EP2847465A1 - Microfluidic pump - Google Patents
Microfluidic pumpInfo
- Publication number
- EP2847465A1 EP2847465A1 EP13767323.2A EP13767323A EP2847465A1 EP 2847465 A1 EP2847465 A1 EP 2847465A1 EP 13767323 A EP13767323 A EP 13767323A EP 2847465 A1 EP2847465 A1 EP 2847465A1
- Authority
- EP
- European Patent Office
- Prior art keywords
- pump
- microchannel
- groove
- less
- substrate
- Prior art date
- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
- Granted
Links
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Classifications
-
- F—MECHANICAL ENGINEERING; LIGHTING; HEATING; WEAPONS; BLASTING
- F04—POSITIVE - DISPLACEMENT MACHINES FOR LIQUIDS; PUMPS FOR LIQUIDS OR ELASTIC FLUIDS
- F04B—POSITIVE-DISPLACEMENT MACHINES FOR LIQUIDS; PUMPS
- F04B43/00—Machines, pumps, or pumping installations having flexible working members
- F04B43/12—Machines, pumps, or pumping installations having flexible working members having peristaltic action
- F04B43/14—Machines, pumps, or pumping installations having flexible working members having peristaltic action having plate-like flexible members
-
- F—MECHANICAL ENGINEERING; LIGHTING; HEATING; WEAPONS; BLASTING
- F04—POSITIVE - DISPLACEMENT MACHINES FOR LIQUIDS; PUMPS FOR LIQUIDS OR ELASTIC FLUIDS
- F04B—POSITIVE-DISPLACEMENT MACHINES FOR LIQUIDS; PUMPS
- F04B19/00—Machines or pumps having pertinent characteristics not provided for in, or of interest apart from, groups F04B1/00 - F04B17/00
- F04B19/006—Micropumps
-
- F—MECHANICAL ENGINEERING; LIGHTING; HEATING; WEAPONS; BLASTING
- F04—POSITIVE - DISPLACEMENT MACHINES FOR LIQUIDS; PUMPS FOR LIQUIDS OR ELASTIC FLUIDS
- F04B—POSITIVE-DISPLACEMENT MACHINES FOR LIQUIDS; PUMPS
- F04B43/00—Machines, pumps, or pumping installations having flexible working members
- F04B43/02—Machines, pumps, or pumping installations having flexible working members having plate-like flexible members, e.g. diaphragms
- F04B43/04—Pumps having electric drive
- F04B43/043—Micropumps
-
- F—MECHANICAL ENGINEERING; LIGHTING; HEATING; WEAPONS; BLASTING
- F04—POSITIVE - DISPLACEMENT MACHINES FOR LIQUIDS; PUMPS FOR LIQUIDS OR ELASTIC FLUIDS
- F04B—POSITIVE-DISPLACEMENT MACHINES FOR LIQUIDS; PUMPS
- F04B43/00—Machines, pumps, or pumping installations having flexible working members
- F04B43/12—Machines, pumps, or pumping installations having flexible working members having peristaltic action
-
- F—MECHANICAL ENGINEERING; LIGHTING; HEATING; WEAPONS; BLASTING
- F04—POSITIVE - DISPLACEMENT MACHINES FOR LIQUIDS; PUMPS FOR LIQUIDS OR ELASTIC FLUIDS
- F04B—POSITIVE-DISPLACEMENT MACHINES FOR LIQUIDS; PUMPS
- F04B43/00—Machines, pumps, or pumping installations having flexible working members
- F04B43/12—Machines, pumps, or pumping installations having flexible working members having peristaltic action
- F04B43/1238—Machines, pumps, or pumping installations having flexible working members having peristaltic action using only one roller as the squeezing element, the roller moving on an arc of a circle during squeezing
- F04B43/1246—Machines, pumps, or pumping installations having flexible working members having peristaltic action using only one roller as the squeezing element, the roller moving on an arc of a circle during squeezing the roller being placed at the outside of the tubular flexible member
-
- F—MECHANICAL ENGINEERING; LIGHTING; HEATING; WEAPONS; BLASTING
- F04—POSITIVE - DISPLACEMENT MACHINES FOR LIQUIDS; PUMPS FOR LIQUIDS OR ELASTIC FLUIDS
- F04B—POSITIVE-DISPLACEMENT MACHINES FOR LIQUIDS; PUMPS
- F04B43/00—Machines, pumps, or pumping installations having flexible working members
- F04B43/12—Machines, pumps, or pumping installations having flexible working members having peristaltic action
- F04B43/1253—Machines, pumps, or pumping installations having flexible working members having peristaltic action by using two or more rollers as squeezing elements, the rollers moving on an arc of a circle during squeezing
- F04B43/1261—Machines, pumps, or pumping installations having flexible working members having peristaltic action by using two or more rollers as squeezing elements, the rollers moving on an arc of a circle during squeezing the rollers being placed at the outside of the tubular flexible member
-
- F—MECHANICAL ENGINEERING; LIGHTING; HEATING; WEAPONS; BLASTING
- F04—POSITIVE - DISPLACEMENT MACHINES FOR LIQUIDS; PUMPS FOR LIQUIDS OR ELASTIC FLUIDS
- F04B—POSITIVE-DISPLACEMENT MACHINES FOR LIQUIDS; PUMPS
- F04B43/00—Machines, pumps, or pumping installations having flexible working members
- F04B43/12—Machines, pumps, or pumping installations having flexible working members having peristaltic action
- F04B43/1253—Machines, pumps, or pumping installations having flexible working members having peristaltic action by using two or more rollers as squeezing elements, the rollers moving on an arc of a circle during squeezing
- F04B43/1292—Pumps specially adapted for several tubular flexible members
Definitions
- the invention relates to micro fluidics technology, and more particularly to a microfiuidic pump for control of fluid flow through microchannels.
- Microfluidics systems are of significant value for acquiring and analyzing chemical and biological information using very small volumes of liquid. Use of microfiuidic systems can increase the response time of reactions, minimize sample volume, and lower reagent and consumables consumption. When volatile or hazardous materials are used or generated, performing reactions in microfiuidic volumes also enhances safety and reduces disposal quantities.
- Microfiuidic devices have becoming increasingly important in a wide variety of fields from medical diagnostics and analytical chemistry to genomic and proteomic analysis. They may also be useful in therapeutic contexts, such as low flow rate drug delivery.
- micropump may be used to mix reagents and transport fluids between a disposable analysis platform component of the system and an analysis instrument (e.g., an analyte reader with display functions). Yet controlling the direction and rate of fluid flow within the confines of a microfiuidic device, or achieving complex fluid flow patterns inside microfiuidic channels is difficult.
- the present invention provides a microfiuidic pump module.
- the microfiuidic pump module includes a first plate element and a second plate element, the first plate element being elastomeric and the second plate element being non-elastomeric.
- the second plate element includes a microchannel formed on a surface of the second plate element, and the first and second plate elements are coupled to form a fluid tight seal along the boundary of the microchannel defining a fluid flow path.
- the invention provides a microfiuidic device utilizing the microfiuidic pump module described herein.
- the microfiuidic device includes (a) a rigid substrate having a microchannel formed on a surface thereof; and (b) a flexible layer coupled to and overlying the rigid substrate thereby enclosing the microchannel, wherein the flexible layer comprises a raised element disposed over a portion or all of the microchannel.
- the device further includes a fluid tight seal formed between the rigid substrate and the flexible layers along a periphery of the microchannel forming an enclosed capillary.
- the invention provides a microfiuidic device utilizing the microfiuidic pump module described herein.
- the microfiuidic device includes (a) a rigid substrate having a microchannel formed on a surface thereof; and (b) a flexible layer coupled to and overlying the rigid substrate thereby enclosing the microchannel, wherein the flexible layer has a flat surface disposed over a portion or all of the microchannel.
- the device further includes a fluid tight seal formed between the rigid substrate and the flexible layers along a periphery of the microchannel forming an enclosed capillary.
- the invention provides a microfiuidic device utilizing the microfiuidic pump module described herein, wherein the pump module comprises at least two independent microchannels arranged in a substantially parallel manner.
- One or more actuators are provided which act upon the two or more microchannels simultaneously, thereby providing means to pump two fluids separate from one another.
- the microchannels have identical cross sectional areas, such that the volume of fluid transported per unit distance of the microchannel is substantially the same.
- the at least two microchannels have different cross sectional areas, in which instance the volume of fluid transported per unit distance of the microchannel is different.
- the invention provides a micro fluidic device utilizing the microfluidic pump module described herein, wherein the pump module comprises at least two independent microchannels arranged concentrically about a point upon which at least one actuator rotates.
- the invention provides a method for performing a microfluidic process.
- the method includes (a) applying a voltage to a microfluidic pump module as described herein.
- the applied voltage activates a motor which advances an actuator element, such as one or more rollers, which is rotatably engaged with the second substrate, causing deformation of the second substrate into the microchannel formed on the surface of the first substrate.
- Deformation of the elastomeric second substrate into the microchannel forces fluid within the microchannel along the microchannel resulting in a fluid flow.
- the first substrate is formed from a material having a Shore D hardness of between about 75 and about 90. Such materials include, but are not limited to, polystyrene, polypropylene,
- the microchannel or groove formed in the surface of the first substrate is dimensionally stable, by which is meant that when the second substrate is deformed into the groove in the first substrate, the width of the groove is at least about 75%, at least about 90%>, at least about 95%>, at least about 97.5%>, at least about 99%), or essentially the same as in the uncompressed state and height the groove is at least about 75%o, at least about 90%>, at least about 95%>, at least about 97.5%>, at least about 99%>, or essentially the same as in the uncompressed state.
- the dimensions of the groove are thus considered to be essentially unchanged as a consequence of the deformation of the second substrate into the first substrate,
- the second substrate is formed from a material having a Shore A hardness of between about 15 and 90.
- Such materials include, but are not thermoplastic elastomer (TPE), polydimethylsiloxane (PDMS), silicone rubber,
- fluoroelastomer and the like are considered to be dimensionally unstable, by which is meant that when a compressive force or a stretching force is applied to such polymeric materials the material deforms, either through elongation in one or more directions, or the material compresses in one or more dimensions.
- the invention provides a method of manufacturing a microfluidic device.
- the method includes coupling a rigid substrate having a microchannel formed on a surface thereof, to a flexible layer overlying the rigid substrate and enclosing the
- a fluid tight seal is formed between the rigid substrate and the flexible layers along a periphery of the microchannel forming an enclosed capillary.
- the rigid substrate and the flexible layer are coupled via a laser welding process. The process includes:
- the invention provides a method of manufacturing a microfluidic device.
- the method includes coupling a rigid substrate having a microchannel formed on a surface thereof, to a flexible layer overlying the rigid substrate and enclosing the
- a fluid tight seal is formed between the rigid substrate and the flexible layers along a periphery of the microchannel forming an enclosed capillary.
- the rigid substrate and the flexible layer are coupled via a process of over-molding.
- the process includes: (a) injecting a first polymer composition into an injection mold cavity to form the rigid substrate;
- Figure 1 is a series of schematics illustrating movement of various components during operation of a microfluidic device in embodiments of the invention.
- Figure 1 A is a cross-sectional view of a portion of a microfluidic device in embodiments of the invention.
- Figure IB is a cross-sectional view of a portion of a microfluidic device in embodiments of the invention.
- Figure 2 is a cross-sectional view of a portion of a microfluidic device in embodiments of the invention.
- Figure 3 is a perspective view of a portion of a microfluidic device in an embodiment of the invention.
- Figure 4 is a top view of a portion of a microfluidic device in an embodiment of the invention.
- Figure 5 is a perspective view of a microfluidic device in an embodiment of the invention.
- Figure 6 is a series of schematics illustrating a microfluidic device in embodiments of the invention.
- Figure 6A is a top view of a microfluidic device in an embodiment of the invention.
- Figure 6B is a top view of a microfluidic device in an embodiment of the invention.
- Figure 6C is a top view of a microfluidic device in an embodiment of the invention.
- Figure 7 is a graphical representation depicting data generated with a microfluidic device in an embodiment of the invention.
- Figure 8 is a graphical representation depicting data generated with a microfluidic device in an embodiment of the invention.
- Figure 9 is a graphical representation depicting data generated with a microfluidic device in an embodiment of the invention.
- Figure 10 is a top view of a portion of a microfluidic device in an embodiment of the invention.
- Figure 11 is a cross-sectional schematic of a drive for use in one embodiment of the invention.
- Figure 12 is a cross-sectional schematic of a drive for use in one embodiment of the invention.
- Figure 13 is a top view schematic of a microfluidic device in an embodiment of the invention. DETAILED DESCRIPTION OF THE INVENTION
- a microfluidic pump and device containing the pump have been developed in order to provide, in embodiments, low cost, high accuracy and low flow rate means for onboard sample handling for disposable assay devices.
- the rate of fluid flow within the pump is essentially constant even at very low flow rates.
- the pump comprises a first substrate and a second substrate secured with respect to one another to provide a structure having one or more microchannels which are sealed along the boundaries of the microchannels thereby defining fluid flow paths.
- microchannel structures (40) are formed in a major surface of a first substrate (20) formed, e.g., of a non- elastomeric or rigid material.
- the second substrate In the compressed state, the second substrate typically occludes a sufficient portion of the microchannel (40) to displace a substantial portion of fluid from microchannel (40) at the site of compression.
- the second substrate may occlude a sufficient portion of the microchannel (40) to separate fluid disposed within microchannel (40) on one side of the site of compression from fluid disposed within microchannel (40) on the other side of the site of compression.
- the second substrate occludes, in the compressed state, at least about 50%, at least about 75%, at least about 90%>, at least about 95%, at least about 97.5%), at least about 99%, or essentially all of the uncompressed cross-sectional area of the groove at the site of compression.
- the compression may create a fluid-tight seal between the first and second substrates within the groove at the site of compression.
- fluid e.g., a liquid
- the fluid-tight seal may be transient, e.g., the second substrate may fully or partially relax upon removal of the compression thereby fully or partially reopening the groove.
- the groove has a first cross-sectional area in an uncompressed state and a second cross-sectional area in the compressed state.
- the portion of the elastomer is compressed into the groove without substantially deforming the groove.
- a ratio of the cross-sectional area at the site of compression in the compressed state to the cross- sectional area at the same site in the uncompressed state may be at least about 0.75, at least about 0.85, at least about 0.925, at least about 0.975, or about 1.
- the height of the groove e.g.
- the maximum height of the groove at the site of compression, in the compressed state may be at least about 75%, at least about 85%, at least about 90%>, at least about 95%), or about 100% of the height of the groove at the same site in the uncompressed state.
- the width of the groove, e.g. , the maximum width of the groove at the site of compression, in the compressed state may be at least about 75%, at least about 85%, at least about 90%>, at least about 95%, or about 100% of the width of the groove at the same site in the uncompressed state.
- a raised element (30), such as a bump, is present on the elastomer (10), which may be placed over the microchannel region (40), thereby increasing the thickness of elastomeric material which may aid sealing of the elastomer into the channel when compressed against the non-elastic component (20).
- the elastomer in the uncompressed state, may have a first thickness overlying the groove and a second thickness spaced apart laterally a first distance from the center of the groove.
- the second thickness is at least about 1 10%, at least about 125%, at least about 150%, at least about 175%, or at least about 200% greater than the first thickness.
- the second thickness may be at least about 500% or less, about 400% or less, about 300%> or less, or at about 250% or less greater than the first thickness.
- the first distance may be at least about 1 mm, at least about 2.5 mm, at least about 5 mm, or at least about 1 cm.
- the first distance may be about 2.5 cm or less, about 2 cm or less, about 1.5 cm or less, or about 1.25 cm or less.
- the first distance is at about 1.5 times greater, about 1.75 times greater, about 2 times greater, or about 4 times greater than a width, e.g., a maximum width, of the groove.
- the first distance may be about 25 times greater or less, about 20 times greater or less, about 15 times greater or less, or about 10 times greater or less than a width, e.g., a maximum width, of the groove.
- a microfluidic pump module (100) is provided utilizing the microfluidic structure described herein.
- the microfluidic pump module (100) includes a first elastomeric plate element (10) and a second rigid plate element (20).
- the second plate element (20) includes a microchannel (40) formed on a surface of the second plate element (20), and the first and second plate elements are coupled to form a fluid tight seal along the boundary of the microchannel (40) defining a fluid flow path.
- the invention provides a microfluidic device (100) utilizing the microfluidic pump module described herein.
- the microfluidic device (100) includes a rigid substrate (20) having a microchannel (40) formed on a surface thereof and a flexible layer (10) coupled to and overlying the rigid substrate (20) thereby enclosing the microchannel (40).
- the invention provides a microfluidic device (100), which again with reference to Figures 1A and IB, the reverse orientation is provided.
- microchannel (40) is formed in flexible layer (10); and rigid substrate (20) is provided with a flat surface profile, such that when flexible layer (10) is coupled to and overlying rigid substrate (20) a microchannel (40) is formed therebetween.
- the flexible layer (10) comprises a raised element (30) disposed over a portion or all of the microchannel (40).
- the raised element (30) provides an increased cross-section thickness in the area which coincides with the microchannel (40).
- the raised element (30) may be one of a number of suitable shapes such as a bump.
- flexible layer (10) has no raised element (30), in which case microchannel (40) is covered entirely by flexible layer (10) which has a flat upper surface profile, which surface is not in contact with rigid substrate (20).
- microchannels (40) may be formed on a surface of the rigid substrate (20) by any number of suitable techniques known in the art.
- microchannels may be formed by deposition of materials through a mask, chemical etching, laser etching, molding of a plastic substrate, and the like.
- a fluid tight seal is also formed between the rigid substrate (20) and the flexible layer (10) along a periphery of the microchannel (40) forming an enclosed capillary having a defined fluid flow path.
- Microchannels may be dimensioned to define the volume within the microchannel and resultant flow rate for a given rate at which the elastomer is progressively deformed into the microchannel.
- the high quality and precision of the so formed microchannel results in a microfluidic pump element that can achieve very slow and consistent flow rates, which may not otherwise be achieved if alternate processes of manufacture were employed.
- microchannel may be dimensioned such that it has a constant width dimension and a constant depth dimension along all or a portion of its length.
- a microchannel will have a constant width dimension and a constant depth dimension along a length of the microchannel which engages a deformation element.
- a microchannel has a width dimension of between 500 to 900 microns and a depth dimension of between 40 to 100 microns.
- the device may be adapted for a flow rate within the microchannel of between 0.001 ⁇ /s to 5.0 ⁇ /s.
- FIG. 1 A and IB depict a microchannel (40) in which the bottom surface of the microchannel is arced and defines a concave circular geometry.
- the microchannel (40) may have a rounded, elliptical or generally U shaped bottom.
- the microchannel has an arced shaped bottom having a radius of curvature of between 0.7 and 0.9 mm.
- Figure 2 is a cross-sectional view of a portion of a microfluidic device in one embodiment of the invention in which specific dimensions (shown in mm) are described for various features.
- microchannels (40) may be modified, for example by varying hydrophobicity.
- hydrophobicity may be modified by application of hydrophilic materials such as surface active agents, application of hydrophobic materials, construction from materials having the desired hydrophobicity, ionizing surfaces with energetic beams, and/or the like.
- a device of the present invention may include a plurality of microchannels (40), each having various geometries and disposed on the rigid substrate (20) (or in the alternate on the flexible layer (10)) in a variety of patterns.
- microchannels (40) may be linear or extend arcuately along the surface of the rigid substrate (20).
- Figures 3 and 4 illustrate microchannels (40) being disposed as generally circular or spiral geometries.
- Figure 3 is a perspective view of a device in which microchannels (40) are disposed as spirals, a smaller volume microchannel disposed within a microchannel having a larger volume.
- Figure 4 is a top view of a device in which the microchannel (40) is disposed in a spiral manner having ports (100) and (110) which may be in fluid communication with one or more additional microchannels or structures.
- the circular or spiral portion of the microchannel has a length of between 20 to 100 mm.
- a spiral or generally circular shaped microchannel allows for fluid to be advanced through the microchannel of the pump module or device by a deformation element (50) that is radially coupled to the device.
- Figure 5 is an illustration depicting a pump module and device of the present invention in which multiple deformation elements (50) are radially coupled and configured to engage a microchannel having a circular or spiral geometry.
- the deformation elements (50) are provided in a housing (80) configured to radially traverse one or more microchannels provided on the microfluidic laminate structure (110) when the structure is placed in contact with the deformation elements (50) (spiral microchannel is disposed on the opposite side of laminate structure (1 10) shown).
- the rotational direction of the deformation elements (50) with relation to the micro fluidic laminate structure (1 10) dictates the direction of flow within the microchannel.
- fluid flow through the pump may be bidirectional.
- Housing (80) may be rotated by applying a voltage to a motor controlling movement thereof.
- the invention further provides a method for performing a microfluidic process which includes applying a voltage to a device as described herein.
- the applied voltage activates a motor which advances at least one deformation element (50), such as one or more rollers, which are rotatably engaged with the elastomeric first plate element (10), causing deformation of a raised element (30) on the flexible layer (10) into the microchannel (40) formed on the surface of the rigid substrate (20).
- a wide range of pulses per second may be applied to the electrical motor thereby effectuating a wide range of flow rates within microchannels
- the fluid flow is essentially constant, with little or no shear force being imposed on the fluid, even at very low flow rates.
- These characteristics of the pump enhance the accuracy of analyses performed with it (e.g., analyte integrity is preserved by minimizing exposure of sample components to shear and degradation), while low flow rates provide sufficient time for chemical reactions to occur.
- a low, constant pumped flow rate can also be very useful in drug delivery, to ensure dosing accuracy.
- between 100 and 10,000 pulses per second may be applied resulting in a flow rate of between 0.001 ⁇ /s to 5.0 ⁇ /s through microchannels.
- the design of the present invention allows forces within microchannels of the present invention to remain fairly constant over a wide range of applied pulses.
- Figures 7-9 are graphs plotting forces generated within
- microchannels as a function of the number of pulses per second. As depicted in the graphs of
- FIGs 7-9 forces generated within the microchannels are relatively constant over a wide ano p nf rm1 « p ;s per second indicating substantially constant flow with minimal shear.
- Figures 6A-6C illustrate various configurations in different embodiments of the invention in which at least one spiral or circular microchannel is provided. Circular or spiral microchannels (40) may be disposed such that they are in fluid communication with one or more additional microchannels (140) through ports (100) and (110). Additional
- microchannels (140) may be provided with various reagents, immobilized therein or otherwise provided such that a biological assay may be performed on a fluid sample.
- a fluid tight seal is formed between the rigid substrate (20) and the flexible layer (10) along a periphery of the microchannel (40) forming an enclosed capillary having a defined fluid flow path.
- Figure 10 illustrates a portion of a device having a generally spiral microchannel in which a fluid tight seal (140) is shown along the periphery of the microchannel (40).
- a variety of methods may be utilized to couple rigid substrate (20) to the elastomer that forms flexible layer (10).
- the parts may be joined together using UV curable adhesive or other adhesive that permits for movement of the two parts relative one another prior to curing of the adhesive/creation of bond.
- Suitable adhesives include a UV curable adhesive, a heat cured adhesive, a pressure sensitive adhesive, an oxygen sensitive adhesive, and a double-sided tape adhesive.
- the parts may be coupled utilizing a welding process.
- a welding process including an ultrasonic welding process, a thermal welding process, and a torsional welding process.
- the parts may be joined using a process of two-shot molding or overmolding, in which case first one polymer and then the other is injected into a mold tool.
- a process of two-shot molding or overmolding in which case first one polymer and then the other is injected into a mold tool.
- elastomeric and non-elastomeric polymers can be joined in this way to achieve fluid tight seals between the parts.
- a process of laser welding includes: (a) exposing one of the first or second plate elements to ultra violet laser energy around the periphery of the microchannel so as to carbonize the surface of the first or second plate element;
- the benefits of such approaches mean that (i) the parts may be manipulated (slid against one another) during manufacture to achieve desired alignments, (ii) intricate forms can be achieved in the non-elastomer - linear or arcuate channels (or combinations thereof) with a plurality of channel geometries, (iii) connections with the device may be made via the non-elastomeric material, which is dimensionally stable.
- additional microchannels and structures may be provided to allow the device to perform a number of different types of biological assays or reactions.
- additional fluid or reagent reservoirs may be provided, one or more of which act as a reaction chamber for example. Additional structure and depicted in the following example which is intended to illustrate but not limit the invention.
- planar circular or spiral peristaltic pump of the present invention for use in low cost diagnostic products consisting of an instrument and consumable, where the consumable requires sealing due to a potential high risk of contamination.
- the method to perform pumping sample fluids to deposited chemicals followed by mixing of sample fluid with deposited chemicals in a low cost manner involves using only one actuator, for example a DC or stepper motor (1) incorporated into the instrument.
- the peristaltic pump consists of a planar circular or spiral annular microchannel (2) as a feature of a substrate (3) of the consumable (4) and the deforming membrane of the pump is provided by an elastomeric layer (5) which is deformed by the pump rollers (6).
- Concentric to the annular pump channels is the mixing chamber (7) which contains a magnetic or magnetized puck (8).
- Concentric to the pump rollers of the instrument is a structure comprising a mixing head (9) which is magnetic or magnetized and is magnetically coupled to the puck.
- the pump and mixing chamber are fluidically connected, thus fluid can be pumped from the pump microchannels into the mixing chamber as the motor rotates in a predetermined direction.
- the instrument component of the pump comprises a suitable mechanism to provide pumping and mixing functionality when the motor is rotated in a certain direction, but only mixing functionality when the motor is rotated in the opposite direction, for example a ratchet system implemented by a pawl (10) and a compression spring (11) whereby the mixing head rotates with the pump rollers in one rotational direction of the motor and whereby the pump rollers disengage from the motor when the motor rotates in the other direction, thus providing rotation of the mixing head only.
- the compression spring may also provide the necessary contact force on the pump channels to facilitate effective pumping.
- FIG. 10 Another embodiment provides an annular mixing chamber internal or external to the pump channels.
- This embodiment could feasibly be produced at a lower cost than the first embodiment and is described with reference to Figure 12.
- the spiral or circular pump channel (1) as a feature in a substrate (2) is overlaid with an elastomeric membrane (3) and deformed by pump rollers (4) in a similar manner to that described in Figure 11.
- the mixing chamber is an annular channel (4) as a concentric feature to the pump channel but located on the reverse face of the pump channel substrate.
- bearing balls (5) Located within this annular channel is one or many bearing balls (5) which are magnetically coupled to a magnetic or magnetized element on the rotor (6) such that as the rotor rotates the bearing balls also rotate in the annular channel, thus providing mixing of chemicals initially deposited inside the annular channel.
- the drive mechanism to achieve mixing and pumping in one rotational direction of the motor and just mixing in the other rotational direction of the motor is envisaged to be similar to that described with reference to Figure 11.
- this peristaltic pump can be designed to accommodate multiple fluidic channels on different radii if desired.
- the sample that is transported is first required to be mixed with stored deposited chemicals (6) located within the mixing chamber (7), followed by a dilution step using a dilution fluid.
- the dilution fluid it is preferable to store the dilution fluid away from the stored chemicals so the stored chemicals do not become affected by the dilution fluid.
- the motor rotates in a certain direction the pump rollers engage with the pumping membrane to transport both sample fluid and dilution fluid into the consumable, as the mixing chamber fills with sample fluid, the dilution fluid fills a secondary chamber (8) which is sized according to the amount of dilution fluid required and the geometry of the dilution fluid pumping channels and the mixing chamber volume.
- an equivalent mechanism as described above could be implemented which rotates the motor in the opposite direction to only provide mixing.
- the motor rotates to engage the pump rollers which transport the sample and dilution fluid to a location inside the consumable which combines the two fluids (9).
- passive mixing features may be included at the fluid combining region.
- the motor continues to rotate to pump the two fluids, the diluted sample can be transported to another location on the consumable, for example a location to carry out detection of an analyte (11).
- Hi p rtinn A n additional feature of the pump design is the ability for the consumable part of the pump to include multiple pump channels such that multiple fluids may be transported using the same motor drive mechanism.
- a wide range of pulses per second may be applied to the electrical motor thereby effectuating a wide range of flow rates within microchannels, including very low flow rates.
- the fluid flow is essentially constant, with little or no shear force being imposed on the fluid, even at very low flow rates.
- These characteristics of the pump enhance the accuracy of analyses performed with it (e.g., analyte integrity is preserved by minimizing exposure of sample components to shear and degradation), while low flow rates provide sufficient time for chemical reactions to occur.
- a low, constant pumped flow rate can also be very useful in drug delivery, to ensure dosing accuracy.
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Abstract
Description
Claims
Applications Claiming Priority (2)
Application Number | Priority Date | Filing Date | Title |
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US201261615786P | 2012-03-26 | 2012-03-26 | |
PCT/US2013/032020 WO2013148312A1 (en) | 2012-03-26 | 2013-03-15 | Microfluidic pump |
Publications (3)
Publication Number | Publication Date |
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EP2847465A1 true EP2847465A1 (en) | 2015-03-18 |
EP2847465A4 EP2847465A4 (en) | 2016-04-06 |
EP2847465B1 EP2847465B1 (en) | 2020-04-15 |
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EP13767323.2A Active EP2847465B1 (en) | 2012-03-26 | 2013-03-15 | Microfluidic pump |
Country Status (5)
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US (1) | US20150050172A1 (en) |
EP (1) | EP2847465B1 (en) |
CN (1) | CN104204523A (en) |
HK (1) | HK1208256A1 (en) |
WO (1) | WO2013148312A1 (en) |
Families Citing this family (9)
Publication number | Priority date | Publication date | Assignee | Title |
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ES2927783T3 (en) * | 2016-04-26 | 2022-11-10 | Remus Brix Anders Haupt | Fluid peristaltic layer pump |
US11904311B2 (en) | 2016-04-26 | 2024-02-20 | Remus Brix A. HAUPT | Fluidic peristaltic layer pump with integrated valves |
US10632464B2 (en) | 2017-02-28 | 2020-04-28 | Alere San Diego, Inc. | Microfluidic devices and related methods |
EP3658283A4 (en) | 2017-10-20 | 2020-06-24 | Hewlett-Packard Development Company, L.P. | Microfluidic device |
EP3483441B1 (en) * | 2017-11-13 | 2020-05-13 | Sumitomo Rubber Industries, Ltd. | Peristaltic tube pump |
CN114126696B (en) * | 2019-08-27 | 2024-03-26 | 深圳迈瑞生物医疗电子股份有限公司 | Method for manufacturing a fluid delivery conduit for a medical device |
WO2021144396A1 (en) | 2020-01-17 | 2021-07-22 | F. Hoffmann-La Roche Ag | Microfluidic device and method for automated split-pool synthesis |
US20230039014A1 (en) | 2020-01-22 | 2023-02-09 | Roche Sequencing Solutions, Inc. | Microfluidic bead trapping devices and methods for next generation sequencing library preparation |
CN116710571A (en) | 2020-10-15 | 2023-09-05 | 卡帕生物***公司 | Electrophoresis apparatus and method for next generation sequencing library preparation |
Family Cites Families (15)
Publication number | Priority date | Publication date | Assignee | Title |
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FR2317526A1 (en) * | 1975-07-08 | 1977-02-04 | Rhone Poulenc Ind | PERISTALTIC PUMP |
US4673657A (en) * | 1983-08-26 | 1987-06-16 | The Regents Of The University Of California | Multiple assay card and system |
KR100865105B1 (en) * | 1999-06-28 | 2008-10-24 | 캘리포니아 인스티튜트 오브 테크놀로지 | Microfabricated elastomeric valve and pump systems |
WO2002018756A1 (en) * | 2000-08-31 | 2002-03-07 | Advanced Sensor Technologies | Micro-fluidic actuator |
US20030153872A9 (en) * | 2000-09-22 | 2003-08-14 | Tanner Howard M. C. | Apparatus and method for micro-volume infusion |
KR100451154B1 (en) * | 2001-07-24 | 2004-10-02 | 엘지전자 주식회사 | Method for handling fluid in substrate and device for it |
KR100421359B1 (en) * | 2001-07-24 | 2004-03-06 | 엘지전자 주식회사 | Method for delivering fluid in elastic substrate and device for it |
US7056475B2 (en) * | 2002-01-30 | 2006-06-06 | Agilent Technologies, Inc. | Fluidically isolated pumping and metered fluid delivery system and methods |
AU2003292821A1 (en) * | 2003-01-30 | 2004-08-23 | Sunarrow Limited | Method for marking key top made of translucent material, key top marked by that method, key unit, and process for producing key unit |
JP2006527093A (en) * | 2003-03-10 | 2006-11-30 | ザ リージェンツ オブ ザ ユニバーシティ オブ ミシガン | Integrated microfluidic control using programmable haptic actuators |
FR2897858B1 (en) * | 2006-02-27 | 2008-06-20 | Commissariat Energie Atomique | METHOD FOR MANUFACTURING A NETWORK OF CAPILLARIES OF A CHIP |
US8079836B2 (en) * | 2006-03-01 | 2011-12-20 | Novartis Ag | Method of operating a peristaltic pump |
CN101354030B (en) * | 2008-02-20 | 2010-09-15 | 重庆大学 | Micro-fluid pump with active control capability |
US8414182B2 (en) * | 2008-03-28 | 2013-04-09 | State Of Oregon Acting By And Through The State Board Of Higher Education On Behalf Of Oregon State University | Micromixers for nanomaterial production |
US20110200802A1 (en) * | 2010-02-16 | 2011-08-18 | Shenping Li | Laser Welding of Polymeric Materials |
-
2013
- 2013-03-15 EP EP13767323.2A patent/EP2847465B1/en active Active
- 2013-03-15 WO PCT/US2013/032020 patent/WO2013148312A1/en active Application Filing
- 2013-03-15 CN CN201380014383.1A patent/CN104204523A/en active Pending
- 2013-03-15 US US14/388,323 patent/US20150050172A1/en not_active Abandoned
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2015
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Also Published As
Publication number | Publication date |
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EP2847465A4 (en) | 2016-04-06 |
CN104204523A (en) | 2014-12-10 |
EP2847465B1 (en) | 2020-04-15 |
WO2013148312A1 (en) | 2013-10-03 |
US20150050172A1 (en) | 2015-02-19 |
HK1208256A1 (en) | 2016-02-26 |
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