WO2010019684A2 - Dispositifs microfluidiques électro-osmotiques à charge induite - Google Patents

Dispositifs microfluidiques électro-osmotiques à charge induite Download PDF

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Publication number
WO2010019684A2
WO2010019684A2 PCT/US2009/053574 US2009053574W WO2010019684A2 WO 2010019684 A2 WO2010019684 A2 WO 2010019684A2 US 2009053574 W US2009053574 W US 2009053574W WO 2010019684 A2 WO2010019684 A2 WO 2010019684A2
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Prior art keywords
electrodes
series
electrode
fluid
combination
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PCT/US2009/053574
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English (en)
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WO2010019684A3 (fr
Inventor
Martin Z. Bazant
Jeremy Levitan
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Massachusetts Institute Of Technology
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Publication of WO2010019684A3 publication Critical patent/WO2010019684A3/fr

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Classifications

    • B—PERFORMING OPERATIONS; TRANSPORTING
    • B01—PHYSICAL OR CHEMICAL PROCESSES OR APPARATUS IN GENERAL
    • B01L—CHEMICAL OR PHYSICAL LABORATORY APPARATUS FOR GENERAL USE
    • B01L3/00—Containers or dishes for laboratory use, e.g. laboratory glassware; Droppers
    • B01L3/50—Containers for the purpose of retaining a material to be analysed, e.g. test tubes
    • B01L3/502—Containers for the purpose of retaining a material to be analysed, e.g. test tubes with fluid transport, e.g. in multi-compartment structures
    • B01L3/5027—Containers for the purpose of retaining a material to be analysed, e.g. test tubes with fluid transport, e.g. in multi-compartment structures by integrated microfluidic structures, i.e. dimensions of channels and chambers are such that surface tension forces are important, e.g. lab-on-a-chip
    • B01L3/50273—Containers for the purpose of retaining a material to be analysed, e.g. test tubes with fluid transport, e.g. in multi-compartment structures by integrated microfluidic structures, i.e. dimensions of channels and chambers are such that surface tension forces are important, e.g. lab-on-a-chip characterised by the means or forces applied to move the fluids
    • B—PERFORMING OPERATIONS; TRANSPORTING
    • B01—PHYSICAL OR CHEMICAL PROCESSES OR APPARATUS IN GENERAL
    • B01F—MIXING, e.g. DISSOLVING, EMULSIFYING OR DISPERSING
    • B01F33/00—Other mixers; Mixing plants; Combinations of mixers
    • B01F33/30—Micromixers
    • B01F33/3031—Micromixers using electro-hydrodynamic [EHD] or electro-kinetic [EKI] phenomena to mix or move the fluids
    • B—PERFORMING OPERATIONS; TRANSPORTING
    • B01—PHYSICAL OR CHEMICAL PROCESSES OR APPARATUS IN GENERAL
    • B01L—CHEMICAL OR PHYSICAL LABORATORY APPARATUS FOR GENERAL USE
    • B01L2400/00—Moving or stopping fluids
    • B01L2400/04—Moving fluids with specific forces or mechanical means
    • B01L2400/0403—Moving fluids with specific forces or mechanical means specific forces
    • B01L2400/0415—Moving fluids with specific forces or mechanical means specific forces electrical forces, e.g. electrokinetic
    • B01L2400/0418—Moving fluids with specific forces or mechanical means specific forces electrical forces, e.g. electrokinetic electro-osmotic flow [EOF]

Definitions

  • the invention relates to the fields of microfluidics, micro-total-analysis systems ( ⁇ TAS) and micro-electro-mechanical systems (MEMS), in particular modulated microfluidic mixers driven by induced-charge electro-osmosis.
  • ⁇ TAS micro-total-analysis systems
  • MEMS micro-electro-mechanical systems
  • microfluidics is a growing area of science and technology with important applications in biomedical devices and portable electronics.
  • electro-osmosis the effective slip of a liquid electrolyte past a solid surface in response to an applied electric field, since it does not involve any moving parts, is unaffected by miniaturization, and integrates well with standard microelectronics and fabrication methods.
  • the standard technique of (capillary) electro-osmosis involves a DC electric field applied down a microchannel made of insulating material to generate a plug flow. The electric field acts on the equilibrium surface charge in the diffuse-part of the double layer, and the resulting electro-osmotic flow is linear in the applied field.
  • Microfluidic devices based on nonlinear electro-osmotic flow have also been developed.
  • nonlinear electro-osmotic flow varying as the square of the applied voltage, termed "AC electro-osmosis" (ACEO)
  • AEO AC electro-osmosis
  • this invention provides a device comprising at least one microfluidic chamber for mixing an electrolyte fluid, said chamber comprising:
  • a source providing an electric field in said chamber, wherein said source applies voltage selectively to said first series such that said voltage is not simultaneously or commensurately applied to second series of electrodes of said plurality; whereby an electroosmotic flow trajectory created by application of voltage to said first series varies from an electroosmotic flow trajectory created by application of voltage to said second series.
  • the at least two series are positioned such that an electroosmotic flow trajectory created by a first series is in a direction opposite to an electroosmotic flow trajectory created by a second series of said at least two series.
  • the first series is so positioned such that an electroosmotic flow trajectory created thereby is parallel to a long axis of said device and said second series is so positioned such that an electroosmotic flow trajectory created thereby is perpendicular thereto, or vice versa.
  • the at least two series are positioned on opposing surfaces of said chamber.
  • the series are arranged asymmetrically with respect to a central axis in the chamber and in another embodiment, the electrodes are arranged in a symmetric pattern in the chamber, while in another embodiment, the electrodes are arranged in an asymmetric pattern in the chamber. In another embodiment, the electrodes are arranged in a gradient pattern in the chamber.
  • the source modulates the magnitude or frequency of the voltages applied to the series of electrodes, and in some embodiments, the magnitude or direction of electroosmotic flow is changed thereby. In some embodiments, the changed electroosomotic flow is slower than electroosmotic flow in said chamber prior to modulation of said magnitude or frequency.
  • the electric field is comprised of a DC electric field, or in another embodiment, the electric field is comprised of an AC or pulsed AC electric field.
  • each series of said plurality of electrodes comprises at least one electrode, or a portion thereof, which is raised with respect to another electrode, or another portion of said at least one electrode in said series, or in another embodiment, which is lowered with respect to another electrode, or another portion of said at least one electrode in said series.
  • each series of said plurality of electrodes comprises at least one electrode or at least a portion thereof having a height or depth which is varied proportionally to a width of another electrode, another portion of said at least one electrode, or a combination thereof, in said series.
  • each series of said plurality of electrodes comprises at least one electrode, or portions thereof, having height or depth variations from about 1% to about 1000% of:
  • At least one electrode is not flat and in another embodiment, positioning of the electrodes in the chamber is varied with respect to gaps between the electrodes, spacing of the electrodes, or a combination thereof.
  • the gaps are between about 1 micron and about 50 microns and in another embodiment, gaps between the electrodes, spacing of the electrodes, height of the electrodes or portions thereof, shapes of the electrodes or portions thereof, surface area of the electrodes or portions thereof, volume of the electrodes or portions thereof, vertical positioning of the electrodes or portions thereof within said chamber or a combination thereof is unequal.
  • gaps between the electrodes, spacing of the electrodes, or a combination thereof is equal.
  • electrode widths are between about 0.1 microns and about 50 microns.
  • At least one electrode of the plurality of electrodes comprises at least one raised portion of the electrode in the form of a cylinder of arbitrary cross section. In another embodiment, at least one electrode of the plurality of electrodes comprises an exposed surface, which is flat, and not coplanar with another exposed surface of the electrode or of another electrode in the series.
  • the chamber is comprised of a transparent material, which in one embodiment is a plastic or in another embodiment is a polymer. In one embodiment, the device is comprised of a material, which is transparent at a given wavelength corresponding to excitation and emission of a fluorophor.
  • the device is comprised of a material, which is transmissive at a certain wavelength, or in some embodiments, at a wavelength that corresponds to excitation/emission of a compound or reagent.
  • the microfluidic channels and/or devices comprising the same are comprised of a material functionalized via SAM, or in another embodiment, comprising an adhesion layer, as described herein.
  • the electrodes are arranged in a gradient pattern in the chamber.
  • the source applies a peak to peak AC voltage of between about 0.1 and about 10 Volts.
  • the AC frequency is between about 1 Hz and about 100 kHz.
  • this invention provides an apparatus comprising a device of this invention.
  • this invention provides a method of mixing a fluid, said method comprising i. applying a fluid to a device of this invention; and ii. selectively applying voltage to the at least two series, such that voltage is not simultaneously or commensurately applied to the at least two series; whereby upon selective application of voltage to the series, electro-osmotic flows with varied trajectories is generated in a region proximal to each of the series, resulting in mixing of the applied fluid.
  • the .method further comprises assay or analysis of the fluid, and in on embodiment, the analysis is a method of cellular analysis.
  • the method comprises the steps of: a. introducing a buffered suspension comprising cells and a reagent for cellular analysis into the microfluidic chamber; and b. analyzing at least one parameter affected by contact between the suspension and the reagent.
  • the reagent is an antibody, a nucleic acid, an enzyme, a substrate, a ligand, or a combination thereof.
  • the reagent is coupled to a detectable marker.
  • the marker is a fluorescent compound, and in another embodiment the device is coupled to a fluorimeter or fluorescent microscope.
  • the method further comprises the step of introducing a cellular lysis agent to the device.
  • the reagent specifically interacts or detects an intracellular compound.
  • the assay or analysis of the fluid is a method of analyte detection or assay.
  • the method further comprises the steps of: a. introducing an analyte to the device; b. introducing a reagent to the device; and c. detecting, analyzing, or a combination thereof, of the analyte.
  • mixing reconstitutes a compound in the device, upon application of the fluid, and in one embodiment, the compound is solubilized slowly in fluids. In one embodiment, the mixing results in high-throughput, multi-step product formation.
  • the method further comprises the steps of: a. introducing a precursor to the device; b. introducing a reagent, catalyst, reactant, cofactor, or combination thereof to the device; c. providing conditions whereby the precursor is converted to a product; and d. optionally, collecting the product from the device.
  • the method further comprises carrying out iterative introductions of the reagent, catalyst, reactant, cofactor, or combination thereof in (b), to the device.
  • the reagent is an antibody, a nucleic acid, an enzyme, a substrate, a ligand, a reactant or a combination thereof.
  • the mixing results in drug processing and delivery.
  • the method further comprises the steps of: i. introducing a drug and a liquid comprising a buffer, a catalyst, or combination thereof to the device; ii. providing conditions whereby the drug is processed or otherwise prepared for delivery to a subject; and iii. collecting the drug, delivering the drug to a subject, or a combination thereof.
  • the method further comprises the step of carrying out iterative introductions of liquid to the device.
  • introduction of the liquid serves to dilute the drug to a desired concentration.
  • Figure 1 schematically depicts embodiments of elements of the devices of this invention.
  • IA asymmetric planar electrodes
  • IB non-planar, stepped 3D electrodes
  • 1C a spatially periodic AC voltage
  • FIG. 2 shows embodiments of the invention capable of rapid fluid mixing.
  • Two electrode arrays arbitrarily referred to as "A" (2-10) and “B" (2-20) are positioned in a chamber (2-30), driving nonlinear electrokinetic flows in different directions. Rapid mixing by chaotic advection is achieved by modulating the AC voltage of each array and switching between on and off states of each array: A. two arrays are positioned on opposite walls of the chamber and switch back and forth in dominance; B. two arrays are positioned on the same wall leaving the opposite wall available for other uses, for example and in some embodiments, providing detection sites for particles, molecules, or cells suspended in the fluid. The voltage of only one array is modulated in time.
  • FIG. 3 shows an embodiment of the invention with four electrode arrays (3-10), (3-20), (3-30), (3-40) in a confined microchamber (3-50).
  • Four different flow patterns are illustrated, representing certain embodiments of this invention, which may arise as a result of modulating application of voltage, etc., in different combinations, for the respective arrays.
  • the fluid content can be trapped in a convection cell, such that, for example, suspended particles may be separated into different convection cells, which then act as traps.
  • traps are illustrated by the dotted line boundary demarcation, which effectively divide the region into separate convection cells. , By alternating between two or more of these states, rapid chaotic mixing can be achieved.
  • Figure 4 depicts an embodiment of the invention directed to mixing in a continuous flow via positioning and activating specific arrays in time to drive flows transverse to the channel axis. Short arrows indicate flow direction.
  • Two opposite walls of channel 4-50 are lined with four electrode arrays (A represents 4-10), (B represents 4-20), (C represents 4-30), (D represents 4-40) in figure 4A for mixing. Other geometries for the electrodes are envisioned for this embodiment, as well.
  • Figure 4B depicts a channel with a larger cross section than figure 4A, which in turn results in slower propulsion across the chamber and longer mixing times therefore.
  • Figure 5 depicts an embodiment of the devices of the invention, which selectively traps, pumps, and mixes a fluid in a microchannel.
  • a periodic pattern of four electrode arrays (5-10), (5-20), is positioned along one wall of a microchannel (5-30).
  • Each array can be turned on separately, and each array may drive flows in alternating directions, when voltage is applied thereto.
  • a (5-10) and B (5-20) are positioned in a chamber, which pump in opposite directions, when both A and B are activated at once, the opposing flows form closed convection cells to trap fluid and/or position particles above each array (5A).
  • Figure 5B depicts activating a single set "A" (5- 10), driving a net flow in a single direction, which for example, may disperse and/or transport trapped fluid or particles therein.
  • Figure 5C depicts activating set “B" (5-20) driving a similar flow in the opposite direction.
  • temporally modulating the sets of electrodes e.g. by switching between states 5A, 5B, and/or 5C, rapid chaotic mixing can be achieved.
  • Net pumping in a desired direction can be achieved at the same time as mixing by tuning the fraction of the time and/or magnitude of the flow (via the voltage) from set A vs. set B, etc.
  • temporal modulation of one or more of these states is superimposed on a system with a background pressure-driven flow, which would also suffice for rapid active mixing of the fluid as it is pumped through the channel.
  • Figure 6 depicts another embodiment of a device of this invention, wherein arrays comprising two sets of electrodes ("A" being 6-10 and "B" being 6-20) drive flows in the same direction. Each set includes a shifted mirror image pattern on the opposite wall of the channel (i.e. 6-30 corresponds to 6-20, in terms of orientation, and 6-40 corresponds to 6-10). When all electrodes are activated, a uniform plug flow is formed which can be used to transport coherent localized volumes of fluid or particles. With temporal modulation of the two sets of electrodes, various pumping strengths and flow recirculation patterns are generated.
  • FIG. 7 depicts an embodiment of modulating the voltage of two or more electrodes on opposite sides of a microchannel.
  • the microchannel contains an array of polarizable (typically metallic or metal coated) posts (7-50; 7-60), which may have symmetric and/or asymmetric geometry and orientation.
  • the device can be subject to time-modulated AC voltages.
  • FIG. 8 depicts an embodiment of a device of the invention where polarizable posts (8-50) and (8-60) are placed in a microfluidic chamber with at least four electrodes placed on different walls, to allow application of dominant electric fields in orthogonal directions.
  • Time modulation strategies can be used to achieve chaotic mixing in the chamber, as described herein. In some embodiments, switching time is comparable to convection time for the dominant fluid vortices amongst the array of posts.
  • This invention provides, in some embodiments, devices and apparatuses comprising the same, for the mixing and/or pumping of relatively small volumes of fluid.
  • Such devices utilize nonlinear electrokinetics as a primary mechanism for driving fluid flow.
  • the term "nonlinear electrokinetic flow” refers to any electically driven fluid flow which scales nonlinearly with the applied voltage or electric field. Examples include induced- charge electro-osmotic (ICEO) flow around polarizable surfaces, AC electro-osmotic (ACEO) flow over electrode arrays, and AC electrothermal flows.
  • ICEO induced- charge electro-osmotic
  • ACEO AC electro-osmotic
  • the invention describes how such time-dependent modulation of a set of such nonlinear electrokinetic flows can be exploited for mixing, pumping, and trapping fluid volumes in microfluidic devices.
  • this invention provides a device comprising at least one microfluidic chamber for mixing an electrolyte fluid, the chamber comprising: > a plurality of electrodes proximal to, positioned on, or comprising at least one surface of the chamber arranged in at least two series; and
  • Figure 1 exemplifies an embodiment of a device of this invention, depicting multiple periodic arrays of microelectrodes, which drive nonlinear electrokinetic flow which pumps fluid over the array in one direction (e.g. from left to right, or vice versa).
  • the plurality of electrodes as depicted in Figure IA comprises an asymmetric planar array of flat electrodes of different widths and gaps within each period in the array.
  • the figure depicts one example for the positioning of the plurality of electrodes and the electrical connections for AC forcing in the device.
  • the skilled artisan will readily appreciate other manner of positioning of electrodes within the device and electrical connections, which may be applied thereto to arrive at the devices of this invention.
  • FIG. IB Another embodiment of a device of this invention is depicted in Figure IB.
  • the means for AC forcing may comprise a power supply, a voltage source, a function generator or a combination thereof.
  • the plurality of electrodes form an array of non-planar stepped electrodes.
  • the plurality of electrodes form an array wherein each electrode is broken into two horizontal surfaces at different heights on dielectric steps (Figure 1C).
  • the plurality of electrodes form a planar array with three-dimensional metal or dielectric structures on the electrodes to further shape the flow by contributing to the directional pumping and/or providing more complex local flows over the array (Figure ID).
  • the devices of this invention may comprise combinations of arrays of electrodes as described herein, such that a device may comprise a series of electrodes positioned such that the trajectories of fluid flow from each series differs, however the electrodes comprising each series are similar in geometry, and dimension, and in some embodiments, in orientation.
  • additional arrays may be incorporated in such devices, which comprise electrodes varying in heights, or comprise electrodes having a portion of such electrode varying in height, referred to herein, in some embodiments as "stepped electrodes".
  • the devices comprise stepped and planar electrodes, wherein flow trajectories of such electrodes are altered with respect to each other, or in some embodiments, are in a similar direction, however, their activation may be modulated in time.
  • such devices may further comprise conducting posts, as described herein. It is to be understood that any combination of arrays or series of electrodes may be positioned within the device, in any order, orientation and/or patterns, to achieve modulated flows as described herein and is to be considered as part of this invention.
  • traveling-wave voltages are applied to the plurality of electrodes or to specific series of electrodes, by appropriate electrical connections.
  • the voltage source produces a four-phase pulse in the electrode array.
  • the plurality of electrodes form a three-dimensional array wherein each electrode comprises portions, such that each portion comprises a horizontal surface at different heights on dielectric steps.
  • the devices comprise three-dimensional metal or dielectric structures on the electrodes to further shape the flow by contributing to the directional pumping and/or providing more complex local flows over the array.
  • this invention makes use of ACEO-based devices which pump and/or mix fluid, by a mechanism which utilizes nonlinear electrokinetic pumps and mixers involving three- dimensional structures in microchannels.
  • the driving principle in these devices is termed "induced- charge electro-osmosis” (ICEO), which, in one embodiment refers to nonlinear (voltage-squared) electro- osmotic flow, which results when an electric field acts on its own induced charge at a polarizable (metal or dielectric) surface.
  • ICEO induced- charge electro-osmosis
  • this invention provides a device comprising at least one microfluidic chamber for mixing an electrolyte fluid, the chamber comprising: > a plurality of electrodes proximal to, positioned on, or comprising at least one surface of the chamber, the electrodes or portions thereof are varied in height or in surface area or in vertical location by at least 1%, wherein:
  • the plurality of electrodes are arranged in at least two series, with each series varying in terms of an electroosmotic flow trajectory created by the series upon application of voltage thereto, from at least a series proximally located thereto on the at least one surface;
  • a source providing an electric field in the chamber, wherein the source applies voltage selectively to the series such that the voltage is not simultaneously or commensurately applied to all series of electrodes of the plurality.
  • this invention provides a microfluidic device comprising:
  • the microfluidic channel comprises: o a passageway for transmitting an electrolyte fluid; and o a plurality of electrodes connected to a source, providing an electric field in the microchannel; wherein the electrodes are parallel- positioned or interdigitated and are co-axial, with respect to each other, in at most one dimension, whereby the electric field produces a dominant electro-osmotic flow across the microfluidic channel.
  • the devices of this invention further comprise at least one inlet port, at least one outlet port and at least one microfluidic channel in fluid communication with the ports.
  • the microfluidic device comprises placement of the elements on a substrate, or in another embodiment, the microfluidic chamber is contiguous with the substrate.
  • the term "a” refers to at least one, which in some embodiments, is one, or in some embodiments two or more, or in some embodiments, pairs of, or in some embodiments, a series of, or in some embodiments, any multiplicity as desired and applicable for the indicated application.
  • the substrate and/or other components of the device can be made from a wide variety of materials including, but not limited to, silicon, silicon dioxide, silicon nitride, glass and fused silica, gallium arsenide, indium phosphide, IH-V materials, PDMS, silicone rubber, aluminum, ceramics, polyimide, quartz, plastics, resins and polymers including polymethylmethacrylate (PMMA), acrylics, polyethylene, polyethylene terepthalate, polycarbonate, polystyrene and other styrene copolymers, polypropylene, polytetrafluoroethylene, superalloys, zircaloy, steel, gold, silver, copper, tungsten, molybdenum, tantalum, KOVAR, KEVLAR, KAPTON, MYLAR, teflon, brass, sapphire, other plastics, or other flexible plastics (polyimide), ceramics, etc., or a combination thereof.
  • PMMA polymethylmeth
  • the substrate may be ground or processed flat.
  • High quality glasses such as high melting borosilicate or fused silicas may be used, in some embodiments, for their UV transmission properties when any of the sample manipulation and/or detection steps require light based technologies.
  • portions of the internal and/or external surfaces of the device may be coated with a variety of coatings as needed, to facilitate the manipulation or detection technique performed, to enhance flow, to promote mixing, or combinations thereof.
  • the substrate comprises a metal-bilayer.
  • such substrates comprise adhesive or bonding layers such as titanium or chrome or other appropriate metal, which is patterned or placed between the electrode surface and another component of the device substrate, for example, between a distal gold electrode and an underlying glass or plastic substrate.
  • the metal-bilayer is such that a metal is attached directly to an electrode, which comprises, or is attached to another component of the substrate.
  • the substrate comprises an adhesive layer between, for example underlying glass or plastic substrate and an electrode such as a polymer, a monolayer, a multilayer, a metal or a metal oxide, comprising iron, molybdenum, copper, vanadium, tin, tungsten, gold, aluminum, tantalum, niobium, titanium, zirconium, nickel, cobalt, silver, chromium or any combination thereof.
  • the substrate comprises electrodes of zinc, gold, copper, magnesium, silver, aluminum, iron, carbon or metal alloys such as zinc, copper, aluminum, magnesium, which may serve as anodes, and alloys of silver, copper, gold as cathodes.
  • the substrate comprises electrode couples including, but not limited to, zinc-copper, magnesium-copper, zinc-silver, zinc-gold, magnesium-gold, aluminum-gold, magnesium- silver, magnesium-gold, aluminum-copper, aluminum-silver, copper-silver, iron-copper, iron-silver, iron- conductive carbon, zinc- conductive carbon, copper-conductive carbon, magnesium- conductive carbon, and aluminum-conductive carbon.
  • electrodes within a single array are comprised of the same material, or in some embodiments, of a different material.
  • electrodes within a single device, but within separate arrays or series of electrodes are comprised of the same material, or in some embodiments, of a different material.
  • an electrode as described herein may be comprised of any conductive material, for example, and in some embodiments, gold, copper, gold-palladium, nickel, or any other suitable material, as weill be appreciated by the skilled artisan.
  • an electrode as described herein may be comprised of any suitable material as herein described.
  • electrodes as described herein may be coated.
  • electrodes as described herein may be plated.
  • the substrate may be further coated with a dielectric and/or a self- assembled monolayer (SAM), to provide specific functionality to the surface of the device to which the material is applied.
  • SAM self- assembled monolayer
  • the term “chambers" "channels" and/or “microchannels” are interchangeable, and refer to a cavity of any size or geometry, which accommodates at least the indicated components and is suitable for the indicated task and/or application.
  • such channels comprise the same materials as the substrate, or in another embodiment, are comprised of a suitable material which prevents adhesion to the channels, or in another embodiment, are comprised of a material which promotes adhesion of certain material to the channels, or combinations thereof. In some embodiments, such materials may be deposited according to a desired pattern to facilitate a particular application.
  • the substrate and/or chambers of the devices of this invention comprise a material which is functionalized to minimize, reduce or prevent adherence of materials introduced into the device.
  • the functionalization comprises coating with extracellular matrix protein/s, amino acids, PEG, or PEG functionalized SAM's or is slightly charged to prevent adhesion of cells or cellular material to the surface.
  • functionalization comprises treatment of a surface to minimize, reduce or prevent background fluorescence.
  • Such functionalization may comprise, for example, inclusion of anti-quenching materials, as are known in the art.
  • the functionalization may comprise treatment with specific materials to alter flow properties of the material through the device.
  • such functionalization may be in discrete regions, randomly, or may entirely functionalize an exposed surface of a device of this invention.
  • the invention provides for a microchip comprising the devices of this invention.
  • the microchip may be made of a wide variety of materials and can be configured in a large number of ways, as described and exemplified herein, in some embodiments and other embodiments will be apparent to one of skill in the art.
  • the composition of the substrate will depend on a variety of factors, including the techniques used to create the device, the use of the device, the composition of the sample, the molecules to be assayed, the type of analysis conducted following assay, the size of internal structures, the placement of electronic components, etc.
  • the devices of the invention will be sterilizable as well, in some embodiments, this is not required.
  • the devices are disposable or, in another embodiment, re-usable.
  • Microfluidic chips used in the methods and devices of this invention may be fabricated using a variety of techniques, including, but not limited to, hot embossing, such as described in H.
  • microfabrication technology applies the tools and processes of semiconductor fabrication to the formation of, for example, physical structures.
  • Microfabrication technology allows one, in one embodiment, to precisely design features (e.g., reservoirs, wells, channels) with dimensions in the range of ⁇ 1 ⁇ m to several centimeters on chips made, in other embodiments, of silicon, glass, or plastics. Such technology may be used to construct the microchannels of the devices of this invention, in one embodiment.
  • fabrication of the device may be accomplished as follows: first, a glass substrate is metallized.
  • the choice of metal can be made with respect to a variety of desired design specifications, including resistance to oxidation, compatibility with biological materials, compatibility with substrates, etc.
  • the metallization layer may be deposited in a specific pattern (i.e. through adhesive or shadow-masked metal evaporation or sputtering), in one embodiment, or, in another embodiment, it may be etched subsequent to deposition.
  • Metals can include, but are not limited to gold, copper, silver, platinum, rhodium, chromium, etc.
  • the substrate may be coated with an initial layer of a thin metal, which promotes adhesion of another metal to the substrate. In some embodiments, metals may also be adhered to the substrate via adhesive.
  • the substrate is ground flat to promote adhesion. In some embodiments, the substrate is roughened to promote metal adhesion.
  • the deposited metal may either be deposited in the final topology (i.e. through a mask) or, in another embodiment, patterned post- deposition. According to the latter embodiment, a variety of methods may be used to create the final pattern, as will be understood by one skilled in the art, including inter-alia, etching and laser ablation. Mechanical forms of removal (milling, etc.) may be used, in other embodiments.
  • gold is deposited on chromium and the gold is etched using a photoresist mask and a wet gold etchant.
  • the chromium remains a uniform film, providing electrical connection for subsequent electrodeposition (forming the anode connection).
  • gold is deposited via electron-beam evaporation onto an adhesion layer of titanium.
  • the gold is patterned using a wet etchant and photoresist mask.
  • the titanium is left undisturbed for subsequent electrodeposition.
  • the metal may be patterned prior to deposition.
  • a shadow mask can be utilized in one embodiment.
  • the desired shape is etched or machined through a thin metal pattern or other substrate. The etched substrate is then held parallel to the base substrate and the material is deposited via evaporation or sputtering through the mask onto the substrate. In some embodiments, this method is desirable in that it reduces the number of etch steps.
  • the patterned surface is formed by transferring a pre-etched or stamped metal film with adhesive onto the substrate.
  • the various devices on the layer have a common electrical connection enabling subsequent electrodeposition, and are deposited strategically so that release and dicing results in proper electrical isolation.
  • a rigid stamp is used to puncture a thin metal film on a relatively pliable elastic (plastic) substrate.
  • the rigid stamp can have, in some embodiments sharp or blunt edges.
  • the thickness of deposited metals is tailored to specific applications.
  • thin metal is deposited onto the surface of the wafer and patterned. According to this aspect of the invention, and in one embodiment, the patterned surface forms a common anodic connection for electroplating into a mold.
  • molding may be used.
  • molding comprises a variety of plastics, ceramics, or other material which is dissimilar to the base substrate.
  • the molding material is removed following electroplating.
  • the molding material is sacrificial.
  • thick (greater than a few microns) metal is deposited and subsequently etched to form raised metal features.
  • welding, assembly via SAMs, selective oxidation of thin metals comprise some of the methods used to form insulating areas and provide electrical isolation.
  • passivation of the metal surfaces with dielectric materials may be conducted, including, but not limited to, spin-on-glass, low temperature oxide deposition, plastics, photoresists, and other sputtered, evaporated, or vapor-deposited insulators.
  • the devices of this invention have at least one inlet and/or at least one outlet.
  • the inlet, or in another embodiment, the outlet may comprise an area of the substrate in fluidic communication with one or more microfluidic channels, in one embodiment, and/or a sample reservoir, in another embodiment.
  • Inlets and outlets may be fabricated in a wide variety of ways, depending upon, in one embodiment, on the substrate material utilized and/or in another embodiment, the dimensions used.
  • inlets and/or outlets are formed using conventional tubing, which prevents sample leakage, when fluid is applied to the device, under pressure.
  • inlets and/or outlets are formed of a material which withstands application of voltage, even high voltage, to the device.
  • the inlet may further comprise a means of applying a constant pressure, to generate pressure-driven flow in the device.
  • a "device” or “apparatus” of this invention will comprise at least the elements as described herein.
  • the devices of this invention comprise at least one microchannel, which may be formed as described herein, or via using other microfabrication means known in the art.
  • the device may comprise a plurality of channels.
  • the devices of this invention will comprise a plurality of channels, or microchannels.
  • the phrase "a plurality of channels" refers to more than two channels, or, in another embodiment, channels patterned according to a desired application, which in some embodiments, refers to channels varying by several orders of magnitude, whether on the scale of tens, hundreds, thousands, etc., as will be appreciated by one skilled in the art.
  • the device comprises microchannels connected to the chamber wherein mixing occurs, whereby the channels convey the mixed fluid from one area of the device to another, via the microchannels.
  • the channels convey mixed fluid out of the device.
  • the chamber is in fact a microchannel.
  • the devices of this invention mix and optionally pump fluids using non-linear electroosmotic flow generated within the device.
  • the devices of this invention comprise electrodes connected to a source providing an electric field in the microchannel, wherein the device comprises two or more parallel or interdigitated electrodes, which when in the presence of electrolyte fluids in the device and application of the field produce electro-osmotic flows so that the electrolyte fluid is driven across the microfluidic channels.
  • electrode is to understood to refer to the metal or other conducting material- electrode per se, as well as a substrate onto which such an electrode is affixed, or which comprises the electrode, or is proximal to the electrode.
  • the electrodes of the devices of this invention will have varied height, in some embodiments, or in other embodiments, will not be co-axial, with regard to Cartesian axes, in more than one dimension. It is to be understood that with reference to varied spatial apportionment of the electrodes, e.g. their height, that such reference is in terms of the vertical placement of the electrode, as well as the electrode placed on an underlying substrate.
  • this invention is to be understood to comprise a chamber comprising a pair of electrodes, wherein the electrodes have a comparable width and depth, however one electrode's height may be 10 micron with another being 40 microns, or with another also being 10 microns, however the electrode is positioned on a substrate of 30 microns in height.
  • the arrangement of the electrodes is such so as to promote mixing of the materials in the microchannel, as will be appreciated by one skilled in the art, and as exemplified hereinbelow.
  • the geometries of the electrodes are varied so as to promote mixing of the fluid in discrete regions of the channel, and/or conveyance of mixed material.
  • flat electrode pairs are arranged in an array on or as part of a substrate.
  • the electrodes are of a rectangular shape.
  • the two rectangular electrodes have the same length and depth, but differ in width. In some embodiment such different in size and in surface area affects the electric field around each electrode, or between two such electrodes.
  • electrode pairs are of a stepped shape.
  • the electrodes are L- shaped, with one area elevated higher than another area in the electrode. In some embodiment such asymmetric geometry of the electrodes affects the electric field around each electrode, or between two such electrodes.
  • the two electrodes forming an electrode pair are placed in different height with respect to the underlying substrate. In one embodiment one electrode is placed higher than another electrode. In some embodiment such asymmetric geometry of the electrodes affects the electric field around each electrode, or between two such electrodes.
  • electrodes contain more than one conducting element. In one embodiment the conducting elements are in contact with each other. In one embodiment an electrode in an electrode pair is made of a planar, rectangular element and a cylindrical element.
  • the cylindrical element is positioned on the planar element and the two elements are in contact.
  • a second electrode in a pair comprises a similar but narrower planar element and lacks the cylindrical element.
  • such arrangement of an electrode pair breaks the symmetry of the electric field around each electrode and between two electrodes.
  • any geometry and shape of electrodes and any number of contacted conductive elements can be used.
  • electrode elements or parts can be flat, thick, thin, cylindrical, spherical, tear-drop shaped, saw-tooth shaped, zig-zaged, wavy, porous, rectangular, square, ball-shaped, triangular, diamond-shaped, star-shaped or any combination thereof.
  • some electrode parts can be higher than others, deeper, thicker, co-axial, incorporated in, surrounding, placed on top of or overlap with, other parts of the electrodes.
  • electrodes are placed on one side of a four-sided chamber. In one embodiment the electrodes are placed on two, three or four sides of a four-sided chamber. In one embodiment electrodes are placed around the inner part of a cylindrical chamber or channel. In one embodiment electrodes and electrode arrays forms circles around the inner part of a channel or a chamber. In one embodiment electrodes form a C-shape which overlaps with the inner part of a cylindrical channel.
  • one, two, three, four or any higher number of close to C-shaped or curved electrodes can align a cross section of a cylindrical channel, with gaps between them.
  • four curved electrodes, each with a length that is smaller than a quarter of the circumference of the inner part of a cylindrical channel are placed around a cross-section of an inner part of the cylindrical chamber.
  • an array of electrodes is placed on the substrate.
  • at least two arrays of electrodes are placed on the substrate.
  • the at least two arrays comprises long rectangular shaped electrodes.
  • the at least two arrays of electrodes are oriented perpendicular to each other with respect to the long axis of the electrodes in each array.
  • perpendicular electrode arrays are placed on the same side of the chamber.
  • the perpendicular arrays are placed on opposite sides of the chamber.
  • perpendicular arrays are placed adjacent to each other.
  • each array can control fluid flow in a different direction through the modulated application of voltage.
  • a fluid flow is induced perpendicular to the long axis of the electrodes in the array. In one embodiment this fluid flow is tangential to the substrate on to which the electrodes are fixed.
  • at least two electrode arrays can be operated simultaneously or alternately by applying various electric fields to the arrays. In one embodiment switching the applied electric field in two perpendicular electrode arrays can control, change, orient or modulate the direction of fluid flow in the chamber.
  • two electrode arrays are placed on one side of a four-sided chamber. In one embodiment two additional electrode arrays are placed on the opposite side of the four-sided chamber. In one embodiment the electrodes are rectangular. In one embodiment applying an electric field to all four electrode arrays induces four fluid currents next to each array. In one embodiment the four fluid currents cause confinement of liquid portions in four areas adjacent to the four electrode arrays. In some embodiments such confinement can be used to trap particles, solutes, or cells in the fluid. In some embodiments such confinement can be used to pump or mix particles, solutes, or cells in the fluid.
  • turning on and off the electric fields applied to each electrode array in a defined way changes the kinetics of fluid circulation in the chamber, for example, with regard to regions of the chamber wherein fluid occupying such regions is more rigorously circulated within the region.
  • one, two, three, four or more fluid-circulating areas can be formed in a channel.
  • the number of fluid circulation areas depends on the number and orientation of the electrode arrays to which electric field is applied.
  • an array of rectangular electrodes is placed on the inner part of a substrate forming a wall of a chamber.
  • the long axis of the rectangular electrodes is parallel to the long axis of the chamber.
  • the long axis of the electrodes is perpendicular to the long axis of the chamber.
  • fluid flow is induced perpendicular to the main fluid flow along the channel.
  • such fluid flow caused by applying an electric field to the electrodes can cause, pumping or mixing of fluid and fluid contents. Such perpendicular fluid flow can slow down the flow in the main flow direction along the channel.
  • Such fluid flow can prolong the time in which particles, solutes or cells spend within the channel or within a special area in the channel.
  • Such perpendicular fluid flow can concentrate a species in a certain area along the channel.
  • Such perpendicular fluid flow can eliminate particles or solutes from certain areas within the channel.
  • Such perpendicular fluid flow can create concentration gradients within the channel.
  • arrays comprising a large number of electrodes can slow down the progression of a fluid in a more efficient way than arrays comprising smaller number of electrodes.
  • multiple arrays of rectangular electrodes are arranged in a row along the long axis of a microfluidic channel.
  • the arrays are defined as "A" and "B" arrays.
  • a "B" array is placed after an "A" array along the long axis of the channel.
  • the electrode array arrangement along the long axis of the channel has the pattern of ABABABABA, with respect to the names of the electrode arrays.
  • "A" and “B” electrode arrays are independently electronically addressed.
  • voltage can be applied to all of the arrays, and in other embodiments voltage can be applied to the "A" arrays or to the "B” arrays only.
  • fluid mixing when voltage is appropriately applied to the "A" and “B” arrays, fluid mixing can be achieved.
  • fluid mixing adjacent to “A” arrays has an opposite fluid flow direction when compared to the fluid flow adjacent to a "B" array.
  • such mixing can trap or hold or confine particles or solutes in the fluid, to areas adjacent to "A" or “B” arrays.
  • applying an electric field to the "A" arrays or to the "B” arrays only can cause fluid flow along alternating directions or opposing directions along the channel. In some embodiments such configuration is used to concentrate species in the fluid, to enhance or reduce chemical reactions between species in a fluid, and to facilitate detection of the fluid content.
  • both set of electrodes (“A" and "B”) drive flows in the same direction.
  • Each set also optionally includes a shifted 'mirror image' pattern on the opposite wall of the channel.
  • the modulation time period is comparable to the mean advection time across each individual electrode array to promote chaotic mixing.
  • arrays of electrodes are placed on opposite sides of the inner walls of a channel.
  • two opposing electrode arrays define an area in the channel.
  • one or more polarizable posts are placed within this area inside the channel.
  • the polarizable posts affect, divert or change the local electric field.
  • the polarizable posts divert, change or affect the fluid flow direction in the vicinity of the posts.
  • modulating the voltage of two or more electrode arrays on opposite sides of a microchannel containing one or more polarizable posts controls the mixing pattern of the fluid in the channel.
  • a device of this invention can be subject to time-modulated AC voltages.
  • a four-electrode array configuration is used.
  • four electrode arrays or four electrodes are positioned on two sides of a four-sided channel.
  • the electrodes or arrays are referred to as "A”, "B", “C”, "D", electrodes, each is placed on one side of the channel.
  • electrodes "A” and “B” are placed on one side and electrodes “C” and “D” are placed on the opposing side.
  • a dominant AC voltage can be applied to “A” and “C” electrodes or to "B” and “D” electrodes.
  • the dominant AC voltage can switch from being between A and C to B and D.
  • One way to control such switching is to apply an AC voltage to each electrode, A-D, and give each a tunable phase shift relative to the others.
  • a and B have zero phase shift (same AC voltage) while C and D have a half-period phase shift (same AC voltage, opposite of A and B).
  • a and C In a second state, A and C have zero phase shift, while B and D have a half-period phase shift.
  • rapid chaotic mixing can be achieved in the channel around the posts.
  • the mixing can be superimposed on a background pressure-driven flow through the post array.
  • broken symmetry in the geometry of the post array leads to time-modulated pumping through the channel, along with the time- modulated mixing.
  • a device of this invention can be subject to time-modulated AC voltages.
  • a four-electrode array configuration is used.
  • four electrode arrays or four electrodes are positioned on four sides of a four-sided channel.
  • the electrodes or arrays are referred to as "A”, “B", “C”, “D", electrodes, each is placed on one side of the channel.
  • electrodes "A” and “C” are placed on opposing sides and electrodes "B" and “D” are placed on opposing sides.
  • polarizable posts are placed in a microfluidic chamber with at least four electrodes placed on different walls as described above.
  • such arrangement allows the application of dominant electric fields in orthogonal directions, e.g. left/right using electrodes B and D, or up/down using electrodes A and B.
  • the same sort of time modulation strategies described above can be used to achieve chaotic mixing in the chamber.
  • the switching time should be comparable to the convection time for the dominant fluid vortices amongst the array of posts.
  • the device is so constructed so as to promote mixing in certain channels and conveyance to other channels, which in turn may comprise additional steps, which require mixing, as described herein.
  • the devices of this invention facilitate deposition of fluids at a site distal to the microchannels, for further processing, or other manipulations of the conveyed material.
  • electroosmosis in the devices of this result in the creation of a dominant flow.
  • the term "dominant flow” refers, in some embodiments, to propulsion of fluid in a desired direction (also referred to as “positive direction”), with minimal, or less propulsion of fluid in an undesired direction (also referred to as "negative direction").
  • planar electrodes which are approximately likewise proportioned in at least two of three dimensions, for example, likewise in terms of height and depth, and varied at most in terms of width, in previous ACEO devices.
  • Devices of this invention are likewise proportioned in at most only one of three dimensions, thus varied in terms of height and depth, of an electrode, or portions thereof.
  • electrodes in devices of this invention are likewise proportioned in terms of width, likewise proportioned in terms of their depth, however the height of each electrode, or in some embodiments, the height of portions of each electrode, or in some embodiments, the height of pairs of electrodes, or in some embodiments, the height of portions of electrode pairs are varied.
  • such height alterations may comprise raised or stepped electrode structures, or lowers or recessed electrode structures in a device to provide vertical differences in the electrode structure.
  • the terms "height alterations" or “height variance” or other grammatical forms thereof, refer to differences in height, which exceed by at least 1.5%, or in some embodiments, 3%, or in some embodiments, 5%, or in some embodiments, 7.5%, or in some embodiments, 10%, or more the referenced electrode.
  • a planar electrode pair in an array may vary in height by up to 0.25 %, as a result, for example, of different deposition of material forming the electrodes on a surface of a channel in the device.
  • height variances between at least two electrodes, or electrode pairs, or series in a given device will be more pronounced, and not a reflection of undesired variance due to material deposition.
  • the term "dominant flow” refers to electroosmotic flows, or flows as a result of application of an electric field in a chamber of the devices of this invention. It is to be understood that a dominant flow may be instituted that is less in magnitude, or varied in direction, for example, than other flows in the device, such as other background flows, pressure-driven flows for applying materials to the device, etc.
  • the devices of this invention may cause flows for mixing or controlling flow rate (faster/slower/stopping/starting%) in a channel which also has a stronger more "dominant" background flow (e.g. pressure-driven from elsewhere), where the device's dominant effect is still smaller than the background flow, yet is nonetheless greater in magnitude than similar electroosmotic flows would be with the use of planar electrodes.
  • "Dominant" in reference to flows caused by the devices/apparatuses/methods of this invention may be understood, in some embodiments, to specifically exclude background flow, or non-electroosmotic flow.
  • This invention in some embodiments, provides for the modulation of such electroosmotic flows, such that chaotic mixing of the fluid is accomplished. In some embodiments, such modulation may result in creating multiple dominant flows, sequentially, as a function of engagement of a particular series of electrodes.
  • two or more series of electrokinetic pumps operating in different directions are turned on and off either at specific intervals, or in some embodiments, at set patterns, or in some embodiments, randomly to mix.
  • series in some embodiment, refers to positioning and modulation of at least one or a group of electrodes as described herein, such that electroosmotic flows arising upon their engagement are in a comparable or similar direction, or in some embodiments, at a comparable or similar flow rate.
  • pumps in a series as described herein may encompass pumps located proximally along a Cartesian axis, wherein the electrodes/pumps have at least one surface of such structure abutting a common substrate.
  • pumps in a series as described herein may encompass pumps located proximally along a Cartesian axis, wherein the electrodes/pumps do not share a common substrate.
  • a series of pumps may be alternating with another series of pumps, such that for example a first series of pumps results in horizontal fluid flows, whereas the second series results in vertical fluid flows, and such series may alternate, such that overall flow may follow a patter, for example, and in one embodiment, wherein flow is horizontal, then vertical, then horizontal and vertical again.
  • the modulation of the voltage is slower than the operating AC frequency of each pump. According to this aspect, and in one embodiment, such control enables each pump the time to generate a quasi-steady flow in its particular direction prior to switching.
  • modulation of the voltage may be periodic and sinusoidal, at a lower frequency than the typical AC operating frequency of each pump.
  • each series may be modulated such that the magnitude, frequency or combination thereof of the voltage applied to each series is varied to maximize chaotic mixing. For example, the voltage of series 1 can be lowered to turn it off, while the voltage of series 2 is raised to turn it on. In some embodiments, the frequency of series 1 can be lowered or raised out of the operating range, while the frequency of series 2 is brought into the operating range.
  • Such transition can be effected by any number of means, for example via ensuring that the modulating waveform (which provides a sinusoidal envelope for the magnitude of the AC voltage at the operating frequency) is phase shifted by 90 degrees (1/4 period) between one pump and the other, so that one is effectively on while the other is off, with the ability to control, in some embodiments, that switching is a smooth transition from one pump to the other, and not sudden.
  • the modulating waveform which provides a sinusoidal envelope for the magnitude of the AC voltage at the operating frequency
  • the characteristic time scale for switching is comparable to the time for flow to circulate at least halfway around the vortex generated by the pump in the cavity. According to this aspect, and in one embodiment, the switching leads to stretching and folding in the two different pumping directions, which produces chaotic streamlines and very rapid mixing in the same way as the rolling of dough in a bakery.
  • the devices/methods of this invention promote chaotic mixing, which in turn results in non-steady time-averaged flow (at the time scale of the applied AC voltage), the latter of which is not very effective for mixing in a fixed volume or cavity of the microfluidic device.
  • chaotic mixing as a function of the methods/devices of this invention outperform steady flow in a fixed volume, the latter of which mainly reduces the length needed for diffusion from the chamber size to the smallest dimension of the flow structure. Chaotic mixing, as achieved by the methods/devices of this invention, may reduce such length, or time for the flow to reach such structure, etc., as well as provide for active contact between the same.
  • electrodes within a series may vary in terms of their height, width, shape, etc.
  • a series as described herein may be defined by the physical placement of the electrodes within the series, or in another embodiment, by the overall flow of fluid once the electrodes which comprise the series are engaged.
  • the device comprises a series of pumps, which if voltage is applied equally and simultaneously thereto would pump in opposing directions (5-10 versus 5-20).
  • the device comprises each series of pumps being arranged on two opposing substrates (5-30 versus 5-40), such that pairs of pumps on opposing substrates ultimately participate cooperatively toward flow in a single direction, and specific.
  • Another embodiment of the device comprises a first series of electrode or electrode-array pumps so arranged such that when engaged, fluid is pumped in the direction of the series of pumps located adjacently on the same substrate, and the second series of pumps, similarly pumps in the direction of its neighbor.
  • a third series of pumps located on a second substrate pumps in a direction opposite to that of the first series of pumps, and the fourth series of pumps.
  • Any number of patterns of engagement of the pumps can be envisioned, which selectively engage a series of pumps in a desired order, to facilitate fluid flow, which results in a desired pattern for mixing fluid contained therein. Depending upon the desired fluid flow direction, selective engagement of one series can then direct flow to a desired location in the device.
  • two or more electrokinetic pumps operating in different directions are turned on and off at specific intervals, or in another embodiment, at set patterns, or in another embodiment, randomly to mix.
  • two or more electrokinetic pumps pumping in opposing directions are turned on and off either at specific intervals, at set patterns, or randomly to mix.
  • the devices thus described may result in regions or temporary interruption of flow, as a function of the equal and opposite flow initiated proximal to the oppositely positioned series of electrodes.
  • Such temporary interruption in flow may, in some embodiments serve as a trap and release for material suspended in the flow, for examples, particles in flow, when two pumps are simultaneously engaged and hence fluid flow proximal to each is equal and opposite in direction.
  • the devices of this invention include an alternating current electrical controller e.g., which is capable of generating a sine or square wave field, or other oscillating field, which allows for modulation of engagement of a particular series of electrodes, as described herein.
  • the devices of this invention include a voltage controller that is capable of applying selectable voltage levels, simultaneously or sequentially, e.g., to a series of electrodes. Such a voltage controller is optionally implemented using multiple voltage dividers and multiple relays to obtain the selectable voltage levels. In some embodiments, multiple independent voltage sources are used. In some embodiments, the voltage controller is as described in U.S. Pat. No. 5,800,690.
  • modulating voltages affects a desired fluid flow characteristic, e.g., continuous or discontinuous (e.g., a regularly pulsed field causing the sample to oscillate direction of travel), and/or direction of such flow, thereby contributing to chaotic mixing as described herein.
  • a desired fluid flow characteristic e.g., continuous or discontinuous (e.g., a regularly pulsed field causing the sample to oscillate direction of travel), and/or direction of such flow, thereby contributing to chaotic mixing as described herein.
  • the devices of this invention provides for induced charge electroosmotic flow over entire arrays of electrodes, and mixing therein, over a large surface area of the chamber of the device.
  • the electrodes and metal structures are all "flat" in the sense that the primary exposed surfaces are co-planar and parallel to at least one surface of the channel, although the electrodes may be arranged at different heights and transverse positions in three-dimensional geometries.
  • the devices comprise periodic arrays of non-flat, three-dimensional electrodes, with raised and lowered sections (on a single electrode).
  • the series as described herein may comprise electrodes of differing heights their placement is varied, however the trajectories of the flow generated thereby are in a comparable direction, or magnitude. In some embodiments, such variance defines different series.
  • At least one electrode of the plurality of electrodes is not flat.
  • the plurality of electrodes comprises at least one electrode, which is raised with respect to another electrode.
  • the plurality of electrodes comprises at least one electrode, which is lowered with respect to another electrode.
  • the plurality of electrodes comprises at least one electrode having a height, which is proportional to a width of another electrode.
  • the plurality of electrodes comprises at least one electrode having a height, which varies by about 1% to about 100% of a width of another electrode.
  • the electrodes are not co-axial, with respect to each other, in any dimension.
  • the positioning of the electrodes in the microfluidic channel is varied with respect to gaps between the electrodes, spacing of the electrodes, or a combination thereof.
  • the electrodes are arranged in a symmetric pattern in the microfluidic channel, and in another embodiment, the gaps between the electrodes, the spacing of the electrodes, or a combination thereof is equal.
  • any variance as described herein with reference to one electrode versus another in the plurality of the devices/apparatuses of this invention is to be taken to refer to portions of electrodes as well, where variance in shape, width, depth, height reflects such variance within a single electrode, in terms of portions of the electrode, different electrodes in the device and any combination thereof.
  • the electrodes are arranged in an asymmetric pattern in the microfluidic channel, and in another embodiment, the gaps between the electrodes, the spacing of the electrodes, or a combination thereof is unequal.
  • the electrodes are arranged in a gradient pattern in the microfluidic channel.
  • gradient refers to an arrangement which has gradual or gradated differences, for example in electrode height, from one terminus of such arrangement to another, or in some embodiments, gradual or gradated differences, for example in electrode width, gradual or gradated differences, for example in electrode depth, gradual or gradated differences, for example in electrode shape, gradual or gradated differences, for example in electrode circumference, gradual or gradated differences, for example in the angle at which each electrode is deposited in an array in a device of the invention, or gradual or gradated differences, in any combination thereof, or any desired parameter of the same.
  • the term gradual or gradated differences refers to differences, which are based on a pattern, in ascending or descending value, which may be consecutive or non-consecutive.
  • the term “gradient” refers to any of parameter with regard to electrode geometry, which may vary by any defined/desired period, for example incrementally, or as a multiple or exponential scale, in one or more directions.
  • the layout (gaps, widths, heights, etc.) of each pair of electrodes in an interdigitated array could be rescaled to get larger (or smaller) with distance along the array in the direction of pumping so that the local pumping flow is slower (or faster).
  • a species is defined by specific intervals in such a gradient arrangement.
  • each graduated change defines a series.
  • changes in flow as a function of placement within a gradient defines a species.
  • the gradient may be a function of the gaps between electrodes, spacing of electrodes, height of electrodes or portions thereof, shapes of electrodes or portions thereof, or a combination thereof.
  • a pair may define a series, or in some embodiments a series is defined by any desired number of electrodes.
  • arrangement of electrodes which vary in at least 2 or 3 dimensions, in a series may be such that when a field is applied, one of the electrodes in the pair promotes fluid conductance in a particular direction, and another series promotes fluid conductance in another direction.
  • such electrodes may be constructed in particular geometries, as described herein, and as will be appreciated by one skilled in the art, such that fluid conductance in the desired direction, versus the alternate direction is optimized.
  • a series of electrodes/pumping units are so positioned as described herein, which promote chaotic mixing, and such series are positioned proximal to another series or pair of series, which in turn, via the methods of modulation as herein described, promotes fluid flow in a dominant direction, such that mixing of the fluid is localized to the electrodes involved in chaotic mixing, and once mixing is sufficient, the fluid is then conveyed in a dominant direction by the latter electrode series.
  • Various permutations of such arrangements to promote mixing and/or conveyance are readily apparent to one skilled in the art.
  • the electrodes may be arranged in a series, with varying at least 2 of the 3 dimensions of at least one electrode in a given series. Such series may be odd- or even- in number.
  • the electrodes in a given series may vary in any way as described herein in terms of electrode geometry, patterning in the device, or a combination thereof, and the devices of this invention may comprise multiple series, which in turn may add to the complexity of the arrays of electrodes and capabilities of the devices of this invention.
  • the gaps are between about 1 micron and about 50 microns, and in another embodiment, the electrode widths are between about 0.1 microns and aboout 50 microns.
  • the term "dominant flow” refers to propulsion of fluid in alternating directions, which may be modulated, for example via varying the frequency or strength of the field applied, and/or varying or modulating the electrode heights, or portions thereof, resulting in a net conveyance of fluid in a desired direction at a specific time or condition. In some embodiments, the term “dominant flow” refers, to greater propulsion of fluid in a positive rather than negative direction.
  • the term "greater propulsion" refers to a net propulsion of 51%, or in another embodiment, 55%, or in another embodiment, 60%, or in another embodiment, 65%, or in another embodiment, 70%, or in another embodiment, 72%, or in another embodiment, 75%, or in another embodiment, 80%, or in another embodiment, 83%, or in another embodiment, 85%, or in another embodiment, 87%, or in another embodiment, 90%, or in another embodiment, 95% of the fluid being conveyed in a device of the invention, in a desired or positive direction.
  • the term “greater propulsion” reflects propulsion of the amount of fluid conveyed in a desired direction as a function of time, with propulsion being greater in a desired direction, predictably, in comparison to a similarly constructed device comprising electrodes of comparable, as opposed to varied height.
  • the term “dominant flow” reflects propulsion of fluid conveyed in a desired direction, wherein such fluid is well mixed during, or prior to conveyance in a net desired direction.
  • the devices of this invention enable conveyance of a fluid, which is an electrolyte fluid.
  • electrolyte fluid refers to a solution, or in another embodiment, a suspension, or, in another embodiment, any liquid which will be conveyed upon the operation of a device of this invention.
  • a fluid may comprise a liquid comprising salts or ionic species.
  • the ionic species may be present, at any concentration, which facilitates conduction through the devices of this invention.
  • the liquid is water, or in another embodiment, distilled deionized water, which has an ionic concentration ranging from about 1OnM to about 0.1M.
  • a salt solution ranging in concentration from about 1OnM to about
  • the fluid comprises solutions or buffered media for use suitable for the particular application of the device, for example, with regards to the method of cellular analysis, the buffer will be appropriate for the cells being assayed.
  • the fluid may comprise a medium in which the sample material is solubilized or suspended.
  • such a fluid may comprise bodily fluids such as, in some embodiments, blood, urine, serum, lymph, saliva, anal and vaginal secretions, perspiration and semen, or in another embodiment, homogenates of solid tissues, as described, such as, for example, liver, spleen, bone marrow, lung, muscle, nervous system tissue, etc., and may be obtained from virtually any organism, including, for example mammals, rodents, bacteria, etc.
  • the solutions or buffered media may comprise environmental samples such as, for example, materials obtained from air, agricultural, water or soil sources, which are present in a fluid which can be subjected to the methods of this invention.
  • such samples may be biological warfare agent samples; research samples and may comprise, for example, glycoproteins, biotoxins, purified proteins, etc.
  • such fluids may be diluted, so as to comprise a final electrolyte concentration which ranges from between about 1OnM - 0.1M.
  • the pH, ionic strength, temperature or combination thereof of the media/solution, etc. may be varied, to affect the assay conditions, as described herein, the rate of transit through the device, mixing within the device, or combination thereof.
  • the devices of this invention comprise a series of electrodes, wherein each series comprises electrodes, which are not flat.
  • the electrodes are so constructed so as to comprise sections having at least two different vertical positions.
  • the transition between sections of different vertical heights is smooth, or in other embodiments, step- wise.
  • the different vertical positions of the sections differ with respect to other sections in the same electrode, and in some embodiments, with other electrodes of which the series is comprised.
  • the devices of this invention comprise electrodes, which are interlaced electrodes, which can be varied to adjust the mixing capability of the device and optionally the frequency response and/or rate of fluid conductance.
  • the elements of the device are so arranged so as to promote passage of mixed fluid over a sensor on, for example, a wall of the microchannel.
  • Electrodes which comprise sections which vary in terms of their vertical position may be readily accomplished by known means in the art.
  • the devices may be fabricated as described herein, with successive electroplatings in order to alter the height, shape, etc. of the electrode.
  • manufacture results in the production of electrodes with smooth transitions between the different vertical positions, and in other embodiments, with step-wise transitions, which vary in terms of the degree of drop between the different vertical positions.
  • Positioning of these electrodes within the device will, in some embodiments, be a reflection of a desired flow rate through the devices of this invention.
  • construction of the devices with such pumping elements facilitates greater flow rate, as a function of a "conveyor-belt" phenomenon, as described and exemplified herein.
  • arrays or electrode series as herein described, and polarity of the respective electrodes may be varied as a function of their placement in the device, as will be appreciated by one skilled in the art.
  • the electrodes are arranged with a variety of geometries, such as a square, hexagon, interlocking or inter-digitating designs, etc., as will be appreciated by one skilled in the art. Such orientation may be particularly useful in promoting mixing of the fluids used in the devices and methods of this invention.
  • the term "mixing" as used herein refers to circulation of materials to promote their distribution in a volume of space, for example, a mixture of 2 species, in a device of this invention, refers, in one embodiment, to a random distribution of the 2 species within a given volume of space of the device, e.g., in a microchannel of the devices of this invention.
  • the term “circulation” and “mixing” are interchangeable.
  • mixing refers to a change in a particular distribution which is not accompanied by agitation of the sample, in one embodiment, or in another embodiment, minimal agitation and/or formation of "bubbles" in the liquid medium in which the species are conveyed.
  • the pumping element will comprise electrodes fashioned to assume a variety of geometries, as described and exemplified herein, to reflect a consideration of a desired trajectory for conducting the fluid in the devices of this invention, to suit a particular application.
  • the geometry may approximate a checkerboard, interlocked "E" designs, designs as depicted herein, or one related thereto.
  • Electrodes and field polarities as "+” and “-” signs throughout all fields can also be AC or DC corresponding to electrode polarities oscillating between + and -, giving rise to the same induced-charge electro-osmotic flow.
  • all of the devices of the invention can operate in AC or DC.
  • the present invention provides for the operation of the device in AC with DC offset, as will be understood by one skilled in the art, for example, as described in U. S. Patent Number 5,907,155.
  • asymmetric driving signals may be used.
  • this invention takes advantage of the fact that there is a competition between regions of oppositely directed electro-osmotic slip on the surfaces of interlaced electrodes of opposite polarity, which in turn results in net pumping over the surface.
  • this aspect of the invention by raising the surfaces pumping in the desired direction (and/or lowering those not pumping in the desired direction) one effectively "buries” the reverse convection rolls. If the height difference is comparable to the width of the buried electrodes, the reverse convection rolls turn over near the upper surface and provide an effective "conveyor belt” for the primary pumping flow over the raised electrodes, as further described and exemplified hereinbelow.
  • the pumping element has raised portions of the electrodes that pump in the dominant direction (up to stagnation points on each electrode), by a height varied proportionally to the width of the unraised region.
  • the devices of this invention comprise raised electrodes, or in other embodiments, raised portions of electrodes, whose height is about proportional to the width of the unraised, recessed or combination thereof electrode, or portion of an electrode.
  • the raised electrodes and/or raised portions of electrodes have a height less than the width of the unraised electrode, or portion thereof.
  • the term "less than” in this context is by a value of about 1%, or about 5%, or about 8%, or about 10%, or about 15%, or about 17%, or about 20%, or about 25% or about 50%, as compared to the referenced value or parameter.
  • the term "about” as used in this invention is to be understood to encompass a value deviating by +/- 1%, or in another embodiment, by +/- 2.5%, or in another embodiment, by +/- 5%, or in another embodiment, by +/- 7.5%, or in another embodiment, by +/- 10%, or in another embodiment, by +/- 15%, or in another embodiment, by +/- 20%, or in another embodiment, by +/- 25%, with respect to the referenced value or parameter.
  • This invention provides, in some embodiments, specific designs for periodic three-dimensional electrode structures, which achieve much faster flows than existing ACEO devices by roughly an order of magnitude, for the same applied voltage and minimum feature size.
  • the design of the devices of this invention exploit the basic idea of positioning electrodes to recessreverse convection rolls as a "conveyor belt" to enhance the pumping flow driven by raised surfaces, and such positioning maximizes fluid mixing thereby.
  • devices with multiple electrodes may comprise electrodes which are all of the same shape, different shapes, different sizes, etc.
  • the electrodes are fashioned as steps, rounded steps, trapezoids, which are continuous along the y-axis, z-axis, or combinations thereof, or in some embodiments, are discontinuous along the y-axis, z-axis, or combinations thereof.
  • the electrodes of which the devices of this invention are comprised are co-axial in at most one dimension.
  • co-axial refers, in some embodiments, to sharing a Cartesian axis with the indicated element.
  • the electrodes in the devices of this invention share an x-axis, a y-axis, but not a z-axis.
  • the electrodes as positioned in the devices of this invention share an x-axis and not a y- or a z-axis. In some embodiments, the electrodes as positioned in the devices of this invention have a comparable overall geometry, which differs in overall scale, or in some embodiments, differ primarily in height. [00167] In some embodiments, electrodes are raised or lowered above the mean level of the microchannel surface, on which such electrodes are patterned or affixed, or the surface of the substrate, which comprises the electrodes as part of the microchannel surface.
  • Such raising or lowering will exceed that of the normal thickness of a metal layer, for example, such raising or lowering will be greater than a typical 1 micron thickness of previous electrodes used in certain microfluidic devices, such that the devices of this invention are more truly 3 dimensional structures.
  • such electrodes may be formed or arranged in any geometry, such that electrodes are coaxial in at most one dimension, when such electrodes result in fluid flows of opposing direction.
  • External circuitry can be used to control electrical connections and/or to fix the voltage/potential of any or all of the electrodes. Background electrode potential can be controlled relative to the pumping element electrodes in magnitude, frequency, and phase lag.
  • the total charge on the electrodes can also be controlled. Charge can be controlled relative to the background electrodes in magnitude, frequency, and phase lag, as above.
  • additional electrode geometries can include rounded portions, which can be fabricated for instance, by evaporating through a narrow slit, or by wet etching a vertical, electroplated electrode.
  • the background electrodes can be arranged in a variety of geometries relative to the pumping electrode.
  • the background electrodes can be parallel to one another and transverse to a background fluid flow, or in other embodiments, they can be parallel to one another and parallel to background fluid flow. In some embodiments, they can have an angle between them, resulting in some electric field gradients, which may enhance fluid mixing.
  • the electrical connections between electrodes and external circuitry can, in some embodiments, be as simple as planar wires connecting the center posts to the external circuits.
  • the electrical connections can be electroplated, in some embodiments.
  • the electrical connections can be buried beneath an insulating material, in some embodiments.
  • Driving and control electronics can be manufactured on-chip along with the electrodes, in some embodiments.
  • the driving and control electronics can be a separate electronics module, in some embodiments, an external stand-alone unit or microfabricated electronics.
  • the microfabricated electronics module in some embodiments, can be wire-bonded to the chip containing the electrodes or can be flip-chip bonded.
  • Fluidic channels can be fabricated by a variety of means, including soft-lithographic molding of polymers on rigid or semi-rigid molds. Channels can also be fabricated in glass via wet etching, plasma etching or similar means. Channels can be formed in plastics via stamping, hot embossing, or other similar machining processes. The channels can then be bonded to the substrate containing the electrode structures. Alignment marks can be incorporated onto the substrate to facilitate assembly. In some instances, metal surfaces can be exposed on substrate and channels to enable metal-to-metal bonding. Glass-to-glass bonding can be done at elevated temperatures and with applied potential. Plastic-to-glass can be facilitated with cleaning of glass surfaces prior to bonding, or fabrication of the fluidic portion of the device can be accomplished by any means known in the art.
  • Raised supports of an insulating or semiconducting nature can be fabricated on the substrate as well, in some embodiments, on which the pumping electrodes and/or background electrode may be mounted, to provide for differences in height, for uses as described herein.
  • this invention provides a device comprising a microfluidic loop.
  • the device will comprise ports and machinery such that fluid injected in one port can be recirculated across one or more regions of the device, for example to regions for the detection of materials, or in some embodiments, separation of material, or in some embodiments, mixing of materials, which may be effected by the micropumps of the devices of this invention, prior to ejection through another port, in some embodiments, as described and exemplified herein.
  • the device is adapted such that analysis of a species of interest may be conducted, in one embodiment, in the device, or in another embodiment, downstream of the device.
  • analysis downstream of the device refers to removal of the obtained product from the device, and placement in an appropriate setting for analysis, or in another embodiment, construction of a conduit from the device, for example, from a collection port, which relays the material to an appropriate setting for analysis.
  • such analysis may comprise signal acquisition, and in another embodiment, a data processor.
  • the signal can be a photon, electrical current/impedance measurement or change in measurements.
  • this invention provides an apparatus comprising a device of this invention, which in some embodiments, comprises the analytical modules as described herein.
  • the device comprises posts that are placed within the chamber.
  • electro-osmotic flow is generated at asymmetric conducting posts.
  • a conductive post placed in an AC or a DC applied fields with broken fore-aft or left-right symmetry generally produce net electro-osmotic pumping along the direction of broken symmetry. Therefore, it is possible to produce linear channel pumps using conductive posts, which possess broken asymmetry.
  • breaking symmetry with respect to the conducting array is achieved using triangular conductive posts.
  • the applied field can either be along the direction of the channel or across the channel, perpendicular to it.
  • electro-osmotic flows are generated by posts with symmetry broken in the channel direction, and an AC or DC field directed along or across the microchannels.
  • Other broken symmetry conducting posts such as conducting posts having a cross-section of a tear-drop or triangle, dielectric or metallic partial coatings, zig-zag or wavy shape, can also be used.
  • the sharpest point of the cross section of the post is directed opposite to the desired flow direction of induced-charge electro-osmotic pumping.
  • the sharpest point of the cross section is directed in the desired direction of induced- charge electro-osmotic pumping.
  • Another embodiment for preparing posts may be to simply place two or more wires of different cross sections against each other to approximate a triangle shape. In this way, an AC electro-osmotic linear-channel pump can be built out of ordinary metal micro-wires of circular cross- section.
  • asymmetric posts can be arranged in extended arrays to provide the distributed forcing needed to drive fluid quickly along lengthy channels.
  • asymmetric conducting posts are of cylindrical shape and are covered with a dielectric or metallic coating.
  • the coatings of the conducting posts are directed opposite the flow direction, in an AC or DC field directed along the microchannel.
  • the conducting posts produces flows that are directed in along the field axis and out perpendicular to the field axis, providing a unique mixing pattern.
  • the asymmetric shape of the conductive posts provides the necessary force to pump fluid through a microchannel. In some embodiments any broken symmetry will facilitate the production of a pump/mixer.
  • the conductive posts are shaped as asymmetric metal ridges patterned on the walls of a microchannel between the electrodes.
  • the electrodes allow reversing their polarities and producing AC or DC fields.
  • the asymmetric ridges are designed to lean in the direction of the flow, in an AC or DC field directed along the microchannel.
  • the surface of the asymmetric ridges is a grooved metallic surface, not connected in any way to the external circuit, which includes normal electrodes positioned in the channel walls on either side of the grooved surface.
  • the conductive post or element is an array of conductive posts or elements, as will be appreciated by one skilled in the art. Some embodiments of arrays of such elements are described hereinabove.
  • the arrays may comprise a lattice, which may have a variety of geometries, such as a square, hexagon, etc., as will be appreciated by one skilled in the art. Such orientation or arrays may be particularly useful in the micromixers of this invention.
  • a single unit functions as both micropump and micromixer, as will be appreciated by one skilled in the art.
  • the term "mixing" as used herein refers to circulation of materials to promote their distribution in a volume of space, for example, a mixture of 2 species, in a device of this invention, refers, in one embodiment, to a random distribution of the 2 species within a given volume of space of the device, e.g., in a microchannel of the devices of this invention.
  • the term “circulation” and “mixing” are interchangeable.
  • mixing refers to a change in a particular distribution which is not accompanied by agitation of the sample, in one embodiment, or in another embodiment, minimal agitation and/or formation of "bubbles" in the liquid medium in which the species are conveyed.
  • the conductive post or element may be fashioned to assume a variety of geometries, as described and exemplified herein. In one embodiment, such design will reflect a consideration of a desired trajectory for a particular application. In some embodiments, the geometry may approximate an arrowhead, a teardrop, or elliptical shape, or one related thereto.
  • this invention provides a method of mixing a fluid, the method comprising applying a fluid to a device of this invention and selectively applying voltage to the at least series of electrodes contained therein, such that the voltage is not simultaneously or commensurately applied to the two series whereby upon selective application of the voltage to the series, electro-osmotic flows with varied trajectories are generated in a region proximal to each of the series, resulting in mixing of the electrolyte fluid.
  • a series of electrodes are so positioned, that when voltage is applied thereto, a dominant electroosmotic flow is generated, which drives the mixed electrolyte fluid across the chamber.
  • modulation of such application of voltage is such that electro-osmotic flows with varied trajectories result, which mix an introduced fluid, following which, via selective modulation of such electrodes, a dominant flow is created to convey the mixed fluid to a desired location within the device, or to exit the device.
  • this invention provides a method of mixing a fluid, comprising applying a fluid to a device or an apparatus of this invention.
  • the invention provides methods, devices and apparatuses for mixing or stirring fluid in a fixed chamber, and may optionally provide for long range pumping down a channel of a device of this invention.
  • stirring may be applied in a multitude of applications, including any of the methods as described herein, or other applications, readily appreciated by one skilled in the art.
  • such methods, devices and apparatuses may find application in bioassays, and may, for example, impart greater speed or sensitivity to such assays.
  • such methods, devices and apparatuses may find application in the construction, probing or assay of DNA arrays, in a fixed chamber, or in another embodiment, in a microfluidic loop arrangement and may, for example, impart greater speed or sensitivity to such assays, allow for smaller sample or probe quantities for such assay, or other advantages apparent to one in the art.
  • the terms “mixing” or “circulating” are to be understood as interchangeable.
  • "circulating" or “mixing" capabilities of the methods, devices and apparatuses of this invention may involve arrangement of the electrodes such that flow over the electrodes impinges on a wall of the channel, resulting in greater mixing.
  • "circulating" or “mixing” capabilities of the methods, devices and apparatuses of this invention may further promote increased diffusion of molecular species or decrease the distance over which diffusion must act, or in some emobidments, eliminate concentration variations in a fluid. Such an effect may reduce the rate of dispersion along the flow by carrying unit volumes of the fluid between fast and slow moving regions. In net effect, i.e., as the fluid progresses through the mixing apparatus, the mixing of the fluid or fluids is increased as the diffusion area is increased and, consequently, the time required to achieve mixing to a desired homogeneity is reduced. [00192] In some embodiments, the methods, devices and apparatuses of this invention may circulate fluid in a "closed box" where fluid is injected into the device by any means known in the art and mixed therein.
  • the term "mixing" refers to fluid in the devices/apparatuses of the invention having at least two varied trajectories, upon applying voltage to a respective series of electrodes.
  • the devices/apparatuses of the invention promote flow along at least one trajectory that effectively stirs the fluid, circulates the fluid, or a combination thereof.
  • the invention provides devices/apparatuses/methods for circuiting/mixing a fluid over a target surface with a bound reagent, or in other embodiments, circulates a fluid having a reagent that specifically fluorescently labels analytes that are bound to that surface, which may be assessed via optical means, or in some embodiments, the surface is so constructed so as to detect changes in gate voltage on a transistor structure when an analyte or reagent binds, and when binding creates electrical, conducting, or semiconducting connections between two electrodes on the surface.
  • Such applications may find use in the methods of this invention, as described herein, and as will be appreciated by one skilled in the art.
  • this invention provides for analysis, detection, concentration, processing, assay, production of any material in a microfluidic device, whose principle of operation comprises electro-osmotically driven fluid flow, for example, the incorporation of a source providing an electric field in a microchannel of the device, and provision of an electrokinetic means for generating fluid motion whereby interactions between the electric field and induced-charge produce electro-osmotic flows, and wherein the electric field is supplied as a function of application of voltage to a series of electrodes arranged in the device, whereby flow in the region proximal to the series is such that flow proximal to a first series has a varied trajectory from that proximal to a second series.
  • Such flows may in turn, find application in mixing of materials, and optionally fluid conductance, and any application which makes use of these principles is to be considered as part of this invention, representing an embodiment thereof.
  • the invention provides methods for circulating fluid in a microfluidic cavity, comprising applying the fluid to a device comprising two or more series of electrodes connected to a source wherein each electrode in each series has stepped or recessed features, which in some embodiments, produces a flow, which has a nonzero component directed toward a boundary of a channel in the device.
  • a device comprising two or more series of electrodes connected to a source wherein each electrode in each series has stepped or recessed features, which in some embodiments, produces a flow, which has a nonzero component directed toward a boundary of a channel in the device.
  • such devices and methods of their use allow for the conveyance of, inter alia, cells, analytes, antibodies, antigens, DNA, polymers, proteins in solution, and others over a desired surface, for example, a detection surface.
  • a capture antibody, or cross-linking agent, or enzyme in solution is applied to such device, and is conducted such that these reagents come into contact with the desired surface.
  • a portion of the device optically transparent, or facilitates optical detection of a label, which may be incorporated in the agents or reagents as described herein, to facilitate detection.
  • at least a portion of the device may be transparent at a wavelength corresponding to excitation and emission for a fluorescent tag, which may be coupled to a reagent or compound in the fluids applied to the device.
  • the device may be constructed to comprise non-transparent sections, to minimize or abrogate photobleaching of sensitive reagents.
  • the method further comprises assay or analysis of the fluid, and in on embodiment, the analysis is a method of cellular analysis.
  • the method comprises the steps of: a. introducing a buffered suspension comprising cells and a reagent for cellular analysis into the microfluidic chamber; and b. analyzing at least one parameter affected by contact between the suspension and the reagent.
  • the reagent is an antibody, a nucleic acid, an enzyme, a substrate, a ligand, or a combination thereof.
  • the reagent is coupled to a detectable marker.
  • the marker is a fluorescent compound, and in another embodiment the device is coupled to a fluorimeter or fluorescent microscope.
  • the method of mixing a fluid further comprises the step of introducing a cellular lysis agent to the device.
  • the reagent specifically interacts or detects an intracellular compound
  • a secondary reagent may also be present in addition to the lysing agent for facilitating further analysis or manipulation of the cells.
  • the surface of the microchannel may be functionalized to reduce or enhance adsorption of species of interest to the surface of the device.
  • the surface of the microchannel has been functionalized to enhance or reduce the operation efficiency of the device.
  • the assay or analysis of the fluid is a method of analyte detection or assay. According to this aspect and in one embodiment, the method further comprises the steps of: a. introducing an analyte to the device; b. introducing a reagent to the device; and c. detecting, analyzing, or a combination thereof, of the analyte
  • mixing reconstitutes a compound in the device, upon application of the fluid, and in one embodiment, the compound is solubilized slowly in fluids.
  • the device is further modified to contain an active agent in the microchannel, or in another embodiment, the active agent is introduced via an inlet into the device, or in another embodiment, a combination of the two is enacted.
  • the microchannel is coated with an enzyme at a region wherein molecules introduced in the inlet will be conveyed past, according to the methods of this invention.
  • the enzyme such as, a protease
  • the enzyme may come into contact with cellular contents, or a mixture of concentrated proteins, and digest them, which in another embodiment, allows for further assay of the digested species, for example, via introduction of a specific protease into an inlet which conveys the enzyme further downstream in the device, such that essentially digested material is then subjected to the activity of the specific protease.
  • a specific protease into an inlet which conveys the enzyme further downstream in the device, such that essentially digested material is then subjected to the activity of the specific protease.
  • any number of other reagents may be introduced, such as an antibody, nucleic acid probe, additional enzyme, substrate, etc.
  • processed sample is conveyed to a separate analytical module.
  • the digestion products may, in another embodiment, be conveyed to a peptide analysis module, downstream of the device.
  • the amino acid sequences of the digestion products may be determined and assembled to generate a sequence of the polypeptide.
  • the peptide Prior to delivery to a peptide analysis module, the peptide may be conveyed to an interfacing module, which in turn, may perform one or more additional steps of separating, concentrating, and or focusing.
  • the microchannel may be coated with a label, which in one embodiment is tagged, in order to identify a particular protein or peptide, or other molecule containing the recognized epitope, which may be a means of sensitive detection of a molecule in a large mixture, present at low concentration.
  • reagents may be incorporated in the buffers used in the methods and devices of this invention, to enable chemiluminescence detection.
  • the method of detecting the labeled material includes, but is not limited to, optical absorbance, refractive index, fluorescence, phosphorescence, chemiluminescence, electrochemiluminescence, electrochemical detection, voltametry or conductivity. In some embodiments, detection occurs using laser-induced fluorescence, as is known in the art.
  • the labels may include, but are not limited to, fluorescent lanthanide complexes, including those of Europium and Terbium, fluorescein, fluorescamine, rhodamine, tetramethylrhodamine, eosin, erythrosin, coumarin, methyl-coumarins, pyrene, Malacite green, stilbene, Lucifer Yellow, Cascade BlueTM, Texas Red, l,l'-[l,3-propanediylbis[(dimethylimino-3,l- propanediyl]]bis[4-[(3-methyl-2(3H)-benzoxazolylidene)methyl]]-,tetraioide, which is sold under the name YOYO-I, Cy and Alexa dyes, and others described in the 9th Edition of the Molecular Probes Handbook by Richard P.
  • fluorescent lanthanide complexes including those of Europium and Terbium, fluorescein, fluorescamine,
  • Labels may be added to 'label' the desired molecule, prior to introduction into the devices of this invention, in some embodiments, and in some embodiments the label is supplied in a microfluidic chamber.
  • the labels are attached covalently as is known in the art, or in other embodiments, via non- covalent attachment.
  • photodiodes confocal microscopes, CCD cameras, or photomultiplier tubes maybe used to image the labels thus incorporated, and may, in some embodiments, comprise the apparatus of the invention, representing, in some embodiments, a "lab on a chip” mechanism.
  • the apparatus may further comprise a light source, detector, and other optical components to direct light onto the microfluidic chamber/chip and thereby collect fluorescent radiation thus emitted.
  • the light source may comprise a laser light source, such as, in some embodiments, a laser diode, or in other embodiments, a violet or a red laser diode.
  • VCSELs, VECSELs, or diode-pumped solid state lasers may be similarly used.
  • a Brewster's angle laser induced fluorescence detector may be used.
  • one or more beam steering mirrors may be used to direct the beam to a desired location for detection.
  • a solution or buffered medium comprising the molecules for assay are used in the methods and for the devices of this invention.
  • such solutions or buffered media may comprise natural or synthetic compounds.
  • the solutions or buffered media may comprise supernatants or culture media, which in one embodiment, are harvested from cells, such as bacterial cultures, or in another embodiment, cultures of engineered cells, wherein in one embodiment, the cells express mutated proteins, or overexpress proteins, or other molecules of interest which may be thus applied.
  • the solutions or buffered media may comprise lysates or homogenates of cells or tissue, which in one embodiment, may be otherwise manipulated for example, wherein the lysates are subject to filtration, lipase or collagenase, etc., digestion, as will be understood by one skilled in the art.
  • processing may be accomplished via introduction of the appropriate reagent into the device, via, coating of a specific channel, in one embodiment, or introduction via an inlet, in another embodiment.
  • any complex mixture comprising two or more molecules, whose assay is desired, may be used for the methods and in the devices of this invention, and represent an embodiment thereof.
  • the mixing results in high-throughput, multi-step product formation.
  • the method f mixing further comprises the steps of: a. introducing a precursor to the device; b. introducing a reagent, catalyst, reactant, cofactor, or combination thereof to the device; c. providing conditions whereby the precursor is converted to a product; and d. optionally, collecting the product from the device.
  • the method further comprises carrying out iterative introductions of the reagent, catalyst, reactant, cofactor, or combination thereof in (b), to the device.
  • the reagent is an antibody, a nucleic acid, an enzyme, a substrate, a ligand, a reactant or a combination thereof.
  • the mixing results in drug processing and delivery.
  • the method further comprises the steps of: i. introducing a drug and a liquid comprising a buffer, a catalyst, or combination thereof to the device; ii. providing conditions whereby the drug is processed or otherwise prepared for delivery to a subject; and iii. collecting the drug, delivering the drug to a subject, or a combination thereof.
  • the method further comprises the step of carrying out iterative introductions of liquid to the device. In one embodiment, introduction of the liquid serves to dilute the drug to a desired concentration.
  • the term "drug processing" refers to reconstitution of a drug, altering a drug, modifying a drug, or any preparation desired to prepare a drug or composition for administration to a subject.
  • the invention provides devices preloaded with a compound, for example a lyophilized drug, which is packaged and distributed as such, under sterile conditions.
  • a fluid is introduced into such a device, and the drug or other compound contained therewithin is reconstituted or diluted or processed, in some embodiments, just prior to delivery to a subject, or for any period of time, or for storage, etc.
  • Metabolic processes and other chemical processes can involve multiple steps of reactions of precursors with an enzyme, or catalyst, or mimetic, etc., in some embodiments, with or without the involvement of cofactors, in other embodiments, to obtain specific products, which in turn are reacted, to form additional products, etc., until a final desired product is obtained.
  • the devices and/or methods of this invention are used for such a purpose.
  • such methodology enables use of smaller quantities of reagents, or precursors, which may be limiting, in other embodiments, wherein such methodology enables isolation of highly reactive intermediates, which in turn may promote greater product formation.
  • such methodology enables greater sensitivity of detection, as well, and use of lesser quantity of compound and/or reagent, due to enhanced mixing of the same. It will be apparent to one skilled in the art that a means for stepwise, isolated or controlled synthesis provides many advantages, and is amenable to any number of permutations.
  • the modulated induced-charge electroosmotic devices of this invention circulate solutions containing probe molecules over target surfaces.
  • the probe may be any molecule, which specifically interacts with a target molecule, such as, for example, a nucleic acid, an antibody, a ligand, a receptor, etc.
  • the probe will have a moiety which can be chemically cross-linked with the desired target molecule, with reasonable specificity, as will be appreciated by one skilled in the art.
  • a microchannel of the device may be coated with a mixture, lysate, sample, etc., comprising a target molecule of interest.
  • such a device provides an advantage in terms of the time needed for assay, the higher sensitivity of detection, lower concentration of sample/reagents needed, since the sample may be recirculated over the target surface, or combination thereof.
  • the second liquid serves to dilute the drug to a desired concentration.
  • the device comprises valves, positioned to regulate fluid flow through the device, such as, for example, for regulating fluid flow through the outlet of the device, which in turn prevents depletion from the device, in one embodiment.
  • the positioning of valves provides an independent means of regulating fluid flow, apart from a relay from signals from the subject, which stimulate fluid flow through the device.
  • this invention provides a device for use in drug delivery, wherein the device conveys fluid from a reservoir to an outlet port.
  • drug delivery according to this aspect of the invention enables mixing of drug concentrations in the device, or altering the flow of the drug, or combination thereof, or in another embodiment, provides a means of continuous delivery.
  • a device may be implanted in a subject, and provide drug delivery in situ.
  • such a device may be prepared so as to be suitable for transdermal drug delivery, as will be appreciated by one skilled in the art.
  • the fast mixing is accomplished by modulating the action of two or more electrokinetic pumps in time.
  • the invention involves nonlinear electrokinetic devices for rapid three- dimensional mixing by chaotic advection in a confined microchamber.
  • the devices contain two or more arrays of electrodes, for example, as designated by (1-10) in figure 1, which comprise electrode-array pumps, such as (but not limited to) those illustrated in Figure 1.
  • Each electrode array is positioned so that it drives nonlinear electrokinetic flow in a different direction from at least one of the others.
  • the set of arrays is thus capable of producing at least two different convection patterns within the microchamber.
  • an array of electrodes is so positioned to give the desired effect.
  • the array of electrodes asymmetric planar electrodes in each period ( Figure IA), while in another embodiment, the array comprises modulating surface height of the electrodes, e.g. via secondary electroplating steps, etc. on even symmetric electrode arrays, or in some embodiments, stepped 3D electrode arrays enable efficient, unidirectional pumping over the array for a wide range of operating conditions (voltage, frequency, concentration, etc.) with non-planar, stepped 3D electrodes (Figure IB), 3D stepped electrodes with non-polarizable side walls (Figure 1C) or general 3D electrodes with raised metal or non-polarizable structures on an underlying pattern (Figure ID).
  • the nonlinear electrokinetic flows over the electrode arrays are modulated in time, in coordination with each other, so as to achieve efficient mixing of the bulk fluid and/or efficient transport of particles to a detection site or sites in the microchamber.
  • Fast chaotic mixing by electrokinetic pump modulation relies, in some embodiments, on: (i) the local time-averaged pumping velocity increasing with the magnitude of the applied voltage, typically as voltage squared.
  • two or more electrokinetic pumps operating in different directions are turned on and off either at specific intervals, or in another embodiment, at set patterns, or in another embodiment, randomly to mix the fluids applied to devices comprising the electrokinetic pumps.
  • the electrode arrays 2-10 and 2-20 cover opposite surfaces of the microchamber 2-30 and are oriented at right angles.
  • the AC voltage to each array is modulated by out of phase signals, so that the system alternates between two flow states, 2-10 on / 2-20 off and 2-10 off / 2-20 on, as shown.
  • the two electrode arrays 2-10 and 2-20 are placed on the same wall of the microchamber, again oriented in perpendicular directions, switching between the states 2-10 on / 2-20 on and 2-10 off / 2- 20 off .
  • Array 2-10 remains on at all times with a constant, unmodulated AC voltage, driving a steady convection roll in one direction, concurrent with array 2-20 being switched between on and off states by modulation of its AC voltage, leading to different, spiral convection patterns during the "on" state.
  • the electrode arrays only occupy one wall of the microchamber, the other walls, especially the large, flat opposite wall, can be used for other purposes, such as distributing surface sites for detecting particles or cells suspended in the fluid, e.g. in protein immunoassays or DNA microarrays.
  • Figure 3 where four electrode arrays (3-10)-(3-40) are placed in a confined microchamber (3-50).
  • the fluid can be introduced into the microchamber from an inlet microchannel using nonlinear electrokinetic flow over one or more of the electrode series.
  • this invention provides for temporal modulation of the magnitude or frequency of the voltages applied to each of two or more pumps (e.g. in a series) so as to effectively turn them on and off at different times. In some embodiments, this modulation of the voltage is much slower than the operating AC frequency of each pump, so that each pump has time to generate a quasi-steady flow in its particular direction prior to switching.
  • the modulation may be random, or in some embodiments, the modulation may be accomplished via the use of a digital/sudden switch turning one off and the other on. In some embodiments, the modulation may be periodic and sinusoidal, at a lower frequency than the typical AC operating frequency of each pump.
  • the modulation which accomplishes the switching may involve the magnitude or frequency of the AC voltage applied to each of the two (or more) pumps. For example, the voltage of one can be lowered to turn it off, while the voltage of the other is raised to turn it on. In some embodiments, the frequency of one can lowered or raised out of the operating range, while the frequency of the other is brought into the operating range.
  • the switching may be accomplished by driving each pump with a voltage consisting of a product of two sinusoidal waveforms, one at the operating frequency and the other at the modulating frequency.
  • the modulating waveform (which provides a sinusoidal envelope for the magnitude of the AC voltage at the operating frequency) is phase shifted by 90 degrees (1/4 period) between one pump and the other, so that one is effectively on while the other is off, with the ability to control, in some embodiments, that switching is a smooth transition from one pump to the other, and not sudden.
  • the characteristic time scale for switching is comparable to the time for flow to circulate at least halfway around the vortex generated by the pump in the cavity. According to this aspect, and in one embodiment, the switching leads to stretching and folding in the two different pumping directions, which produces chaotic streamlines and very rapid mixing in the same way as the rolling of dough in a bakery.
  • the device is used for mixing multiple fluids in the cavity, or for dispersing molecules or colloidal particles suspended in a fluid.
  • the molecules can be efficiently and uniformly brought to detection sites on the non-pumping surfaces, as in DNA microarrays or other biological assays.
  • the convection produced by the mixer could quickly and thoroughly pass all molecules in solution all detection spots in the microarray, thereby reducing the detection time and increasing the sensitivity of the device, compared to the usual case of no flow, where the detection relies on bulk diffusion alone for transport to the surface.
  • advantages of using devices and apparatuses comprising the electrokinetic pumps of this invention include the ability to operate such devices at low, battery voltages (a few volts) and low power (milliwatts), while generating fast flows, up to mm/sec.
  • Another advantage of using devices and apparatuses comprising the electrokinetic pumps of this invention is that such pumps may be easily and cheaply constructed by a variety of microfabrication methods.
  • mixing in a continuous flow along a microfluidic channel is achieved using electrode arrays positioned and activated in time as shown in Figure 3 to drive flows transverse to the channel axis.
  • FIG 4A two opposite walls of the channel are lined with the four electrode arrays (4-10)-(4-40) for mixing in steady flow.
  • the electrodes need not be positioned in parallel strips, but form any desired pattern, for example, a wavy or herringbone pattern, to further enhance mixing.
  • the mixing section of the channel has a larger cross section to slow down the fluid, causing it to spend more time inside the mixer before proceeding downstream.
  • the devices/methods of this invention allow for trapping, pumping and mixing of materials in a fluid sample ( Figure 5).
  • selective trapping, pumping, and mixing of a fluid or suspension of particles may be accomplished.
  • a periodic pattern of electrode arrays (5-10), (5-20) is positioned along at least one wall of a microchannel (5-30), which drive flows in alternating directions when turned on.
  • both sets 5-10 and 5-20 are activated at once as in Fig 5A, the opposing flows form closed convection cells to trap fluid and/or position particles above each array.
  • a net flow is driven in one direction, which disperses and transports the trapped fluid or particles. (Hydrodynamic dispersion results from nonuniform slip flows.)
  • a similar flow is driven in the opposite direction.
  • temporally modulating the sets of electrodes e.g. by switching between states 5A, 5B, and/or 5C, rapid chaotic mixing can be achieved.
  • Net pumping can in a desired direction be achieved at the same time as mixing by tuning the fraction of the time and/or magnitude of the flow (via the voltage) from set 5-10 versus set 5-20.
  • each series may be modulated such that the magnitude, frequency or combination thereof of the voltage applied to each series is varied to maximize chaotic mixing.
  • a signal generator may be used to operate the respective array of pumps at various AC.
  • Modulation may further comprise a step whereby once the material has been mixed for a desired period of time, the fluid is conveyed in a desired dominant direction.
  • Figure 6 in a similar device to that described for Figure 5, both sets of electrodes may be so modulated so as to drive flows in the same direction.
  • each set also may optionally include a shifted mirror image pattern on the opposite wall of the channel (e.g. array 6-10 vs. array 6-20 in figure 6).
  • a shifted mirror image pattern on the opposite wall of the channel (e.g. array 6-10 vs. array 6-20 in figure 6).
  • this invention provides devices/methods including modulated devices comprising ICEO-driven microfluidic pumps comprising polarizable surfaces.
  • Figure 7 shows the general concept modulating the voltage of two or more electrodes on opposite sides of a microchannel containing an array of one or more polarizable (typically metallic or metal coated) posts, which may have symmetric and/or asymmetric arrangements and cross sections. Applying a steady AC voltage between an opposing pair of electrodes such as 7-10 and 7-30 or 7-20 and 7-40 to cause mixing driven by induced- charge electro-osmotic flows around the polarizable structures (such flows can also cause transverse pumping due to broken left-right symmetry) can be extended to incorporate time-modulated AC voltages.
  • polarizable typically metallic or metal coated
  • the dominant AC voltage can switch from being between 7-10 and 7-30 to 7-20 and 7-40.
  • One way to control such switching is to apply an AC voltage to each electrode, (7-10)-(7-40), and give each a tunable phase shift relative to the others.
  • 7-10 and 7-20 have zero phase shift (same AC voltage) while 7-30 and 7-40 have a half-period phase shift (same AC voltage, opposite of 7-10 and 7-20); this is equivalent to having simply two larger electrodes on opposite sides of the channel applying a uniform transverse (up/down) AC field.
  • a second state 7-10 and 7-30 have zero phase shift, while 7-30 and 7-40 have a half-period phase shift; this is equivalent to imposing a primarily longitudinal (left/right) AC field.
  • rapid chaotic mixing can be achieved in the channel around the posts.
  • the mixing can be superimposed on a background pressure- driven flow through the post array.
  • broken symmetry in the geometry of the post array leads to time-modulated pumping through the channel, along with the time-modulated mixing.
  • the devices will comprise more than one polarizable post .
  • Figure 8 depicts another embodiment of the invention, where the polarizable posts (8-50) and (8-60) are placed in a microfluidic chamber with at least four electrodes placed on different walls, to allow for application of dominant electric fields in orthogonal directions, e.g. left/right using electrodes 8-20 and 8-40, or up/down using electrodes 8-10 and 8-30.
  • the same sort of time modulation strategies can be used to achieve chaotic mixing in the chamber.
  • the switching time should be comparable to the convection time for the dominant fluid vortices amongst the array of posts.
  • each series may be modulated such that the magnitude, frequency or combination thereof of the voltage applied to each series is to maximize chaotic mixing.
  • Modulation in this aspect may further comprise a step whereby once the material has been mixed for a desired period of time, the fluid is conveyed in a desired dominant direction.

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Abstract

Cette invention porte sur des dispositifs et sur des appareils les comprenant, pour un mélange efficace de volumes relativement petits de fluide et de matériaux en suspension dans le fluide. Ces dispositifs utilisent une électrocinétique non linéaire comme mécanisme principal pour entraîner un écoulement de fluide, et un tel écoulement est modulé de façon à favoriser un mélange chaotique. L'invention porte également sur des procédés d'analyse cellulaire et sur la formation de produit à étape multiple et à haut débit de production à l'aide de dispositifs selon cette invention.
PCT/US2009/053574 2008-08-12 2009-08-12 Dispositifs microfluidiques électro-osmotiques à charge induite WO2010019684A2 (fr)

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JP2012187553A (ja) * 2011-03-14 2012-10-04 Canon Inc 流体混合装置
EP3646021A4 (fr) * 2017-06-29 2021-03-31 Technion Research & Development Foundation Limited Dispositifs et procédés pour commander un flux à l'aide d'un flux électro-osmotique
WO2021156319A1 (fr) * 2020-02-03 2021-08-12 Vrije Universiteit Brussel Inducteur de tourbillon de silicium sur isolant structuré sur puce
EP4202431A1 (fr) * 2021-12-23 2023-06-28 Imec VZW Dispositif de mise au point de gradient de champ électrique

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US20030006140A1 (en) * 2001-02-28 2003-01-09 Giacomo Vacca Microfluidic control using dielectric pumping
US20050129526A1 (en) * 2003-12-10 2005-06-16 Dukhin Andrei S. Method of using unbalanced alternating electric field in microfluidic devices
US20070240989A1 (en) * 2001-12-18 2007-10-18 Jeremy Levitan Microfluidic pumps and mixers driven by induced-charge electro-osmosis
US20070267292A1 (en) * 2003-07-21 2007-11-22 Eksigent Technologies Llc Bridges for electroosmotic flow systems
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US20020144895A1 (en) * 2001-02-15 2002-10-10 Caliper Technologies Corp. Methods and systems for enhanced fluid delivery of electrical currents to fluidic systems
US20030006140A1 (en) * 2001-02-28 2003-01-09 Giacomo Vacca Microfluidic control using dielectric pumping
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US20070267292A1 (en) * 2003-07-21 2007-11-22 Eksigent Technologies Llc Bridges for electroosmotic flow systems
US20050129526A1 (en) * 2003-12-10 2005-06-16 Dukhin Andrei S. Method of using unbalanced alternating electric field in microfluidic devices
US20080000772A1 (en) * 2006-02-02 2008-01-03 Bazant Martin Z Induced-charge electro-osmotic microfluidic devices

Cited By (4)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JP2012187553A (ja) * 2011-03-14 2012-10-04 Canon Inc 流体混合装置
EP3646021A4 (fr) * 2017-06-29 2021-03-31 Technion Research & Development Foundation Limited Dispositifs et procédés pour commander un flux à l'aide d'un flux électro-osmotique
WO2021156319A1 (fr) * 2020-02-03 2021-08-12 Vrije Universiteit Brussel Inducteur de tourbillon de silicium sur isolant structuré sur puce
EP4202431A1 (fr) * 2021-12-23 2023-06-28 Imec VZW Dispositif de mise au point de gradient de champ électrique

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