Microfluidic detection chip for multi-channel rapid detection

Abstract

A microfluidic detection chip for multi-channel rapid detection, including a chip body. A chip sampling port, a plurality of independent detection chambers, and a microfluidic channel are disposed on the chip body, and the chip sampling port is connected to the detection chambers by means of the microfluidic channel. The chip body further includes an electrode. The detection chambers are connected to the electrode. The microfluidic channel includes a main flow channel and a plurality of branching microfluidic channels. A tail end of the main flow channel is divided into the plurality of branching microfluidic channels, and the plurality of branching microfluidic channels are connected to the plurality of independent detection chambers in a one-to-one corresponding manner. And, the other end of the main flow channel is connected to the chip sampling port.

Claims

1. A microfluidic detection chip for multi-channel rapid detection, comprising a chip body, a chip sampling port, a plurality of independent detection chambers, and a microfluidic channel being disposed on the chip body, the chip sampling port being connected to the detection chambers by means of the microfluidic channel, wherein the chip body further comprises an electrode, and the detection chambers are connected to the electrode; the microfluidic channel comprises a main flow channel and a plurality of branching microfluidic channels, a tail end of the main flow channel is divided into the plurality of branching microfluidic channels, and the plurality of branching microfluidic channels are connected to the plurality of independent detection chambers in a one-to-one corresponding manner; and the other end of the main flow channel is connected to the chip sampling port, wherein the chip body comprises a bottom plate layer, an intermediate layer, and an upper cover layer in sequence from bottom to top, the bottom plate layer, the intermediate layer, and the upper cover layer cooperatively defining a closed microfluidic channel and the plurality of independent detection chambers; the microfluidic channel and the detection chambers are located in the intermediate layer; a liquid injection port and a plurality of exhaust holes are disposed on the upper cover layer, the plurality of exhaust holes are disposed on one side of the upper cover layer corresponding to a tail end of the microfluidic channel, and the liquid injection port is connected to a front end of the microfluidic channel; and the electrode is disposed on the bottom plate layer, wherein the plurality of independent detection chambers are distributed in a fan shape, and the tail end of the main flow channel is divided into the plurality of branching microfluidic channels, and the plurality of branching microfluidic channels are then connected to the plurality of independent detection chambers, wherein the chip sampling port is composed of the liquid injection port; the chip sampling port is connected to the main flow channel, and a liquid receiving port is disposed on one end of the main flow channel corresponding to the liquid injection port; and the other end of the main flow channel is connected to all of the branching microfluidic channels, wherein the liquid injection port, a funnel region, and a notch are all arc-shaped and having different radians; the liquid injection port and the funnel region are semicircular arc-shaped, and a radius of the funnel region is not less than an arc radius of the liquid injection port; a curved main flow channel in the funnel region is divided into the plurality of branching microfluidic channels which are connected to the plurality of independent detection chambers in a one-to-one corresponding manner; and an area of the notch is smaller than an area of the funnel region; or the main flow channel is the funnel region; the liquid injection port is arc-shaped, and overlaps with a part of the funnel region; the funnel region is converged inward from an opening to form a horn shape, so that samples gradually flow inward without stopping at the opening, thereby avoiding loss of the samples; and the funnel region is inwardly divided into the plurality of branching microfluidic channels at the tail end thereof, and the plurality of branching microfluidic channels are connected to the plurality of independent detection chambers in a one-to-one correspondence manner.

2. The microfluidic detection chip for multi-channel rapid detection according to claim 1, wherein the bottom plate layer, the intermediate layer, and the upper cover layer are integrally bonded together by means of double-sided gluing of the intermediate layer.

3. The microfluidic detection chip for multi-channel rapid detection according to claim 1, wherein the intermediate layer is a pressure-sensitive adhesive tape; a material of the upper cover layer and/or the bottom plate layer is any one of PMMA, PP, PE, and PET; and surfaces of the upper cover layer and the bottom plate layer each has a hydrophilic membrane, so that the samples flow rapidly through the chip sampling port into the main flow channel, and then are distributed to each of the branching microfluidic channels.

4. The microfluidic detection chip for multi-channel rapid detection according to claim 3, wherein a thickness of the intermediate layer is 0.1 mm-1.0 mm; the surface of the bottom plate layer is flat; a depth of the closed microfluidic channel cooperatively defined by the bottom plate layer, the intermediate layer, and the upper cover layer is 0.1 mm-1.0 mm and a width of the detection chambers cooperatively defined by the bottom plate layer, the intermediate layer, and the upper cover layer is 1.0 mm-2.0 mm.

5. The microfluidic detection chip for multi-channel rapid detection according to claim 3, wherein a nozzle is disposed at a junction of each of the branching microfluidic channels and the corresponding detection chamber, and each of the branching microfluidic channels has the corresponding electrode; each of the electrode comprises an input high-side electrode and an input low-side electrode, and the thickness of the electrode is 50 μm.

Description

BRIEF DESCRIPTION OF THE DRAWINGS

(1) The detailed description is further provided below with reference to the accompanying drawings and embodiments of the present invention.

(2) FIG. 1 is a schematic planar structural diagram of Embodiment 1 of a microfluidic detection chip for multi-channel rapid detection according to the present invention;

(3) FIG. 2 is a schematic perspective structural diagram of Embodiment 1 of a microfluidic detection chip for multi-channel rapid detection according to the present invention;

(4) FIG. 3 is an overall structural diagram of Embodiment 1 of a microfluidic detection chip for multi-channel rapid detection according to the present invention;

(5) FIG. 4 is a schematic planar structural diagram of Embodiment 2 of a microfluidic detection chip for multi-channel rapid detection according to the present invention;

(6) FIG. 5 is a schematic perspective structural diagram of Embodiment 2 of a microfluidic detection chip for multi-channel rapid detection according to the present invention;

(7) FIG. 6 is an overall structural diagram of Embodiment 2 of a microfluidic detection chip for multi-channel rapid detection according to the present invention;

(8) FIG. 7 is a schematic planar structural diagram of Embodiment 3 of a microfluidic detection chip for multi-channel rapid detection according to the present invention;

(9) FIG. 8 is a schematic perspective structural diagram of Embodiment 3 of a microfluidic detection chip for multi-channel rapid detection according to the present invention; and

(10) FIG. 9 is an overall structural diagram of Embodiment 3 of a microfluidic detection chip for multi-channel rapid detection according to the present invention.

DETAILED DESCRIPTION OF THE EMBODIMENT

(11) Embodiment 1: the microfluidic detection chip for multi-channel rapid detection includes a chip body. A chip sampling port 7, a plurality of independent detection chambers 8, and a microfluidic channel 5 are disposed on the chip body. The chip sampling port 7 is connected to the detection chambers 8 by means of the microfluidic channel 5. The chip body further includes an electrode 4. The detection chambers 8 are connected to the electrode 4. The microfluidic channel 5 includes a main flow channel 501 and five branching microfluidic channels 502. A tail end of the main flow channel 501 is divided into five branching microfluidic channels 502, and the five branching microfluidic channels 502 are connected to five independent detection chambers 8 in a one-to-one corresponding manner. The other end of the main flow channel 501 is connected to the chip sampling port 7. The chip body includes a bottom plate layer 1, an intermediate layer 2, and an upper cover layer 3 in sequence from bottom to top. The bottom plate layer 1, the intermediate layer 2, and the upper cover layer 3 cooperatively define a closed microfluidic channel 5 and a plurality of independent detection chambers 8. The microfluidic channel 5 and the detection chambers 8 are located in the intermediate layer 2. A liquid injection port 701 and five exhaust holes 6 are disposed on the upper cover layer 3. The five exhaust holes 6 are disposed on one side of the upper cover layer corresponding to the tail end of the microfluidic channel 5, and the liquid injection port 701 is connected to a front end of the microfluidic channel 5. An electrode 4 is disposed on the bottom plate layer 1, and the detection chambers 8 are connected to the electrode 4. The provision of the exhaust holes 6 is beneficial to the flow of the samples and facilitates the sample injection. If no exhaust hole 6 is disposed, the samples cannot flow into the detection chamber 8 for reaction. Detection reagents are embedded in the detection chambers 8 of the chip in advance. Five independent detection chambers 8 are distributed in a fan shape, and the tail end of the main flow channel 501 is divided into five branching microfluidic channels 502, and the plurality of branching microfluidic channels 502 are then connected to five independent detection chambers 8. The bottom plate layer 1, the intermediate layer 2, and the upper cover layer 3 are integrally bonded together by means of double-sided gluing of the intermediate layer 2. The intermediate layer 2 is a pressure-sensitive adhesive tape. The material of the upper cover layer 3 and/or the bottom plate layer 1 is any one of PMMA, PP, PE and PET, and the surfaces of the upper cover layer 3 and the bottom plate layer 1 each has a hydrophilic membrane, so that the samples flow rapidly through the chip sampling port 7 into the main flow channel 501, and then are distributed to each branching microfluidic channel 502. The thickness of the intermediate layer 2 is 0.1 mm-1.0 mm. The surface of the bottom plate layer 1 is flat. The depth of the closed microfluidic channel 5 cooperatively defined by the bottom plate layer 1, the intermediate layer 2, and the upper cover layer 3 is 0.1 mm-1.0 mm, and the width of the detection chambers 8 cooperatively defined by the bottom plate layer 1, the intermediate layer 2, and the upper cover layer 3 is 1.0 mm-2.0 mm. A nozzle is disposed at the junction of each of the branching microfluidic channels 502 and the corresponding detection chamber 8, and each of the branching microfluidic channels 502 has a corresponding electrode 4. Each electrode 4 comprises an input high-side electrode and an input low-side electrode, and the thickness of the electrode 4 is 50 μm. The electrode 4 is provided for applying a pulse voltage while receiving a signal generated by the blood reaction in the detection chambers. An electrode tip 401 is inserted into a detection instrument, and a detection result is obtained by detecting an electrochemical signal generated by the reaction in cooperation with the supporting detection instrument. The electrode tip 401 is a part of the integrally bonded bottom plate layer 1, intermediate layer 2 and upper cover layer 3 that is exposed outside relative to the upper cover layer 3 and the intermediate layer 2, so that the electrode tip 401 may be inserted into the detection instrument more easily and conveniently, so as to obtain the detection result. As shown in FIG. 1 to FIG. 3, the chip sampling port 7 is a liquid injection port 701 and is connected to the main flow channel 501, a liquid receiving port 702 is disposed on one end of the main flow channel 501 corresponding to the liquid injection port 701, and the other end of the main flow channel 501 is connected to all the branching microfluidic channels 502.

(12) Embodiment 2: the differences from Embodiment 1 are in that: the structure of the chip sampling port 7 is different, and the bottom plate layer 1, the intermediate layer 2 and the upper cover layer 3 cooperatively defining a closed microfluidic channel 5, detection chambers 8, and a funnel region 9. A notch 10 is disposed on one side of a lower end of the bottom plate layer 1. The liquid injection port 701, the funnel region 9, and the notch 10 are respectively disposed at corresponding positions on the upper cover layer 3, the intermediate layer 2, and the bottom plate layer 1 and have different sizes. The chip sampling port 7 is composed of the liquid injection port 701, the funnel region 9, and the notch 10 and the chip sampling port 7 is connected to the bottom of the detection chambers 8 by means of the microfluidic channel 5. Specifically, the microfluidic detection chip for multi-channel rapid detection includes a chip body. A chip sampling port 7, a plurality of independent detection chambers 8, and a microfluidic channel 5 are disposed on the chip body. The chip sampling port 7 is connected to the detection chambers 8 by means of the microfluidic channel 5. The chip body further includes an electrode 4. The detection chambers 8 are connected to the electrode 4. The microfluidic channel 5 includes a main flow channel 501 and five branching microfluidic channels 502, a tail end of the main flow channel 501 is divided into five branching microfluidic channels 502, and the five branching microfluidic channels 502 are connected to five independent detection chambers 8 in a one-to-one corresponding manner. The other end of the main flow channel 501 is connected to the chip sampling port 7. The chip body includes a bottom plate layer 1, an intermediate layer 2, and an upper cover layer 3 in sequence from bottom to top. The bottom plate layer 1, the intermediate layer 2, and the upper cover layer 3 cooperatively define a closed microfluidic channel 5 and a plurality of independent detection chambers 8. The microfluidic channel 5 and the detection chambers 8 are located in the intermediate layer 2. A liquid injection port 701 and five exhaust holes 6 are disposed on the upper cover layer 3. The five exhaust holes 6 are provided on one side of the upper cover layer corresponding to the tail end of the microfluidic channel 5, and the liquid injection port 701 is connected to a front end of the microfluidic channel 5. An electrode 4 is disposed on the bottom plate layer 1, and the detection chambers 8 are connected to the electrode 4. The provision of the exhaust holes 6 is beneficial to the flow of the samples and facilitates the sample injection. If no exhaust hole 6 is disposed, the samples cannot flow into the detection chamber 8 for reaction. Detection reagents are embedded in the detection chambers 8 of the chip in advance. Five independent detection chambers 8 are distributed in a fan shape, and the tail end of the main flow channel 501 is divided into five branching microfluidic channels 502, and the plurality of branching microfluidic channels 502 are then connected to five independent detection chambers 8. The bottom plate layer 1, the intermediate layer 2, and the upper cover layer 3 are integrally bonded together by means of double-sided gluing of the intermediate layer 2. The intermediate layer 2 is a pressure-sensitive adhesive tape. The material of the upper cover layer 3 and/or the bottom plate layer 1 is any one of PMMA, PP, PE and PET, and the surfaces of the upper cover layer 3 and the bottom plate layer 1 each has a hydrophilic membrane, so that the samples flow rapidly through the chip sampling port 7 into the main flow channel 501, and then are distributed to each branching microfluidic channel 502. The thickness of the intermediate layer 2 is 0.1 mm-1.0 mm. The surface of the bottom plate layer 1 is flat. The depth of the closed microfluidic channel 5 cooperatively defined by the bottom plate layer 1, the intermediate layer 2, and the upper cover layer 3 is 0.1 mm-1.0 mm, and the width of the detection chambers 8 defined is 1.0 mm-2.0 mm. A nozzle is disposed at the junction of each of the branching microfluidic channels 502 and the corresponding detection chamber 8, and each of the branching microfluidic channels 502 has a corresponding electrode 4. Each electrode 4 comprises an input high-side electrode and an input low-side electrode, and the thickness of the electrode 4 is 50 μm. The electrode 4 is provided for applying a pulse voltage while receiving a signal generated by the blood reaction in the detection chambers. An electrode tip 401 is inserted into a detection instrument, and a detection result is obtained by detecting an electrochemical signal generated by the reaction in cooperation with the supporting detection instrument. The electrode tip 401 is a part of the integrally bonded bottom plate layer 1, intermediate layer 2 and upper cover layer 3 that is exposed outside relative to the upper cover layer 3 and the intermediate layer 2, so that the electrode tip 401 may be inserted into the detection instrument more easily and conveniently, so as to obtain the detection result. As shown in FIG. 4 to FIG. 6, the bottom plate layer 1, the intermediate layer 2, and the upper cover layer 3 cooperatively defining a closed microfluidic channel 5, detection chambers 8, and a funnel region 9. A notch 10 is disposed on one side of a lower end of the bottom plate layer 1. The liquid injection port 701, the funnel region 9, and the notch 10 are respectively disposed at corresponding positions on the upper cover layer 3, the intermediate layer 2, and the bottom plate layer 1 and have different sizes. The chip sampling port 7 is composed of the liquid injection port 701, the funnel region 9, and the notch 10 and the chip sampling port 7 is connected to the bottom of the detection chambers 8 by means of the microfluidic channel 5. The main flow channel 501 is the funnel region 9. The liquid injection port 701 is arc-shaped, and overlaps with a part of the funnel region 9. The funnel region 9 is converged inward from an opening to form a horn shape, and the funnel region 9 is inwardly divided into five branching microfluidic channels 502 at the tail end thereof, and the five branching microfluidic channels 502 are connected to the five independent detection chambers 8 in a one-to-one corresponding manner. The liquid injection port 701 is set to an arc shape, and overlaps with a part of the funnel region 9. The funnel region 9 is converged inward from an opening to form a horn shape, so that samples gradually flow inward without stopping at the opening, thereby avoiding sample loss.

(13) Embodiment 3: the differences from Embodiment 1 are in that: the structure of the chip sampling port is different, and the bottom plate layer 1, the intermediate layer 2 and the upper cover layer 3 cooperatively defining a closed microfluidic channel 5, detection chambers 8, and a funnel region 9. A notch 10 is disposed on one side of a lower end of the bottom plate layer 1. The liquid injection port 701, the funnel region 9, and the notch 10 are respectively disposed at corresponding positions on the upper cover layer 3, the intermediate layer 2, and the bottom plate layer 1 and have different sizes. The chip sampling port 7 is composed of the liquid injection port 701, the funnel region 9, and the notch 10 and the chip sampling port 7 is connected to the bottom of the detection chambers 8 by means of the microfluidic channel 5. Specifically, the microfluidic detection chip for multi-channel rapid detection includes a chip body. A chip sampling port 7, a plurality of independent detection chambers 8, and a microfluidic channel 5 are disposed on the chip body. The chip sampling port 7 is connected to the detection chambers 8 by means of the microfluidic channel 5. The chip body further includes an electrode 4. The detection chambers 8 are connected to the electrode 4. The microfluidic channel 5 includes a main flow channel 501 and five branching microfluidic channels 502. A tail end of the main flow channel 501 is divided into five branching microfluidic channels 502, and the five branching microfluidic channels 502 are connected to five independent detection chambers 8 in a one-to-one corresponding manner. The other end of the main flow channel 501 is connected to the chip sampling port 7. The chip body includes a bottom plate layer 1, an intermediate layer 2, and an upper cover layer 3 in sequence from bottom to top. The bottom plate layer 1, the intermediate layer 2, and the upper cover layer 3 cooperatively define a closed microfluidic channel 5 and a plurality of independent detection chambers 8.

(14) The microfluidic channel 5 and the detection chambers 8 are located in the intermediate layer 2. A liquid injection port 701 and five exhaust holes 6 are disposed on the upper cover layer 3. The five exhaust holes 6 are disposed on one side of the upper cover layer corresponding to the tail end of the microfluidic channel 5, and the liquid injection port 701 is connected to a front end of the microfluidic channel 5. An electrode 4 is disposed on the bottom plate layer 1, and the detection chambers 8 are connected to the electrode 4. The provision of the exhaust holes 6 is beneficial to the flow of the samples and facilitates the sample injection. If no exhaust hole 6 is provided, the samples cannot flow into the detection chamber 8 for reaction. Detection reagents are embedded in the detection chambers 8 of the chip in advance. Five independent detection chambers 8 are distributed in a fan shape, and the tail end of the main flow channel 501 is divided into five branching microfluidic channels 502, and the plurality of branching microfluidic channels 502 are then connected to five independent detection chambers 8. The bottom plate layer 1, the intermediate layer 2, and the upper cover layer 3 are integrally bonded together by means of double-sided gluing of the intermediate layer 2. The intermediate layer 2 is a pressure-sensitive adhesive tape. The material of the upper cover layer 3 and/or the bottom plate layer 1 is any one of PMMA, PP, PE and PET, and the surfaces of the upper cover layer 3 and the bottom plate layer 1 each has a hydrophilic membrane, so that the samples flow rapidly through the chip sampling port 7 into the main flow channel 501, and then are distributed to each branching microfluidic channel 502. The thickness of the intermediate layer 2 is 0.1 mm-1.0 mm. The surface of the bottom plate layer 1 is flat. The depth of the closed microfluidic channel 5 cooperatively defined by the bottom plate layer 1, the intermediate layer 2, and the upper cover layer 3 is 0.1 mm-1.0 mm, and the width of the detection chambers 8 cooperatively defined by the bottom plate layer 1, the intermediate layer 2, and the upper cover layer 3 is 1.0 mm-2.0 mm. A nozzle is disposed at the junction of each of the branch microfluidic channels 502 and the corresponding detection chamber 8, and each of the branch microfluidic channels 502 has a corresponding electrode 4. Each electrode 4 comprises an input high-side electrode and an input low-side electrode, and the thickness of the electrode 4 is 50 μm. The electrode 4 is provided for applying a pulse voltage while receiving a signal generated by the blood reaction in the detection chambers. An electrode tip 401 is inserted into a detection instrument, and a detection result is obtained by detecting an electrochemical signal generated by the reaction in cooperation with the supporting detection instrument. The electrode tip 401 is a part of the integrally bonded bottom plate layer 1, intermediate layer 2 and upper cover layer 3 that is exposed outside relative to the upper cover layer 3 and the intermediate layer 2, so that the electrode tip 401 may be inserted into the detection instrument more easily and conveniently, so as to obtain the detection result. As shown in FIG. 7 to FIG. 9, the bottom plate layer 1, the intermediate layer 2, and the upper cover layer 3 cooperatively define a closed microfluidic channel 5, detection chambers 8, and a funnel region 9. A notch 10 is disposed on one side of a lower end of the bottom plate layer 1. The liquid injection port 701, the funnel region 9, and the notch 10 are respectively disposed at corresponding positions on the upper cover layer 3, the intermediate layer 2, and the bottom plate layer 1 and have different sizes. The chip sampling port 7 is composed of the liquid injection port 701, the funnel region 9, and the notch 10 and the chip sampling port 7 is connected to the bottom of the detection chambers 8 by means of the microfluidic channel 5. The liquid injection port 701, the funnel region 9, and the notch 10 are all arc-shaped and have different radians. The liquid injection port 701 and the funnel region 9 are semicircular arc-shaped, and the radius of the funnel region 9 is not less than the arc radius of the liquid injection port 701. A curved main flow channel 501 in the funnel region 9 is divided into five branching microfluidic channels 502 which are connected to the five independent detection chambers 8 in a one-to-one corresponding manner. The area of the notch 10 is smaller than the area of the funnel region 9. Here, the liquid injection port 701 is semicircular arc-shaped. Under the condition of the same area, such a 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 may fully accommodate the sample liquid injected from the liquid injection port, without sample loss. The curved flow channel is provided so that the samples slowly flow into the detection chambers 8, without causing a sudden increase in the atmospheric pressure of the detection chambers 8.

(15) In specific use:

(16) Samples are injected into the chip sampling port 7, and simultaneously flow through the main flow channel 501 to the plurality of branching microfluidic channels 502, and then flow into the plurality of independent detection chambers 8. The samples are reacted with the detection reagents pre-embedded in the detection chambers 8, and the microfluidic detection chip for multi-channel rapid detection is inserted into the detection instrument by means of the electrode tip 401. The detection result is obtained by detecting the electrochemical signal generated by the reaction in cooperation with the supporting detection instrument. In this way, the plurality of samples can be simultaneously detected, and the multi-channel effect is achieved, thereby improving the detection efficiency.

(17) The basic principles, main features and advantages of the present invention are shown and described above. Those skilled in the art should understand that the present invention is not limited to the foregoing embodiments. The foregoing embodiments and description merely illustrate the principles of the present invention. Various changes and improvements, such as some other slight adjustments of the shape and structure of the chip sampling port, can also be made to the present invention, without departing from the spirit and scope of the present invention. These changes and improvements fall within the protection scope of the present invention. The protection scope of the present invention is defined by the appended claims and equivalents thereof.