particularly relates to a multi-channel rapid detection microfluidic detection chip.
  • Microfluidics is a technology applied across a variety of disciplines including engineering, physics, chemistry, microtechnology, and biotechnology. Microfluidics involves the study of trace fluids and how to manipulate, control, and use such small amounts of fluids in various microfluidic systems and devices such as microfluidic chips.
  • microfluidic biochips (known as "chip labs") are used in the field of molecular biology to integrate assay operations for purposes such as analyzing enzymes and DNA, detecting biochemical toxins and pathogens, and diagnosing diseases.
  • Microfluidic chips are a hot area for the development of current Miniaturized Total Analysis Systems.
  • Microfluidic chip analysis uses chip as the operating platform, at the same time is based on analytical chemistry, is based on micro-electromechanical processing technology, uses micro-pipeline networks as structural features, and uses life science as the main application object at present. It is the current micro-full analysis system field. Development focus. Its goal is to integrate the functions of the entire laboratory, including sampling, dilution, reagent addition, reaction, separation, detection, etc. on a microchip.
  • the microfluidic chip is the main platform for microfluidic technology implementation.
  • microfluidic chips have the characteristics of controllable liquid flow, minimal consumption of samples and reagents, and increased analysis speeds by ten to hundreds of times. They can be used in minutes or even less. Simultaneous analysis of hundreds of samples can be carried out in-house, and the entire process of sample pretreatment and analysis can be realized online. The purpose of its application is to realize the ultimate goal of micro-total analysis system-chip laboratory.
  • the key application field of current work development is the field of life sciences.
  • a microfluidic chip in which a glass substrate layer, an intermediate layer and an overlying layer are sequentially stacked from bottom to top, and the glass substrate layer, the intermediate layer and the overlying layer are defined in cooperation with each other.
  • a closed annular microfluidic channel and a detection chamber the microfluidic channel is located outside the detection chamber and communicates with the detection chamber, and one side of the upper cover layer is provided with a fluid injection port communicating with the microfluidic channel, and the upper The cover layer is provided with a plurality of exhaust holes at the other end of the microchannel.
  • the technical problem to be solved by the present invention is to provide a multi-channel rapid detection microfluidic detection chip with a reasonably designed sample inlet to avoid sample contamination, large detection throughput, and high detection efficiency and accuracy.
  • the multi-channel rapid detection microfluidic detection chip includes a chip body, and the chip body is provided with a chip sampling port, a plurality of mutually independent detection chambers, and a microfluidic channel.
  • the chip sampling port communicates with the detection chamber through a microfluidic channel, the chip body further includes an electrode, and the detection chamber is connected to the electrode;
  • the microfluidic channel includes a mainstream channel and a plurality of micro-channels.
  • a fluid channel, the end of the main channel is divided into a plurality of the micro fluid channels, and the plurality of micro fluid channels are in one-to-one correspondence with a plurality of mutually independent detection chambers;
  • the chip sampling port is connected.
  • the microfluidic chip detection has the characteristics of high accuracy, fast speed and low detection cost, which is suitable for detection in the precise medical link.
  • the mainstream channel of specific structural forms and multiple sub-microfluidic channels For guiding the flow of blood samples, one sample chamber can simultaneously inject samples into multiple reaction chambers without contaminating the sample, and easy to inject; after sampling by the chip sampling port, the mainstream channel flows to multiple microfluidic channels at the same time.
  • the chip structure is simple, the operation is convenient, the detection efficiency is improved, and greatly reduced
  • the consumption of resources is realized; the rapid detection is realized, and the cost is reduced.
  • the chip body includes a bottom layer, an intermediate layer and an upper cover layer in order from bottom to top, and the bottom layer, the middle layer and the upper cover layer cooperate to define a closed microfluidic channel and a plurality of mutual Independent detection chamber;
  • the microchannel and detection chamber are in the middle layer;
  • the upper cover layer is provided with a liquid injection port and a plurality of exhaust holes, and the plurality of exhaust holes are provided in the upper cover layer
  • One side of the microfluidic channel is provided at a position corresponding to the end of the microfluidic channel, the liquid injection port is in communication with the front end of the microfluidic channel; an electrode is provided on the bottom plate layer, and the detection chamber and The electrodes are connected.
  • the chip with a three-layer structure of the bottom layer, the middle layer and the upper cover layer has a reasonable design, a simple and compact structure, and reduced costs, and has a chip sampling port that is easy to sample; by providing multiple exhaust holes in the upper cover, The flow resistance of the fluid to be measured is reduced, and the flow is faster, so that the detection chamber can be filled quickly.
  • the exhaust hole is set to facilitate the flow of the sample and facilitate the sampling. If there is no exhaust hole, the sample cannot flow into the detection chamber for reaction.
  • the detection reagent is embedded in the chip detection chamber in advance.
  • the invention is further improved in that a plurality of mutually independent detection chambers are distributed in a fan shape, and the ends of the mainstream channels are shunted into a plurality of microfluidic channels and then communicated to a plurality of mutually independent detection chambers.
  • the invention is further improved in that the chip sampling port is composed of a liquid injection port, the chip sampling port is in communication with the main channel, and one end of the main channel is provided with a connection at a position corresponding to the liquid injection port. Liquid port; the other end of the mainstream channel is connected to all micro-fluidic channels.
  • the chip sampling port adopting this structure is easy to sample, is not polluted, has a simple structure, and has low cost.
  • the invention is further improved in that the bottom layer, the middle layer and the upper cover layer cooperate to define a closed microfluidic channel, a detection chamber and a funnel area; a lower end of the bottom layer is provided with a gap, and the liquid injection
  • the inlet, the funnel area and the notch are respectively provided at corresponding positions on the upper cover layer, the middle layer and the bottom layer and have different sizes;
  • the chip sampling port is composed of a liquid injection port, the funnel area and the notch and passes through the microfluid
  • the channel is connected to the bottom of the detection chamber.
  • the chip sampling port is set as a funnel sample with a large floor area, a small cover area and a middle funnel. This structure is reasonable and simple, making the sample easier to enter without being contaminated and improving the detection efficiency.
  • the invention is further improved in that the liquid injection port, the funnel region and the gap are all arc-shaped and have different radians; the liquid injection port and the funnel region are all semi-circular arcs, and the radius of the funnel region is not less than the liquid Note the arc radius of the entrance; the funnel region is dispersed through the curved mainstream channel to a plurality of microfluidic channels and communicate with the plurality of independent detection chambers one by one; the area of the gap is smaller than the area of the funnel region ;
  • the main channel is a funnel area
  • the liquid injection port is arc-shaped, which overlaps with a part of the funnel area
  • the funnel area has an opening that converges inward to form a horn shape, and the funnel area is at its tail
  • a plurality of micro-fluidic channels are dispersed inward at the ends, and a plurality of mutually independent detection chambers are connected through the plurality of micro-fluidic channels in a one-to-one correspondence.
  • the liquid injection port has a semi-circular arc shape.
  • this structure sets the largest amount of sample injected, and the radius of the funnel region is not less than the arc radius of the liquid injection port, so that the funnel region can fully accommodate There is no loss of sample liquid injected from the liquid injection port; a curved flow channel is provided so that the sample slowly flows into the detection chamber, which will not cause a sudden increase in the atmospheric pressure of the detection chamber.
  • the liquid injection port is set in an arc shape, which overlaps with a part of the funnel region; the funnel region converges inward at the opening to form a horn shape so that the sample gradually flows in, and does not stay at the opening to avoid sample loss, for example
  • the speed of the blood sample entering the sampling port in the funnel area using this structure is about 1 second, and the blood sample is quickly sucked into the sampling port; the function of the gap is to fit the finger belly to facilitate sampling.
  • the invention is further improved in that the bottom plate layer, the middle layer and the upper cover layer are integrated into a single body by means of double-sided gluing of the middle layer.
  • the intermediate layer is a pressure-sensitive adhesive tape
  • the material of the upper cover layer and / or the bottom layer is any one of PMMA, PP, PE, and PET
  • the upper cover The surface of the layer and the bottom plate layer both have a hydrophilic film, so that the sample flows quickly into the mainstream channel through the chip sampling port, and then is shunted to each of the sub-microfluidic channels.
  • each detection chamber of the microfluidic chip is small, the consistency is high, and the accuracy of the detection is improved; the surface of the upper cover layer and the bottom layer is provided with a hydrophilic film, which can make the sample flow into the mainstream through the chip sampling port more quickly. Channels are shunted to each of the microfluidic channels, which speeds up the flow rate and improves detection efficiency.
  • the thickness of the intermediate layer is 0.1 to 1.0 mm; the surface of the bottom layer is flat, and the bottom layer, the middle layer, and the upper cover layer cooperate to define a closed microchannel.
  • the depth of the test chamber is 0.1 to 1.0 mm, and the width of the detection chamber defined by cooperation is 1.0 to 2.0 mm.
  • each of the microfluidic channels has a nozzle at a connection with the detection chamber, and each of the microfluidic channels has a corresponding electrode, and each electrode includes an input height.
  • the side electrode and the input low-side electrode have a thickness of 50um.
  • the nozzle is arranged at the connection between the micro-fluidic channel and the detection chamber to make the sample flow into the detection chamber more easily and quickly; the function of the electrode is to apply a pulse voltage while receiving the signal generated by the blood reaction in the detection chamber; the end of the electrode is inserted into the detection instrument
  • the detection result is obtained by detecting the electrochemical signal generated by the reaction, and the matching detection equipment is used to obtain the detection result.
  • the electrode end is the bottom plate layer, the middle layer and the upper cover layer are integrated into a single body and exposed to the upper cover layer and the middle layer. This makes it easier and more convenient for the electrode tip to be inserted into the test instrument.
  • the multi-channel rapid detection microfluidic detection chip is designed to guide the flow of blood samples by designing mainstream channels of specific structural forms and multiple sub-microfluidic channels, so that one sample chamber can simultaneously The sample is injected into each reaction chamber without contaminating the sample, which is easy to inject. After sampling by the chip sampling port, the mainstream channel flows to multiple microfluidic channels at the same time and then enters multiple independent detection chambers. This can achieve simultaneous detection of multiple Each sample has the effect of multiple channels; the chip has a simple structure and is easy to operate, which improves the detection efficiency and accuracy, and greatly reduces the consumption of resources; realizes rapid detection and reduces costs.
  • FIG. 1 is a schematic plan view of a multi-channel rapid detection microfluidic detection chip according to the first embodiment of the present invention
  • FIG. 2 is a schematic diagram of a three-dimensional structure of a multi-channel rapid detection microfluidic detection chip according to the first embodiment of the present invention
  • Embodiment 3 is an overall structural diagram of Embodiment 1 of a multi-channel rapid detection microfluidic detection chip according to the present invention
  • FIG. 4 is a schematic plan view of a multi-channel rapid detection microfluidic detection chip according to a second embodiment of the present invention.
  • FIG. 5 is a schematic diagram of a three-dimensional structure of a multi-channel rapid detection microfluidic detection chip according to a second embodiment of the present invention.
  • Embodiment 2 of a multi-channel rapid detection microfluidic detection chip according to the present invention
  • FIG. 7 is a schematic plan view of a multi-channel rapid detection microfluidic detection chip according to a third embodiment of the present invention.
  • Embodiment 8 is a schematic diagram of a three-dimensional structure of Embodiment 3 of the multi-channel rapid detection microfluidic detection chip of the present invention.
  • Embodiment 9 is an overall structural diagram of Embodiment 3 of a multi-channel rapid detection microfluidic detection chip according to the present invention.
  • 1-bottom layer 2-intermediate layer; 3-overlying layer; 4-electrode; 401-electrode end; 5-microchannel; 501-mainstream channel; 502-microfluidic channel; 6-exhaust hole 7-chip sampling port; 701-liquid injection port; 702-liquid port; 8- detection chamber; 9- funnel area; 10-notch.
  • the multi-channel rapid detection microfluidic detection chip includes a chip body, and the chip body is provided with a chip sampling port 7, a plurality of mutually independent detection chambers 8 and a microchannel 5, and the chip sampling port 7
  • the microchannel 5 is in communication with the detection chamber 8.
  • the chip body further includes an electrode 4, and the detection chamber 8 is connected to the electrode 4.
  • the microchannel 5 includes a mainstream channel 501 and 5 points.
  • the other end of the channel 501 is in communication with the chip sampling port 7;
  • the chip body includes a bottom layer 1, an intermediate layer 2 and an upper cover layer in order from bottom to top, and the bottom layer 1, the intermediate layer 2 and the upper cover layer 3 cooperates to define a closed microfluidic channel 5 and a plurality of independent detection chambers 8;
  • the microfluidic channel 5 and the detection chamber 8 are in the middle layer 2;
  • the upper cover layer 3 is provided with a liquid injection port 701 And 5 exhaust holes 6, which are arranged on one side of the upper cover layer and At a position corresponding to the end of the microfluidic channel 5, the liquid injection port 701 is in communication with the front end of the microfluidic channel 5; an electrode 4 is provided on the floor layer 1, and the detection chamber
  • the five independent detection chambers 8 are distributed in a fan shape.
  • the end of the mainstream channel 501 is divided into five sub-microfluidic channels 502 and then connected to the five independent detection chambers 8; the floor layer 1, the middle layer 2 It is integrated with the upper cover layer 3 by double-sided gluing of the middle layer 2.
  • the middle layer 2 is a pressure-sensitive adhesive tape, and the material of the upper cover layer 3 and / or the bottom plate layer 1 is PMMA, PP, PE.
  • any of PET and PET, and the surface of the upper cover layer 3 and the bottom layer 1 has a hydrophilic film, so that the sample quickly flows through the chip sampling port 7 into the mainstream channel 501, and then shunted to each of the sub-microfluidic channels 502
  • the thickness of the intermediate layer 2 is 0.1 to 1.0 mm; the surface of the bottom layer 1 is flat, so The bottom layer 1, the middle layer 2 and the upper cover layer 3 cooperate to define a closed microchannel 5 having a depth of 0.1 to 1.0 mm, and the width of the detection chamber 8 defined by the cooperation is 1.0 to 2.0 mm; each One of the microfluidic channels 502 has a nozzle at the connection point with the detection chamber 8, and each of the microfluidic channels 502 has a corresponding electrode 4, and each electrode 4 includes an input high-side electrode and an input.
  • the thickness of the electrode 4 is 50um; the function of the electrode 4 is to apply a pulse voltage and simultaneously receive the signal generated by the blood reaction in the detection chamber; the electrode end 401 is inserted into the detection instrument, and the electrochemical signal generated by the detection reaction is matched with The matching test equipment obtains the test results; the electrode end 401 is the part of the bottom layer 1, the middle layer 2 and the upper cover layer 3 that are exposed to the outside with respect to the upper cover layer 3 and the middle layer 2, so that the electrode end 401 can be more easily and conveniently inserted into the testing instrument, and the test results are obtained; as shown in FIGS.
  • the chip sampling port 7 is a liquid injection port 701, the chip sampling port 7 and the mainstream channel 501 Connected One end of the main flow channel 501 is provided with a liquid inlet connection 702 of the injection at a position corresponding to the liquid inlet 701; the other end of the main duct 501 is connected to all the sub-microfluidic channel 502.
  • Embodiment 2 The difference from Embodiment 1 lies in the structure of the chip sampling port 7.
  • the bottom layer 1, the middle layer 2 and the upper cover layer 3 cooperate to define a closed microchannel 5, a detection chamber 8, and a funnel. Area 9; a notch 10 is provided on one side of the lower end of the bottom layer 1, and the liquid injection port 701, the funnel region 9 and the notch 10 are respectively provided on the upper cover layer 3, the middle layer 2 and the bottom layer 1 respectively The positions and sizes are different;
  • the chip sampling port 7 is composed of a liquid injection port 701, a funnel region 9 and a gap 10, and is connected to the bottom of the detection chamber 8 through the microfluidic channel 5; specifically: the multiple The channel rapid detection microfluidic detection chip includes a chip body, and the chip body is provided with a chip sampling port 7, a plurality of mutually independent detection chambers 8 and a microfluidic channel 5, and the chip sampling port 7 passes through the microfluidic channel 5 and The detection chamber 8 is in communication, and the chip body further includes an
  • the detection chamber 8 is connected to the electrode 4.
  • the microfluidic channel 5 includes a mainstream channel 501 and five micro-fluidic channels 502.
  • the end of the main channel 501 is divided into 5 micro-fluid channels 5 02, 5 said microfluidic channels 502 are in one-to-one correspondence with 5 independent detection chambers 8; the other end of the main channel 501 is in communication with the chip sampling port 7; the chip body is from bottom to top
  • the bottom layer 1, the middle layer 2 and the upper cover layer 3 are included in this order.
  • the bottom layer 1, the middle layer 2 and the upper cover layer 3 cooperate to define a closed microfluidic channel 5 and a plurality of independent detection chambers 8;
  • the microfluidic channel 5 and the detection chamber 8 are in the middle layer 2;
  • the upper cover layer 3 is provided with a liquid injection port 701 and 5 exhaust holes 6, and the 5 exhaust holes 6 are provided in the upper cover
  • One side of the layer is provided at a position corresponding to the end of the microfluidic channel 5, the liquid injection port 701 is in communication with the front end of the microfluidic channel 5;
  • the bottom plate layer 1 is provided with an electrode 4
  • the detection chamber 8 is connected to the electrode 4; the arrangement of the exhaust hole 6 facilitates the flow of the sample and facilitates the sampling.
  • the sample cannot flow into the detection chamber 8 for reaction, and the detection of the chip Detection reagents are pre-embedded in the chamber 8; five independent detection chambers 8 are fan-shaped, and are divided into five branches by the ends of the main channel 501.
  • the fluid channel 502 is further connected to five independent detection chambers 8; the bottom layer 1, the middle layer 2 and the upper cover layer 3 are bonded together by means of double-sided gluing of the middle layer 2; the middle layer 2 is pressure-sensitive Adhesive tape, the material of the cover layer 3 and / or the bottom layer 1 is any one of PMMA, PP, PE, PET, and the surfaces of the cover layer 3 and the bottom layer 1 have a hydrophilic film, so that the sample Quickly flows through the chip sampling port 7 into the mainstream channel 501, and then shunts to each micro-fluidic channel 502; the thickness of the intermediate layer 2 is 0.1 to 1.0 mm; the surface of the bottom plate layer 1 is flat, so The bottom layer 1, the middle layer 2 and the upper cover layer 3 cooperate to define a closed microchannel 5 having a depth of 0.1 to 1.0 mm, and the width of the detection chamber 8 defined by the cooperation is 1.0 to 2.0 mm; each One of the microfluidic channels 502 has a nozzle at the connection point
  • the thickness of the electrode 4 is 50um; the function of the electrode 4 is to apply a pulse voltage while receiving The signal generated by the blood reaction in the test room; the electrode end 401 is inserted into the detection instrument, and the detection result is obtained by detecting the electrochemical signal generated by the reaction with the supporting detection instrument; the electrode end 401 is the bottom layer 1, the middle layer 2 and the upper layer
  • the cover layer 3 keys are integrated into the exposed part relative to the upper cover layer 3 and the middle layer 2 so that the electrode end 401 can be more easily and conveniently inserted into the testing instrument and the test results are shown; as shown in Figures 4-6
  • the bottom layer 1, the middle layer 2 and the upper cover layer 3 cooperate to define a closed microfluidic channel 5, a detection chamber 8, and a funnel region 9; a notch 10 is provided on one side of the lower end of the bottom layer 1,
  • the liquid injection port 701, the funnel region 9 and the notch 10 are respectively provided at corresponding positions on the upper cover layer 3, the middle layer 2 and the bottom plate layer 1 and have different sizes; the
  • Funnel area 9 part area overlap The funnel region 9 converges inwardly at the opening to form a horn shape, and the funnel region 9 disperses five micro-fluidic channels 502 inwardly at its tail end, and passes through the five micro-fluidic channels 502 one by one.
  • Five independent detection chambers 8 are connected correspondingly; the liquid injection port 701 is set in an arc shape, which overlaps a part of the funnel region 9; the funnel region 9 has an opening that converges inward to form a horn shape so that the sample gradually Inflow, do not stay in the opening to avoid sample loss.
  • Embodiment 3 The difference from Embodiment 1 lies in the structure of the chip sampling port.
  • the bottom layer 1, the middle layer 2 and the upper cover layer 3 cooperate to define a closed microchannel 5, a detection chamber 8, and a funnel area. 9; a notch 10 is provided on one side of the lower end of the bottom plate layer 1, and the liquid injection port 701, the funnel region 9 and the notch 10 are respectively provided at corresponding positions on the upper cover layer 3, the middle layer 2 and the bottom layer 1
  • the chip sampling port 7 is composed of a liquid injection port 701, a funnel region 9 and a gap 10, and is connected to the bottom of the detection chamber 8 through the microchannel 5; specifically: the multi-channel
  • the rapid detection microfluidic detection chip includes a chip body, and the chip body is provided with a chip sampling port 7, a plurality of mutually independent detection chambers 8 and a microchannel 5, and the chip sampling port 7 communicates with the microchannel 5 through the microchannel 5
  • the detection chamber 8 is in communication, the chip body further includes an electrode 4, and
  • the microfluidic channel 5 includes a mainstream channel 501 and five micro-fluidic channels 502.
  • the end of the main flow channel 501 is divided into 5 micro-fluidic channels 50 2, 5 said microfluidic channels 502 are in one-to-one correspondence with 5 independent detection chambers 8; the other end of the main channel 501 is in communication with the chip sampling port 7; the chip body is from bottom to top
  • the bottom layer 1, the middle layer 2 and the upper cover layer 3 are included in this order.
  • the bottom layer 1, the middle layer 2 and the upper cover layer 3 cooperate to define a closed microfluidic channel 5 and a plurality of independent detection chambers 8;
  • the microfluidic channel 5 and the detection chamber 8 are in the middle layer 2;
  • the upper cover layer 3 is provided with a liquid injection port 701 and 5 exhaust holes 6, and the 5 exhaust holes 6 are provided in the upper cover
  • One side of the layer is provided at a position corresponding to the end of the microfluidic channel 5, the liquid injection port 701 is in communication with the front end of the microfluidic channel 5;
  • the bottom plate layer 1 is provided with an electrode 4
  • the detection chamber 8 is connected to the electrode 4; the arrangement of the exhaust hole 6 facilitates the flow of the sample and facilitates the sampling.
  • the sample cannot flow into the detection chamber 8 for reaction, and the detection of the chip Detection reagents are pre-embedded in the chamber 8; 5 independent detection chambers 8 are fan-shaped, and are divided into 5 micro-microns by the ends of the main channel 501.
  • the fluid channel 502 is further connected to five independent detection chambers 8; the bottom layer 1, the middle layer 2 and the upper cover layer 3 are bonded together by means of double-sided gluing of the middle layer 2; the middle layer 2 is pressure-sensitive Adhesive tape, the material of the cover layer 3 and / or the bottom layer 1 is any one of PMMA, PP, PE, PET, and the surfaces of the cover layer 3 and the bottom layer 1 have a hydrophilic film, so that the sample Quickly flows through the chip sampling port 7 into the mainstream channel 501, and then shunts to each micro-fluidic channel 502; the thickness of the intermediate layer 2 is 0.1 to 1.0 mm; the surface of the bottom plate layer 1 is flat, so The bottom layer 1, the middle layer 2 and the upper cover layer 3 cooperate to define a closed microchannel 5 having a depth of 0.1 to 1.0 mm, and the width of the detection chamber 8 defined by the cooperation is 1.0 to 2.0 mm; each One of the microfluidic channels 502 has a nozzle at the connection point
  • the thickness of the electrode 4 is 50um; the function of the electrode 4 is to apply a pulse voltage while receiving The signal generated by the blood reaction in the test room; the electrode end 401 is inserted into the detection instrument, and the detection result is obtained by detecting the electrochemical signal generated by the reaction with the supporting detection instrument; the electrode end 401 is the bottom layer 1, the middle layer 2 and the upper layer
  • the cover layer 3 keys are integrated into the exposed part relative to the upper cover layer 3 and the middle layer 2 so that the electrode end 401 can be more easily and conveniently inserted into the testing instrument and the test results are shown; as shown in Figures 7-9
  • the bottom layer 1, the middle layer 2 and the upper cover layer 3 cooperate to define a closed microfluidic channel 5, a detection chamber 8, and a funnel region 9; a notch 10 is provided on one side of the lower end of the bottom layer 1,
  • the liquid injection port 701, the funnel region 9 and the notch 10 are respectively provided at corresponding positions on the upper cover layer 3, the middle layer 2 and the bottom plate layer 1 and have different sizes; the
  • the funnel region 9 disperses five micro-fluidic channels 502 and The five independent detection chambers 8 are connected one by one; the area of the gap 10 is smaller than the area of the funnel region 9.
  • the liquid injection port 701 has a semi-circular arc shape. Under the condition of the same area, this structure provides the largest number of injected samples, and the radius of the funnel region 9 is not less than the arc radius of the liquid injection port 701, so that the funnel region 9 It can fully contain the sample liquid injected from the liquid injection port without loss; the curved flow channel is set so that the sample slowly flows into the detection chamber 8 without causing a sudden increase in the atmospheric pressure of the detection chamber 8.
  • a sample is injected into the chip sampling port 7, and the sample flows through the mainstream channel 501 to a plurality of microfluidic channels 502 at the same time, and then enters a plurality of mutually independent detection chambers 8.
  • the samples react with the detection reagents embedded in the detection chamber 8 in advance.

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Abstract

一种多通道快速检测微流体检测芯片，包括芯片本体，芯片本体上设置有芯片采样口（7）、多个相互独立的检测室（8）和微流道（5），芯片采样口（7）通过微流道（5）与检测室（8）连通，芯片本体还包括电极（4），检测室（8）与电极（4）相连接；微流道（5）包括一条主流通道（501）和多个分微流体通道（502），主流通道（501）的末端分流出多个分微流体通道（502），多个分微流体通道（502）与多个相互独立的检测室（8）一一对应连通；主流通道（501）的另一端与芯片采样口（7）连通。通过设计主流通道（501）和多个分微流体通道（502），用于引导血液样本的流动，使得一个样品腔室，能够同时向多个反应腔室注入样品且不污染样品，易进样，同时检测多个样本，具有多通道效果；芯片结构简单，操作方便，提高了检测效率，减少了资源的消耗，降低了成本。

Description

一种多通道快速检测微流体检测芯片 技术领域
本发明属于医疗设备技术领域，尤其是涉及一种多通道快速检测微流体检测芯片。
背景技术
微流体学是跨包括工程学、物理学、化学、微技术和生物技术的各种学科来应用的技术。微流体学涉及到对微量流体的研究以及对如何在诸如微流体芯片之类的各种微流体系统和设备中操纵、控制和使用这样的少量流体的研究。例如：微流体生物芯片(被称为“芯片实验室”)在分子生物学领域中用于整合化验操作，以用于诸如分析酶和DNA，检测生物化学毒素和病原体、诊断疾病等目的。
微流控芯片(microfluidic chip)是当前微全分析系统(Miniaturized Total Analysis Systems)发展的热点领域。微流控芯片分析以芯片为操作平台，同时以分析化学为基础，以微机电加工技术为依托，以微管道网络为结构特征，以生命科学为目前主要应用对象，是当前微全分析系统领域发展的重点。它的目标是把整个化验室的功能，包括采样、稀释、加试剂、反应、分离、检测等集成在微芯片上。微流控芯片是微流控技术实现的主要平台。其装置特征主要是其容纳流体的有效结构(通道、检测室和其它某些功能部件)至少在一个纬度上为微米级尺度。由于微米级的结构，流体在其中显示和产生了与宏观尺度不同的特殊性能。因此发展出独特的分析产生的性能。微流控芯片的特点及发展优势：微流控芯片具有液体流动可控、消耗试样和试剂极少、分析速度成十倍上百倍地提高等特点，它可以在几分钟甚至更短的时间内进行上百个样品的同时分析，并且可以在线实现样品的预处理及分析全过程。其产生的应用目的是实现微全分析系统的终极目标－芯片实验室，目前工作发展的重点应用领域是生命科学领域。
当前国际研究现状：创新多集中于分离、检测体系方面；对芯片上如何引入实际样品分析的诸多问题，如样品引入、换样、前处理等有关研究还十分薄弱。它的发展依赖于多学科交叉的发展。
在中国专利文献CN205361375U中，公开了一种微流体芯片，从下往上依次迭接有玻璃基板层、中间层和上盖层，所述玻璃基板层、中间层与上盖层相配合界定出封闭的环形的微流道和检测室，所述微流道位于检测室的外侧，并与检测室连通，所述上盖层一侧设有与微流道连通的流体注入口，所述上盖层在微流道的另一端设有多个排气孔。但上述技术方案检测通量小，结构复杂成本高，进样口设计不合理容易致样本污染。
因此，有必要开发一种合理设计的进样口避免样本被污染且检测通量大、检测效率和精确度均高的多通道快速检测微流体检测芯片。
发明内容
本发明要解决的技术问题是提供一种合理设计的进样口避免样本被污染且检测通量大、检测效率和精确度均高的多通道快速检测微流体检测芯片。
为解决上述技术问题，本发明采用的技术方案是，该多通道快速检测微流体检测芯片，包括芯片本体，所述芯片本体上设置有芯片采样口、多个相互独立的检测室和微流道，所述芯片采样口通过微流道与所述检测室连通，所述芯片本体还包括电极，所述检测室与所述电极相连接；所述微流道包括一条主流通道和多个分微流体通道，所述主流通道的末端分流出多个所述分微流体通道，多个所述分微流体通道与多个相互独立的检测室一一对应连通；所述主流通道的另一端与所述芯片采样口连通。
采用上述技术方案，微流控芯片检测具有精度高，速度快，检测成本较低的特点，适合进行精准医疗环节进行的检测，通过设计特定结构形式的主流通道和多个分微流体通道，用于引导血液样本的流动，使得一个样品腔室，能够同时向多个反应腔室注入样品且不污染样品，易进样；芯片采样口采样后，由主流通道同时分别流向多个分微流体通道，再进入多个相互独立的检测室，检测室内预先包埋有检测试剂，这样可以实现同时检测多个样本，具有多通道的效果；芯片结构简单，操作方便，提高了检测效率，并大大减少了资源的消耗；实现快速检测，降低了成本。
本发明进一步改进在于，所述芯片本体从下往上依次包括底板层、中间层和上盖层，所述底板层、中间层与上盖层相配合界定出封闭的微流道和多个相互独立的检测室；所述微流道和检测室在所述中间层；所述上盖层设有液体注入口和多个排气孔，所述多个排气孔设置在所述上盖层的一侧且设置在与所述微流道的末端相对应的位置处，所述液体注入口与所述微流道的前端相连通；所述底板层上设有电极，所述检测室与所述电极相连接。采用底板层、中间层和上盖层的三层结构的芯片，设计合理，结构简单紧凑，且降低了成本，具有易进样的芯片采样口；通过在上盖设置多个排气孔，使得待测流体的流动阻力减小，流动更快速，实现快速填充检测室；排气孔的设置有利于样本的流动，方便进样，若没有设置排气孔，则样本不能流进检测室进行反应，芯片检测室内预先包埋检测试剂。
本发明进一步改进在于，多个相互独立的检测室呈扇形分布，由所述主流通道的末端分流成多个分微流体通道再连通至多个相互独立的检测室。通过设计特定结构形式的主流通道和多个分微流体通道，用于引导血液样本的流动，使得一个样品腔室，能够同时向多个反应腔室注入样品，使得流动更快捷，提高检测效率。
本发明进一步改进在于，所述芯片采样口由液体注入口构成，所述芯片采样口与所述主流通道连通，所述主流通道的一端在与所述液体注入口相对应的位置处设置有接液口；所述主流通道的另一端连接所有的分微流体通道。采用这种结构的芯片采样口易于采样，且不被污染，结构简单，成本低。
本发明进一步改进在于，所述底板层、中间层与上盖层相配合界定出封闭的微流道、检测室和漏斗区域；所述底板层的下端的一侧设有一缺口，所述液体注入口、漏斗区域和缺口分别设置在上盖层、中间层和底板层上相对应的位置处且大小不同；所述芯片采样口由液体注入口、漏斗区域和缺口一起构成且通过所述微流道与所述检测室的底部相连接。将芯片采样口设置成漏斗样，底板面积大，顶盖面积小，中间层漏斗，这样的结构设置合理且结构简单，使样品更容易进入，且不被污染，提高检测的效率。
本发明进一步改进在于，所述液体注入口、漏斗区域和缺口均为弧形且弧度不同；所述液体注入口、漏斗区域均为半圆弧形，且所述漏斗区域的半径不小于所述液体注入口的圆弧半径；所述漏斗区域通过弯曲的主流通道分散出多个分微流体通道与所述多个相互独立的检测室一一连通；所述缺口的面积小于所述漏斗区域的面积；
或所述主流通道为漏斗区域，所述液体注入口为弧形，其与所述漏斗区域部分区域重叠；所述漏斗区域有开口处向内收敛形成喇叭状，且所述漏斗区域在其尾端处向内分散出多个分微流体通道，通过多个所述分微流体通道一一对应连接多个相互独立的检测室。其中液体注入口为半圆弧形，在面积相同的条件下，这种结构设置注入的样本量最多，且漏斗区域的半径不小于所述液体注入口的圆弧半径，使得漏斗区域可全部容纳从液体注入口注入的样本液体，不会有损失；设置弯曲流道，使得样本缓慢流入检测室，不至于造成检测室大气压的突增。
其中将液体注入口设置为弧形，其与所述漏斗区域部分区域重叠；所述漏斗区域有开口处向内收敛形成喇叭状使得样本逐渐向内流入，不在开口处停留，避免样本流失，例如使用这种结构的漏斗区域血液样本进入到采样口的速度在1秒左右，实现了血液样本快速吸进采样口里；设置缺口的作用是与手指肚相贴合，方便取样。
本发明进一步改进在于，所述底板层、中间层与上盖层通过是通过中间层双面胶合的方式键合成一体。
作为本发明的优选技术方案，所述中间层为压敏胶带，所述上盖层和/或所述底板层的材料为PMMA、PP、PE、PET中的任一种，且所述上盖层和所述底板层的表面均具有亲水膜，使样本快速通过所述芯片采样口流动进入主流通道，再分流到每一个分微流体通道。采用此技术方案，材料易得，且压敏胶带的制作工艺可以精度的控制其厚度，所以采用此技术方案，可以精确的控制微流道的深度和大小，同时也便于控制检测室的深度，使得微流体芯片的各 个检测室的厚度偏差小，一致性高，提高了检测的准确度；上盖层和底板层的表面均设置亲水膜，可以使样品更快速地通过芯片采样口流入主流通道并分流到每个分微流体通道，这样加快流动速度，可以提高检测效率。
作为本发明的优选技术方案，所述中间层的厚度为0.1～1.0mm；所述底板层的表面是平的，所述底板层、中间层与上盖层相配合界定出封闭的微流道的深度为0.1～1.0mm，相配合界定出的所述检测室的宽度为1.0～2.0mm。
作为本发明的优选技术方案，每一个所述分微流体通道在与所述检测室的连接处均具有喷嘴，并且每一个所述分微流体通道都具有相应的电极，每个电极包括输入高侧电极和输入低侧电极，所述电极的厚度为50um。在分微流体通道与检测室的连接处设有喷嘴是为了使样本更容易更快速地流入检测室；电极的作用是施加脉冲电压同时接受检测室中血液反应产生的信号；电极末端插入检测仪器中，通过检测反应产生的电化学信号，配合配套检测仪器得出检测结果；电极末端为所述底板层、中间层与上盖层键合成一体后相对于所述上盖层和中间层裸露在外的部分，使得电极末端能够更容易且方便地插到检测仪器中。
与现有技术相比，该多通道快速检测微流体检测芯片通过设计特定结构形式的主流通道和多个分微流体通道，用于引导血液样本的流动，使得一个样品腔室，能够同时向多个反应腔室注入样品且不污染样品，易进样；芯片采样口采样后，由主流通道同时分别流向多个分微流体通道，再进入多个相互独立的检测室，这样可以实现同时检测多个样本，具有多通道的效果；芯片结构简单，操作方便，提高了检测效率和精度，并大大减少了资源的消耗；实现快速检测，降低了成本。
附图说明
下面结合附图和本发明的实施方式进一步详细说明：
图1是本发明多通道快速检测微流体检测芯片实施例1的平面结构示意图；
图2是本发明多通道快速检测微流体检测芯片实施例1的立体结构示意图；
图3是本发明多通道快速检测微流体检测芯片实施例1的整体结构图；
图4是本发明多通道快速检测微流体检测芯片实施例2的平面结构示意图；
图5是本发明多通道快速检测微流体检测芯片实施例2的立体结构示意图；
图6是本发明多通道快速检测微流体检测芯片实施例2的整体结构图；
图7是本发明多通道快速检测微流体检测芯片实施例3的平面结构示意图；
图8是本发明多通道快速检测微流体检测芯片实施例3的立体结构示意图；
图9是本发明多通道快速检测微流体检测芯片实施例3的整体结构图；
其中：1-底板层；2-中间层；3-上盖层；4-电极；401-电极末端；5-微流道；501-主流通 道；502-分微流体通道；6-排气孔；7-芯片采样口；701-液体注入口；702-接液口；8-检测室；9-漏斗区域；10-缺口。
具体实施方式
实施例1：该多通道快速检测微流体检测芯片，包括芯片本体，所述芯片本体上设置有芯片采样口7、多个相互独立的检测室8和微流道5，所述芯片采样口7通过微流道5与所述检测室8连通，所述芯片本体还包括电极4，所述检测室8与所述电极4相连接；所述微流道5包括一条主流通道501和5个分微流体通道502，所述主流通道501的末端分流出5个所述分微流体通道502，5个所述分微流体通道502与5个相互独立的检测室8一一对应连通；所述主流通道501的另一端与所述芯片采样口7连通；所述芯片本体从下往上依次包括底板层1、中间层2和上盖层3，所述底板层1、中间层2与上盖层3相配合界定出封闭的微流道5和多个相互独立的检测室8；所述微流道5和检测室8在所述中间层2；所述上盖层3设有液体注入口701和5个排气孔6，所述5个排气孔6设置在所述上盖层的一侧且设置在与所述微流道5的末端相对应的位置处，所述液体注入口701与所述微流道5的前端相连通；所述底板层1上设有电极4，所述检测室8与所述电极4相连接；排气孔6的设置有利于样本的流动，方便进样，若没有设置排气孔6样本不能流进检测室8进行反应，芯片的检测室8内预先包埋检测试剂；5个相互独立的检测室8呈扇形分布，由所述主流通道501的末端分流成5个分微流体通道502再连通至5个相互独立的检测室8；所述底板层1、中间层2与上盖层3通过中间层2双面胶合的方式键合成一体；所述中间层2为压敏胶带，所述上盖层3和/或所述底板层1的材料为PMMA、PP、PE、PET中的任一种，且上盖层3和底板层1的表面具有亲水膜，使样本快速通过所述芯片采样口7流动进入主流通道501，再分流到每一个分微流体通道502；所述中间层2的厚度为0.1～1.0mm；所述底板层1的表面是平的，所述底板层1、中间层2与上盖层3相配合界定出封闭的微流道5的深度为0.1～1.0mm，相配合界定出的所述检测室8的宽度为1.0～2.0mm；每一个所述分微流体通道502在与所述检测室8的连接处均具有喷嘴，并且每一个所述分微流体通道502都具有相应的电极4，每个电极4包括输入高侧电极和输入低侧电极，所述电极4的厚度为50um；电极4的作用是施加脉冲电压同时接受检测室中血液反应产生的信号；电极末端401插入检测仪器中，通过检测反应产生的电化学信号，配合配套检测仪器得出检测结果；电极末端401为所述底板层1、中间层2与上盖层3键合成一体后相对于所述上盖层3和中间层2裸露在外的部分，使得电极末端401能够更容易且方便地插到检测仪器中，出来检测结果；其中如图1～3所示，所述芯片采样口7为液体注入口701，所述芯片采样口7与所述主流通道501连通，所述主流通道501的一端在与所述液体注入口701相对应的位置处设置有接液口702；所述主流通道501的另一端连 接所有的分微流体通道502。
实施例2：与实施例1不同之处在于芯片采样口7的结构不同，所述底板层1、中间层2与上盖层3相配合界定出封闭的微流道5、检测室8和漏斗区域9；所述底板层1的下端的一侧设有一缺口10，所述液体注入口701、漏斗区域9和缺口10分别设置在上盖层3、中间层2和底板层1上相对应的位置处且大小不同；所述芯片采样口7由液体注入口701、漏斗区域9和缺口10一起构成且通过所述微流道5与所述检测室8的底部相连接；具体地：该多通道快速检测微流体检测芯片，包括芯片本体，所述芯片本体上设置有芯片采样口7、多个相互独立的检测室8和微流道5，所述芯片采样口7通过微流道5与所述检测室8连通，所述芯片本体还包括电极4，所述检测室8与所述电极4相连接；所述微流道5包括一条主流通道501和5个分微流体通道502，所述主流通道501的末端分流出5个所述分微流体通道502，5个所述分微流体通道502与5个相互独立的检测室8一一对应连通；所述主流通道501的另一端与所述芯片采样口7连通；所述芯片本体从下往上依次包括底板层1、中间层2和上盖层3，所述底板层1、中间层2与上盖层3相配合界定出封闭的微流道5和多个相互独立的检测室8；所述微流道5和检测室8在所述中间层2；所述上盖层3设有液体注入口701和5个排气孔6，所述5个排气孔6设置在所述上盖层的一侧且设置在与所述微流道5的末端相对应的位置处，所述液体注入口701与所述微流道5的前端相连通；所述底板层1上设有电极4，所述检测室8与所述电极4相连接；排气孔6的设置有利于样本的流动，方便进样，若没有设置排气孔6样本不能流进检测室8进行反应，芯片的检测室8内预先包埋检测试剂；5个相互独立的检测室8呈扇形分布，由所述主流通道501的末端分流成5个分微流体通道502再连通至5个相互独立的检测室8；所述底板层1、中间层2与上盖层3通过中间层2双面胶合的方式键合成一体；所述中间层2为压敏胶带，所述上盖层3和/或所述底板层1的材料为PMMA、PP、PE、PET中的任一种，且上盖层3和底板层1的表面具有亲水膜，使样本快速通过所述芯片采样口7流动进入主流通道501，再分流到每一个分微流体通道502；所述中间层2的厚度为0.1～1.0mm；所述底板层1的表面是平的，所述底板层1、中间层2与上盖层3相配合界定出封闭的微流道5的深度为0.1～1.0mm，相配合界定出的所述检测室8的宽度为1.0～2.0mm；每一个所述分微流体通道502在与所述检测室8的连接处均具有喷嘴，并且每一个所述分微流体通道502都具有相应的电极4，每个电极4包括输入高侧电极和输入低侧电极，所述电极4的厚度为50um；电极4的作用是施加脉冲电压同时接受检测室中血液反应产生的信号；电极末端401插入检测仪器中，通过检测反应产生的电化学信号，配合配套检测仪器得出检测结果；电极末端401为所述底板层1、中间层2与上盖层3键合成一体后相对于所述上盖层3和中间层2裸露在外的部分，使得电极末端401能够更容易且方便地 插到检测仪器中，出来检测结果；如图4～6所示，所述底板层1、中间层2与上盖层3相配合界定出封闭的微流道5、检测室8和漏斗区域9；所述底板层1的下端的一侧设有一缺口10，所述液体注入口701、漏斗区域9和缺口10分别设置在上盖层3、中间层2和底板层1上相对应的位置处且大小不同；所述芯片采样口7由液体注入口701、漏斗区域9和缺口10一起构成且通过所述微流道5与所述检测室8的底部相连接；所述主流通道501为漏斗区域9，所述液体注入口701为弧形，其与所述漏斗区域9部分区域重叠；所述漏斗区域9有开口处向内收敛形成喇叭状，且所述漏斗区域9在其尾端处向内分散出5个分微流体通道502，通过5个所述分微流体通道502一一对应连接5个相互独立的检测室8；其中将液体注入口701设置为弧形，其与所述漏斗区域9部分区域重叠；所述漏斗区域9有开口处向内收敛形成喇叭状使得样本逐渐向内流入，不在开口处停留，避免样本流失。
实施例3：与实施例1不同之处在于芯片采样口的结构不同，所述底板层1、中间层2与上盖层3相配合界定出封闭的微流道5、检测室8和漏斗区域9；所述底板层1的下端的一侧设有一缺口10，所述液体注入口701、漏斗区域9和缺口10分别设置在上盖层3、中间层2和底板层1上相对应的位置处且大小不同；所述芯片采样口7由液体注入口701、漏斗区域9和缺口10一起构成且通过所述微流道5与所述检测室8的底部相连接；具体地：该多通道快速检测微流体检测芯片，包括芯片本体，所述芯片本体上设置有芯片采样口7、多个相互独立的检测室8和微流道5，所述芯片采样口7通过微流道5与所述检测室8连通，所述芯片本体还包括电极4，所述检测室8与所述电极4相连接；所述微流道5包括一条主流通道501和5个分微流体通道502，所述主流通道501的末端分流出5个所述分微流体通道502，5个所述分微流体通道502与5个相互独立的检测室8一一对应连通；所述主流通道501的另一端与所述芯片采样口7连通；所述芯片本体从下往上依次包括底板层1、中间层2和上盖层3，所述底板层1、中间层2与上盖层3相配合界定出封闭的微流道5和多个相互独立的检测室8；所述微流道5和检测室8在所述中间层2；所述上盖层3设有液体注入口701和5个排气孔6，所述5个排气孔6设置在所述上盖层的一侧且设置在与所述微流道5的末端相对应的位置处，所述液体注入口701与所述微流道5的前端相连通；所述底板层1上设有电极4，所述检测室8与所述电极4相连接；排气孔6的设置有利于样本的流动，方便进样，若没有设置排气孔6样本不能流进检测室8进行反应，芯片的检测室8内预先包埋检测试剂；5个相互独立的检测室8呈扇形分布，由所述主流通道501的末端分流成5个分微流体通道502再连通至5个相互独立的检测室8；所述底板层1、中间层2与上盖层3通过中间层2双面胶合的方式键合成一体；所述中间层2为压敏胶带，所述上盖层3和/或所述底板层1的材料为PMMA、PP、PE、PET中的任一种，且上盖层3和底板层1的表面具有亲水膜，使样本快速通过所述 芯片采样口7流动进入主流通道501，再分流到每一个分微流体通道502；所述中间层2的厚度为0.1～1.0mm；所述底板层1的表面是平的，所述底板层1、中间层2与上盖层3相配合界定出封闭的微流道5的深度为0.1～1.0mm，相配合界定出的所述检测室8的宽度为1.0～2.0mm；每一个所述分微流体通道502在与所述检测室8的连接处均具有喷嘴，并且每一个所述分微流体通道502都具有相应的电极4，每个电极4包括输入高侧电极和输入低侧电极，所述电极4的厚度为50um；电极4的作用是施加脉冲电压同时接受检测室中血液反应产生的信号；电极末端401插入检测仪器中，通过检测反应产生的电化学信号，配合配套检测仪器得出检测结果；电极末端401为所述底板层1、中间层2与上盖层3键合成一体后相对于所述上盖层3和中间层2裸露在外的部分，使得电极末端401能够更容易且方便地插到检测仪器中，出来检测结果；如图7～9所示，所述底板层1、中间层2与上盖层3相配合界定出封闭的微流道5、检测室8和漏斗区域9；所述底板层1的下端的一侧设有一缺口10，所述液体注入口701、漏斗区域9和缺口10分别设置在上盖层3、中间层2和底板层1上相对应的位置处且大小不同；所述芯片采样口7由液体注入口701、漏斗区域9和缺口10一起构成且通过所述微流道5与所述检测室8的底部相连接；其中所述液体注入口701、漏斗区域9和缺口10均为弧形且弧度不同；所述液体注入口701、漏斗区域9均为半圆弧形，且所述漏斗区域9的半径不小于所述液体注入口701的圆弧半径；所述漏斗区域9通过弯曲的主流通道501分散出5个分微流体通道502与所述5个相互独立的检测室8一一连通；所述缺口10的面积小于所述漏斗区域9的面积。其中液体注入口701为半圆弧形，在面积相同的条件下，这种结构设置注入的样本量最多，且漏斗区域9的半径不小于所述液体注入口701的圆弧半径，使得漏斗区域9可全部容纳从液体注入口注入的样本液体，不会有损失；设置弯曲流道，使得样本缓慢流入检测室8，不至于造成检测室8大气压的突增。
具体使用时：
向芯片采样口7注入样本，样本通过由主流通道501同时分别流向多个分微流体通道502，再进入多个相互独立的检测室8，样本与检测室8内预先包埋的检测试剂进行反应，并将该多通道快速检测微流体检测芯片通过电极末端401插入检测仪器中，通过检测反应产生的电化学信号，配合配套检测仪器得出检测结果；这样可以实现同时检测多个样本，具有多通道的效果；提高了检测效率。
以上显示和描述了本发明的基本原理、主要特征及优点。本行业的技术人员应该了解，本发明不受上述实施例的限制，上述实施例和说明书中描述的只是说明本发明的原理，在不脱离本发明精神和范围的前提下，本发明还会有各种变化和改进，例如芯片采样口的形状和结构做一些其它微略的调整，这些变化和改进都落入要求保护的本发明范围内。本发明要求 保护范围由所附的权利要求书及其等效物界定。

Claims (10)

  1. 一种多通道快速检测微流体检测芯片，包括芯片本体，所述芯片本体上设置有芯片采样口、多个相互独立的检测室和微流道，所述芯片采样口通过微流道与所述检测室连通，其特征在于，所述芯片本体还包括电极，所述检测室与所述电极相连接；所述微流道包括一条主流通道和多个分微流体通道，所述主流通道的末端分流出多个所述分微流体通道，多个所述分微流体通道与多个相互独立的检测室一一对应连通；所述主流通道的另一端与所述芯片采样口连通。
  2. 根据权利要求1所述的多通道快速检测微流体检测芯片，其特征在于，所述芯片本体从下往上依次包括底板层、中间层和上盖层，所述底板层、中间层与上盖层相配合界定出封闭的微流道和多个相互独立的检测室；所述微流道和检测室在所述中间层；所述上盖层设有液体注入口和多个排气孔，所述多个排气孔设置在所述上盖层的一侧且设置在与所述微流道的末端相对应的位置处，所述液体注入口与所述微流道的前端相连通；所述底板层上设有电极，所述检测室与所述电极相连接。
  3. 根据权利要求2所述的多通道快速检测微流体检测芯片，其特征在于，多个相互独立的检测室呈扇形分布，由所述主流通道的末端分流成多个分微流体通道再连通至多个相互独立的检测室。
  4. 根据权利要求3所述的多通道快速检测微流体检测芯片，其特征在于，所述芯片采样口由液体注入口构成，所述芯片采样口与所述主流通道连通，所述主流通道的一端在与所述液体注入口相对应的位置处设置有接液口；所述主流通道的另一端连接所有的分微流体通道。
  5. 根据权利要求3所述的多通道快速检测微流体检测芯片，其特征在于，所述底板层、中间层与上盖层相配合界定出封闭的微流道、检测室和漏斗区域；所述底板层的下端的一侧设有一缺口，所述液体注入口、漏斗区域和缺口分别设置在上盖层、中间层和底板层上相对应的位置处且大小不同；所述芯片采样口由液体注入口、漏斗区域和缺口一起构成且通过所述微流道与所述检测室的底部相连接。
  6. 根据权利要求5所述的多通道快速检测微流体检测芯片，其特征在于，所述液体注入口、漏斗区域和缺口均为弧形且弧度不同；所述液体注入口、漏斗区域均为半圆弧形，且所述漏斗区域的半径不小于所述液体注入口的圆弧半径；所述漏斗区域通过弯曲的主流通道分散出多个分微流体通道与所述多个相互独立的检测室一一连通；所述缺口的面积小于所述漏斗区域的面积；
    或所述主流通道为漏斗区域，所述液体注入口为弧形，其与所述漏斗区域部分区域重叠；所 述漏斗区域有开口处向内收敛形成喇叭状，使得样本逐渐向内流入，不在开口处停留，避免样本流失；且所述漏斗区域在其尾端处向内分散出多个分微流体通道，通过多个所述分微流体通道一一对应连接多个相互独立的检测室。
  7. 根据权利要求5所述的多通道快速检测微流体检测芯片，其特征在于，所述底板层、中间层与上盖层通过是通过中间层双面胶合的方式键合成一体。
  8. 根据权利要求3-7任一项所述的多通道快速检测微流体检测芯片，其特征在于，所述中间层为压敏胶带，所述上盖层和/或所述底板层的材料为PMMA、PP、PE、PET中的任一种，且所述上盖层和所述底板层的表面均具有亲水膜，使样本快速通过所述芯片采样口流动进入主流通道，再分流到每一个分微流体通道。
  9. 根据权利要求8所述的多通道快速检测微流体检测芯片，其特征在于，所述中间层的厚度为0.1～1.0mm；所述底板层的表面是平的，所述底板层、中间层与上盖层相配合界定出封闭的微流道的深度为0.1～1.0mm，相配合界定出的所述检测室的宽度为1.0～2.0mm。
  10. 根据权利要求8所述的多通道快速检测微流体检测芯片，其特征在于，每一个所述分微流体通道在与所述检测室的连接处均具有喷嘴，并且每一个所述分微流体通道都具有相应的电极，每个电极包括输入高侧电极和输入低侧电极，所述电极的厚度为50um。
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Cited By (2)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
CN120515509A (zh) * 2025-07-23 2025-08-22 湖南宏怡生物科技有限公司 干式生化微流控检测芯片、干化学试纸及其组合
WO2025217812A1 (zh) * 2024-04-16 2025-10-23 深圳华大智造科技股份有限公司 微流控芯片、样本处理系统及其应用、以及样本处理方法

Families Citing this family (30)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
CN108745429B (zh) * 2018-06-12 2023-11-24 南京岚煜生物科技有限公司 一种多通道快速检测微流体检测芯片
CN109709316A (zh) * 2018-12-27 2019-05-03 天津昌和生物医药技术有限公司 一种多靶项微流测试卡及制备方法
CN109682878B (zh) * 2019-03-01 2024-07-05 南京岚煜生物科技有限公司 一种具有五层结构的多通道微流体凝血检测芯片
CN209829010U (zh) * 2019-03-01 2019-12-24 南京岚煜生物科技有限公司 一种多通道微流体凝血检测芯片
CN111912769B (zh) * 2019-05-09 2025-08-05 苏州中科苏净生物技术有限公司 一种生乳体细胞计数仪及其计数方法
CN111912770A (zh) * 2019-05-09 2020-11-10 磐创精准(北京)生物科技有限公司 一种手持式白细胞计数仪及白细胞计数方法
CN111912771B (zh) * 2019-05-09 2025-10-21 苏州中科苏净生物技术有限公司 一种免疫检测联合白细胞计数的同步检测装置及其检测方法
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CN111912766B (zh) * 2019-05-09 2025-10-21 苏州中科苏净生物技术有限公司 免疫检测与细胞分析用组合检测卡及联合检测方法
CN111912669B (zh) * 2019-05-09 2025-07-18 苏州中科苏净生物技术有限公司 一种狭缝式液体取样检测腔室结构及取样方法
CN111912768B (zh) * 2019-05-09 2025-07-25 苏州中科苏净生物技术有限公司 一种白细胞计数仪及白细胞计数方法
CN111912765B (zh) * 2019-05-09 2025-07-25 苏州中科苏净生物技术有限公司 一种生乳细胞分析用微流控芯片及微流控取样装置
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WO2021164021A1 (en) * 2020-02-21 2021-08-26 Boe Technology Group Co., Ltd. Microfluidic structure, microfluidic system, microfluidic method, and method of fabricating microfluidic structure
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CN116474848A (zh) * 2023-04-25 2023-07-25 苏州中科苏净生物技术有限公司 一种电化学微流控芯片及核酸检测方法
CN117686435A (zh) * 2023-12-07 2024-03-12 华中农业大学 用于透明流体类食品检测的微流控芯片及制造方法
WO2025123586A1 (zh) * 2023-12-14 2025-06-19 苏州先达基因科技有限公司 一种具有反应腔和检测腔的双腔室核酸检测离心微流控芯片及检测方法

Citations (8)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
CN102841213A (zh) * 2012-09-09 2012-12-26 浙江大学 无动力顺序进样的微流体自动进样装置及应用
CN103755777A (zh) * 2014-01-16 2014-04-30 国家纳米科学中心 一种气控固相多肽合成微流控芯片装置及其应用
US20150111196A1 (en) * 2013-07-16 2015-04-23 Premium Genetics (Uk) Ltd. Microfluidic chip
CN105289763A (zh) * 2015-09-24 2016-02-03 基蛋生物科技股份有限公司 一种定量分流的多指标检测微流控芯片
CN205361375U (zh) 2015-12-30 2016-07-06 深圳市合川科技有限公司 一种微流体芯片
CN206701297U (zh) * 2017-03-10 2017-12-05 山东华芯电子有限公司 一种多指标检测微流控芯片
CN206756858U (zh) * 2016-10-11 2017-12-15 赵天贤 一种液体样本导流装置、检测试条及检测仪器
CN108745429A (zh) * 2018-06-12 2018-11-06 南京岚煜生物科技有限公司 一种多通道快速检测微流体检测芯片

Family Cites Families (11)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US5902731A (en) * 1998-09-28 1999-05-11 Lifescan, Inc. Diagnostics based on tetrazolium compounds
CN1325658C (zh) * 2001-04-23 2007-07-11 三星电子株式会社 包含mosfet分子检测芯片和采用该芯片的分子检测装置以及使用该装置的分子检测方法
US7108775B2 (en) * 2002-11-08 2006-09-19 Applera Corporation Apparatus and method for confining eluted samples in electrophoresis systems
GB0324641D0 (en) * 2003-10-22 2003-11-26 Unipath Ltd Coagulation detection method
US20080297169A1 (en) * 2007-05-31 2008-12-04 Greenquist Alfred C Particle Fraction Determination of A Sample
CN104697987B (zh) * 2013-12-06 2019-01-22 中国科学院深圳先进技术研究院 一种微流控液体波导电化学发光检测装置
CN203899622U (zh) * 2014-06-19 2014-10-29 博奥生物集团有限公司 一种微流控芯片
CN106622408A (zh) * 2016-11-01 2017-05-10 南京邮电大学 一种基于mhd控制的微流控芯片
CN107855142B (zh) * 2017-11-01 2024-07-05 深圳市第二人民医院 一种基于微流控技术的检测芯片及检测设备
CN107942083B (zh) * 2017-11-14 2020-10-02 东南大学 用于秀丽线虫的微流控电阻抗检测分选芯片、系统及方法
CN208554242U (zh) * 2018-06-12 2019-03-01 南京岚煜生物科技有限公司 一种多通道快速检测微流体检测芯片

Patent Citations (8)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
CN102841213A (zh) * 2012-09-09 2012-12-26 浙江大学 无动力顺序进样的微流体自动进样装置及应用
US20150111196A1 (en) * 2013-07-16 2015-04-23 Premium Genetics (Uk) Ltd. Microfluidic chip
CN103755777A (zh) * 2014-01-16 2014-04-30 国家纳米科学中心 一种气控固相多肽合成微流控芯片装置及其应用
CN105289763A (zh) * 2015-09-24 2016-02-03 基蛋生物科技股份有限公司 一种定量分流的多指标检测微流控芯片
CN205361375U (zh) 2015-12-30 2016-07-06 深圳市合川科技有限公司 一种微流体芯片
CN206756858U (zh) * 2016-10-11 2017-12-15 赵天贤 一种液体样本导流装置、检测试条及检测仪器
CN206701297U (zh) * 2017-03-10 2017-12-05 山东华芯电子有限公司 一种多指标检测微流控芯片
CN108745429A (zh) * 2018-06-12 2018-11-06 南京岚煜生物科技有限公司 一种多通道快速检测微流体检测芯片

Non-Patent Citations (1)

* Cited by examiner, † Cited by third party
Title
See also references of EP3698872A4

Cited By (2)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
WO2025217812A1 (zh) * 2024-04-16 2025-10-23 深圳华大智造科技股份有限公司 微流控芯片、样本处理系统及其应用、以及样本处理方法
CN120515509A (zh) * 2025-07-23 2025-08-22 湖南宏怡生物科技有限公司 干式生化微流控检测芯片、干化学试纸及其组合

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