CN111229346B - Electroosmosis micropump system based on dynamic coating and application thereof - Google Patents
Electroosmosis micropump system based on dynamic coating and application thereof Download PDFInfo
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Abstract
The invention relates to an electroosmosis micropump system based on a dynamic coating, which comprises a microfluidic chip and gel, wherein the microfluidic chip is provided with a pump body channel, one end of the pump body channel is filled with the gel, the pump body channel is filled with buffer solution, and the buffer solution contains a surfactant. The invention also relates to the application of the electroosmotic micropump system in chromatographic separation and/or electrophoretic separation. The electroosmosis micropump system has the advantages of being simple to manufacture, free of influence of chip materials, easy to accurately control and not prone to being influenced by the environment.
Description
Technical Field
The invention belongs to the technical field of microfluidics, and particularly relates to an electroosmosis micropump system based on a dynamic coating and application thereof.
Background
Microfluidics (Microfluidics), also known as Lab-on-a-chip, is a method for processing and manipulating micro-fluids using microchannels and microstructures on a scale of tens to hundreds of micrometers. By means of unique fluid properties in a microscale environment, analysis and detection realized in a chip not only have the advantages of rapidness, portability, small consumption of samples and solvents and the like, but also are easy for multi-step and multi-functional integration, and show huge application potential in the fields of chemistry, biology, medicine and the like.
Pressure driven fluids are one of the most common fluid manipulation approaches in microfluidic technology. The pressure-driven flow can effect transport, enrichment, and separation of samples in microchannels by a precisely controllable pumping system. On-chip pumps, represented by syringe pumps and peristaltic pumps, may be connected to microfluidic channels on a chip via interfaces or switching valves to generate pressure-driven flows. However, on the one hand, there is a huge dead volume at the interface of such pumps and chips, and dynamic control of the fluid in the microchannel is not possible; on the other hand, the external interface structure is easy to cause the leakage problem.
Building a built-in pump on the chip not only avoids the interface problem, but also improves the pumping efficiency of the fluid in the microchannel. The chip built-in pump is usually designed and manufactured by using the principles of electromotion, machinery, thermopneumaticity, electrochemistry and the like. Among them, the electric control micro pump is widely concerned because of its easy processing, stable and accurate control of the pumping fluid speed. In designing electrically controlled micropumps, a method of introducing an electroosmotic flow velocity difference in a microchannel is generally employed. This electroosmotic flow velocity difference will automatically create a pressure driven flow to maintain flow balance due to conservation of fluid volume in the microchannel. This electroosmotic flow velocity difference can be achieved by differences in the surface characteristics of the microchannel or differences in the electrical flux in the microchannel. However, the modification of the wall in the micro channel or the construction of the microstructure to change the electric flux increases the processing difficulty of the micro pump or limits the applicable chip material, and is easily interfered by an electric field or a sample in the use of the micro pump, thereby limiting the application of the electroosmosis micro pump. Therefore, there is a need to develop an electroosmotic micropump system that is simple to manufacture, easy to precisely manipulate, and less susceptible to the environment.
Disclosure of Invention
The invention provides an electroosmosis micropump system based on a dynamic coating, aiming at the defects of high processing difficulty, limited chip material, easy environmental interference and the like of the existing electroosmosis micropump.
The technical scheme adopted by the invention is as follows:
an electroosmosis micropump system based on a dynamic coating comprises a microfluidic chip and gel, wherein the microfluidic chip is provided with a pump body channel, one end of the pump body channel is filled with the gel, a buffer solution is filled in the pump body channel, and the buffer solution contains a surfactant.
In the electroosmosis micropump system, gel is filled at one end of a pump body channel, a buffer solution containing a surfactant is filled in the pump body channel so as to form a dynamic coating on the wall of the channel, the buffer solution can form directional electroosmotic flow under the action of an electric field, and the electroosmotic flow has a speed difference between the pump body channel and the gel, so that pressure countercurrent is automatically generated on the interface between the interior of the pump body channel and the gel, and the function of the micropump is realized.
The electroosmosis micropump system based on the dynamic coating can realize the accurate control of the flow speed of 0.1-12mm/s under the driving voltage of 10-3000V, can be integrated with other microfluidic functional units by arranging an external channel, is simple to manufacture and control, is not influenced by the material of a microfluidic chip, and expands the application of the electroosmosis pump in a polymer chip.
The electroosmosis micro-pump system based on the dynamic coating can be well applied to chip chromatography and chip electrophoresis separation improvement.
Specifically, the gel is polyacrylamide gel or agarose gel.
Specifically, the buffer solution is prepared from any one of borax solution, phosphoric acid solution and Tris-HCl buffer solution and a surfactant; the surfactant is a cationic surfactant, a neutral polymer or an anionic surfactant.
Further, the cationic surfactant is any one or more of cetyl trimethyl ammonium bromide, cetyl trimethyl ammonium chloride and didodecyl dimethyl ammonium bromide; the neutral polymer is any one or more of polydimethylacrylamide, polyhydroxyethylacrylamide, hydroxyethyl cellulose, hydroxypropyl methylcellulose and polyethylene glycol; the anionic surfactant is sodium dodecyl sulfate or anionic polymer dextran sulfate.
Specifically, the material of the microfluidic chip is any one of cyclic olefin copolymer, polymethyl methacrylate, polycarbonate, polydimethylsiloxane and glass.
Specifically, the micro-control flow chip has a length of 20-100mm, a width of 10-100mm and a thickness of 0.1-0.6 mm.
Specifically, the length of the pump body channel is 2-80mm, the width is 50-500 microns, and the depth is 20-100 microns.
Furthermore, the micro-fluidic chip is also provided with an external channel communicated with the pump body channel.
Furthermore, one end of the external channel is connected between two ends of the pump body channel, and the other end of the external channel is divided into three branch channels.
By arranging the external channel and designing a channel network, the electroosmosis micropump can be integrated with other microfluidic functional units on one microfluidic chip to obtain an integrated chip.
The invention also provides the application of the electroosmosis micropump system in chromatographic separation and/or electrophoretic separation.
For a better understanding and practice, the invention is described in detail below with reference to the accompanying drawings.
Drawings
FIG. 1 is a schematic diagram of the construction of an electroosmotic micropump system based on a dynamic coating according to the present invention;
FIG. 2 is a schematic diagram of the operation of the dynamic coating-based electroosmotic micropump system of the present invention;
FIG. 3 is a schematic diagram illustrating the effect of the feasibility evaluation experiment performed on the electroosmotic micro-pump system in example 1;
FIG. 4 is a graph showing the effect of comparative experiments on microfluidic chips without gel filling in example 1;
FIG. 5 is a schematic view of the structure of the electroosmotic micropump system based on dynamic coating of example 2;
FIG. 6 is a graph showing the results of a liquid chromatography separation experiment in example 2, illustrating the control of the migration velocity of a fluorescent dye sample by the electroosmotic micropump system of example 2, wherein FIG. 6(a) is a chromatogram of a chip, and FIG. 6(b) is a graph of the migration velocity versus operating voltage;
FIG. 7 is a schematic structural diagram of the electroosmotic micropump system based on dynamic coating of example 3;
fig. 8 is a graph showing the result of the electrophoretic separation experiment in example 3, showing the effect of the electroosmotic micropump system of example 3 on the electrophoretic separation degree of a fluorescent dye mixture sample, wherein fig. 8(a) is an electrophoretic spectrum at different operating voltages, and fig. 8(b) is a graph showing the relationship between the electrophoretic separation degree and different operating voltages.
Description of reference numerals:
1. a microfluidic chip; 11. a pump body channel; 111. dynamic coating; 112. electroosmotic flow; 113. a pressure stream; 12. a gel pool; 13. a liquid storage tank; 14. connecting a channel externally; 15. gelling; 21. a sample channel; 22. a sample cell; 23. a waste liquid channel; 24. a waste liquid tank; 25. a separation channel; 26. a sample outlet pool; 27. a buffer channel; 28. a buffer liquid pool; a. a microscope detection area; b. and (3) laser-induced fluorescence detection zone.
Detailed Description
Referring to fig. 1, the electroosmotic micropump system based on the dynamic coating of the present invention includes a microfluidic chip 1 and a gel 15, wherein the microfluidic chip 1 is provided with a pump channel 11, one end of the pump channel 11 is filled with the gel 15, and the pump channel 11 is filled with a buffer solution, and the buffer solution contains a surfactant.
Specifically, one end of the pump body channel 11 is provided with a gel pool 12, the other end is provided with a liquid storage pool 13, and the gel 15 is filled in the gel pool 12.
The micro-fluidic chip 1 is further provided with an external channel 14 communicated with the pump body channel 11, the external channel 14 is perpendicular to the pump body channel 11, and one end of the external channel is connected between two ends of the pump body channel 11. The pump body channel 11 and the external channel 14 are both straight micro-channels and are perpendicular to each other.
Specifically, the microfluidic chip 1 is a Cyclic Olefin Copolymer (COC) microfluidic chip, and may be any one of a polymethyl methacrylate (PMMA) microfluidic chip, a Polycarbonate (PC) microfluidic chip, a Polydimethylsiloxane (PDMS) microfluidic chip, and a glass microfluidic chip.
The micro flow control chip has a length of 20-100mm, a width of 10-100mm and a thickness of 0.1-0.6 mm. The length of the pump body channel 11 is 2-80mm, the width is 50-500 μm, and the depth is 20-100 μm.
The gel 15 may be a polyacrylamide gel or an agarose gel.
The buffer solution is prepared by any one of borax solution, phosphoric acid solution and Tris-hydrochloric acid buffer solution and surfactant. The surfactant may be a cationic surfactant, a neutral polymer, or an anionic surfactant. Specifically, the cationic surfactant can be selected from any one or more of cetyltrimethyl ammonium bromide (CTAB), cetyltrimethyl ammonium chloride (CTAC) and didodecyldimethyl ammonium bromide (DDAB); the neutral polymer can be selected from one or more of Polydimethylacrylamide (PDMA), polyhydroxyethylacrylamide, Hydroxyethylcellulose (HEC), hydroxypropyl methylcellulose (HPMC), and polyethylene glycol (PEG); the anionic surfactant may be Sodium Dodecyl Sulphate (SDS) or the anionic polymer dextran sulphate.
Referring to fig. 2, the electroosmotic micropump system operates according to the following principle: the buffer forms a dynamic coating 111 on the inner wall of the pump body channel 11, and when a voltage is applied to the two ends of the pump body channel 11, the buffer can form a directional electroosmotic flow 112 under the action of an electric field, and the electroosmotic flow 112 has a velocity difference between the pump body channel 11 and the gel 15, so that a pressure flow 113 is automatically generated at the interface between the inside of the pump body channel 11 and the gel 15. The regulation and control range of the driving voltage is 10-3000V, and the speed of the generated pressure flow is 0.1-12 mm/s.
The electroosmosis micropump system based on the dynamic coating can realize accurate control of pressure flow speed by controlling driving voltage, can be integrated with other microfluidic function units through the external channel 14, is simple to manufacture and control, is not influenced by the material of the microfluidic chip 1, and expands the application of the electroosmosis pump in a polymer chip.
Alternatively, the end of the external channel 14 not connected to the pump body channel 11 may be divided into three branch channels to realize other microfluidic functions. Specifically, the three branch channels are all straight micro channels, the center line of one branch channel coincides with the center line of the external channel 14, and the center lines of the other two branch channels coincide and are perpendicular to the external pipeline.
Example 1
In the electroosmotic micropump system based on the dynamic coating of this embodiment, the microfluidic chip 1 is a Cyclic Olefin Copolymer (COC) microfluidic chip, and has a length of 20mm, a width of 15mm, and a thickness of 0.2 mm.
The pump body channel 11 has a length of 8mm, a width of 100 μm and a depth of 60 μm.
The buffer solution is 0.1mmol/L borax solution containing 0.01% hexadecyl trimethyl ammonium bromide (w/w).
Manufacturing the micropump: transferring 125 mu L of gel prepolymer acrylamide/methylene bisacrylamide solution (37.5:1) with the concentration of 40% (w/v) into a centrifuge tube, diluting the gel prepolymer solution to 1mL by using a buffer solution, wherein the concentration of the gel prepolymer is 5% (w/v), then adding 7.5 mu L of 5% (w/v) ammonium persulfate solution into the centrifuge tube, finally adding 1.5 mu L of tetramethyl ethylenediamine, placing the mixed solution on an oscillator to swirl, uniformly mixing, transferring the mixed solution into a gel pool 12 at one end of a pump body channel 11, and standing for 5-10min to obtain polyacrylamide gel filled at one end of the pump body channel 11.
A buffer solution is used for preparing a rhodamine B sample solution with the concentration of 1 mu mol/L for evaluating the feasibility of the electroosmosis micro-pump system for generating pressure flow, and a comparative experiment is carried out to further verify the effect of the gel 15 on the operation of the electroosmosis micro-pump system.
Feasibility assessment experiment: before the experiment, a pump body channel 11, a gel pool 12, a liquid storage pool 13 and an external channel 14 are filled with buffer solution; then, the buffer solution in the liquid storage tank 13 is replaced by the rhodamine B sample solution, and electrodes are respectively placed in the gel tank 12 and the liquid storage tank 13 and connected with a power supply. Referring to fig. 3, in the experiment, a voltage of 500V is applied to the gel cell 12, the liquid cell 13 is grounded, and the microscope detection area a is photographed to record the migration phenomenon of the rhodamine B sample (in fig. 3, the dotted line frame is the detection area a, and the screenshot indicated by the hollow arrow is the photograph of the detection area a, which shows the flow direction of the rhodamine B sample). As shown in FIG. 3, under the action of an electric field, the rhodamine B sample in the liquid storage tank 13 flows to the gel tank 12 along with the buffer solution, and simultaneously a part of the rhodamine B sample flows out from the external channel 14. Since no electric field exists on the external channel 14, namely no electric seepage exists, pressure flow is necessary for driving the rhodamine B sample to migrate.
Comparative experiment: the conditions and steps of the feasibility evaluation experiment are also carried out on the microfluidic chip 1 of the embodiment without gel filling, and the result is shown in fig. 4 (in fig. 4, the dotted line frame is the detection area a, and the screenshot indicated by the hollow arrow is a photograph of the detection area a, which shows the flow direction of the rhodamine B sample), and it can be seen from the figure that under the action of the electric field, the rhodamine B sample in the liquid storage tank 13 only flows to the gel tank 12 along with the buffer solution and does not enter the external channel 14. The micro-fluidic chip 1 without the gel structure can not generate pressure flow, and the key effect of the gel 15 on the operation of the electroosmosis micro-pump system is further verified.
Example 2
As shown in fig. 5, the electroosmotic micropump system based on dynamic coating of this embodiment includes the configuration of the electroosmotic micropump system described in embodiment 1, and further has the following configuration: one end of the external channel 14, which is not connected with the pump body channel 11, is divided into three branch channels, the three branch channels are all straight micro-channels, one branch channel is a waste liquid channel 23, the central line of the branch channel coincides with the central line of the external channel 14, the other two branch channels are a separation channel 25 and a sample channel 21 respectively, and the separation channel 25 coincides with the central line of the sample channel 21 and is perpendicular to the external channel; a waste liquid pool 24 is arranged at the tail end of the waste liquid channel 23, a sample outlet pool 26 is arranged at the tail end of the separation channel 25, and a sample pool 22 is arranged at the tail end of the sample channel 21; all the channels are communicated with each other to form a channel network. Therefore, the present embodiment integrates the chip chromatography function on the microfluidic chip 1, and realizes that the pressure flow generated by the electroosmosis micropump is used as the driving force of the chip chromatography mobile phase.
A buffer solution is used for preparing a rhodamine B sample solution with the concentration of 1 mu mol/L, and the electroosmosis micropump system of the embodiment is utilized to carry out a liquid chromatography separation experiment, and the operation steps are as follows:
before the experiment, firstly, a buffer solution is filled in the whole channel network, then the buffer solution in the sample pool 22 is replaced by rhodamine B sample solution, and electrodes are respectively placed in the gel pool 12, the liquid storage pool 13, the sample pool 22, the waste liquid pool 24 and the sample outlet pool 26 and connected with a power supply;
the experiment used a gated sample injection mode to introduce rhodamine B sample solution into the separation channel 25:
(1) 300V of operation voltage is applied to the sample cell 22, 600V of operation voltage is respectively applied to the gel cell 12, the waste liquid cell 24 and the sample outlet cell 26, and the liquid storage cell 13 is grounded;
(2) reducing the operating voltage of the sample cell 22 to 0V, increasing the operating voltage of the liquid storage cell 13 to 600V, keeping the rest voltages unchanged, and enabling the rhodamine B sample to enter the separation channel 25;
(3) after 1s, the operation voltage of the sample cell 22 is increased to 0.5 psi, the operation voltages of the gel cell 12, the waste liquid cell 24 and the sample outlet cell 26 are increased to psi, the operation voltage of the liquid storage cell 13 is reduced to 0V, and liquid chromatography separation is carried out;
and recording a fluorescence signal in a laser-induced fluorescence detection area b (a dotted circle part in the figure 5 is a detection area b) by utilizing a laser-induced fluorescence detection technology to obtain a chip chromatogram. FIG. 6(a) is a rhodamine B chromatogram obtained with a micropump operating voltage of 2700V. The migration speed of rhodamine B in the separation channel 25 can be calculated according to the detection distance and the sample chromatogram peaking time. FIG. 6(B) shows the effect of different micropump control voltages psi on the migration speed of rhodamine B samples. The migration speed of the rhodamine B sample in the separation channel 25 increases linearly with the increase of the micropump manipulation voltage ψ. The linear equation obtained is y-2 × 10-5x(R20.9904). It was confirmed that the migration speed of the sample in the separation channel 25 can be precisely controlled by controlling the operation voltage ψ of the micro pump.
Example 3
As shown in fig. 7, the electroosmotic micropump system based on dynamic coating of this embodiment includes the configuration of the electroosmotic micropump system described in embodiment 1, and further has the following configuration: one end of the external channel 14, which is not connected with the pump body channel 11, is divided into three branch channels, the three branch channels are all straight micro-channels, one branch channel is a sample channel 21, the central line of the branch channel coincides with the central line of the external channel 14, the other two branch channels are a buffer solution channel 27 and a waste liquid channel 23, the central lines of the buffer solution channel 27 and the waste liquid channel 23 coincide and are perpendicular to the external channel, and the external channel 14 is also used as a separation channel 25; a waste liquid pool 24 is arranged at the tail end of the waste liquid channel 23, a sample pool 22 is arranged at the tail end of the sample channel 21, and a buffer liquid pool 28 is arranged at the tail end of the buffer liquid channel 27; all the channels are communicated with each other to form a channel network. Therefore, the present embodiment integrates the chip electrophoresis function on the microfluidic chip 1, and realizes that the pressure flow generated by the electroosmosis micropump is utilized to prolong the retention time of the sample in the separation electric field, thereby improving the separation degree.
A mixed solution of rhodamine B and rhodamine 6G with the total concentration of 1 mu mol/L is prepared by using a buffer solution as a sample solution, and an electrophoresis separation experiment is carried out by using the electroosmosis micro-pump system of the embodiment, and the operation steps are as follows:
before the experiment, firstly, buffer solution is used for filling the whole channel network, then the buffer solution in the sample pool 22 is replaced by sample solution, and electrodes are respectively placed in the gel pool 12, the liquid storage pool 13, the sample pool 22, the waste liquid pool 24 and the buffer solution pool 28 and connected with a power supply;
the experiment introduced the sample to the separation channel 25 using a gated injection mode:
(1) applying 500V operation voltage to the gel pool 12, the liquid storage pool 13 and the waste liquid pool 24, and grounding the sample pool 22 and the buffer liquid pool 28;
(2) adjusting the operating voltage of the buffer liquid pool 28 to 500V, keeping the rest voltage unchanged, and enabling the mixed sample of rhodamine B and rhodamine 6G to enter the separation channel 25;
(3) after 1s, the operating voltage of the buffer liquid pool 28 is reduced to 0V, the operating voltages of the gel pool 12 and the waste liquid pool 24 are adjusted to 1500V, the operating voltage of the liquid pool 13 is adjusted to psi, the operating voltage of the sample pool 22 is kept not to be 0V, and electrophoretic separation is carried out;
and recording a fluorescence signal in the laser-induced fluorescence detection area b (the dotted circle part in the figure 7 is the detection area b) by using a laser-induced fluorescence detection technology to obtain an electrophoresis spectrogram. Fig. 8(a) is an electrophoresis spectrum of the mixed fluorescent dye sample at the laser-induced fluorescence detection region b obtained by different micropump operation voltages ψ. When the operating voltage psi is 1500V, the micro pump does not work, and when the operating voltage psi is gradually reduced from 1500V to 1200V, the pumping effect is gradually enhanced. As shown in fig. 8(a), when the micro-pump operation voltage ψ is gradually reduced from 1500V to 1200V, the peak-out time of the mixed fluorescent dye sample is longer, the residence time in the separation field is longer, and the separation effect is better. The separation degree R of the rhodamine B and the rhodamine 6G in the chip electrophoresis system is calculated by analyzing the separation electrophoresis spectrogram of the mixed fluorescent dye sample, and the specific result is shown in figure 8 (B). It is proved that the migration speed of the sample in the separation channel 25 can be regulated and controlled by controlling the operating voltage psi of the micropump, and the separation degree of the chip electrophoresis is improved.
The above-mentioned embodiments only express several embodiments of the present invention, and the description thereof is more specific and detailed, but not construed as limiting the scope of the invention. It should be noted that, for a person skilled in the art, several variations and modifications can be made without departing from the inventive concept, which falls within the scope of the present invention.
Claims (10)
1. An electroosmotic micropump system based on a dynamic coating, characterized in that: the micro-fluidic chip is provided with a pump body channel, one end of the pump body channel is filled with the gel, the pump body channel is filled with a buffer solution, and the buffer solution contains a surfactant; the electroosmotic micropump system is driven by applying a voltage across the pump body channel.
2. The electroosmotic micropump system of claim 1, wherein: the gel is polyacrylamide gel or agarose gel.
3. The electroosmotic micropump system of claim 1, wherein: the buffer solution is prepared by any one of borax solution, phosphoric acid solution and Tris-HCl buffer solution and a surfactant; the surfactant is a cationic surfactant, a neutral polymer or an anionic surfactant.
4. An electroosmotic micropump system according to claim 3, wherein: the cationic surfactant is any one or more of cetyl trimethyl ammonium bromide, cetyl trimethyl ammonium chloride and didodecyl dimethyl ammonium bromide; the neutral polymer is any one or more of polydimethylacrylamide, polyhydroxyethylacrylamide, hydroxyethyl cellulose, hydroxypropyl methylcellulose and polyethylene glycol; the anionic surfactant is sodium dodecyl sulfate or anionic polymer dextran sulfate.
5. The electroosmotic micropump system of claim 1, wherein: the material of the micro-fluidic chip is any one of cyclic olefin copolymer, polymethyl methacrylate, polycarbonate, polydimethylsiloxane and glass.
6. An electroosmotic micropump system according to any one of claims 1-5, wherein: the length of the micro-fluidic chip is 20-100mm, the width is 10-100mm, and the thickness is 0.1-0.6 mm.
7. An electroosmotic micropump system according to any one of claims 1-5, wherein: the length of the pump body channel is 2-80mm, the width is 50-500 microns, and the depth is 20-100 microns.
8. The electroosmotic micropump system of claim 1, wherein: the micro-fluidic chip is also provided with an external channel communicated with the pump body channel.
9. The electroosmotic micropump system of claim 8, wherein: one end of the external channel is connected between two ends of the pump body channel, and the other end of the external channel is divided into three branch channels.
10. Use of an electroosmotic micropump system according to any one of claims 1-9 for chromatographic separations and/or electrophoretic separations.
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| Application Number | Priority Date | Filing Date | Title |
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| CN202010086996.8A CN111229346B (en) | 2020-02-11 | 2020-02-11 | Electroosmosis micropump system based on dynamic coating and application thereof |
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| CN202010086996.8A CN111229346B (en) | 2020-02-11 | 2020-02-11 | Electroosmosis micropump system based on dynamic coating and application thereof |
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| CN111229346A CN111229346A (en) | 2020-06-05 |
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Citations (5)
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| TW551387U (en) * | 2002-04-22 | 2003-09-01 | Ind Tech Res Inst | Water gel actuated micro pump |
| CN1469120A (en) * | 2002-07-18 | 2004-01-21 | 中国科学院大连化学物理研究所 | Inner surface pretreating process for polymer chip microchannel |
| CN102428274A (en) * | 2009-02-24 | 2012-04-25 | 奥斯莫泰克斯股份有限公司 | Charged particle motion inducing apparatus |
| CN103620398A (en) * | 2011-05-06 | 2014-03-05 | 基因徽型器件有限公司 | Device and method for applying a continuous electric field |
| CN110479391A (en) * | 2019-08-05 | 2019-11-22 | 湖北医药学院 | A kind of low-voltage high-performance electric osmose Micropump chip based on solid-state track etching nano-pore |
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Patent Citations (5)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| TW551387U (en) * | 2002-04-22 | 2003-09-01 | Ind Tech Res Inst | Water gel actuated micro pump |
| CN1469120A (en) * | 2002-07-18 | 2004-01-21 | 中国科学院大连化学物理研究所 | Inner surface pretreating process for polymer chip microchannel |
| CN102428274A (en) * | 2009-02-24 | 2012-04-25 | 奥斯莫泰克斯股份有限公司 | Charged particle motion inducing apparatus |
| CN103620398A (en) * | 2011-05-06 | 2014-03-05 | 基因徽型器件有限公司 | Device and method for applying a continuous electric field |
| CN110479391A (en) * | 2019-08-05 | 2019-11-22 | 湖北医药学院 | A kind of low-voltage high-performance electric osmose Micropump chip based on solid-state track etching nano-pore |
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| CN111229346A (en) | 2020-06-05 |
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