CN108474802A - Detection device - Google Patents
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- CN108474802A CN108474802A CN201580085443.8A CN201580085443A CN108474802A CN 108474802 A CN108474802 A CN 108474802A CN 201580085443 A CN201580085443 A CN 201580085443A CN 108474802 A CN108474802 A CN 108474802A
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- C12Q1/00—Measuring or testing processes involving enzymes, nucleic acids or microorganisms; Compositions therefor; Processes of preparing such compositions
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- G01N35/08—Automatic analysis not limited to methods or materials provided for in any single one of groups G01N1/00 - G01N33/00; Handling materials therefor using a stream of discrete samples flowing along a tube system, e.g. flow injection analysis
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Abstract
A kind of detection device (10,20,30), it includes a substrate (100,700), a lid (200,800), a micro- sensor chip (300, and a micro-channel structure (400) 900), wherein at least one of substrate (100,700) and lid (200,800) include porous material.Substrate (100,700) there is first surface (101), there is recessed portion (102 on first surface (101), 702), recessed portion (102,702) include bottom (103) and slope (104), wherein bottom (103) are embedded in substrate (100,700) in, slope (104) connects first surface (101) and bottom (103) and is configured at recessed portion (102,702) close to one end of an inlet (402,810).Lid (200,800) has the second surface (201) towards first surface (101).Micro- sensor chip (300,900) is embedded in the substrate (100,700).Micro-channel structure (400) is embedded in second surface (201) and forms a fluid channel (401,802) with the first surface (101).A specimen (600) is from inlet (402,810) via fluid channel (401,802) enter recessed portion (102,702) and subnatant (601) and upper liquid (602) are separated into, subnatant (601) rests on bottom (103), upper liquid (602) is from recessed portion (102,702) it flow to micro- sensor chip (300,900), and the process of a specimen (600) is detected all without application extra power in detection device (10,20,30).
Description
The invention relates to a kind of detection devices, and in particular to a kind of tool portability and checkout procedure is without under additionaling power, and the molecule of heavier mass in a specimen is separated with the molecule of lighter weight and at the same time carrying out the detection device of related check.
In the detection device of existing microfluid, it is formed by capillary phenomenon by the difference between the cohesive force of adhesive force and a specimen itself between a specimen and fluid channel, flows a specimen in fluid channel.After a specimen passes through a test section in fluid channel, micro- sensor chip in test section can be detected for a specimen.Finally, the read detection signal of micro- sensor chip is sent in external analysis instrument by researcher, carries out relevant research and analyzed with data.However, detection device now all must additionaling power drive the microfluidic flow in fluid channel, be thus greatly lowered the portability of detection device.
In the detection program of certain specific specimen, researcher needs first to screen a specimen to obtain and examine intracorporal specific molecular, is then analyzed and is studied for the specific molecular again.Such as a specimen, when being blood, in order to separate blood cell with blood plasma, blood is separated into blood cell and blood plasma with centrifugal separator by characteristic of the known detection mode using blood cell and blood plasma with different quality.Therefore, using the above-mentioned known techniques practice, not only program is miscellaneous, and detection time is tediously long, so very inconvenient with greater need for offer centrifuge separation electro-mechanical force to be detected.
Summary of the invention
In view of this, the purpose of the present invention is to provide a kind of detection devices, a specimen can be directly separated into the molecule of heavier mass and the molecule of lighter weight, and it is detected for a specimen for separated molecule, therefore it does not need to separate a specimen with centrifugal separator, not only simplifying detection program has convenience, more there is the environmentally protective concept for saving the energy.
Another object of the present invention is to provide a kind of detection devices, have height portability, a detection specimen is in the process without additionaling power.
In order to achieve the above objectives, detection device of the invention includes: a substrate, has a first surface, there is a recessed portion on first surface, recessed portion includes a bottom and a slope, and bottom is embedded in substrate, slope connection first surface and bottom and the one end for being configured at recessed portion；One lid, has
One second surface is towards first surface；One micro- sensor chip, is embedded in substrate；An and micro-channel structure, it is embedded in second surface, wherein lid is covered in after the substrate, first surface is mutually closely sealed with second surface, so that micro-channel structure and first surface is coupled to a fluid channel includes that an at least inlet and a volume controlled slot control flow of the specimen in fluid channel, the specimen enters recessed portion via fluid channel from inlet, a specimen is separated into a subnatant and a upper liquid in recessed portion, subnatant rests on the bottom, and upper liquid flow to micro- sensor chip from the recessed portion；Wherein fluid channel includes first-class choked flow road and a reactive tank, reactive tank are to be connected to micro- sensor chip, and flow resistance runner is formed between reactive tank and the volume controlled slot；Wherein at least one of substrate and lid include porous material.
In one embodiment of this invention, an above-mentioned specimen is blood, and subnatant is blood cell, and upper liquid is blood plasma.
In one embodiment of this invention, one end of above-mentioned fluid channel has a volume controlled slot, can control flow of the specimen in fluid channel.
In one embodiment of this invention, above-mentioned slope is configured at one end in the recessed portion close to the inlet.
In one embodiment of this invention, above-mentioned micro- sensor chip has an at least detection structure, biological particle or biopolymer in the energetic specimen of detection structure.
In one embodiment of this invention, above-mentioned detection device further includes a plurality of terminals, on substrate and is connected to micro- sensor chip, a plurality of terminals can be coupled to a reading device.
In one embodiment of this invention, above-mentioned multiple terminals are to be connected to micro- sensor chip in a manner of wire bonding (wire bonding).
In one embodiment of this invention, above-mentioned detection structure is the sensor using nanometer sensing material as the resistor-type on basis, capacitive, impedance type or transistor type or electrochemistry type or attribute or photoelectric type, nano material is selected from antibody, aptamer or glycan molecule or ferment by a high molecular functionalization of biology, the boiomacromolecule.Other than based on nanometer sensing material, pure electrochemistry type or photoelectric type sensor is also may be selected in detection structure.
In one embodiment of this invention, above-mentioned nanometer sensing material is selected from carbon nanotubes, graphene (graphene), reduction state graphene oxide (reduced graphene oxide, rGO), graphene oxide (graphene oxide, GO), nano wire band graphene (nanoribbon graphene), silicon nanowire, nanometer InP line, nano GaN line, Nano semiconductor line or Nanometer Semiconductor Films.
In one embodiment of this invention, the material of above-mentioned substrate is acryl (polymethylmethacrylate, PMMA), polyethylene terephthalate (polyethylene terephthalate, PET), polycarbonate (polycarbonate, PC), porous polydimethylsiloxanes
Alkane (polydimethylsilicon, PDMS), porous silica gel, rubber, plastic cement or glass.
In one embodiment of this invention, the material of above-mentioned lid is acryl (polymethylmethacrylate, PMMA), porous polyethylene terephthalate (polyethylene terephthalate, PET), polycarbonate (polycarbonate, PC), porous dimethyl silicone polymer (polydimethylsilicon, PDMS), porous silica gel, rubber or plastic cement.
In one embodiment of this invention, there is a pre-treatment portion between recessed portion and inlet, suitable for carrying out separation to the specimen or mixing with other reagents.
In one embodiment of this invention, when above-mentioned second surface and first surface are assembled, the sideline of second surface is located on the inside of the sideline of first surface.
In one embodiment of this invention, the detection device after above-mentioned completion evacuation is encapsulated in a vacuum packaging bag.
In one embodiment of this invention, the top surface of above-mentioned first surface and micro- sensor chip is same plane.
In one embodiment of this invention, region of the above-mentioned fluid channel between micro- sensor chip and recessed portion, the channel cross-sectional area in the fluid channel reduce.
In order to achieve the above objectives, a kind of detection device of the invention includes: a substrate, and having a first surface includes a recessed portion and an at least reactive tank；One lid is covered in the first surface of lid with a second surface；One micro- sensor chip is embedded in substrate, includes an at least sensing area；One first inlet；One second inlet；And one micro sprue system be formed between substrate and lid, be formed in the first surface of substrate including one first fluid channel and a little reactive tanks of connection and the second inlet, one second fluid channel are formed in the second surface of lid and a volume controlled slot is formed in the second surface of lid and is connected to the second fluid channel and a third fluid channel connects a little reactive tanks to micro- sensor chip at least sensing area；Wherein the second fluid channel includes a first part and a second part, and first part is to extend to volume controlled slot by the first inlet and be connected to recessed portion, and second part is that an at least reactive tank is extended to by volume controlled slot；Wherein at least one of substrate and lid include porous material.
In order to achieve the above objectives, a kind of detection device of the invention includes: a substrate, and having a first surface includes a recessed portion and a decomposer；There is one lid a second surface to be covered in the lid first surface；One micro- sensor chip is embedded in substrate, includes a sensing area；One fluid channel is formed between substrate and lid, and is connected to the sensing area of recessed portion and micro- sensor chip；One heating component is formed in a part lower section of fluid channel；Wherein at least one of substrate and lid include porous material；Wherein a decomposed solution includes after the specimen with DNA is full of decomposer and recessed portion and adds through being flowed to by fluid channel
Above hot component, it is heated component circulating-heating and massive duplication, then flows to the sensing area of micro- sensor chip via fluid channel.
In order to which above and other objects, features and advantages of the invention can be clearer and more comprehensible, embodiment is cited below particularly out and institute's attached drawing is cooperated to elaborate.
Fig. 1 is the stereoscopic schematic diagram of the detection device of one embodiment of the invention.
Fig. 2 is the substrate stereoscopic schematic diagram of the detection device of one embodiment of the invention.
Fig. 3 is the recessed portion stereoscopic schematic diagram of one embodiment of the invention.
Fig. 4 is the substrate and lid perspective exploded view of the detection device of one embodiment of the invention.
Fig. 5 is the substrate and lid perspective exploded view of the detection device of another embodiment of the present invention.
Fig. 6 is the specimen schematic diagram in the recessed portion of one embodiment of the invention.
Fig. 7 is the reduced cross-sectional area schematic diagram in the fluid channel of one embodiment of the invention
Fig. 8 is the schematic diagram of the pre-treatment portion of one embodiment of the invention.
Fig. 9 is the detection device experimental record table of one embodiment of the invention.
Figure 10 is the stereoscopic schematic diagram of another embodiment of the present invention.
Figure 11 A and Figure 11 B are the schematic top plan view of another embodiment of the present invention.
Figure 12 to Figure 16 is the different embodiments for the recessed portion for showing another embodiment of the present invention about substrate.
Figure 17 is the birds-eye perspective for showing another embodiment of the present invention.
Figure 18 is the birds-eye perspective for showing another embodiment of detection device of the present invention.
Symbol description
10,20,30: detection device
100,700: substrate
101: first surface
102,702: recessed portion
103: bottom
104: slope
200,800: lid
300,900: micro- sensor chip
814: the first sensing chambers
816: the second sensing chambers
818: third senses chamber
820: the four sensing chambers
400: micro-channel structure
401,802,804,704: fluid channel
402: inlet
403,803: quantitative control structure
404: pre-treatment portion
405,805: volume controlled slot
408,808: flow resistance runner
409: reactive tank
500,720: terminal support plate
501,721: a plurality of terminals
600: a specimen (blood)
601: subnatant (blood cell)
602: upper liquid (blood plasma)
603: biomarker
604: aptamer
706: the first reactive tanks
708: the second reactive tanks
710: third reactive tank
712: the four reactive tanks
750: heating component
751: heating chip
752: resistive conductor
752a, 752b: conducting end
760: decomposer
809: sensing chamber
810: the first inlets
812: the second inlets
Unless otherwise specified, all technical and scientific terms used here have the meaning understood as those skilled in the art.
" one " word used herein, it is such as not specified, refer to the quantity of at least one (one or more).
Fig. 1 is schematically shown as the stereoscopic schematic diagram of the detection device of one embodiment of the invention, Fig. 2 is schematically shown as the substrate stereoscopic schematic diagram of the detection device of one embodiment of the invention, Fig. 3 is schematically shown as the recessed portion stereoscopic schematic diagram of one embodiment of the invention, Fig. 4 is schematically shown as the substrate and lid perspective exploded view of the detection device of one embodiment of the invention, and Fig. 5 is schematically shown as the substrate and lid perspective exploded view of the detection device of another embodiment of the present invention.Fig. 1, Fig. 2, Fig. 3, Fig. 4 and Fig. 5 are please referred to, detection device 10 of the invention includes substrate 100, lid 200, micro- sensor chip 300 and micro-channel structure 400.On the substrate 100, there is first surface 101, and on first surface 101, there is a recessed portion 102.Recessed portion 102 is made of bottom 103 and slope 104, wherein bottom 103 is embedded in substrate 101, and slope 104 is one end in recessed portion 102 close to inlet 402.
Further, in an embodiment of the present invention, at least one of substrate 100 and lid 200 include porous material, there is second surface 201 on lid 200, when in the covering to substrate 100 of lid 200, first surface 101 is mutually closely sealed between the two towards second surface 201.There is micro-channel structure 400 on second surface 201, when lid 200 is covered in substrate 100, micro-channel structure 400 is combined with first surface 101 forms a fluid channel 401, after forming vacuum state on the inside of at least porous material of one of substrate 100 and lid 200 and fluid channel 401, a specimen 600 is placed in the inlet 402 of fluid channel 401, the suction generated by vacuum in fluid channel 401, a specimen 600 is driven to enter the recessed portion 102 via fluid channel 401 from inlet 402, a specimen 600 is separated into subnatant 601 and upper liquid 602 (as shown in Figure 6) in recessed portion 102, subnatant 601 rests on the bottom 103, upper liquid 602 flow to micro- sensor chip 30 from the recessed portion 102 0.
In an embodiment of the present invention, a specimen 600 can refer to body fluid (Body fluid), the solution including blood, celiolymph, gastric juice and various digestive juices, sperm, saliva, tear, sweat, urine, vaginal secretion etc. or containing a specimen 600.In the present embodiment by taking blood as an example, when blood enters recessed portion 102 along fluid channel 401, the blood cell (subnatant 601) of heavier mass can be deposited in the bottom 103 of recessed portion 102, and the blood plasma (upper liquid 602) of lighter weight can leave from recessed portion 102 and enter micro- sensor chip 300 along fluid channel 401.When a specimen 600 is more thick, for example, blood when, to make a specimen 600 is more smooth to be injected by inlet 402, the bottom of inlet 402 and/or side wall can be coated with an anticoagulant.
It is noted that the slope 104 of recessed portion 102 of the invention, which has, ensures that a specimen 600 can be recessed
The isolated function of concave portion 102.In known technology, a specimen 600 often because what is separated is ineffective, when the specimen 600 after leading to separation is via micro- 300 interpretation of sensor chip, produces the result of erroneous judgement.In detection device 10 of the invention, recessed portion 102 has the function of keeping a specimen 600 more smooth when flowing in fluid channel 401 close to the slope 104 of one end of inlet 402, when a specimen 600 can be smooth in fluid channel 401 when flowing to recessed portion 102, the molecule of different weight can be under relatively small number of external interference, different settling rates is generated according to the difference of weight, also therefore, the molecule of different weight can more efficiently carry out separating.In order to increase the effect that recessed portion 102 separates a specimen 600, the suspended matter that microcylinder (micro pillars) distance of array-like arrangement intercepts less than 3 microns 3 microns or more can be formed in the intersection of recessed portion 102 and fluid channel 401, or form microcylinder of the distance between 10 to 100 microns, plural size of arranging in pairs or groups again is greater than the plural microsphere of plural microcylinder distance to form plural gap, to intercept the suspended matter for being greater than void size, gradient and/or the surface roughness on the slope 104 of recessed portion 102 can also be increased to intercept more suspended matters.The surface on 102 bottom 103 of recessed portion and slope 104 can be handled by oxygen plasma or surfactant etc. to increase hydrophily, promote the probability of suspended substance sedimentation in a specimen 600.If a specimen 600 is the blood containing blood platelet, can be fallen in recessed portion 102 in the bottom of recessed portion 102 103 and the coagulant of the coating of slope 104 for example, calcium chloride (CaCl) with promoting blood cell condensation aggregation.If a specimen 600 is a non-blood specimen for the body cell for example, in lactogenesis, a mixture can be added comprising fibrin ferment (Thrombin), fibronectin (fibrinogen) and calcium ion (Calcium ion) to form a web (fibrin mesh) in the bottom of recessed portion 102 103 and the coating of slope 104 or in a specimen 600, increase suspended substance sedimentation in the probability of recessed portion 102.
When a specimen 600 is during separation, research project, which is usually also included, carries out quantitative analysis to isolated sample.In an embodiment of the present invention, there is a volume controlled slot 405 relative to the other end of inlet 402 in fluid channel 401, purpose analyzes designed structure aiming at a quantitative specimen 600., can be by recessed portion 102 and micro- sensor chip 300 after 600 self seeding mouth 402 of a specimen enters fluid channel 401, the last storage of a specimen 600 is into volume controlled slot 405.After a specimen 600 is filled with volume controlled slot 405, fluid channel 401 would not be entered back into a specimen 600 for inlet 402, so the signal that micro- sensor chip 300 is detected, is exactly the signal as caused by the quantitative specimen 600 in volume controlled slot 405.In this example, it is assumed that volume controlled slot 405 has the capacity of 0.5cc, although the specimen 600 for being applied to inlet 402 is much larger than 0.5cc, the signal specimen 600 that can be detected by micro- sensor chip 300 only has 0.5cc.If by the signal detected by micro- sensor chip 300 divided by 0.5cc, the unit of signal if, is presented with concentration style.In the present embodiment, there is a certain amount of control structure 403 on second surface 201, the volume controlled can be formed by the combination of first surface 101 and quantitative control structure 403
Slot 405.
In one embodiment of this invention, micro- sensor chip 300 is embedded in substrate 100, and the top surface of micro- sensor chip 300 and first surface 101 are necessary for same plane and can flow into micro- sensor chip 300 with the specimen 600 ensured in fluid channel 401.In the present embodiment, fluid channel 401 and in another embodiment, can also be passed through an at least detection structure for micro- sensor chip 300 from the top through an at least detection structure for micro- sensor chip 300 by fluid channel 401 from below.Each detection structure is modified using biological coupling, the biological particle or biopolymer that can be directed in a specimen 600 are quantified, it can also be further via such as resistor-type on micro- sensor chip 300, it is capacitive, impedance type, or transistor type, or electrochemistry type includes nanometer or non-nano, or attribute, photoelectric type includes nanometer or non-nano sensing element, it is converted into electrical signals, the I/O weld pad of last micro- sensor chip 300 is electrically connected at a plurality of terminals 501, extraneous reading device is electrically connected to by a plurality of terminals 501 again, signal output be will test to provide relevant research and analysis.In an embodiment of the present invention, the mode that a plurality of terminals 501 also can use wire bonding (wire bonding) is connected to micro- sensor chip 300.In certain embodiments, micro- sensor chip 300 also may include amplifier circuit, detect faint electric signal with amplification.
When measuring a specimen 600 using detection device 10, in order to carry out the detection of a low concentration specimen 600, region of the present invention in fluid channel 401 between micro- sensor chip 300 and recessed portion 102, it designs the reduced cross-sectional area in fluid channel 401, reduce by 600 flow velocity of a specimen into micro- sensor chip 300, it so can be increased a specimen 600 in micro- 300 residence time of sensor chip, a most specimen 600 can also be made closer to micro- sensor chip 300, with the detection of a sharp low concentration specimen 600.As shown in Figure 7, in one embodiment of this invention, the flow channel depth of fluid channel 401 was 60 μm originally, flow channel depth between micro- sensor chip 300 and recessed portion 102 can be gently reduced to 10 μm with a slope, so allow the biomarker 603 of 401 upstream depth runner (60 μm) of fluid channel therefore through slope, slow down its flow velocity, and limit its suspension range, and therefore rush at the aptamer 604 of 401 bottom of fluid channel, so that most biomarkers 603 is all gone to the capture of aptamer 604 of 401 bottom of fluid channel, since flow velocity is low, therefore all biomarkers 603 being caught in can be all fixed on aptamer 604.
In detection device 10 of the invention, detection structure be using nanometer sensing material as basis resistor-type, capacitive, impedance type or transistor type, electrochemistry type, attribute sensor, nanometer sensing material passes through the functionalization of boiomacromolecule, which particularly relates at least antibody or aptamer (aptamer) or one of glycan molecule or ferment molecule.Sensor can be a plurality of or array type, to provide the quantitative testing of a variety of subject matters in a specimen 600.Can be nano wire (nanowire) such as carbon nanotubes, silicon nanowire, the nanometer InP line suitable for sensing in above-mentioned nanometer sensing material, nano GaN line etc. has the material or Nano semiconductor line of characteristic of semiconductor,
Or Nanometer Semiconductor Films, or graphene (graphene), reduction state graphene oxide (reduced graphene oxide, rGO), graphene oxide (graphene oxide, GO), nano wire band graphene (nanoribbon graphene) etc..Other than based on nanometer sensing material, pure electrochemistry type or photoelectric type sensor is also may be selected in detection structure.
In the embodiment of detection device 10 of the invention, the material of substrate 100 can be acryl (polymethylmethacrylate, PMMA), polyethylene terephthalate (polyethylene terephthalate, PET), polycarbonate (polycarbonate, PC), porous dimethyl silicone polymer (polydimethylsilicon, PDMS), porous silica gel, rubber, plastic cement or glass；The material of lid 200 can be acryl (polymethylmethacrylate, PMMA), polyethylene terephthalate (polyethylene terephthalate, PET), polycarbonate (polycarbonate, PC), porous dimethyl silicone polymer (polydimethylsilicon, PDMS), porous silica gel, rubber or plastic cement.
It raises one to be mentioned that, when selecting the material of substrate 100 and lid 200, it is necessary in view of substrate 100 and the material property of lid 200 between the two.When lid 200 is covered in substrate 100, must be evacuated to form vacuum state to provide the driving suction that a specimen 600 flows in fluid channel 401 on the inside of fluid channel 401.Therefore, at least substrate 100 and lid 200 one of them must be porous material, preferably, the material hardness characteristic of substrate 100 and lid 200 between the two can be one firmly soft with one.By taking one embodiment of the invention as an example, 100 material of substrate is to select the higher plastic cement of hardness, and lid 200 is to select the lower porosity dimethyl silicone polymer of hardness (polydimethylsilicon, PDMS), and micro-channel structure 400 is formed on the lower lid 200 of hardness, so when being evacuated in fluid channel 401, the lower porosity dimethyl silicone polymer (polydimethylsilicon of hardness, PDMS it) will be pasted on the higher plastic substrate 100 of hardness, the intrapore air of PDMS can be extracted simultaneously, to maintain vacuum state in fluid channel 401.When detection device 10 exposes under normal atmospheric pressures an, porosity dimethyl silicone polymer (polydimethylsilicon, PDMS hole vacuum state) can be inserted gradually by outside air, as long as can provide 401 negative pressure of fluid channel but not and before extraneous pressure balance to drive a specimen 600 to flow.
In the above embodiments, substrate 100 is to select the higher plastic material of hardness, and the material of lid 200 is to select hardness lower and the porous dimethyl silicone polymer (polydimethylsilicon, PDMS) of tool.And invention is not limited thereto, substrate 100 is also possible to select the lower material of hardness, and lid 200 is the higher material of hardness.It is worth noting that, in order to can be with mass production by the present invention, in addition to the material of selection substrate 100 and lid 200 must be can be applied in the technology of injection moulding (mold injection), the substrate 100 that in addition combine and vacuumize for pre- tetrandra root and lid 200 because of
It transports and generates collision in handling process so that can not closely sealed maintenance vacuum state between the substrate 100 and lid 200, the present invention is specifically designed when first surface 101 and second surface 201 are bonded to each other assembling, and the sideline of second surface 201 is all located on the inside of the sideline of first surface 101 (as shown in Figure 1).Because to produce seam when being bonded to each other thin for both first surface 101 and second surface 201, in mass production, it is thin that automation equipment need only use sealing close the seam, can vacuumize for inlet implementation, make to form vacuum state inside fluid channel.In an embodiment of the present invention, the detection device 10 after completing evacuation is encapsulated in a vacuum packaging bag.
In another embodiment of the invention, recessed portion 102, micro- sensor chip 300, micro-channel structure 400 and quantitative control structure 403 are arranged on substrate 100, in another embodiment, recessed portion 102, micro- sensor chip 300, micro-channel structure 400 and quantitative control structure 403 can also be configured on lid 200.In another preferred embodiment of the present invention, a plurality of fluid channel 401, multiple recessed portions 102, multiple micro- sensor chips 300 and multiple quantitative control structures 403 can be configured on substrate 100, it is combined via special substrate 100 with the configuration of lid 200, it can make single detection device 10 while handle multinomial test sample, it is not only efficient and save time cost；And there is a pre-treatment portion 404 (as shown in Figure 8) in another embodiment of the invention, between recessed portion 102 and inlet 402, be suitable for carrying out separation to a specimen 600 or mixed with other reagents.Certain special specimen 600 are before actually detected, it is necessary to the impurity in an original specimen 600 is got rid of, or is mixed in advance with other substances, and the pre-treatment portion 404 of the present invention have the function of providing above-mentioned separation with mix.
It is worth noting that, detection device 10 of the invention is in the way of vacuumizing, one of substrate 100 and lid 200 arrange in pairs or groups as porous material, the fluid channel 401 for keeping it internal, recessed portion 102 and volume controlled slot 405 are relative to outside atmospheric pressure one negative pressure of generation, when a specimen 600 is placed in inlet 402, by the pressure difference of atmospheric pressure and negative pressure, a specimen 600 is just able to flow through recessed portion 102 along fluid channel 401, micro- sensor chip 300 is to volume controlled slot 405, complete this detection, and extra power need not be provided using such as dynamical elements such as pump or valve member in the detection process to drive a specimen 600 to flow.Fig. 9 is the 10 experimental record table of detection device of one embodiment of the invention, referring to Fig. 9, in test sample 1, because detection device 10 does not first pass through vacuumize process, although a specimen 600 is dropped to inlet 402, after one day, a specimen 600 can not still flow to recessed portion 102；In test sample 2 to 6, for detection device 10 respectively after 6 points of 30 seconds to 7 minutes vacuumize processs, which about needs 14 to 17 clocks to flow to micro- 300 entrance of sensor chip.Therefore learnt from experiment, detection device 10 of the invention after the vacuumize process of specific time, the type of flow in the detection device 10 of a specimen 600 it is with uniformity with it is repeated.
Referring to Fig. 10, a plurality of terminals of detection device 10 of the present invention can be formed in another embodiment
In on a terminal support plate 500, and terminal support plate 500 is formed on the first surface 101 of substrate 100 and protrudes from the side of substrate 100.Micro- sensor chip 300 of the present embodiment can be similar to previous embodiment；Lid 200, volume controlled slot 405, inlet 402, recessed portion 102 and fluid channel 401 can also be similar to previous embodiment.
Please refer to Figure 11 A and Figure 11 B, the detection device 10 of foregoing embodiments of the present invention can also include: first-class choked flow road 408 is formed in fluid channel 401；And one reactive tank 409 be connected to micro- sensor chip 300, wherein flow resistance runner 408 is formed between volume controlled slot 405 and reactive tank 409, further to postpone the time that a specimen 600 flows to quantitative control structure 403, increase the time that a specimen 600 is reacted with micro- sensor chip 300, and then promotes the accuracy of detection.Since a specimen 600 is suspended in specimen liquid comprising specimen liquid and subject matter to be measured, must have enough subject matters to be measured to be deposited on micro- sensor chip 300 can make most correct analysis, flow resistance runner 408 can be such that a specimen 600 reaches 3~7 minutes full of the time for making a specimen 600 rest on reactive tank 409 after reactive tank 409, it, can be of about 5 minutes in an embodiment.The effect that flow resistance runner 408 slows down 600 flow velocity of a specimen can be such that an a certain amount of specimen 600 adequately reacts with micro- sensor chip 300, when the cavity corresponding to the reactive tank 409 is filled with a specimen 600, a specimen 600 is continued to flow toward volume controlled slot 405 from flow resistance runner 408, only the volume relative response slot 40 of flow resistance runner 408 is very small, therefore before a specimen 600 flow to volume controlled slot 405, a specimen 600 in reactive tank 409 can be considered static state, i.e. within a unit time, micro- sensor chip 300 is reacted with an a certain amount of specimen 600, therefore the volume for the cavity that reactive tank 409 is combined with substrate 100 can be used as the unit of a certain amount of analysis.Flow resistance runner 408 can have zigzag pattern, as Figure 11 A complications number is more, tortuous amplitude is short and width of flow path is narrow form or 11B scheme that tortuous number is less, tortuous amplitude is longer and the wider form of width of flow path.
Figure 12 to Figure 16 is please referred to, is to show that the recessed portion 102 of the substrate 100 of detection device 10 of the invention there can be different variations.As shown in figure 12, the flat bottom 103 of recessed portion 102 is compared with slope 104 close to inlet 401.As shown in figure 13, recessed portion 102 can only have slope 104 without flat bottom, and the depth on slope 104 is deeper further away from inlet 401.As shown in figure 14, recessed portion 102 can only have slope 104 without flat bottom, and the depth on slope 104 is more shallow further away from inlet 401.As shown in figure 15, the width of recessed portion 102 can be in narrower further away from inlet 401.As shown in figure 16, the width of recessed portion 102 can be in wider further away from inlet 401.
In conclusion detection device 10 of the invention can separate the molecule of heavier mass in a specimen 600 with the molecule of lighter weight by the design of recessed portion 102.Because without using centrifugal separator, and the separation of a specimen 600 can be directly carried out, so detection device 10 of the invention is in use with convenience and the environmentally protective concept for saving the energy.When detection device 10 of the invention be electrically connected at it is external
When device, a specimen 600 after separation can will test signal and be uploaded to external device while being detected, and personnel for deliberation carry out subsequent relevant research and analysis, thus detection device 10 of the invention also have the advantages that detect quickly with it is easy to operate.
The birds-eye perspective for please referring to Figure 17 is display another embodiment of detection device of the present invention.Detection device 20 of the present invention includes: a substrate 700 includes a recessed portion 702, a fluid channel 704 and an at least reactive tank can be for example comprising one first reactive tank 706, one second reactive tank 708, a third reactive tank 710 and one the 4th reactive tank 712, wherein the first~tetra- reactive tank is connected to by fluid channel 704；One lid 900, which senses chamber 814, at least one sensing chamber comprising plural inlet such as one first inlet 810, one second inlet 812, fluid channel 802,804, one first, for example to sense chamber 818 and one the 4th sensing chamber 820 and a certain amount of control structure 803 comprising one second sensing chamber 816, a third；One micro- sensor chip 900 is embedded in substrate 700；And one terminal support plate 720 connect micro- sensor chip 900 and surface is formed with a plurality of terminals 721.Fluid channel 802 may include that a first part is located between the first inlet 810 and quantitative control structure 803 and a second part is roughly parallel to first part and is extended by quantitative control structure 803 towards the second inlet 812, and wherein the first part of fluid channel 802 and second part are two different locations for being connected to quantitative control structure 803.Lid 800 can further include the first part that first-class choked flow road 808 is formed in fluid channel 802.By previously described embodiment it is found that quantitative control structure 803 also may be formed at substrate 700 other than it can be formed in lid 800.
It is the higher plastic cement of hardness or hydrophilic material that the material of substrate 700, which can be similar to previous embodiment, it is the softer porosity PDMS or other hydrophobic materials of hardness that the material of lid 800, which can be similar to previous embodiment, implies that the hydrophobicity of lid 800 is high compared with substrate 700.Behind the covering of lid 800 to substrate 700, the first part of fluid channel 802 is first sensing area of one of the recessed portion 702 for being connected to substrate 700 and micro- sensor chip 900, first reactive tank 706, the second reactive tank 708, third reactive tank 710 and the 4th reactive tank 712 top coverd part 800 close and be connected to respectively by the branch of the second part of fluid channel 802, the quantitative control structure 803 and substrate 100 of lid 800 form a volume controlled slot 805.Behind the covering of lid 800 to substrate 700, it is four different detecting parts for being respectively overlay in second sensing area of one of micro- sensor chip 900 that first sensing chamber 814, second, which senses chamber 816, third sensing chamber 818 and the 4th sensing chamber 820, and the first sensing chamber 814, second senses chamber 816, third sensing chamber 818 and the 4th sensing chamber 820 and is connected to the first reactive tank 706, the second reactive tank 708, third reactive tank 710 and the 4th reactive tank 712 through a fluid channel 804 respectively.The first part of fluid channel 802 optionally broadens at the micro- sensor chip 900 of correspondence.Fluid channel 802,804,704, volume controlled slot 805 can be considered a micro sprue system.Although there are four reactive tank four sensing chambers of collocation for the tool of detection device 20 of the present embodiment, in other embodiments, detection device 20 also can be only anti-with one
Answer slot and a sensing chamber.Although the detection device 20 of the present embodiment has two sensing areas, also can only have a sensing area in other embodiments.Substrate 700 has hydrophily due to lid 800 is with hydrophobicity, therefore when being passed through a specimen by the first inlet 810 and entering fluid channel 802, a specimen can be adsorbed automatically by the side of substrate 700 in fluid channel 802, fluid channel 802 can be just full of more than a specimen after its hydrophilic saturation value until substrate 700 adsorbs a specimen, therefore it when a specimen flow to for example, groove bodies such as recessed portion 702 or volume controlled slot 805, can also be flowed full of being flowed out again from fluid channel 802 after groove body toward next groove body.
The detection device 20 of the present embodiment can be applied to liquefaction resistance, such as following steps:
1: the first reactive tank 706 of Step, the second reactive tank 708, third reactive tank 710 and the 4th reactive tank 712 insert four kinds of antibiotic (not shown) for being directed to a bacterium in advance, are attached at each groove body bottom with patch form.
2: the first inlet 810 of Step instills specimen (not shown), and a specimen enters recessed portion 702 via the first part of fluid channel 802 with impurity screening.The vacuum state of the fluid channel 802 of detection device 20 can be such that a specimen flows automatically toward 805 direction of volume controlled slot known to previous embodiment, can press volume controlled slot 805 by lid 800 when necessary and generate deformation to form negative pressure, to drive the flowing of a specimen.
Step 3: after recessed portion 702 fills up, a filtered specimen arrives at the first sensing area of micro- sensor chip 900 via the first part of fluid channel 802, and micro- sensor chip 900 can first judge whether there is the bacterium that detect drug resistance in a specimen at this time.
Step 4: culture solution is instilled by the second inlet 812, since the first reactive tank 706, the second reactive tank 708, third reactive tank 710 and the 4th reactive tank 712 are connected to by fluid channel 704, the reaction groove height using connecting pipe principle by the liquid surface height controlling of four reactive tanks 95%.
Step 5: a filtered specimen is by injection capacity control flume 805 after the completion of the preliminary interpretation of micro- sensor chip 900, after volume controlled slot 805 collects a full specimen after filtering, a specimen after filtering begins to be injected separately into the first reactive tank 706, the second reactive tank 708, third reactive tank 710 and the 4th reactive tank 71 via four branches of the second part of fluid channel 802, after four reactive tanks are filled with, a specimen after filtering fills the first sensing chamber 814, second sensing chamber 816, third sensing chamber 818 and the 4th sensing chamber 82 via fluid channel 804 immediately.
Step 6: four electric signals of four detecting parts of micro- 900 second sensing area of sensor chip are read.
After Bacteria Culture about half an hour in 7: the first reactive tank 706 of Step, the second reactive tank 708, third reactive tank 710 and the 4th reactive tank 71, four electric signals of four detecting parts of micro- 900 second sensing area of sensor chip are read again.
Step 8: comparing the electric signal of Step 6 Yu Step7, if there is significant change, that is, can determine whether to correspond to
The drug resistance of antibiotic.Such as, if comparing Step6 in the electric signal of the corresponding first sensing chamber 814 of the micro- sensor chip 900 of Step7 to increase, representing bacterium has drug resistance to the antibiotic in the first reactive tank 706, if the electric signal on the contrary in the corresponding first sensing chamber 814 of the micro- sensor chip 900 of Step7 compares Step6 without obviously increasing, representing the antibiotic in the first reactive tank 706 has the effect of inhibiting this bacterial growth.
The detection device 20 of the present embodiment is equally applicable for the allochthon (exosome) in detection blood, such as following steps:
Step 1: being instilled the blood (not shown) for having exosome by the first inlet 810, and blood blood cell after the first part of fluid channel enters recessed portion 702 is intercepted by recessed portion 702, and blood plasma continues to flow toward micro- sensor chip 900.The vacuum state of the fluid channel 802 of detection device 20 can be such that blood plasma flows automatically toward 805 direction of volume controlled slot known to previous embodiment, can press volume controlled slot 805 by lid 800 when necessary and form negative pressure, to drive the flowing of blood plasma.
Step 2: cell lysis (1ysis buffer) is instilled by the second inlet 812, since the first reactive tank 706, the second reactive tank 708, third reactive tank 710 and 712 system of the 4th reactive tank are connected to by fluid channel 704, reaction groove height based on connecting pipe principle, by the liquid surface height controlling of four reactive tanks 95%.Due to that needn't judge whether allochthon is preset type when detection device 20 is applied to the allochthon in detection blood, one of micro- sensor chip 900 of detection device 20, which only can also have a sensing area, a reactive tank and be connected to micro- sensor chip 900, senses chamber.
Step 3: full blood plasma is collected by the first part of fluid channel 802 to volume controlled slot 805, blood plasma is just injected separately into the first reactive tank 706, the second reactive tank 708, third reactive tank 710 and the 4th reactive tank 712 by four branches of the second part of fluid channel 803 and reacts with cell lysis, and cell lysis can decompose the cell wall of allochthon to expose the protein of allochthon.After four reactive tanks are filled with, it is reacted after blood plasma immediately via fluid channel 804 fill the first sensing chamber 814, second sensing chamber 816, third sensing chamber 818 and the 4th sensing chamber 82.
Step 4: four electric signals of four detecting parts of micro- 900 second sensing area of sensor chip are read.
After external in 5: four reactive tanks of Step starts reaction about half an hour, four electric signals of four detecting parts of micro- 900 second sensing area of sensor chip are read again.
Step 6: comparing the electric signal of Step 5 Yu Step4, and the concentration of allochthon can be calculated by the variation of two step electric signals.
Figure 18 is please referred to, is the birds-eye perspective for showing another embodiment of detection device of the present invention.Detection device 30 includes: a substrate 700 includes a recessed portion 702 and a decomposer 760；One lid 800 includes a fluid channel 802, one sensing chamber 809, one first inlet 810 and one second inlet 812；One micro- sensor chip 900 is embedded in the substrate 700 and there is a sensing area to be connected by the sensing chamber 809
It is logical；One heating component 750 is formed on heating chip 751 with heating chip 751 and 752 meander-like of a resistive conductor comprising one；And one terminal support plate 720 connect micro- sensor chip 900 and surface is formed with a plurality of terminals 721.Recessed portion 702 can be the recessed portion of foregoing embodiments, such as the different form of Figure 12 to 16, and/or the microcylinder (micro pillars, not shown) of array-like arrangement or other structures having revealed that are formed with the intersection of fluid channel 802 can increase the suspended substance sedimentation probability of a specimen.There are two conducting ends 752a, 752b to be electrically connected in two contacts of a power supply unit (not shown) for 752 system of resistive conductor of heating component 750, the temperature of resistive conductor 752 can rise and heat the fluid channel 802 of top, the temperature of heating chip 751 then controllable resistive conductor 752.Detection device 30 may include that a volume controlled slot 805 its quantitative control structure can be formed in lid 800 or substrate 700 again；And first-class choked flow road 808 is formed in fluid channel 802 and is located between volume controlled slot 805 and sensing chamber 809.
The detection device 30 of the present embodiment can be applied to polymerization Enzyme chain reaction (Polymerase Chain Reaction, PCR the detection of DNA) is extracted, one specimen with DNA is, for example, that blood (not shown) can inject decomposer 760 by the first inlet 810, and a cell lysis can then be injected by the second inlet 812.Cell lysis can flow to recessed portion 702 by fluid channel 802 together with a specimen after being full of decomposer 760, a specimen can be filtered in recessed portion 702, then 750 top of heating component is flowed to by fluid channel 802 and be heated, fluid channel 802 is tortuous in heating component 750 and its tortuous direction is substantially vertical with the meander-like direction of resistive conductor 752, be uniformly heated a specimen can.After a specimen is heated component 750 circulating-heating is multiple between 95 degree of C and 65 degree of C, the DNA included is largely to replicate, then sensing chamber 809 is flowed to by fluid channel 802 and is reacted with micro- sensor chip 900, can also have plural detecting part to do different detections to DNA on micro- sensor chip 900.Identically as previous embodiment, the analysis that the collocation of flow resistance runner 808 volume controlled slot 805 can make detection device 30 quantitative.
Though the present invention is disclosed above with embodiment; so its is non-to limit the scope of the invention, any to be familiar with this those skilled in the art, is not departing from scope of the invention; when can do a little change and retouching, therefore protection scope of the present invention is subject to view appended claims institute defender.
Claims (30)
- A kind of detection device, comprising:One substrate has a first surface, has a recessed portion on the first surface, which includes a bottom and a slope, which is embedded in the substrate, which connects the first surface and the bottom and be configured at one end of the recessed portion；One lid has a second surface towards the first surface；One micro- sensor chip, is embedded in the substrate；AndOne micro-channel structure, it is embedded in the second surface, wherein the lid is covered in after the substrate, the first surface and the second surface are mutually closely sealed, so that the micro-channel structure and the first surface is coupled to a fluid channel includes that an at least inlet and a volume controlled slot control flow of the specimen in the fluid channel, the specimen enters the recessed portion via the fluid channel from the inlet, the specimen is separated into a subnatant and a upper liquid in the recessed portion, the subnatant rests on the bottom, which flow to micro- sensor chip from the recessed portion；Wherein the fluid channel includes first-class choked flow road and a reactive tank, the reactive tank are to be connected to micro- sensor chip, which is formed between the reactive tank and the volume controlled slot；Wherein at least one of the substrate and the lid include porous material.
- Detection device as described in claim 1, wherein the specimen is blood, which is blood cell, and the upper liquid is blood plasma.
- Detection device as described in claim 1, wherein the slope is configured at one end in the recessed portion close to the inlet.
- Detection device as described in claim 1, wherein micro- sensor chip has an at least detection structure, biological particle or biopolymer in the energetic specimen of the detection structure.
- Detection device as described in claim 1 further includes a plurality of terminals, on the substrate and is connected to micro- sensor chip, those terminals can be coupled to a reading device.
- Detection device as claimed in claim 5, wherein those terminals are to be connected to micro- sensor chip in a manner of wire bonding (wire bonding).
- Detection device as claimed in claim 5, wherein the detection structure is resistor-type, capacitive or transistor type or electrochemistry the sensor using nanometer sensing material as basis, nano material is by a high molecular functionalization of biology, the boiomacromolecule is the electrochemistry type or photoelectric type sensor selected from antibody, aptamer or glycan molecule or ferment or the detection structure comprising non-nano.
- Detection device as claimed in claim 7, wherein this nanometer of sensing material is selected from carbon nanotubes, graphene (graphene), reduction state graphene oxide (reduced graphene oxide, rGO), graphene oxide (graphene oxide, GO), nano wire band graphene (nanoribbon graphene), silicon nanowire, nanometer InP line, nano GaN line, Nano semiconductor line or Nanometer Semiconductor Films.
- Detection device as described in claim 1, wherein the material of the substrate is acryl (polymethylmethacrylate, PMMA), polyethylene terephthalate (polyethylene terephthalate, PET), polycarbonate (polycarbonate, PC), dimethyl silicone polymer (polydimethylsilicon, PDMS), porous silica gel, rubber, plastic cement or glass.
- Detection device as described in claim 1, wherein the material of the lid is acryl (polymethylmethacrylate, PMMA), polyethylene terephthalate (polyethylene terephthalate, PET), polycarbonate (polycarbonate, PC), dimethyl silicone polymer (polydimethylsilicon, PDMS), porous silica gel, rubber or plastic cement.
- Detection device as described in claim 1, wherein there is a pre-treatment portion between the recessed portion and the inlet, suitable for carrying out separation to the specimen or mixing with other reagents.
- Detection device as described in claim 1, wherein the second surface and this first When surface-assembled combines, the sideline of the second surface is located on the inside of the sideline of the first surface.
- Detection device as described in claim 1, wherein the bottom and slope of the recessed portion are coated with calcium chloride or a mixture comprising fibrin ferment (Thrombin), fibronectin (fibrinogen) and calcium ion (Calcium ion) to form a web (fibrin mesh).
- Detection device as described in claim 1, wherein the recessed portion and the intersection of the fluid channel are formed with the microcylinder distance of array-like arrangement less than 3 microns, or the intersection of the recessed portion and the fluid channel is formed with the microcylinder distance of array-like arrangement between 10 to 100 microns, then a plurality of sized micro-spheres of arranging in pairs or groups form plural gap greater than the spacing between those microcylinders to intercept the suspended matter in the specimen.
- Detection device as described in claim 1, wherein the fluid channel is located at the region between micro- sensor chip and the recessed portion, and the channel cross-sectional area in the fluid channel reduces.
- Detection device as described in claim 1, wherein the slope is configured at one end in the recessed portion far from the inlet.
- Detection device as described in claim 1, wherein the flow resistance runner is in tortuous pattern.
- Detection device as described in claim 1, wherein the width of the recessed portion is gradually wide further away from the inlet in a top view, or tapered further away from the inlet.
- A kind of detection device, comprising:One substrate, having a first surface includes a recessed portion and an at least reactive tank；One lid is covered in the first surface of the lid with a second surface；One micro- sensor chip is embedded in the substrate, includes an at least sensing area；One first inlet；One second inlet；AndOne micro sprue system is formed between the substrate and the lid, be formed in the first surface of the substrate including one first fluid channel and be connected to those reactive tanks and second inlet, One second fluid channel is formed in the second surface of the lid and a volume controlled slot is formed in the second surface of the lid and is connected to second fluid channel and a third fluid channel connects those reactive tanks at least one sensing area of micro- sensor chip；Wherein second fluid channel includes a first part and a second part, which is to extend to the volume controlled slot by first inlet and be connected to the recessed portion, which is that an at least reactive tank is extended to by the volume controlled slot；Wherein at least one of the substrate and the lid include porous material.
- Detection device as claimed in claim 19, wherein the lid compares the hydrophobicity height of the substrate.
- Detection device as claimed in claim 19, wherein the micro sprue system, an at least reactive tank and the recessed portion are in vacuum state before not detected.
- Detection device as claimed in claim 19, wherein the lid corresponds to and generates deformation at the volume controlled slot for pressing.
- Detection device as claimed in claim 19 is also formed in the first part of second fluid channel comprising first-class choked flow road.
- Detection device as claimed in claim 19 is also electrically connected at micro- sensor chip comprising a terminal support plate and has a plurality of terminals.
- Detection device as claimed in claim 19, wherein the sensing area includes that one first sensing area is connected to and one second sensing area is connected to by the third fluid channel by the first part of second fluid channel.
- A kind of detection device, comprising:One substrate, having a first surface includes a recessed portion and a decomposer；One lid is covered in the first surface of the lid with a second surface；One micro- sensor chip is embedded in the substrate, includes a sensing area；One fluid channel is formed between the substrate and the lid, and is connected to the recessed portion and the sensing area of micro- sensor chip；One heating component is formed in a part lower section of the fluid channel；Wherein a decomposed solution includes the specimen with DNA and is full of after the decomposer and the recessed portion through being flowed to above the heating component by the fluid channel, the massive duplication by the heating component circulating-heating, then the sensing area of micro- sensor chip is flowed to via the fluid channel；Wherein at least one of the substrate and the lid include porous material.
- Detection device as claimed in claim 26, wherein the recessed portion and the intersection of the fluid channel are formed with the microcylinder distance of array-like arrangement less than 3 microns, or the intersection of the recessed portion and the fluid channel is formed with the microcylinder distance of array-like arrangement between 10 to 100 microns, then a plurality of sized micro-spheres of arranging in pairs or groups form plural gap greater than the spacing between those microcylinders to intercept the suspended matter in the specimen.
- Detection device as claimed in claim 26 further includes one first inlet to inject the specimen and one second inlet to inject the decomposed solution.
- Detection device as claimed in claim 26, it further include first-class choked flow road, a volume controlled slot and a sensing chamber, wherein the sensing chamber is connected to the fluid channel and is connected to the sensing area, which is formed in the fluid channel and between the volume controlled slot and the sensing chamber.
- Detection device as claimed in claim 26, wherein the heating component includes a heating chip and positioned at the heating core on piece and at a resistive conductor of meander-like, which is located at that the part on the resistive conductor is also tortuous and its tortuous direction is vertical with the tortuous direction of the resistive conductor.
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| PCT/CN2015/098146 WO2017107025A1 (en) | 2015-12-21 | 2015-12-21 | Detection device |
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| TWI742603B (en) * | 2020-04-09 | 2021-10-11 | 伊諾司生技股份有限公司 | A sensor with a chamber |
| TWI786896B (en) * | 2021-10-21 | 2022-12-11 | 醫流體股份有限公司 | Finger-pressed transistor microfluidic chip and operation method thereof |
Citations (10)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US20080073297A1 (en) * | 2006-09-27 | 2008-03-27 | Fujifilm Corporation | Method and tool for collecting blood plasma |
| CN101258397A (en) * | 2005-07-14 | 2008-09-03 | 毫微创新科技公司 | Microfluidic devices and methods of preparing and using the same |
| WO2011051405A1 (en) * | 2009-10-30 | 2011-05-05 | Dublin City University | Microfludic device providing degassing driven fluid flow |
| CN102680683A (en) * | 2012-05-30 | 2012-09-19 | 中国人民解放军第306医院 | Periodontal bacteria impedance immunosensor based on conductive polymer |
| CN102980920A (en) * | 2012-11-14 | 2013-03-20 | 华东师范大学 | Silicon nanowire chip simultaneously detecting miRNAs and protein markers and detection method and application of silicon nanowire chip |
| TW201319563A (en) * | 2011-11-08 | 2013-05-16 | Jung-Tang Huang | Detection system with integrating IC chip and plastic microfluidic substrate |
| CN103901083A (en) * | 2014-01-10 | 2014-07-02 | 中国科学院苏州生物医学工程技术研究所 | Micro-fluidic chip for detecting endotoxin by adopting electrochemical method |
| WO2015021425A1 (en) * | 2013-08-09 | 2015-02-12 | The Regents Of The University Of California | Digital fluid sample separation apparatus and methods for one-step quantitative sample analysis |
| CN104508146A (en) * | 2012-07-04 | 2015-04-08 | 可瑞斯生物概念公司 | Method and device for rapid detection of amplified nucleotide sequences |
| CN104593256A (en) * | 2015-01-06 | 2015-05-06 | 上海交通大学 | PCR chip with repeatedly used electrode |
Family Cites Families (5)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| WO2006056219A1 (en) * | 2004-11-24 | 2006-06-01 | Preventor Utbc Gmbh | Process for separation of dispersions and an apparatus |
| CN100491390C (en) * | 2005-06-13 | 2009-05-27 | 中国科学院电子学研究所 | Reversible packaged micro fluent chip for separating and purifying biological sample |
| US8980106B2 (en) * | 2010-12-15 | 2015-03-17 | Abbott Laboratories | Apparatus and method for separation of whole blood into plasma or serum and cells |
| US8741234B2 (en) * | 2011-12-27 | 2014-06-03 | Honeywell International Inc. | Disposable cartridge for fluid analysis |
| CN104569393A (en) * | 2013-10-28 | 2015-04-29 | 天津禄浩科技有限公司 | Granulocyte myeloperoxidase detection chip |
-
2015
- 2015-12-21 CN CN201580085443.8A patent/CN108474802A/en active Pending
- 2015-12-21 WO PCT/CN2015/098146 patent/WO2017107025A1/en active Application Filing
Patent Citations (10)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN101258397A (en) * | 2005-07-14 | 2008-09-03 | 毫微创新科技公司 | Microfluidic devices and methods of preparing and using the same |
| US20080073297A1 (en) * | 2006-09-27 | 2008-03-27 | Fujifilm Corporation | Method and tool for collecting blood plasma |
| WO2011051405A1 (en) * | 2009-10-30 | 2011-05-05 | Dublin City University | Microfludic device providing degassing driven fluid flow |
| TW201319563A (en) * | 2011-11-08 | 2013-05-16 | Jung-Tang Huang | Detection system with integrating IC chip and plastic microfluidic substrate |
| CN102680683A (en) * | 2012-05-30 | 2012-09-19 | 中国人民解放军第306医院 | Periodontal bacteria impedance immunosensor based on conductive polymer |
| CN104508146A (en) * | 2012-07-04 | 2015-04-08 | 可瑞斯生物概念公司 | Method and device for rapid detection of amplified nucleotide sequences |
| CN102980920A (en) * | 2012-11-14 | 2013-03-20 | 华东师范大学 | Silicon nanowire chip simultaneously detecting miRNAs and protein markers and detection method and application of silicon nanowire chip |
| WO2015021425A1 (en) * | 2013-08-09 | 2015-02-12 | The Regents Of The University Of California | Digital fluid sample separation apparatus and methods for one-step quantitative sample analysis |
| CN103901083A (en) * | 2014-01-10 | 2014-07-02 | 中国科学院苏州生物医学工程技术研究所 | Micro-fluidic chip for detecting endotoxin by adopting electrochemical method |
| CN104593256A (en) * | 2015-01-06 | 2015-05-06 | 上海交通大学 | PCR chip with repeatedly used electrode |
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|---|---|
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