Patent Application
20070113907
The invention relates generally to devices and methods that use fluid-transporting features of differing fluid dwell times. In particular, the invention relates to fluidic devices and methods that use fluid-transporting features of differing dwell times to produce an output stream that exhibits at least one desired characteristic, e.g. a concentration gradient, which in turn may be exploited for applications such microfluidic separation.
Analysis of a fluid sample often involves separating the sample into its constituents. For example, liquid chromatography (LC) separation typically involves employing a mobile phase to convey a multiconstituent sample past surfaces of a stationary phase, e.g., separation media. The speed at which any sample constituent travels past the stationary phase depends on its partition between mobile phase and stationary phase.
Separation performance can vary according to the stationary phase used. In reverse phase liquid chromatography, for example, wherein sample constituents are separated according to their hydrophobicity, a stationary phase is provided having hydrophobic surfaces. A mobile phase, e.g., a mixture of water and organic solvent, is also provided. As the sample is conveyed past the stationary phase by the mobile phase, the least hydrophobic sample constituents will tend to travel past the stationary phase first, followed by constituents with increasing hydrophobicity.
Separation performance can vary according to the mobile phase employed in LC. Typically, the mobile phase exhibits at least one desired characteristic keyed for separation performance. For example, isocratic LC employs a mobile phase having a constant composition over time. In contrast, gradient LC employs a mobile phase that exhibits a varying composition during separation.
In general, gradient LC offers a number of advantages over isocratic LC. For example, gradient LC is well suited to separation a wide range of compounds with high speed and resolution. In addition, the composition of the mobile phase may be controllably varied, e.g., to exhibit a concentration gradient, so as to trap certain sample components at an upstream portion of the stationary phase, thereby allowing interfering compounds such as salts to be washed away. As a result, gradient LC allows of injection of large sample volumes without compromising separation efficiency and is well-suited for analysis of low concentration samples.
Microfluidic techniques have been successfully used to carry out gradient LC. For example, an integrated microfluidic LC device is described in U.S. Patent Application Publication No. 2003/0017609 to Yin et al. Such microfluidic devices may be formed as a lab-on-a-chip from a substrate and a cover plate that incorporate a plurality of functionalities e.g., sample injection, separation and flow switching, on a single integrated device. Since microfluidic technologies generally involve the use of small volumes of fluids, microfluidic technologies are particularly desirable in applications that involve fluids that are extremely rare and/or expensive.
Accordingly, there is a need for smooth gradients for microfluidic applications. It is not, however, a trivial matter to produce and deliver a mobile phase that exhibits a gradient at an appropriate flow rate for microfluidic applications. For example, when a mobile phase is required that exhibits a concentration gradient of two compositionally different fluids, e.g., a first fluid and a second fluid, the fluids may be mixed in a manner such that the ratio of the first and second fluids are changed over time. In such a case, two pumps may be used to pump the two fluids independently. However, conventional LC pumps typically perform well only within a certain flow-rate range, generally above 1 μl/min. Accordingly, when a linear gradient of the first and second fluids is desired, one of the two pumps may have to convey fluid at a much lower flow-rate than the combined flow-rate, sometimes out of the optimum flow-rate range of the pump.
One way in which a fluid may be delivered by a pump at a rate lower than its optimum flow rate is operate the pump at its optimum flow rate but to divert excess fluid flow. For example, fluid conveyed by a LC pump may be split into a plurality of streams. Some of the streams are delivered while the other streams are not. In such a case, however, diverted fluid represents a source of potential waste.
In addition, it is not a trivial matter to produce and deliver a mobile phase having a concentration gradient at a low flow rate without an excessive delay time. Delay time is total time it takes to generate a mobile phase having a concentration gradient and to deliver the mobile phase. To generate a concentration gradient in a mobile phase, mixing of compositionally different fluids is required. Such mixing typically involves equipment that requires a volume of the different fluids for operability. Thus, for example, in a system that includes a conventional LC pump, a pressure damper, and mixer having a combined, the delay time may be equal to the quotient of the combined volume and the flow-rate. Since the delay time is inversely proportional to the flow rate, an excessively low flow rate will result in an excessively high delay time.
In any case, numerous publications and patents describe gradient generation technologies. Exemplary publications include: Dentinger, S. (2001), “Generation of gradients having complex shapes using microfluidic networks,” Analytical Chemistry, 72:1240-46; Deguchi et al. (2004), “Nanoflow gradient generator for capillary high-performance liquid chromatography,” Analytical Chemistry, 76:1524-28; Xie et al. (2004), “An electrochemical pumping system for on-chip gradient generation,” Analytical Chemistry, 76:3756-63; Bihan et al. (2001), “Nanoflow Gradient Generator Coupled with μLC-ESI-MS/MS for Protein Identification,” Analytical Chemistry, 73:1307-15; U.S. Patent Application Publication No. 2003/0180449 to Wiktorowicz et al.; and U.S. Pat. No. 4,942,018 to Munk. Nevertheless, such technologies generally suffer from problems such as high waste, high complexity, low repeatability, and long delay times.
To overcome such problems, on-chip gradient generation and fluid introduction technologies have been proposed. For example, U.S. Pat. No. 6,702,256 to Killeen et al. describes a device that employs a slidably switchable valve for controlling microfluidic flow that may be used in an LC application. In addition, techniques for on-chip generation of a mobile-phase gradient using a network of channels are described in U.S. Patent Application Publication No. 2003/0159993 to Yin et al.
Nevertheless, there exist opportunities to provide alternatives and improved fluidic technologies to overcome the drawbacks associated with known techniques for producing and delivering a mobile phase.
The invention provides a fluidic device that includes a plurality of fluid-transporting features extending from a common inlet to a common outlet and a means for effecting fluid flow through the fluid-transporting features. The features are associated with differing fluid dwell times. The means for effecting fluid flow cooperates with the fluid-transporting features to merge fluids from the fluid-transporting features in a manner effective to produce an output stream from the common outlet that exhibits at least one desired characteristic generated as a result of the differing dwell times.
The fluid-transporting features may be varied in construction and/or arrangement. For example, the features may have substantially identical or different lengths, substantially identical and/or different cross-sectional area. In some instances, the features may be constructed in a manner that allows fluid flowing through each feature to exhibit a substantially identical flow rate. The features may be grouped in different stages wherein the features of the same stage have a substantially identical construction and the features of different stages have a different construction.
In some instances, at least one fluid-transporting feature may exhibit different cross-sectional areas between the inlet and outlet. For example, a fluid-transporting feature may include a flow restriction portion and a dwell-time controlling portion. The flow restriction portion may be upstream or downstream from the dwell-time controlling portion. These portions may vary in arrangement and construction as well
In some microfluidic embodiments, a plurality of substrates may also be provided, e.g., in a stack. For example, at least one fluid-transporting feature may be provided as a conduit defined at least in part by a channel located on an interior surface of the stack. When three or more substrates are provided, fluid-transporting features may be formed between any neighboring substrates of the stack.
The invention may be used with a plurality of fluid sources upstream from the inlet. A switching valve may be used to provide alternating communication between the inlet and any of the sources. When the fluids from the fluid sources are compositionally different, the invention may be used to produce an output stream exhibiting a desired concentration profile, e.g., a substantially linear gradient of the fluids.
The invention also provides a method for producing a fluid stream exhibiting at least one desired characteristic. The method involves providing a plurality of fluid-transporting features extending from a common inlet to a common outlet, wherein each fluid-transporting feature is associated with a differing fluid dwell time. Fluid is introduced into the common inlet, thereby effecting fluid flow through the fluid-transporting features, which, in turn, merges to produce an output stream from the common outlet. The output stream exhibits at least one desired characteristic generated as a result of the differing dwell times.
Typically, first and second fluids are introduced in succession into the common inlet so that the output stream exhibits a desired profile of the first and second fluids. For example, the first and second fluids are compositionally different such that the output stream exhibits a desired concentration profile of the first and second fluids as a mixture. Optionally, one or more additional fluids may be introduced, successively or in parallel, into the common inlet as well to produce an output stream that exhibits a desired profile of the fluids.
Before describing the present invention in detail, it is to be understood that the invention is not limited to specific separation devices or types of analytical instrumentation, as such may vary. It is also to be understood that the terminology used herein is for the purpose of describing particular embodiments only, and is not intended to be limiting.
In addition, as used in this specification and the appended claims, the singular article forms “a,” “an,” and “the” include both singular and plural referents unless the context clearly dictates otherwise. Thus, for example, reference to “a conduit” includes a plurality of conduit as well as a single conduit, reference to “substrate” includes a single substrate as well as a combination of substrates, and the like.
Furthermore, terminology indicative or suggestive of a particular spatial relationship between elements of the invention is to be construed in a relative sense rather an absolute sense unless the context of usage clearly dictates to the contrary. For example, the terms “over” and “on” as used to describe the spatial orientation of a second substrate relative to a first substrate does not necessarily indicate that the second substrate is located above the first substrate. Thus, in a device that includes a second substrate placed over a first substrate, the second substrate may be located above, at the same level as, or below the first substrate depending on the device's orientation. Similarly, an “upper” surface of a substrate may lie above, at the same level as, or below other portions of the substrate depending on the orientation of the substrate.
In this specification and in the claims that follow, reference will be made to a number of terms that shall be defined to have the following meanings, unless the context in which they are employed clearly indicates otherwise:
The term “dwell time” as used herein refers to the time it takes a fluid to flow through a fluid-transporting feature. In general, the dwell time of a fluid-transporting feature is a product of the volume of the feature and the volumetric flow rate of the fluid flowing through the feature. However, other factors may effect the dwell time as well and include the type of fluid flow (e.g., Pouseuille or electro-osmotic flow), any interactions between the fluid and the feature, the compressibility of the fluid, the used volume of the feature, and the like.
The term “flow path” as used herein refers to the route or course along which a fluid travels or moves. Flow paths may be formed from one or more fluid-transporting features of a microfluidic device.
The term “fluid-transporting feature” as herein refers to an arrangement of solid bodies or portions thereof that direct fluid flow. As used herein, the term includes, but is not limited to, capillaries, tubing, chambers, reservoirs, conduits and channels. The term “conduit” as used herein refers to a three-dimensional enclosure formed by one or more walls and having an inlet opening and an outlet opening through which fluid may be transported. The term “channel” is used herein to refer to an open groove or a trench in a surface. A channel in combination with a solid piece over the channel forms a conduit.
The term “fluid-tight” is used herein to describe the spatial relationship between two solid surfaces in physical contact such that fluid is prevented from flowing into the interface between the surfaces.
The prefix “micro” refers to items having dimensions on the order of micrometers or having volumes on the order of microliters. Thus, for example, the term “microfluidic device” refers to a device having features of micron or submicron dimensions, and which can be used in any number of processes, chemical or otherwise, involving very small amounts of fluid. Such processes include, but are not limited to, electrophoresis (e.g., capillary electrophoresis or CE), chromatography (e.g., μLC), screening and diagnostics (using, e.g., hybridization or other binding means), and chemical and biochemical synthesis (e.g., DNA amplification as may be conducted using the polymerase chain reaction, or “PCR ”) and analysis (e.g., through peptidic digestion). The features of the microfluidic devices are adapted to their particular use. For example, microfluidic devices that are used in separation processes, e.g., CE, may contain microchannels (termed “microconduits” herein when enclosed, i.e., when the second substrate is in place on the microchannel-containing first substrate surface) on the order of 1 μm to 200 μm in diameter, typically 10 μm to 75 μm in diameter, and approximately 0.1 to 50 cm in length. Microfluidic devices that are used in chemical and biochemical synthesis, e.g., DNA amplification, will generally contain reaction zones (termed “reaction chambers” herein when enclosed, i.e., again, when the second substrate is in place on the microchannel-containing first substrate surface) having a volume of about 1 nl to about 100 μl, typically about 10 nl to 20 μl. Other terms containing the prefix “micro,” e.g., “microfeature,” are to be construed in a similar manner.
The term “substantially identical” as used to describe a plurality of items is used to indicate that the items are identical to a considerable degree, but that absolute identicalness is not required. For example, when fluids are described herein as flowing through different fluid-transporting features at a “substantially identical flow rate,” the flow rates may be identical or sufficiently near identical such that any differences in the flow rates are trivial in nature. The terms “substantial” and “substantially” are used analogously in other contexts involve an analogous definition.
Thus, the invention generally relates fluidic devices and methods that employ a plurality of fluid-transporting features associated with differing fluid dwell times. The features typically have a common inlet and a common outlet. Typically, different fluids are introduced in succession into the common inlet but are split into different streams that travel along the different flow paths defined by the fluid-transporting features. The fluids from the different flow paths then merge to produce an output stream from the common outlet. The output stream exhibits at least one desired characteristic generated as a result of the differing dwell times of the fluids traveling therethrough.
The invention may be used in a number of different applications. For example, the invention may be used to generate an output stream having a desired characteristic such as pH, temperature, or viscosity profile. Typically, though, the invention is used to generate an output stream exhibits desired concentration gradient suitable for microfluidic separation applications. For example, when a first liquid, i.e., liquid A, is mixed with a second liquid of a different composition, i.e., liquid B, a different proportions over time form an output stream such that the output stream may exhibit a linear concentration gradient of liquid B over time that is well suited for use in gradient LC applications.
The first and second microchannels share a common inlet terminus 24 at their respective upstream ends. The first and second microchannels each terminate at their downstream ends at a mixing feature 20. As shown, the first microchannel 18A has a length that is about half of that of the second microchannel 18B. However, the microchannels 18A and 18B have a substantially identical cross-sectional shape, though identical cross-sectional microchannel shapes are not a requirement of the invention.
The microfluidic device 10 also includes a second substrate 40 that is complementarily shaped with respect to the first substrate 12 and has first and second substantially planar opposing surfaces indicated at 42 and 44, respectively. The second substrate 40 can be comprised of any suitable material for forming the first substrate 12 as described below. The contact surface 42 of the second substrate 40 is capable of interfacing closely with the contact surface 14 of the first substrate 12 to achieve fluid-tight contact between the surfaces. The second substrate 40 may include a variety of features. As shown, inlet 46 is provided as a conduit extending through the second substrate 40 in a direction orthogonal to the second substrate contact surface 42 to result in fluid communication between surfaces 42 and 44. Similarly, outlet 48 is provided as a conduit extending from surface 42 to surface 44.
The second substrate 40 is substantially immobilized over the first substrate contact surface 14. As a result, the second substrate contact surface 42 in combination with the first microchannel 18A defines the first conduit or first stage 19A. Similarly, the second substrate 40, in combination with the second microchannel 18B defines a second conduit or second stage 19B. Likewise, the second substrate 40, in combination with the mixing feature 20, forms a mixing chamber 21. Because the contact surfaces of the second substrate and the first substrate are in fluid-tight contact, conduits 19A and 19B as well as mixing chamber 21 are all generally fluid-tight.
Flow rates for conduits may be adjusted by changing their geometry (cross-sectional area, cross-sectional shape, and/or length) or flow resistance. The geometry of microchannels 18A and 18B may be chosen for both conduits to allow for through-flow of substantially identical fluids at substantially identical flow rates, even though the second conduit 19B is about twice as long as the first conduit 19A. While the conduits may have generally the same cross-sectional shape (rectangular, circular, etc.), the conduits do not have the same cross-sectional areas. In addition or in the alternative, the conduits may be constructed to provide flow rates that effect a desired final gradient profile. In any case, inlet 46 is located over the inlet terminus 24 and therefore fluidly communicates with each conduit. Similarly, outlet 48 is aligned the mixing feature 20 and therefore fluidly communicates with mixing chamber 21.
Accordingly, two different flow paths are formed in the microfluidic device 10. The first flow path extends from the inlet 46, through the first conduit 19A, through the mixing chamber 21, and to the outlet 48. The second flow path extends from the inlet 46, through the second conduit 19A, through the mixing chamber 21, and to the outlet 48. The mixing chamber 21 has a size and shape effective to provide sufficient mixing action between the fluids from the conduits 19A and 19B such that any output stream emerging from outlet 48 is provided as a substantially uniform mixture of the fluids. Optimally, the dwell time associated with the mixing chamber is small relative to the dwell time associated with the conduits 19A and 19B.
In
In
In
In operation, liquid A is introduced into the inlet 46 to fill all fluid-transporting features and to form an output stream from outlet 48 that includes merged fluids from the fluid-transporting features. Then liquid B may be introduced into inlet 46. Initially, the output stream will consist essentially of liquid A. After a short delay time to allow liquid B to travel through the shortest fluid-transporting feature 19A, liquid B will then start to flow out of the feature 19A at a first point in time, T1, to merge into the output stream out, thereby raising the percentage of liquid B contained in the output stream. After awhile, liquid B will start to flow out of the next shortest feature 19B at a second point in time, T2, again raising the percentage of liquid B in the output stream. As the features are successively filled in their entirety with liquid B, the percentage of liquid B in the output stream will increase at successive points in time, T3, T4, T5, and T6 at which liquid B flows out of features 19C, 19D, 19E, and 19F, respectively.
Although the invention does not require fluid-transporting features that have identical or substantially identical volumetric fluid flow rates, it is often more convenient to carry out the invention using such features. From a design perspective, identical or substantially identical volumetric flow rates make it easier to calculate dwell times. Identical or substantially volumetric flow rates are typically also desirable from a manufacturing perspective.
Identical volumetric flow rates for fluid-transporting features can be achieved by accounting for flow resistance of the features. In general, the volumetric flow rate for any fluid-transporting feature is the product of its length and flow resistance. Thus, to produce a fluid-transporting feature having a length, 2L that has the same flow rate as one having that has a length, L, one may have to produce the features such that the longer feature has a flow resistance that is half that of the shorter feature. Furthermore, when the features have the same cross-sectional shape but different lengths, the longer feature will typically require a larger effective cross-sectional area to ensure the same flow rate for both features.
Nevertheless, as suggested in
Thus, for embodiments of the invention that exhibit Pouseuille flow, the second fluid will start to flow out of the feature earlier than the dwell time that is implied solely by feature volume and fluid flow rate and the percentage of the second fluid flowing out will not be 100%. It will take longer than the implied time before 100% of the second fluid will be flowing out of the feature. In contrast, flow in a conduit that is based solely on electro-osmosis may have a dwell time based solely on the feature volume and the fluid flow rate. One of ordinary skill in the art will be able to account for such differences when employing the invention for a particular desired dwell times
In addition, the fluid-transporting features are shown arranged in three stages rather than six. For example, the first stage includes a single fluid-transporting feature 19A having a length L. The second stage includes two features 19B and 19C having a substantially shape and size, so as to have substantially identical fluid-conveying capabilities. The second stage 19B and 19C is twice as long as the feature 19A of the first stage. Similarly, the third stage includes three fluid-transporting features 19D-19F having substantially identical fluid-conveying capabilities and is thrice as long as feature 19A. Assuming that flow resistance for fluid-transporting features of the same cross-sectional area is proportional to the length of the features, the overall volumetric flow rate for each of the three stages should be substantially identical.
The gradient generator of
As discussed above, the volumetric flow rate for any fluid-transporting feature is generally the product of its length and flow resistance. Similarly, stages that include longer fluid-transporting features require a larger effective cross-section to provide a flow rate equal to stages that have shorter fluid-transporting features. Accordingly, for the inventive embodiment exemplified in
Accordingly, it may be difficult to produce an output stream exhibiting a linear concentration gradient of a particular fluid, e.g., liquid B, relative to another fluid, e.g., liquid A, over time using a multistage generator similar to that depicted in
Accordingly, an increasing number of stages generally lead to an asymptotic approach to an inverse parabolic profile of percent B output with respect to time. That is, an increase in the number of stages does not necessarily lead to an output stream with a linear gradient. A nonlinear gradient profile may be formed instead. In some instances, single stage devices may be more suited for forming an output stream with a linear gradient that a multi-stage device.
For
The different features of the invention described above may be combined in different ways. For example, certain features may be selected such that, given a particular input pressure or flow rate, a particular gradient profile can be generated. In addition, different modules may be designed to carry out different aspects of the invention. By selectively combined the different modules, it may be possible to produce output streams for any specific application.
Modules may be provided in the form of microfluidic devices, e.g., as shown and described in
The materials used to form the substrates of the microfluidic devices of the invention as described above are selected with regard to physical and chemical characteristics that are desirable for proper functioning of the microfluidic device. The substrate may be fabricated from a material that enables formation of high definition (or high “resolution ”) features, i.e., microchannels, chambers and the like, that are of micron or submicron dimensions. That is, the material must be capable of microfabrication so as to have desired miniaturized surface features.
Preferably, the substrate is capable of being microfabricated in such a manner as to form features in, on and/or through the surface of the substrate. This may be done using materials removal techniques, e.g., dry etching, wet etching, laser etching, laser ablation or the like. However, any material removal technique should be employed with care so as to avoid uncontrolled materials removal. For example careful selection of etch compositions and/or parameters may be required to avoid uncontrolled undercutting, that may accompany etching processes.
Microstructures can also be formed on the surface of a substrate by other techniques. For example, features may be molded and/or embossed on the surface of a substrate. In addition, additive techniques may be used. For example, microstructres may be formed by adding material to a substrate, e.g., using photo-imageable polyimide to form polymer channels on the surface of a glass substrate. Also, all device materials used should be chemically inert and physically stable with respect to any substance with which they come into contact when used to introduce a fluid sample (e.g., with respect to pH, electric fields, etc.).
Suitable materials for forming the present devices include, but are not limited to, polymeric materials, ceramics (including aluminium oxide and the like), glass, metals, composites, and laminates thereof In general, the terms “metallic,” “ceramic,” “semiconductor” and “polymeric” are used herein in their ordinary sense. For example, the term “metallic” generally describes any of a category of electropositive elements that usually have a shiny surface, are generally good conductors of heat and electricity, and can be formed into thin sheets or wires. Similarly, the term “semiconductor” is used to indicate any of various solid crystalline substances having electrical conductivity greater than insulators but less than good conductors. Exemplary semiconductors include elemental solids such as Si and Ge and compound semiconductors such as GaAs. The term “ceramic” is used to indicate to a hard, brittle, heat-resistant and corrosion-resistant dielectric material made typically made by heating an inorganic compound, e.g., single or mixed metal oxides such as aluminum, zirconium or silicon oxides, nitrides, and carbides, at a high temperature. A ceramic material may be single crystalline, multicrystalline, or, as in the case of glass, amorphous.
Polymeric materials are particularly preferred herein, and will typically be organic polymers that are homopolymers or copolymers, naturally occurring or synthetic, crosslinked or uncrosslinked. Specific polymers of interest include, but are not limited to, polyimides, polycarbonates, polyesters, polyamides, polyethers, polyurethanes, polyfluorocarbons, polystyrenes, polysulfones, poly(acrylonitrile-butadiene-styrene)(ABS), acrylate and acrylic acid polymers such as polymethyl methacrylate, and other substituted and unsubstituted polyolefins, and copolymers thereof In some instances, halogenated polymers may be used. Exemplary commercially available fluorinated and/or chlorinated polymers include polyvinylchloride, polyvinylfluoride, polyvinylidene fluoride, polyvinylidene chloride, polychorotrifluoroethylene, polytetrafluoroethylene, polyhexafluoropropylene, and copolymers thereof.
Generally, at least one of the substrates comprises a biofouling-resistant polymer when the microfluidic device is employed to transport biological fluids. Polyimide is of particular interest and has proven to be a highly desirable substrate material in a number of contexts. Polyimides are commercially available, e.g., under the tradename Kapton® (DuPont, Wilmington, Del.) and Upilex® (Ube Industries, Ltd., Japan). Polyetheretherketones (PEEK) also exhibit desirable biofouling resistant properties.
The devices of the invention may also be fabricated from a “composite,” i.e., a composition comprised of unlike materials. The composite may be a block composite, e.g., an A-B-A block composite, an A-B-C block composite, or the like. Alternatively, the composite may be a heterogeneous combination of materials, i.e., in which the materials are distinct from separate phases, or a homogeneous combination of unlike materials. As used herein, the term “composite” is used to include a “laminate” composite. A “laminate” refers to a composite material formed from several different bonded layers of identical or different materials. Other preferred composite substrates include polymer laminates, polymer-metal laminates, e.g., polymer coated with copper, a ceramic-in-metal or a polymer-in-metal composite. One preferred composite material is a polyimide laminate formed from a first layer of polyimide such as Kapton®., that has been co-extruded with a second, thin layer of a thermal adhesive form of polyimide known as KJ®, also available from DuPont (Wilmington, Del.).
The embodiments of the invention in the form of microfluidic devices can be fabricated using any convenient method, including, but not limited to, micromolding and casting techniques, embossing methods, surface micro-machining and bulk-micromachining. The latter technique involves formation of microstructures by etching directly into a bulk material, typically using wet chemical etching or reactive ion etching (“RIE ”). Surface micro-machining involves fabrication from films deposited on the surface of a substrate.
A preferred technique for preparing the present microfluidic devices is laser ablation. In laser ablation, short pulses of intense ultraviolet light are absorbed in a thin surface layer of material. When laser ablation technique is used, the laser must be selected according to the material to be removed. For example, the energy required to vaporize glass is typically five to ten times higher than that required for organic materials. Laser ablation will typically involve use of a high-energy photon laser such as an excimer laser of the F2, ArF, KrCl, KrF, or XeC1 type or of solid Nd-YAG or Ti:sapphire types. However, other ultraviolet light sources with substantially the same optical wavelengths and energy densities may be used as well. Laser ablation techniques are described, for example, by Znotins et al. (1987) Laser Focus Electro Optics, at pp. 54-70, and in U.S. Pat. Nos. 5,291,226 and 5,305,015 to Schantz et al. Preferred pulse energies for certain materials are greater than about 100 millijoules per square centimeter and pulse durations are shorter than about 1 microsecond. Under these conditions, the intense ultraviolet light photo-dissociates the chemical bonds in the substrate surface. The absorbed ultraviolet energy is concentrated in such a small volume of material that it rapidly heats the dissociated fragments and ejects them away from the substrate surface. Because these processes occur so quickly, there is no time for heat to propagate to the surrounding material. As a result, the surrounding region is not melted or otherwise damaged.
The fabrication technique that is used must provide for features of sufficiently high definition, i.e., microscale components, channels, chambers, etc., such that precise alignment “microalignment” of these features is possible, i.e., the laser-ablated features are precisely and accurately aligned, including, e.g., the alignment of complementary microchannels with each other, projections and mating depressions, grooves and mating ridges, and the like.
To immobilize the substrates of the inventive device relative to each other, fluid-tight pressure sealing techniques may be employed. In some instances, external means may be used to urge the pieces together (such as clips, tension springs or associated clamping apparatus). Internal means such as male and female couplings or chemical means such as welds may be advantageously used as well. Similarly, a seal may be provided between substrates. Any of a number of materials may be used to form the seal. Adhesives such as those in the form of a curable mass, e.g., as a liquid or a gel, may be placed between the substrates and subjected to curing conditions to form an adhesive polymer layer therebetween. Additional adhesives, e.g., pressure-sensitive adhesives or solvent-containing adhesive solutions may be used as well.
Thus, the invention provides previously unknown advantages in the fluidic arts. For example, the invention allows the use of a single high pressure pump, a low pressure pump, a microfluidic or macrofluidic device, and a single switching valve to generate high, medium, and low pressure LC gradients. Each pump may be used to pump a single liquid. The invention also facilitates the production of repeatable LC gradients that are only dependent on the geometry of the device, the composition of fluids used, and the precision of the pressure or flow rate in the high pressure pump operation. Furthermore, the invention may be advantageously used to decrease delay time between gradient generation in a mobile phase and the arrival of the mobile phase in microfluidic LC separation applications. This is especially important for low flow rate applications where delay times may become a significant portion of the total run time of the analysis. Solvent waste may reduced in gradient generating applications since almost all pumped solvent is used for the gradient generating. Other advantages include: low flow rate gradients at high pressure with low complexity devices; repeatability; and absolute knowledge of the total volumes of fluid pumps
Variations of the present invention will be apparent to those of ordinary skill in the art in view of the disclosure contained herein. For example, the inventive device may be constructed to contain or exclude specific features according to the intended use of the device. When the device is not intended for biofluidic applications, the device may not require a biofouling resistant material. In addition, the invention is scale invariant and may be incorporated for devices of almost any size, microfluidic or otherwise. Furthermore, while the fluid transporting microfeatures of
When mixing is required, any of a number of mixing technologies known in the art may be used. For example, mixing technologies other than those depicted in
It is to be understood that, while the invention has been described in conjunction with the preferred specific embodiments thereof, the foregoing description merely illustrates and does not limit the scope of the invention. Numerous alternatives and equivalents exist which do not depart from the invention set forth above. For example, any particular embodiment of the invention, e.g., those depicted in any drawing herein, may be modified to include or exclude features of other embodiments. Other aspects, advantages, and modifications within the scope of the invention will be apparent to those skilled in the art to which the invention pertains.
All patents and patent applications mentioned herein are hereby incorporated by reference in their entireties to the extent not inconsistent with the description set forth above.
