CN215843043U - Microfluidic detection device for blood type detection - Google Patents
Microfluidic detection device for blood type detection Download PDFInfo
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- CN215843043U CN215843043U CN202120061952.XU CN202120061952U CN215843043U CN 215843043 U CN215843043 U CN 215843043U CN 202120061952 U CN202120061952 U CN 202120061952U CN 215843043 U CN215843043 U CN 215843043U
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Abstract
The utility model discloses a microfluidic detection device for blood type detection, which comprises a microfluidic chip, wherein the microfluidic chip comprises a disc-shaped chip body, a driving groove arranged in the middle of the chip body and at least one detection flow channel unit which is arranged around the periphery of the driving groove and can independently detect blood types; the detection flow channel unit comprises sample adding ports, sample adding flow channels, a plurality of sample adding cavities, a plurality of long and narrow connecting flow channels communicated among the sample adding cavities, a plurality of detection cavities in one-to-one correspondence with each sample adding cavity and a waste liquid cavity communicated with one sample adding cavity at the tail end. According to the utility model, through the structural design of the sample adding cavity with the functions of sample adding and quantification, the structure of the detection flow channel can be simplified, and the use of a micro-fluidic chip is facilitated; through the structural design of the sample adding flow channel, the phenomenon that pollution is easily caused due to liquid leakage between adjacent detection cavities can be avoided.
Description
Technical Field
The utility model relates to the technical field of microfluidics, in particular to a microfluidic detection device for blood type detection.
Background
The blood transfusion compatibility test is a necessary condition for ensuring the safety of clinical blood transfusion, and the main test contents comprise three parts: blood type verification, antibody verification and cross matching; according to different infusion components, the method can be divided into a red blood cell blood group compatibility test and a platelet blood group compatibility test. Taking red blood cell typing as an example, the examination determines the red blood cell types of recipients and donors, and most importantly, determines the ABO blood type and the RhD blood type because their blood type compatibility is the most clinically significant for safe transfusion. The human ABO blood group is determined by its erythrocyte antigens and ABO antibodies in the blood, and is routinely assayed by agglutination assays: checking the erythrocyte antigen to be detected with anti-A and anti-B, called positive typing; the antibody in the serum to be detected is detected by using red blood cells A and B, called as reverse typing, and the normal typing of healthy people is consistent. Only newborns can be positively typed to determine their ABO blood type within 4-6 months of life because of their blood ABO antibody activity and the presence of maternal derived antibodies. Different blood typing protocols and different antibody reagents need to be applied.
The blood type detection device adopting the microfluidic chip as the carrier can quickly and accurately identify various blood types, and has the advantages of high detection flux, simplicity in operation and the like, so that the device is widely applied. For example, chinese patent CN206292243U discloses a microfluidic chip for blood type detection, which can realize blood type detection by using a plurality of microfluidic units in combination with a centrifugal operation and an optical detection device, but during the use, it is found that the microfluidic chip has some defects: 1. the microfluid unit comprises a sample adding cavity and a plurality of quantitative cavities, so that sample adding and quantitative adding are respectively completed by two cavities, the flow channel structure is complicated, and operation steps are added; 2. the sample adding cavity is communicated with the quantitative cavities through a sample separating channel, so that when the microfluidic chip is operated in the follow-up mode to carry out reciprocating oscillation centrifugation, part of liquid leaked from the detection cavity can enter other detection cavities after passing through the sample separating channel and the quantitative cavities, pollution is caused, and the final detection result can be influenced.
Therefore, a more reliable solution is now needed.
SUMMERY OF THE UTILITY MODEL
The technical problem to be solved by the present invention is to provide a microfluidic device for blood type detection, which is designed to overcome the above-mentioned shortcomings in the prior art.
In order to solve the technical problems, the utility model adopts the technical scheme that: a micro-fluidic detection device for blood type detection comprises a micro-fluidic chip, wherein the micro-fluidic chip comprises a disc-shaped chip body, a driving groove arranged in the middle of the chip body and at least one detection flow channel unit which is arranged around the periphery of the driving groove and can independently detect blood types;
the detection flow channel unit comprises sample adding ports, a sample adding flow channel, a plurality of sample adding cavities, a plurality of long and narrow connecting flow channels communicated among the sample adding cavities, a plurality of detection cavities corresponding to each sample adding cavity one by one, and a waste liquid cavity communicated with one sample adding cavity at the tail end;
the sample adding port is communicated with a sample adding cavity of the head end through the sample adding flow channel, and a centrifugal micro valve is arranged between the sample adding cavity and the detection cavity.
Preferably, the sample application chamber is prismatic in shape having an inlet end and an outlet end.
Preferably, the inlet end and the outlet end are in opposite positions, and an extension line of a connecting line of the inlet end and the outlet end passes through the center of the chip body.
Preferably, the plurality of sample adding cavities are uniformly arranged at intervals and are sequentially communicated through the plurality of connecting flow channels.
Preferably, the connecting flow channel is U-shaped and has a first end and a second end, the first end of the connecting flow channel is communicated with the outlet end of the sample adding cavity, and the second end of the connecting flow channel is communicated with the inlet end of the adjacent sample adding cavity.
Preferably, the total volume of the single detection flow channel unit is 180-.
Preferably, the depths of the sample adding port and the sample adding flow channel are both 0.7-1.2mm, and the depths of the sample adding cavity, the connecting flow channel and the detection cavity are all 1.2-1.8 mm.
Preferably, the driving groove is a semicircular groove.
Preferably, the diameter of the chip body is 90mm-120mm, and the thickness is 2.0-6.0 mm.
Preferably, the chip body is provided with 4 detection flow channel units surrounding the driving groove, and each detection flow channel unit comprises 6 sample adding cavities communicated in sequence.
The utility model has the beneficial effects that:
the micro-fluidic chip adopted by the utility model can simplify the structure of the detection flow channel by the structural design of the sample adding cavity with the functions of sample adding and quantification, and is beneficial to the use of the micro-fluidic chip; through the structural design of the sample adding flow channel, the phenomenon that pollution is easily caused due to liquid leakage between adjacent detection cavities can be avoided.
Drawings
Fig. 1 is a schematic structural diagram of a microfluidic chip in an embodiment of the present invention.
Description of reference numerals:
1-chip body; 2-driving the trough; 3-detecting the flow channel unit; 301-sample addition port; 302-sample addition flow channel; 303-sample application cavity; 304-centrifugal microvalves; 305 — a detection chamber; 306-waste liquid chamber; 307-connecting flow channels; 3031 — the inlet end; 3032-outlet end; 3071-first end; 3072-second end.
Detailed Description
The present invention is further described in detail below with reference to examples so that those skilled in the art can practice the utility model with reference to the description.
It will be understood that terms such as "having," "including," and "comprising," as used herein, do not preclude the presence or addition of one or more other elements or groups thereof.
The microfluidic detection device for blood type detection of this embodiment includes a microfluidic chip, referring to fig. 1, the microfluidic chip includes a disc-shaped chip body 1, a driving groove 2 provided in the middle of the chip body 1, and at least one detection flow channel unit 3 which is provided around the periphery of the driving groove and can independently perform detection;
the detection flow channel unit 3 comprises a sample addition port 301, a sample addition flow channel 302, a plurality of sample addition cavities 303, a plurality of long and narrow connecting flow channels 307 communicated among the sample addition cavities 303, a plurality of detection cavities 305 corresponding to each sample addition cavity 303 one by one, and a waste liquid cavity 306 communicated with one sample addition cavity 303 at the tail end;
the sample adding port 301 is communicated with a sample adding cavity 303 at the head end through a sample adding flow channel 302, and a centrifugal micro valve 304 is arranged between the sample adding cavity 303 and the detection cavity 305.
In the utility model, the sample adding cavities 303 have the same size, and the sample adding cavities 303 have the functions of sample adding and quantification, so that the structure of the detection flow channel can be simplified.
During the use, detect chamber 305 and encapsulate reagent in advance, for example blood group antibody encapsulates after cold wind drying or freeze-drying, and the reagent of encapsulation is different in the different detection chamber 305 to realize the detection of multiple blood group, it does not contain the reagent to leave one of the detection chamber 305, is regarded as the reference.
In one embodiment, the drive slot 2 is a semi-circular slot. The driving groove 2 is used for being in driving connection with a centrifugal device so as to provide rotating power for the microfluidic chip to control the movement of fluid through centrifugal force.
In one embodiment, an exhaust port (not shown) is further provided in the detection flow path unit 3.
In a preferred embodiment, the loading chamber 303 is prismatic in shape, having an inlet end 3031 and an outlet end 3032;
the inlet end 3031 and the outlet end 3032 are in opposite positions, the extension line of the connecting line of the inlet end 3031 and the outlet end 3032 passes through the center of the chip body 1, and the plurality of sample adding cavities 303 are uniformly arranged at intervals and are sequentially communicated through the plurality of connecting flow channels 307. The design of the sample adding cavity 303 enables a sample to smoothly flow into each sample adding cavity 303 in sequence when the sample is added through the sample adding port 301, so that smooth sample adding is ensured; and when the chip body 1 rotates at a certain rotation speed, the sample in the sample adding cavity 303 can smoothly break through the obstruction of the centrifugal micro valve 304 and enter the detection cavity 305.
The connecting flow channel 307 is U-shaped, and has a first end 3071 and a second end 3072, the first end 3071 of the connecting flow channel 307 is communicated with the outlet end 3032 of the sample-adding cavity 303, and the second end 3072 of the connecting flow channel 307 is communicated with the inlet end 3031 of the adjacent sample-adding cavity 303. The connecting flow channel 307 is a U-shaped long and narrow channel, and has a certain resistance, and when sample is loaded, the sample can be injected at a certain pressure to overcome the resistance, so that the sample can smoothly flow into each sample loading cavity 303 in sequence; when in use, the narrow connecting flow channel 307 is easy to form an air column, when the chip body 1 is subjected to reciprocating oscillation centrifugation, the proper resistance provided by the connecting flow channel 307 with the structure and the existence of the air column can form a barrier between the sample adding cavities 303 to play a role of isolation, therefore, the phenomenon that liquid is mixed between adjacent detection chambers 305 to cause contamination can be prevented (reagents pre-sealed in different detection chambers 305 are generally different, during centrifugation, although liquid in the detection chambers 305 basically does not flow out due to the action of the centrifugal micro-valve 304, a small amount of liquid inevitably breaks through the centrifugal micro-valve 304 and is "leaked" into the sample adding chamber 303, and if no resistance for connecting the flow channel 307 exists, the adjacent detection chambers 305 are easily contaminated due to liquid leakage, which affects the final detection result).
In one embodiment, the total volume of a single detection flow channel unit 3 is 180-.
In one embodiment, the depths of the sample loading port 301 and the sample loading channel 302 are 0.7-1.2mm, and the depths of the sample loading cavity 303, the connecting channel 307 and the detection cavity 305 are 1.2-1.8 mm. By appropriately increasing the depth of the flow channel, the resistance to the flow of fluid therein can be reduced.
In one embodiment, the chip body 1 has a diameter of 90mm to 120mm and a thickness of 2.0 to 6.0 mm.
In one embodiment, the chip body 1 is made of a material with high light transmittance, such as Polystyrene (PS), Polycarbonate (PC), acrylic (PMMA), or COP.
In a preferred embodiment, the chip body 1 is provided with 4 detection flow channel units 3 around the driving groove 2, each detection flow channel unit 3 comprises 6 sample adding cavities 303 which are sequentially communicated, wherein 5 different blood type antigens are respectively packaged, and 1 sample adding cavity 303 is used as a blank control. The microfluidic detection device for blood type detection further comprises a centrifugal driving mechanism for providing rotary power for the microfluidic chip and an optical detection device for detecting the detection cavity 305, wherein the microfluidic chip is in driving connection with the centrifugal driving mechanism through the driving groove 2. The centrifugal driving mechanism can be conventional centrifugal equipment, and the optical detection equipment can be conventional products.
The following is further described with reference to the detection steps of the microfluidic detection device, which include:
1) a sample to be analyzed is added into the detection flow channel unit 3 through the sample adding port 301, and the redundant sample flows into the waste liquid cavity 306 after the sample adding flow channel 302, the plurality of sample adding cavities 303 and the connecting flow channel 307 are filled; at this time, the sample adding cavity 303 is filled, and the quantification of the sample is realized;
2) enabling the centrifugal driving mechanism to drive the microfluidic chip to rotate at a first rotating speed (centrifugation at 1000rpm for 5s), enabling the sample in the sample adding cavity 303 to break through the resistance of the centrifugal micro valve 304, then entering the detection cavity 305, and contacting with a reagent packaged in the detection cavity 305 in advance;
3) the centrifugal driving mechanism drives the microfluidic chip to perform clockwise-anticlockwise alternate reciprocating rotation at a second rotating speed (the clockwise rotating speed is 100rpm, the time is 3s, the anticlockwise rotating speed is 100rpm, and the time is 3 s; circulating for 10 times) to generate reciprocating type oscillation centrifugation, so that the sample and the reagent are fully mixed under the action of oscillation force; in the process, due to the resistance effect of the connecting flow channel 307 and the blocking effect of the air column formed in the connecting flow channel 307, a small amount of liquid leaked from the detection cavity 305 in the process enters the corresponding sample adding cavity 303 and cannot enter the adjacent sample adding cavity 303, so that the adjacent detection cavity 305 cannot be guided to cause pollution;
4) enabling the centrifugal driving mechanism to drive the microfluidic chip to rotate at a third rotation speed (rotation speed 2200rpm for 10s), so that the reaction product in the detection cavity 305 is centrifuged to the side wall to be detected under the action of centrifugal force;
5) the centrifugal driving mechanism drives the microfluidic chip to perform clockwise-anticlockwise alternate reciprocating rotation at a fourth rotating speed (clockwise rotating speed of 100rpm for 3s, anticlockwise rotating speed of 100rpm for 3 s; cycle 10 times) to generate reciprocating shaking centrifugation to make the clumps formed by the reaction products in the detection chamber 305 with positive reaction fall off from the side wall of the detection, and make the red blood cells in the detection chamber 305 with negative reaction re-suspended in the detection chamber 305; in the same process, the existence of the connecting flow channel 307 can also avoid the problem of contamination between adjacent detection chambers 305;
6) the detection chamber 305 is manually interpreted or the detection chamber 305 is subjected to detection by an optical detection device to discriminate positive reactions from negative reactions (which can be realized by an optical detection device of a conventional device).
While embodiments of the utility model have been disclosed above, it is not limited to the applications listed in the description and the embodiments, which are fully applicable in all kinds of fields of application of the utility model, and further modifications may readily be effected by those skilled in the art, so that the utility model is not limited to the specific details without departing from the general concept defined by the claims and the scope of equivalents.
Claims (10)
1. The microfluidic detection device for blood type detection is characterized by comprising a microfluidic chip, wherein the microfluidic chip comprises a disc-shaped chip body, a driving groove formed in the middle of the chip body and at least one detection flow channel unit which is arranged around the periphery of the driving groove and can independently detect blood types;
the detection flow channel unit comprises sample adding ports, a sample adding flow channel, a plurality of sample adding cavities, a plurality of long and narrow connecting flow channels communicated among the sample adding cavities, a plurality of detection cavities corresponding to each sample adding cavity one by one, and a waste liquid cavity communicated with one sample adding cavity at the tail end;
the sample adding port is communicated with a sample adding cavity of the head end through the sample adding flow channel, and a centrifugal micro valve is arranged between the sample adding cavity and the detection cavity.
2. The microfluidic device for blood group testing according to claim 1, wherein the sample application chamber is prismatic in shape having an inlet end and an outlet end.
3. The microfluidic device for blood group testing according to claim 2, wherein the inlet and outlet ends are in opposite positions and an extension line of a connecting line of the inlet and outlet ends passes through the center of the chip body.
4. The microfluidic device for blood group typing according to claim 3, wherein a plurality of the sample loading chambers are arranged at regular intervals and are sequentially connected through a plurality of the connecting flow channels.
5. The microfluidic device for blood group typing according to claim 4, wherein the connecting channel is U-shaped and has a first end and a second end, the first end of the connecting channel is connected to the outlet end of the sample loading chamber, and the second end of the connecting channel is connected to the inlet end of the adjacent sample loading chamber.
6. The microfluidic detection device for blood group detection according to claim 1, wherein the total volume of the single detection flow channel unit is 180 and 200 uL.
7. The microfluidic detection device for blood type detection according to claim 1, wherein the depth of the sample loading port and the sample loading flow channel is 0.7-1.2mm, and the depth of the sample loading cavity, the connecting flow channel and the detection cavity is 1.2-1.8 mm.
8. The microfluidic device for blood group testing according to claim 1, wherein the driving groove is a semicircular groove.
9. The microfluidic device for blood group testing according to claim 1, wherein the chip body has a diameter of 90mm to 120mm and a thickness of 2.0 to 6.0 mm.
10. The microfluidic detection device for blood group detection according to claim 5, wherein the chip body is provided with 4 detection flow channel units around the driving groove, and each detection flow channel unit comprises 6 sample adding cavities which are sequentially communicated.
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| Application Number | Priority Date | Filing Date | Title |
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| CN202120061952.XU CN215843043U (en) | 2021-01-11 | 2021-01-11 | Microfluidic detection device for blood type detection |
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| Application Number | Priority Date | Filing Date | Title |
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| CN202120061952.XU CN215843043U (en) | 2021-01-11 | 2021-01-11 | Microfluidic detection device for blood type detection |
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| CN215843043U true CN215843043U (en) | 2022-02-18 |
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| CN202120061952.XU Active CN215843043U (en) | 2021-01-11 | 2021-01-11 | Microfluidic detection device for blood type detection |
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