CN108982824B - Reagent disk testing device - Google Patents
Reagent disk testing device Download PDFInfo
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- CN108982824B CN108982824B CN201810450478.2A CN201810450478A CN108982824B CN 108982824 B CN108982824 B CN 108982824B CN 201810450478 A CN201810450478 A CN 201810450478A CN 108982824 B CN108982824 B CN 108982824B
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- 239000003153 chemical reaction reagent Substances 0.000 title claims abstract description 136
- 238000012360 testing method Methods 0.000 title claims abstract description 18
- 230000003287 optical effect Effects 0.000 claims abstract description 146
- 210000004369 blood Anatomy 0.000 claims abstract description 99
- 239000008280 blood Substances 0.000 claims abstract description 99
- 238000006243 chemical reaction Methods 0.000 claims abstract description 62
- 210000002381 plasma Anatomy 0.000 claims abstract description 52
- 238000000926 separation method Methods 0.000 claims description 43
- 230000007704 transition Effects 0.000 claims description 37
- 238000003860 storage Methods 0.000 claims description 24
- 210000003743 erythrocyte Anatomy 0.000 claims description 22
- 238000005452 bending Methods 0.000 claims description 19
- 238000007789 sealing Methods 0.000 claims description 12
- 238000004891 communication Methods 0.000 claims description 9
- 239000007788 liquid Substances 0.000 claims description 9
- 239000002775 capsule Substances 0.000 claims description 7
- 230000001105 regulatory effect Effects 0.000 claims description 6
- XAGFODPZIPBFFR-UHFFFAOYSA-N aluminium Chemical compound [Al] XAGFODPZIPBFFR-UHFFFAOYSA-N 0.000 claims description 3
- 229910052782 aluminium Inorganic materials 0.000 claims description 3
- 210000004204 blood vessel Anatomy 0.000 claims description 3
- 238000007639 printing Methods 0.000 abstract description 4
- 238000001514 detection method Methods 0.000 description 31
- 230000009471 action Effects 0.000 description 12
- 238000000034 method Methods 0.000 description 6
- 238000013461 design Methods 0.000 description 5
- 230000000694 effects Effects 0.000 description 4
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- 238000009534 blood test Methods 0.000 description 3
- 210000004027 cell Anatomy 0.000 description 3
- 230000000151 anti-reflux effect Effects 0.000 description 2
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- 238000007723 die pressing method Methods 0.000 description 2
- 238000011031 large-scale manufacturing process Methods 0.000 description 2
- 230000007246 mechanism Effects 0.000 description 2
- 238000002156 mixing Methods 0.000 description 2
- 238000012986 modification Methods 0.000 description 2
- 230000004048 modification Effects 0.000 description 2
- 238000012856 packing Methods 0.000 description 2
- 238000011002 quantification Methods 0.000 description 2
- 239000007787 solid Substances 0.000 description 2
- 208000019838 Blood disease Diseases 0.000 description 1
- 208000035473 Communicable disease Diseases 0.000 description 1
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- 238000004458 analytical method Methods 0.000 description 1
- 230000009286 beneficial effect Effects 0.000 description 1
- 230000005540 biological transmission Effects 0.000 description 1
- 210000000601 blood cell Anatomy 0.000 description 1
- 210000001772 blood platelet Anatomy 0.000 description 1
- 238000009582 blood typing Methods 0.000 description 1
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- 208000007475 hemolytic anemia Diseases 0.000 description 1
- 210000003734 kidney Anatomy 0.000 description 1
- 230000003907 kidney function Effects 0.000 description 1
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Classifications
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- G—PHYSICS
- G01—MEASURING; TESTING
- G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
- G01N33/00—Investigating or analysing materials by specific methods not covered by groups G01N1/00 - G01N31/00
- G01N33/48—Biological material, e.g. blood, urine; Haemocytometers
- G01N33/483—Physical analysis of biological material
- G01N33/487—Physical analysis of biological material of liquid biological material
- G01N33/48707—Physical analysis of biological material of liquid biological material by electrical means
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- G—PHYSICS
- G01—MEASURING; TESTING
- G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
- G01N1/00—Sampling; Preparing specimens for investigation
- G01N1/28—Preparing specimens for investigation including physical details of (bio-)chemical methods covered elsewhere, e.g. G01N33/50, C12Q
- G01N1/38—Diluting, dispersing or mixing samples
-
- G—PHYSICS
- G01—MEASURING; TESTING
- G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
- G01N33/00—Investigating or analysing materials by specific methods not covered by groups G01N1/00 - G01N31/00
- G01N33/48—Biological material, e.g. blood, urine; Haemocytometers
- G01N33/483—Physical analysis of biological material
- G01N33/487—Physical analysis of biological material of liquid biological material
- G01N33/4875—Details of handling test elements, e.g. dispensing or storage, not specific to a particular test method
Abstract
The application relates to a reagent disk testing device, comprising: the optical disk, be equipped with first reagent pond, with first quantitative device, the whole blood pond of first reagent pond intercommunication, with the separator of whole blood pond intercommunication, with the second quantitative device of separator intercommunication, second reagent pond, with the third quantitative device of second reagent pond intercommunication and with the buffer memory pond of third quantitative device intercommunication on the optical disk respectively, first quantitative device, second quantitative device and buffer memory pond communicate with the reaction tank respectively, be provided with the inlet hole on the whole blood pond, second reagent pond, buffer memory pond and first quantitative device all communicate with the whole blood pond, the optical disk is rotatory printing opacity optical disk, and the axle center setting that is used for the optical disk rotation is at the optical disk center. The application can automatically separate the blood plasma by utilizing centrifugal force, quantitatively distribute the blood plasma and automatically quantitatively add the reagent into the blood plasma.
Description
Technical Field
The application relates to the field of blood detection, in particular to a reagent disk testing device.
Background
Clinical blood tests can be categorized into general blood tests, laboratory tests for hemolytic anemia, bone marrow cytology tests, blood typing and cross-matching tests. Can detect the blood-learning sign of common hematopathy.
Of these, blood is most commonly detected (i.e., blood routine). The quality and quantity of three systems, namely red blood cells, white blood cells and platelets, are detected and analyzed. Detection related to various diseases, such as blood disease, bone marrow cell detection, blood cytochemical staining analysis, etc. besides blood routine detection; blood detection items for liver diseases and kidney patients mainly comprise detection of liver functions, kidney functions and the like; for some infectious diseases, detection of antibodies in blood is an important diagnostic criterion.
The traditional detection means is to detect a certain index or a certain specific substance after the sample is collected, the detection procedures are more, the conventional detection needs multi-person and multi-equipment operation, the detection time is long, the detection cost is high, and the method is outstanding in characteristics. Particularly, in some cases where reagents are required for detection, various interference factors such as sample errors, tool errors, human errors and the like affect the detection result. Although the popularity of automated testing equipment has increased significantly in recent years, the cost of purchasing hundreds of thousands or even millions of automated testing equipment has been very difficult for general hospitals and testing facilities to afford. In particular, blood test parameters are numerous, and the test equipment is inevitably targeted, and on the other hand, the trend is aggravated.
Disclosure of Invention
The application aims to provide a reagent disk testing device capable of automatically separating plasma by centrifugal force, quantitatively distributing plasma and automatically quantitatively adding reagent into the plasma.
The application adopts the following technical scheme:
a reagent disk testing device, comprising: the optical disk, be equipped with first reagent pond, with first quantitative device, the whole blood pond of first reagent pond intercommunication, with the separator of whole blood pond intercommunication, with the second quantitative device of separator intercommunication, second reagent pond, with the third quantitative device of second reagent pond intercommunication and with the buffer memory pond of third quantitative device intercommunication on the optical disk respectively, first quantitative device, second quantitative device and buffer memory pond communicate with the reaction tank respectively, be provided with the inlet hole on the whole blood pond, second reagent pond, buffer memory pond and first quantitative device all communicate with the whole blood pond, the optical disk is rotatory printing opacity CD, and the axle center setting for the optical disk is at the optical disk center, the reaction tank is printing opacity reaction tank.
Preferably, the first quantitative device comprises a first quantitative pool and a first overflow pool, wherein the rear right side surface of the first quantitative pool is communicated with the first reagent pool through a first flow guide pipe, the front right side surface of the first quantitative pool is communicated with the first overflow pool through a first guide pipe, the rear left side surface of the first quantitative pool is communicated with the reaction pool through a first bending pipe, a first exhaust pipe is arranged at the top of the first overflow pool, and the first exhaust pipe is communicated with the whole blood pool;
the first bending pipe comprises a first connecting pipe, a first stop pipe communicated with the first connecting pipe, a first transition section communicated with the first stop pipe and a first delivery pipe communicated with the first transition section, and the first delivery pipe is communicated with the reaction tank;
the distance between each point of the front side surface of the first quantitative pool, which is positioned in the same height, and the center of the optical disk is equal;
the minimum distance between the first transition section and the center of the optical disc is smaller than the minimum distance between the first guide pipe and the center of the optical disc;
the minimum distance between the first overflow pool and the center of the optical disc is smaller than the minimum distance between the first quantitative pool and the center of the optical disc.
Preferably, the separation device comprises a separation tank, and a blood inlet pipe and a blood outlet pipe, wherein the blood inlet pipe is communicated with the separation tank and used for conveying whole blood, the blood outlet pipe is used for conveying blood plasma, and the other end of the blood inlet pipe is communicated with the whole blood tank;
the separation tank is divided into a red blood cell storage part and a plasma storage part, the volume ratio of the red blood cell storage part to the plasma storage part is 2:3, the red blood cell storage part is positioned at the outer side of the plasma storage part, the blood inlet pipe is communicated with the red blood cell storage part, and the blood outlet pipe is communicated with the plasma storage part;
the blood outlet tube is provided with a bending part, and the distance between the bending part and the center of the optical disk is smaller than the minimum distance between the separation tank and the center of the optical disk;
the center line of the separating pool passes through the center of the optical disc relative to the vertical projection of the optical disc;
the maximum distance between the whole blood pool and the center of the optical disk is smaller than the minimum distance between the separation pool and the center of the optical disk.
Preferably, the second dosing device comprises a second dosing tank, a second overflow tank and a second introducing device, wherein the second introducing device comprises a second introducing pipe, a second shunt pipe communicated with the second introducing pipe, a second return pipe communicated with the second shunt pipe and a second delivery pipe communicated with the second return pipe; the input end of the second quantitative pool is communicated with a second shunt tube; the output end of the second quantitative pool is communicated with the second overflow pool;
the second quantitative pool is positioned at one side of the second shunt pipe close to the center of the optical disc; the second overflow pool is positioned at one side of the second quantifying pool, which is close to the center of the optical disc;
the second overflow tank comprises a second tank A and a second tank B communicated with the second tank A; the second pool B is positioned at one side of the second pool A close to the second quantitative pool; the output end of the second quantitative pool is communicated with the second pool A;
a second transition section A is arranged at the communication part of the second check pipe and the second delivery pipe; the minimum distance between the second transition section A and the center of the optical disk is smaller than the minimum distance between the second overflow pool and the center of the optical disk;
a second transition section B is arranged at the communication part of the second ingress pipe and the second shunt pipe; a second transition section C is arranged at the communication part of the second shunt pipe and the second check pipe, and the second transition section A, the second transition section B and the second transition section C are all broken lines;
the other end of the second delivery pipe is communicated with the reaction tank, and the second ingress pipe is communicated with the bending part on the blood vessel.
Preferably, the third metering device comprises a third metering tank, a third overflow tank and a third guide pipe, and the third overflow tank is arranged at one side of the third metering tank, which is close to the center of the optical disc; the second reagent pool is arranged at one side of the third quantitative pool, which is close to the center of the optical disk; one end of the third flow guide pipe is communicated with the second reagent tank, and the other end of the third flow guide pipe is communicated with the third quantitative tank;
the third guide pipe comprises a third guide pipe A, a U-shaped pipe connected with the third guide pipe A and a third guide pipe B connected with the U-shaped pipe;
the other end of the third conduit A is connected with a second reagent pool; the other end of the third conduit B is connected with the input end of the third measuring tank; the minimum diameter of the third conduit A is larger than the maximum diameter of the U-shaped pipe; the minimum diameter of the third conduit A is larger than the maximum diameter of the third conduit B;
the third overflow tank comprises a third tank A and a third tank B connected with the third tank A; the third pool B is positioned at one side of the third pool A away from the center of the optical disc; the third quantitative pool is connected with a third pool A; the joint of the third metering tank and the third tank A is positioned on the side surface of the third tank A, which is far away from the center of the optical disc;
the second reagent tank is provided with an air pressure balance pipe; the other end of the air pressure balance tube is communicated with the whole blood pool.
Preferably, the third conduit C is connected with the buffer pool; the buffer pool is positioned at one side of the third quantitative pool, which is close to the center of the optical disc; the other end of the third conduit C is connected with the input end of the third measuring tank;
the buffer pool is also provided with a pressure regulating pipe; the other end of the pressure regulating tube is communicated with the whole blood pool; a fourth delivery pipe is further arranged on the cache pool, and the other end of the fourth delivery pipe is communicated with the reaction pool; a return pipe is communicated between the second reagent pool and the buffer pool;
the minimum distance between the third conduit C and the center of the optical disc is smaller than the minimum distance between the second reagent reservoir and the center of the optical disc.
Preferably, the reaction tank is communicated with two feeding pipes, an exhaust pipe is communicated with the reaction tank, an exhaust bin is arranged on the exhaust pipe, and the other end of the exhaust pipe is communicated with the whole blood tank;
the first delivery pipe is communicated with the feeding pipe, and the fourth delivery pipe and the second ingress pipe are respectively communicated with the exhaust bin;
the inner wall of the reaction tank is in arc transition, the arc length of the horizontal section of the reaction tank along the rotation direction of the optical disk is larger than the length of the horizontal section of the reaction tank perpendicular to the rotation direction, the horizontal section of the reaction tank is elliptical, and the short axis of the reaction tank passes through the rotation center of the optical disk.
Preferably, the first reagent tank and the second reagent tank are respectively provided with reagent packs.
Preferably, the reagent pack is a capsule type reagent pack, and the capsule type reagent pack comprises films connected together, a sealed pool formed between the films and a liquid reagent filled in the sealed pool; the three sides of the two films are provided with edge sealing, and the edge sealing forms closed-loop sealing; the cross section of the sealing pool is trapezoid, the upper bottom edge, the lower bottom edge and one waist edge of the trapezoid are provided with edge sealing edges, and the film is an aluminum film.
The application has the beneficial effects that:
the application can automatically separate the blood plasma by utilizing centrifugal force, quantitatively distribute the blood plasma and automatically quantitatively add the reagent into the blood plasma.
The application can separate out the plasma in one plasma separation work, and has higher separation efficiency. When in use, the blood is injected into the whole blood pool, the blood is separated into plasma and blood cells under the action of centrifugal force, and the plasma flows into the reaction pool, so that the separation time can be greatly shortened, and the separation efficiency is improved.
The first quantifying tank, the second quantifying tank and the third quantifying tank have certain volumes, can accurately quantify the required dosage, and the redundant parts are automatically transferred into the first overflow tank, the second overflow tank and the third overflow tank respectively so as to ensure that each quantifying tank is filled. The separated plasma can directly enter the reaction tank and then be added with the reagent R1 and the reagent R2 for reaction, and the reagent R1 and the reagent R2 are directly used for detection operation after reaction, so that the detection time is effectively shortened, and particularly secondary pollution and quantitative errors possibly occurring in manual separation operation are avoided, and solid guarantee can be provided for subsequent detection operation.
The carrier used in the application is a plastic optical disc, and the manufacturing cost of the optical disc can be quickly lowered in a large-scale production mode, thereby reducing the purchasing cost of hospitals and other using institutions. More people can get medical services.
And the existing plasma quantification needs to be subjected to a plurality of operation processes such as collection, separation, quantification and the like, and different tools and equipment are needed to be used in the middle, so that the use cost and the time cost are high. When the plasma quantitative operation is carried out by using the plasma quantitative detection device, all the works can be completed by only one optical disc, so that a great deal of time cost and tool consumption can be saved, the detection time can be shortened, and the detection efficiency can be improved.
The application has lower acquisition cost and higher acquisition efficiency. The traditional acquisition mode is manual acquisition or machine acquisition, and workers use droppers, balances and the like to operate during manual acquisition, so that the equipment precision, human errors, operation errors and other interference factors are very large, and accurate measurement is difficult to carry out; machine acquisition is very accurate, but equipment meeting such accuracy is also very expensive, and is also unacceptable to general hospitals and use institutions. The application innovatively adopts the optical disc design, can reduce the manufacturing cost of the optical disc to be very low through large-scale production, and especially, the optical disc is only affected by the manufacturing precision during the acquisition, thereby thoroughly avoiding various interference factors during the manual acquisition, rapidly improving the acquisition precision and achieving very good balance in the aspects of cost and efficiency.
The overflow pool adopts a double-body design, and when the optical disk rotates forward, the reagent transferred from the third quantitative pool enters the third pool A, and finally the reagent is transferred into the third pool B under the action of centrifugal force. When the optical disk rotates reversely, the reagent in the third pool B has a movement trend away from the center of the optical disk, but the third pool B is not connected with the quantitative pool, so that when the reagent in the quantitative pool flows out, the reagent in the third pool B is kept still, the reagent collection amount can be ensured to be equal to the volume of the third quantitative pool, and the collection precision is ensured.
When the optical disk rotates reversely, the hydraulic pressure in the third conduit A is higher than the hydraulic pressure in the U-shaped pipe and the third conduit B. The reagent in the dosing tank can only flow out of the third conduit C during the outflow. The anti-reflux design can also improve the acquisition accuracy.
The application adopts a disc type centrifugal structure, whole blood is separated in the separating tank, and as the blood plasma is lighter and the red blood cells are heavier, the optical disc generates centrifugal force through rotation, under the action of the centrifugal force, the heavier red blood cells are positioned at the outer side end of the separating tank, the lighter blood plasma is positioned at the inner side end of the separating tank, and then the blood plasma is separated and conveyed to the next process through a blood outlet tube to be mixed with other reagents, so that the automatic separation and conveying are realized. The use is simpler and more convenient.
The reaction tank is arranged on the optical disk, liquid in the reaction tank is mixed by centrifugal force generated by rotation of the optical disk, and the exhaust bin arranged on the exhaust pipe can accelerate gas discharge, so that bubbles in the reaction tank are effectively avoided, and the influence on detection is prevented.
The arc transition inner wall of the reaction tank can effectively prevent liquid from being piled up at corners to influence the mixing effect, and the mixing is more uniform, so that the detection accuracy is ensured. The application is suitable for optical path detection, and detects the reaction tank by utilizing the optical path in the optical disk rotation process, increases the length of the reaction tank in the optical disk rotation direction, can effectively increase the detection reaction time of the sensor, eliminates the detection error, and has more accurate detection result.
Drawings
Fig. 1 is a schematic structural view of the present application.
Fig. 2 is a schematic structural view of the first metering device.
FIG. 3 is a schematic diagram of the structure of a separation cell.
Fig. 4 is a schematic structural view of the second quantitative device.
Fig. 5 is a schematic structural diagram of a third metering device and a buffer pool.
FIG. 6 is a schematic structural view of a reaction tank.
Fig. 7 is a schematic structural view of the encapsulated reagent pack.
In the drawing, 1-CD, 2-first reagent tank, 3-whole blood tank, 4-second reagent tank, 5-buffer tank, 6-reaction tank, 7-separation tank, 8-reagent pack, 111-first draft tube, 121-first metering tank, 122-first overflow tank, 123-first conduit, 104-transition section, 105-first exhaust tube, 131-first connecting tube, 132-first stop tube, 133-first delivery tube, 202-inlet tube, 206-outlet tube, 208-kink, 303-second transition section A, 304-second transition section B, 305-second transition section C, 311-second ingress tube, 312-second shunt tube, 313-second return-stopping tube, 314-second delivery tube, 315-second overflow tank, 321-second metering tank, 322-second tank A, 323-second tank B, 104-third conduit C, 405-regulator tube, 406-fourth delivery tube, 404-equilibrium tube, 408-second metering return tube, 413-third conduit B, 414-third conduit A, 31-second overflow tube, 82-second conduit B, 31-second overflow tank, 73-second conduit B, 315-second overflow tank, 315-second conduit, 315-second overflow tank, 315-third conduit B, 81-third conduit B, and the like.
Detailed Description
As shown in fig. 1 to 7, a reagent disk testing apparatus includes: the optical disk 1, be equipped with first reagent pond 2, with first metering device, whole blood pond 3, with the separator of whole blood pond 3 intercommunication, with the second metering device of separator intercommunication, second reagent pond 4, with the third metering device of second reagent pond 4 intercommunication and with the buffer memory pond 5 of third metering device intercommunication on the optical disk 1 respectively, first metering device, second metering device and buffer memory pond 5 communicate with reaction tank 6 respectively, be provided with the inlet hole 31 on the whole blood pond 3, second reagent pond 4, buffer memory pond 5 and first metering device all communicate with whole blood pond 3, optical disk 1 is rotatory printing opacity optical disk, and the axle center setting that is used for optical disk 1 to rotate is at the optical disk center.
Preferably, the first metering device comprises a first metering tank 121 and a first overflow tank 122, wherein the rear right side surface of the first metering tank 121 is communicated with the first reagent tank 2 through a first flow guide pipe 111, the front right side surface of the first metering tank 121 is communicated with the first overflow tank 122 through a first conduit pipe 123, the rear left side surface of the first metering tank 121 is communicated with the reaction tank 6 through a first bending pipe, a first exhaust pipe 105 is arranged at the top of the first overflow tank 122, and the first exhaust pipe 105 is communicated with the whole blood tank 3;
the first bending pipe comprises a first connecting pipe 131, a first stop pipe 132 communicated with the first connecting pipe 131, a first transition section 104 communicated with the first stop pipe 132 and a first delivery pipe 133 communicated with the first transition section 104, wherein the first delivery pipe 133 is communicated with the reaction tank 6;
each point of the front side of the first quantifying tank 121 located in the same height is equidistant from the center of the optical disc;
the minimum distance between the first transition section 104 and the center of the optical disc is smaller than the minimum distance between the first conduit 123 and the center of the optical disc;
the minimum distance between the first overflow tank 122 and the center of the optical disc is smaller than the minimum distance between the first quantifying tank 121 and the center of the optical disc.
Preferably, the separation device comprises a separation tank 7, and a blood inlet pipe 202 and a blood outlet pipe 206, wherein the blood inlet pipe 202 is communicated with the separation tank 7 and used for conveying whole blood, the blood outlet pipe 206 is communicated with the whole blood tank 3 at the other end of the blood inlet pipe 202;
the separation tank 7 is divided into a red blood cell reservoir 701 and a plasma reservoir 702, wherein the volume ratio of the red blood cell reservoir to the plasma reservoir is 2:3, the red blood cell reservoir 701 is positioned outside the plasma reservoir 702, the blood inlet tube 202 is communicated with the red blood cell reservoir 701, and the blood outlet tube 206 is communicated with the plasma reservoir 702;
the blood tube 206 is provided with a bending part 208, and the distance between the bending part 208 and the center of the optical disc is smaller than the minimum distance between the separation tank 7 and the center of the optical disc;
the center line 703 of the separation tank 7 passes through the center of the optical disc 1 with respect to the vertical projection thereof;
the maximum distance between the whole blood pool 3 and the center of the optical disk is smaller than the minimum distance between the separation pool 7 and the center of the optical disk.
Preferably, the second dosing device includes a second dosing tank 321, a second overflow tank 315, and a second introduction device including a second introduction pipe 311, a second shunt pipe 312 communicating with the second introduction pipe 311, a second return pipe 313 communicating with the second shunt pipe 312, and a second delivery pipe 314 communicating with the second return pipe 313; the input end of the second quantifying tank 321 is communicated with the second shunt tube 312; the output end of the second quantifying tank 321 is communicated with the second overflow tank 315;
the second quantifying tank 321 is located at one side of the second shunt 312 near the center of the optical disc; the second overflow pool 315 is located at one side of the second quantifying pool 321 near the center of the optical disc;
the second overflow tank 315 includes a second tank a322 and a second tank B323 in communication with the second tank a 322; the second tank B323 is positioned at one side of the second tank A322 close to the second quantitative tank 321; the output end of the second quantifying tank 321 is communicated with a second tank A322;
a second transition section a303 is arranged at the communication position of the second check pipe 313 and the second delivery pipe 314; the minimum distance between the second transition section a303 and the center of the optical disc is smaller than the minimum distance between the second overflow pool 315 and the center of the optical disc;
a second transition section B304 is arranged at the communication position of the second ingress pipe 311 and the second shunt pipe 312; a second transition section C305 is arranged at the connection position of the second shunt tube 312 and the second check tube 313, and the second transition section a303, the second transition section B304 and the second transition section C305 are all fold lines;
the other end of the second guiding tube 314 is connected to the reaction tank 6, and the second guiding tube 311 is connected to the bending portion 208 of the blood vessel 206.
Preferably, the third metering device includes a third metering tank 412, a third overflow tank 415, and a third flow guide pipe, where the third overflow tank 415 is disposed at one side of the third metering tank 412 near the center of the optical disc; the second reagent pool 4 is arranged at one side of the third measuring pool 412 close to the center of the optical disc; one end of the third flow guiding pipe is communicated with the second reagent tank 4, and the other end of the third flow guiding pipe is communicated with the third metering tank 412;
the third guide pipe comprises a third guide pipe A421, a U-shaped pipe 422 connected with the third guide pipe A421 and a third guide pipe B423 connected with the U-shaped pipe 422;
the other end of the third conduit A421 is connected with the second reagent pool 4; the other end of the third conduit B423 is connected with the input end of the third metering tank 412; the minimum diameter of the third conduit A421 is larger than the maximum diameter of the U-shaped tube 422; the minimum diameter of the third conduit A421 is larger than the maximum diameter of the third conduit B423;
the third overflow tank 415 includes a third tank a413 and a third tank B414 connected to the third tank a 413; the third pool B414 is positioned at one side of the third pool A413 away from the center of the optical disc; the third quantitative pool 412 is connected with a third pool A413; the connection between the third quantitative pool 412 and the third pool A413 is positioned on the side surface of the third pool A413 away from the center of the optical disc;
the second reagent tank 4 is provided with an air pressure balance pipe 407; the other end of the air pressure balance tube 407 communicates with the whole blood pool 3.
Preferably, the third conduit C404 is connected to the buffer pool 5; the buffer pool 5 is located at one side of the third measuring pool 412 near the center of the optical disc; the other end of the third conduit C404 is connected with the input end of a third metering tank 412;
the buffer pool 5 is also provided with a pressure regulating pipe 405; the other end of the pressure regulating tube 405 is communicated with the whole blood pool 3; a fourth delivery pipe 406 is further arranged on the buffer tank 5, and the other end of the fourth delivery pipe 406 is communicated with the reaction tank; a return pipe 408 is communicated between the second reagent tank 4 and the buffer tank 5;
the minimum distance between the third conduit C404 and the center of the optical disc is smaller than the minimum distance between the second reagent reservoir 4 and the center of the optical disc.
Preferably, the reaction tank 6 is communicated with two feeding pipes 611, an exhaust pipe 610 is communicated with the reaction tank 6, an exhaust bin 612 is arranged on the exhaust pipe 610, and the other end of the exhaust pipe 610 is communicated with the whole blood tank 3;
the first delivery pipe 133 is communicated with the feeding pipe 611, and the fourth delivery pipe 406 and the second feeding pipe 311 are respectively communicated with the exhaust bin 612;
the inner wall of the reaction tank 6 is in arc transition, the arc length of the horizontal section of the reaction tank along the rotation direction of the optical disk is larger than the length of the horizontal section of the reaction tank perpendicular to the rotation direction, the horizontal section of the reaction tank is elliptical, and the short axis of the reaction tank passes through the rotation center of the optical disk.
Preferably, the first reagent tank 2 and the second reagent tank 4 are respectively provided with reagent packs 8.
Preferably, the reagent pack 8 is a capsule type reagent pack, and the capsule type reagent pack comprises films 81 connected together, a sealed pool formed between the films 81 and liquid reagent filled in the sealed pool; the three sides of the two films 81 are provided with sealing edges 82, and the sealing edges form a closed-loop seal; the cross section of sealed pond is trapezoidal, and trapezoidal upper base, lower base and a waist limit are equipped with the banding, film 81 adopts the aluminium film, utilizes centrifugal force, and the one side of not banding is automatic to be broken under the effect of centrifugal force. The present application is disposable, and a capsule type reagent pack is put in advance when the first reagent reservoir 2 and the second reagent reservoir 4 are manufactured.
In use, the first quantifying tank 121 quantifies the amount of the reagent R1, the second quantifying tank 321 quantifies the amount of the plasma, the third quantifying tank 412 quantifies the amount of the reagent R2, and the required dosage can be accurately quantified, the excess reagent R1 in the first quantifying tank 121 flows into the first overflow tank 122, the excess plasma in the second quantifying tank 321 flows into the second overflow tank 315, the excess reagent R2 in the third quantifying tank 412 flows into the third overflow tank 415, and the first quantifying tank 121, the second quantifying tank 321 and the third quantifying tank 412 are all filled. The separated plasma can directly enter the reaction tank 6 and then be added with the reagent R1 for reaction, and the reagent is buffered in the buffer tank 5 and then enters the reaction tank 6 for reaction and then is directly used for detection operation, so that the detection time is effectively shortened, secondary pollution and quantitative error which can occur in manual separation operation are particularly avoided, and solid guarantee can be provided for subsequent detection operation.
The present application needs to cooperate with a dedicated centrifugal operation device in which the rotational time and rotational speed required for each operation of the optical disc are stored. The centrifugal operation device is not within the scope of the application and will not be described in detail.
The optical disc mentioned in the present application is made of polymer plastic, the first reagent tank 2 and the first measuring tank 121 are made of die pressing, the first guide pipe 111 and the first guide pipe 123 are made of precision die pressing or etching, and the optical disc is integrated on one optical disc.
In use, a proper amount of reagent is injected into the first reagent tank 2, the centrifugal operation device drives the optical disk to rotate, and the reagent flows into the first metering tank 121 through the first flow guide pipe 111 under the action of centrifugal force. In order to further improve the ease of handling, the optical disk may be packaged directly in the first reagent reservoir 2 by packing the reagent during manufacture, and may be punctured during use or automatically ruptured by the pressure of the reagent against the packing bag.
The first flow guide tube 111 is connected to the outer surface of the first cuvette 121, and fills the first cuvette 121 from the outside to the inside with the reagent under the action of centrifugal force. After the first measuring tank 121 is filled, excess reagent is transferred to the first overflow tank 122 through the first conduit 123. The connection between the first flow guide tube 111 and the first overflow tank 122 is closer to the center of the optical disc, so that the pressure of the reagent in the first flow guide tube 111 gradually decreases in the direction of flowing to the first overflow tank 122, and the reagent can smoothly flow into the first overflow tank 122. Meanwhile, the first overflow pool 122 is closer to the center of the optical disc, so that the liquid pressure at the joint of the first diversion pipe 111 and the first overflow pool 122 is always smaller than the liquid pressure at the joint of the first quantitative pool 121 and the first diversion pipe 111, and the problem that the reagent in the first overflow pool 122 flows out along with the reagent flowing out of the first quantitative pool 121, so that the collection precision is reduced is avoided.
During the filling of the first dosing tank 121 from outside to inside, the air in the first dosing tank 121 is pressed into the first overflow tank 122. With the rotation of the optical disc, bubbles possibly existing in the reagent can be separated out and finally transferred into the first overflow tank 122, so that bubbles in the reagent can be removed simultaneously during quantitative collection, and the collection precision is ensured.
The surface of the first measuring cell 121 near the center of the optical disc is a front side surface, and the surface far from the center of the optical disc is a rear side surface. The front side and the rear side are designed with cambered surfaces, and the center of the cambered surfaces coincides with the center of the optical disc, so that the reagent can be ensured to be uniformly distributed in the first quantitative tank 121, and the gas inside the first quantitative tank is completely extruded into the first overflow tank 122. This is also designed to ensure acquisition accuracy.
The minimum distance between the first overflow tank 122 and the center of the optical disc is smaller than the minimum distance between the first quantifying tank 121 and the center of the optical disc, so that the air pressure in the quantifying tank 21 is always higher than the air pressure in the first overflow tank 122, and when the air in the first quantifying tank 121 is transferred to the first overflow tank 122, no resistance occurs.
During the reagent entering the first dosing tank 121, the atmospheric pressure of the first connecting tube 131 and the first dosing tank 121 is greater than the atmospheric pressure at the junction of the first conduit 123 and the first dosing tank 121. Thus, the reagent gradually fills the first measuring cell 121 instead of flowing out of the first connecting tube 131.
The following explanation is made for pressure: the atmospheric pressure of the first connecting pipe 131 and the first measuring tank 121 is provided by the first stopper pipe 132, and the atmospheric pressure at the junction of the first conduit 123 and the first measuring tank 121 is mainly provided by the first conduit 123. The first connecting pipe 131 and the first conduit 123 are connected with the outside, that is, the medium in the first connecting pipe and the first conduit is air, and the pressure is provided by the air under the action of centrifugal force. The pressure formula p=pgh of the reference liquid, and the magnitude of the pressure is determined by h in the case where ρ and g are the same. When the diameters of the first connection pipe 131 and the first guide pipe 123 are the same in a direction approaching the center of the optical disc, when the length of the first connection pipe 131 is greater than the length of the first guide pipe 123, the atmospheric pressure at the junction of the first connection pipe 131 and the first measuring tank 121 is greater than the atmospheric pressure at the junction of the first guide pipe 123 and the first measuring tank 121. In a practical product, the diameters of the first connecting tube 131 and the first conduit 123 are similar, and the length of the first connecting tube 131 is far greater than the length of the first conduit 123 in the direction approaching the center of the optical disc, so as to ensure that the pressure difference exists there all the time.
The first overflow pool 122 is further externally connected with a first exhaust pipe 105, and the free end of the first exhaust pipe 105 is connected with the atmosphere, so that the air pressure in the first overflow pool 122 is always equal to the atmospheric pressure, and the back pressure in the first overflow pool 122 is avoided during quantitative collection.
After the quantitative completion, the optical disc rotates reversely, and the reagent in the first quantitative tank 121 has a movement trend opposite to the rotation direction of the optical disc, and is sequentially transferred to the reaction tank 6 through the first connection pipe 131, the first stopper pipe 132 and the first delivery pipe 133 under the action of the centrifugal force, so that the subsequent reaction is performed.
The application comprises an optical disc 1, a separation tank 7 arranged on the optical disc 1, a blood inlet tube 202 for conveying whole blood and a blood outlet tube 206 for conveying blood plasma, wherein the blood inlet tube 202 and the blood outlet tube 206 are respectively communicated with the separation tank 7, the optical disc 1 is arranged on a rotating mechanism, the optical disc 1 is driven to rotate under the action of the rotating mechanism, preferably, the optical disc 1 adopts a round shape, and the center of the circle of the optical disc 1 is used as the axis for rotation.
The other end of the blood inlet tube 202 is communicated with the whole blood tank 3, the whole blood tank 3 is provided with a feeding hole 31 for feeding whole blood, and the maximum distance between the whole blood tank 3 and the rotation axis is smaller than the minimum distance between the separation tank 7 and the rotation axis. Whole blood is added into the whole blood tank 3, and the whole blood enters the separation tank 7 through the blood inlet tube 202 under the rotation action of the optical disk 1, and is centrifugally separated. Compared with the separation tank 7, the whole blood tank 3 is closer to the rotation axis, so that the whole blood can be effectively ensured to smoothly enter the separation tank 7.
Since the blood plasma is lighter and the red blood cells are heavier, the red blood cell storage part 701 and the blood plasma storage part 702 are formed in the separation tank under the action of centrifugal force, the red blood cell storage part is positioned on the outer side of the blood plasma storage part, and since the red blood cells account for about 40% of whole blood, the volume ratio of the limited red blood cell storage part to the blood plasma storage part is 2:3, the blood inlet tube 202 is communicated with the red blood cell storage part, the blood tube 206 is communicated with the blood plasma storage part, the blood plasma discharged from the blood tube 206 can be effectively ensured, the red blood cells are not doped, and the detection accuracy is ensured.
The center line 703 of the separation tank 7 passes through the rotation center of the optical disc 1 with respect to the perpendicular projection of the optical disc 1, helping to ensure the centrifugal effect.
A bending portion 208 is disposed on the outlet tube 206, and a distance between the bending portion 208 and a rotation center of the optical disc 1 is smaller than a minimum distance between the separation tank 7 and the rotation center. The bending part 208 is closer to the rotation center, so that the liquid needs more pressure to pass through the bending part 208 and then enter the next process, the residence time of the whole blood in the separation tank 7 can be prolonged, the full centrifugal separation is performed, the separation effect is very good, and only the plasma can be discharged from the blood tube 206.
The blood tube 206 can be connected with the reaction tank 6, and the blood tube 206 is directly transferred, so that the loss and pollution of a blood sample are avoided.
When it is necessary to dose plasma, a certain amount of plasma is injected through the second introduction tube 311, and the plasma starts to flow along the second introduction tube 311 as the optical disk 1 rotates. At this time, the air pressure in the second check pipe 313 is greater than the air pressure at the junction of the second quantitative tank 321 and the second shunt pipe 312, the plasma flows into the second quantitative tank 321, and the surplus flows into the second overflow tank 315. The second overflow pool 315 is divided into two parts, a second pool A322 and a second pool B323, and the excess plasma flows first into the second pool A322 and then into the second pool B323 under the action of centrifugal force. The amount of plasma injected is tightly controlled to ensure that there is no residual in the second reservoir a 322. Then, the optical disc 1 rotates in the reverse direction, so that the plasma in the second tank B323 cannot escape, and the plasma in the second quantitative tank 321 flows out by the centrifugal force, flows along the second shunt tube 312 and the second return tube 313 to the second delivery tube 314, and finally flows from the second delivery tube 314 to the reaction tank 6.
The application can quantitatively collect the reagent by utilizing the principle of combining centrifugation and quantitative collection. The reagent R2 is filled in the second reagent reservoir 4 or the reagent is directly contained in the optical disc 1 when the optical disc 1 is manufactured. When the optical disc 1 rotates, the reagent is transferred to the third quantitative tank 412 by centrifugal force, and the surplus is transferred to the third overflow tank 415. After the transfer is completed, the optical disc 1 rotates reversely, and the reagent in the third quantitative reservoir 412 flows out along the third conduit C404. The reagent amount is determined by the volume of the third quantitative pool 412, so that the interference of various factors such as tool errors, human errors, sight errors and the like during manual quantitative operation is avoided, and the quantitative accuracy can be effectively improved.
The third overflow tank of the application adopts a double-body design, when the optical disc 1 rotates forward, the reagent R2 transferred from the third metering tank 412 enters the tank A413 in a third way, and the reagent R2 is finally transferred into the third tank B414 under the action of centrifugal force. When the optical disc 1 rotates reversely, the reagent R2 in the third pool B414 has a movement trend away from the center of the optical disc, but the third pool B414 is not connected with the third quantitative pool 412, so that when the reagent R2 in the third quantitative pool 412 flows out, the reagent in the third pool B414 is kept still, the collection amount of the reagent R2 can be ensured to be equal to the volume of the fixed third quantitative pool 412, the collection precision is ensured, and finally the reagent R2 enters the reaction pool 6 after being buffered in the buffer pool 5.
When the optical disc 1 rotates in the reverse direction, the hydraulic pressure in the third conduit a421 is higher than the hydraulic pressures in the U-shaped pipe 422 and the third conduit B423. The reagent in the third dosing tank 412 can only flow out of the third conduit C404 during the outflow. The anti-reflux design can also improve the acquisition accuracy.
The sample after the reaction in the reaction tank 6 is directly used for the detection of a scattering electron microscope, a transmission electron microscope and a fluorescence electron microscope.
Finally, it should be noted that the above embodiments are merely for illustrating the technical solution of the present application, and not for limiting the same, and although the present application has been described in detail with reference to the above embodiments, it should be understood by those skilled in the art that modifications may be made to the technical solution described in the above embodiments or equivalents may be substituted for some technical features thereof, and these modifications or substitutions do not depart from the spirit and scope of the technical solution of the embodiments of the present application.
Claims (5)
1. A reagent disk testing device, comprising: the optical disk is provided with a first reagent pool, a first quantitative device communicated with the first reagent pool, a whole blood pool, a separation device communicated with the whole blood pool, a second quantitative device communicated with the separation device, a second reagent pool, a third quantitative device communicated with the second reagent pool and a buffer pool communicated with the third quantitative device, wherein the first quantitative device, the second quantitative device and the buffer pool are respectively communicated with the reaction pool, an adding hole is formed in the whole blood pool, the second reagent pool, the buffer pool and the first quantitative device are communicated with the whole blood pool, and the optical disk is a rotary light-transmitting optical disk;
the first quantitative device comprises a first quantitative pool and a first overflow pool, wherein the rear right side surface of the first quantitative pool is communicated with a first reagent pool through a first guide pipe, the front right side surface of the first quantitative pool is communicated with the first overflow pool through a first guide pipe, the rear left side surface of the first quantitative pool is communicated with the reaction pool through a first bending pipe, a first exhaust pipe is arranged at the top of the first overflow pool, and the first exhaust pipe is communicated with the whole blood pool;
the first bending pipe comprises a first connecting pipe, a first stop pipe communicated with the first connecting pipe, a first transition section communicated with the first stop pipe and a first delivery pipe communicated with the first transition section, and the first delivery pipe is communicated with the reaction tank;
the distance between each point of the front side surface of the first quantitative pool, which is positioned in the same height, and the center of the optical disk is equal;
the minimum distance between the first transition section and the center of the optical disc is smaller than the minimum distance between the first guide pipe and the center of the optical disc;
the minimum distance between the first overflow pool and the center of the optical disk is smaller than the minimum distance between the first quantitative pool and the center of the optical disk;
the separation device comprises a separation tank, a blood inlet pipe for conveying whole blood and a blood outlet pipe for conveying blood plasma, wherein the blood inlet pipe and the blood outlet pipe are respectively communicated with the separation tank, and the other end of the blood inlet pipe is communicated with the whole blood tank;
the separation tank is divided into a red blood cell storage part and a plasma storage part, the volume ratio of the red blood cell storage part to the plasma storage part is 2:3, the red blood cell storage part is positioned at the outer side of the plasma storage part, the blood inlet pipe is communicated with the red blood cell storage part, and the blood outlet pipe is communicated with the plasma storage part;
the blood outlet tube is provided with a bending part, and the distance between the bending part and the center of the optical disk is smaller than the minimum distance between the separation tank and the center of the optical disk;
the center line of the separating pool passes through the center of the optical disc relative to the vertical projection of the optical disc;
the maximum distance between the whole blood pool and the center of the optical disk is smaller than the minimum distance between the separation pool and the center of the optical disk;
the first reagent pool and the second reagent pool are respectively provided with a reagent pack, the reagent packs are capsule type reagent packs, and the capsule type reagent packs comprise films connected together, a sealed pool formed between the films and liquid reagents filled in the sealed pool; the four sides and the three sides of the two films are provided with edge sealing, and the edge sealing forms closed-loop sealing; the cross section of the sealing pool is trapezoid, the upper bottom edge, the lower bottom edge and one waist edge of the trapezoid are provided with edge sealing edges, and the film is an aluminum film.
2. The reagent disk testing apparatus according to claim 1, wherein the second quantitative device comprises a second quantitative tank, a second overflow tank, and a second introduction device comprising a second introduction pipe, a second shunt pipe communicating with the second introduction pipe, a second return pipe communicating with the second shunt pipe, and a second delivery pipe communicating with the second return pipe; the input end of the second quantitative pool is communicated with a second shunt tube; the output end of the second quantitative pool is communicated with the second overflow pool;
the second quantitative pool is positioned at one side of the second shunt pipe close to the center of the optical disc; the second overflow pool is positioned at one side of the second quantifying pool, which is close to the center of the optical disc;
the second overflow tank comprises a second tank A and a second tank B communicated with the second tank A; the second pool B is positioned at one side of the second pool A close to the second quantitative pool; the output end of the second quantitative pool is communicated with the second pool A;
a second transition section A is arranged at the communication part of the second check pipe and the second delivery pipe; the minimum distance between the second transition section A and the center of the optical disk is smaller than the minimum distance between the second overflow pool and the center of the optical disk;
a second transition section B is arranged at the communication part of the second ingress pipe and the second shunt pipe; a second transition section C is arranged at the communication part of the second shunt pipe and the second check pipe, and the second transition section A, the second transition section B and the second transition section C are all broken lines;
the other end of the second delivery pipe is communicated with the reaction tank, and the second ingress pipe is communicated with the bending part on the blood vessel.
3. The reagent disk testing device according to claim 2, wherein the third metering device comprises a third metering tank, a third overflow tank and a third flow guide pipe, wherein the third overflow tank is arranged at one side of the third metering tank close to the center of the optical disk; the second reagent pool is arranged at one side of the third quantitative pool, which is close to the center of the optical disk; one end of the third flow guide pipe is communicated with the second reagent tank, and the other end of the third flow guide pipe is communicated with the third quantitative tank;
the third guide pipe comprises a third guide pipe A, a U-shaped pipe connected with the third guide pipe A and a third guide pipe B connected with the U-shaped pipe;
the other end of the third conduit A is connected with a second reagent pool; the other end of the third conduit B is connected with the input end of the third measuring tank; the minimum diameter of the third conduit A is larger than the maximum diameter of the U-shaped pipe; the minimum diameter of the third conduit A is larger than the maximum diameter of the third conduit B;
the third overflow tank comprises a third tank A and a third tank B connected with the third tank A; the third pool B is positioned at one side of the third pool A away from the center of the optical disc; the third quantitative pool is connected with a third pool A; the joint of the third metering tank and the third tank A is positioned on the side surface of the third tank A, which is far away from the center of the optical disc;
the second reagent tank is provided with an air pressure balance pipe; the other end of the air pressure balance tube is communicated with the whole blood pool.
4. A reagent disk testing device according to claim 3, wherein the buffer pool is connected to a third conduit C; the buffer pool is positioned at one side of the third quantitative pool, which is close to the center of the optical disc; the other end of the third conduit C is connected with the input end of the third measuring tank;
the buffer pool is also provided with a pressure regulating pipe; the other end of the pressure regulating tube is communicated with the whole blood pool; a fourth delivery pipe is further arranged on the cache pool, and the other end of the fourth delivery pipe is communicated with the reaction pool; a return pipe is communicated between the second reagent pool and the buffer pool;
the minimum distance between the third conduit C and the center of the optical disc is smaller than the minimum distance between the second reagent reservoir and the center of the optical disc.
5. The device for testing the reagent disk according to claim 4, wherein two feeding pipes are communicated with the reaction tank, an exhaust pipe is communicated with the reaction tank, an exhaust bin is arranged on the exhaust pipe, and the other end of the exhaust pipe is communicated with the whole blood tank;
the first delivery pipe is communicated with the feeding pipe, and the fourth delivery pipe and the second ingress pipe are respectively communicated with the exhaust bin;
the inner wall of the reaction tank is in arc transition, the arc length of the horizontal section of the reaction tank along the rotation direction of the optical disk is larger than the length of the horizontal section of the reaction tank perpendicular to the rotation direction, the horizontal section of the reaction tank is elliptical, and the short axis of the reaction tank passes through the rotation center of the optical disk.
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