WO2022146770A1 - Plaque à puits basée sur une plateforme de dilution en série microfluidique faisant appel à une phase immiscible exempte d'huile entraînée par des pipetteurs manuels ou électroniques et procédé de fonctionnement - Google Patents

Plaque à puits basée sur une plateforme de dilution en série microfluidique faisant appel à une phase immiscible exempte d'huile entraînée par des pipetteurs manuels ou électroniques et procédé de fonctionnement Download PDF

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Publication number
WO2022146770A1
WO2022146770A1 PCT/US2021/064512 US2021064512W WO2022146770A1 WO 2022146770 A1 WO2022146770 A1 WO 2022146770A1 US 2021064512 W US2021064512 W US 2021064512W WO 2022146770 A1 WO2022146770 A1 WO 2022146770A1
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Prior art keywords
fluidic
traps
channels
fluid
trap
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PCT/US2021/064512
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English (en)
Inventor
Deepak SOLOMON
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Neofluidics Llc
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Priority claimed from US17/134,737 external-priority patent/US20210114022A1/en
Application filed by Neofluidics Llc filed Critical Neofluidics Llc
Publication of WO2022146770A1 publication Critical patent/WO2022146770A1/fr

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Classifications

    • 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
    • B01F33/3035—Micromixers using surface tension to mix, move or hold 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
    • B01F33/304—Micromixers the mixing being performed in a mixing chamber where the products are brought into contact
    • 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
    • B01F33/80—Mixing plants; Combinations of mixers
    • B01F33/81—Combinations of similar mixers, e.g. with rotary stirring devices in two or more receptacles
    • B01F33/811—Combinations of similar mixers, e.g. with rotary stirring devices in two or more receptacles in two or more consecutive, i.e. successive, mixing receptacles or being consecutively arranged
    • B—PERFORMING OPERATIONS; TRANSPORTING
    • B01—PHYSICAL OR CHEMICAL PROCESSES OR APPARATUS IN GENERAL
    • B01F—MIXING, e.g. DISSOLVING, EMULSIFYING OR DISPERSING
    • B01F35/00—Accessories for mixers; Auxiliary operations or auxiliary devices; Parts or details of general application
    • B01F35/80—Forming a predetermined ratio of the substances to be mixed
    • B01F35/81—Forming mixtures with changing ratios or gradients

Definitions

  • microfluidic devices that can achieve storage of nano-pico liter volumes of1 droplets use either upstream mechanisms (such as T-junction or Y-junctions) or external force2 driven methods ( electric, magnetic or acoustic). See, for example, the following published3 applications and patents US PGPUB 20070195127, WO 2010111231, US Patent No. 723826,4 US Patent No. 7708949, EP2364774, US Patent No. 8765485 and W02006096571.
  • Passive5 methods include the fragmentation of a long slug of fluid into droplets in a hydrophobic6 microfluidic network by using an immiscible phase (usually oil).
  • the well-plate includes a plurality of fluidic traps, a plurality of hydrophilic capillary constriction channels and a plurality of bypass channels.
  • Each of the plurality of bypass channels is associated with one of the plurality of fluidic traps
  • each of the plurality of hydrophilic capillary constriction channels is associated with one of the plurality of fluidic traps
  • each of the plurality of fluidic traps is associated with one of the plurality of bypass channels and one of the plurality of hydrophilic capillary constriction channels.
  • the well-plate further includes an inlet, an outlet, and a main channel with a plurality of portions that connects the inlet to the plurality of fluidic traps, associated hydrophilic capillary constriction channels and associated bypass channels, and the outlet.
  • the well-plate includes a plurality of fluidic traps, a plurality of hydrophobic capillary constriction channels, and a plurality of bypass channels.
  • Each of the plurality of bypass channels is associated with one of the plurality of fluidic traps
  • each of the plurality of hydrophobic capillary constriction channels is associated with one of the plurality of fluidic traps
  • each of the plurality of fluidic traps is associated with one of the plurality of bypass channels and one of the plurality of hydrophobic capillary constriction channels.
  • the well-plate also includes an inlet, an outlet, and a main channel with a plurality of portions that connects the inlet to the plurality of fluidic traps, associated hydrophobic capillary constriction channels and associated bypass channels, and the outlet.
  • FIGS. 1A-1D are diagrams illustrating a hydrophilic embodiment of a microfluidic serial dilution platform based well-plate using an oil-free immiscible phase driven by manual or electronic pipettors.
  • FIG. IE is a diagram illustrating an entire well-plate, with cover, that includes an embodiment of a microfluidic serial dilution platform using an oil-free immiscible phase driven by manual or electronic pipettors.
  • FIGS. 2A-2C are diagrams illustrating a hydrophilic operation of a hydrophilic embodiment of the microfluidic serial dilution platform based well-plate using an oil-free immiscible phase driven by manual or electronic pipettors, particularly a fluid trapping process of the operation.
  • FIG. 3 is a series of images illustrating the fluid trapping process of an embodiment of the microfluidic serial dilution platform based well-plate using an oil-free immiscible phase driven by manual or electronic pipettors.
  • FIGS. 4A-4D are diagrams illustrating a hydrophilic operation of a hydrophilic embodiment of the microfluidic serial dilution platform based well-plate using an oil-free immiscible phase driven by manual or electronic pipettors, particularly a serial dilution process of the operation.
  • FIG. 5 is a series of images illustrating the serial dilution process of an embodiment of the microfluidic serial dilution platform based well-plate using an oil-free immiscible phase driven by manual or electronic pipettors.
  • FIGS. 6A-6B are diagrams illustrating a hydrophobic operation of a hydrophobic embodiment of the microfluidic serial dilution platform based well-plate using an oil-free immiscible phase driven by manual or electronic pipettors, particularly a serial dilution process of the operation.
  • FIGS. 7 A-7C are graphs illustrating data from dilutions using a hydrophilic embodiment of the microfluidic serial dilution platform based well-plate using an oil-free immiscible phase driven by manual or electronic pipettors.
  • FIGS. 8A-8B are graphs illustrating data from dilutions using a hydrophobic embodiment of the microfluidic serial dilution platform based well-plate using an oil-free immiscible phase driven by manual or electronic pipettors.
  • FIG. 9A is a table illustrating results of an experiment using a hydrophobic embodiment of the microfluidic serial dilution platform based well-plate using an oil-free immiscible phase driven by manual or electronic pipettors as a hemocytometer.
  • FIG. 9B is a diagram illustrating a hydrophobic embodiment of the microfluidic serial dilution platform based well-plate using an oil-free immiscible phase driven by manual or electronic pipettors used a hemocytometer.
  • FIG. 9C is a chart illustrating advantages of hydrophobic embodiment of the microfluidic serial dilution platform based well-plate using an oil-free immiscible phase driven by manual or electronic pipettors versus a standard hemocytometer.
  • FIGS. 10A and 10B are diagrams illustrating an embodiment of a microfluidic serial dilution platform based well-plate using an oil-free immiscible phase driven by manual or electronic pipettors with a cover on top of the well-plate to maintain humidity and control evaporation from the fluidic trap.
  • FIG. 10C is a graph illustrating average evaporation rates using the embodiment shown in FIGS. lOA and 10B.
  • FIG. 11 shows a diagram of an embodiment of a microfluidic serial dilution platform based well-plate of the disclosed invention, which has two inlets and can be driven by manual or electronic pipettors.
  • FIG. 12 shows a diagram of an embodiment with multiplexed well-plate for multiplexed screening of delivery vehicle for gene therapy using mixing with static filled traps (nanoliters- microliters).
  • FIGS. 13A-13D show shown are embodiments on in-vitro screening of cells against drugs.
  • FIG. 14 shows trapped culture and maintain suspension cells with flow after fluidic constriction is filled with fluid.
  • FIG. 15 shows a flowchart for a method of operating a microfluidic serial dilution platform based well-plate of the disclosed invention.
  • FIG. 16 shows a flowchart for a method of operating a microfluidic serial dilution platform based well-plate of the disclosed invention for in-vitro screening of cells against drugs.
  • FIGS. 17A-17B show a top view of the fluidic trap and a cross-sectional view of section A- A’ shown in FIG. 17 A, respectively.
  • Embodiments overcome the problems described above. For example, embodiments provide a passive method based device for storage and serial dilution of fluids in a microfluidic storage network. Embodiments include a microfluidic platform based well-plate using an oil-free immiscible phase driven by manual or electronic pipettors. Embodiments provide a novel mechanism for storage and serial dilution of droplets in a hydrophilic microfluidic device using conventional pipetting system.
  • Embodiments overcome the problems of the prior art. For example, by using an airbased immiscible phase for droplet trapping, embodiments eliminate the possibility of a reaction between typically-used oil-based immiscible phases and trapped fluid. Likewise, the novel serial dilution by the formation of micro-droplets in the network provided by embodiments prevents the composition of the diluting slug from being changed. Additionally, the elimination of precise fluidic control allows the storage and dilution of droplets in the network to be accomplished by conventional pipetting systems. The incorporation of these networks into a well-plate based device that integrates with multi-head robotic and manual pipettors eliminates the need for any additional capital equipment.
  • Embodiments provide a similar or higher throughput compared to currently available robotic high-throughput screening systems. Moreover, embodiments provide the ability to remove fluids trapped in square hydrodynamic traps with a reversal of the direction of flow in one step without the formation of emulsions. Embodiments also enable uniform trapping of cells and other particles suspended in a fluid over the entire network of traps. This is particularly important in cell-based screening studies.
  • FIGS. 1A-D shown are four hydrophilic embodiments of a microfluidic serial dilution platform based well-plate 100 using an oil-free immiscible phase driven by manual or electronic pipettors.
  • Each embodiment of well-plate 100 includes a network of one or more fluidic traps 102.
  • the drawings shown in FIGS. 1A-1C illustrate only a portion a well-plate and the network of fluidic traps 102 on the well-plate.
  • FIG. 1A shows an embodiment of well-plate 100 with a parallel network of four (4) traps 102 with associated bypass channels 104.
  • the well-plate with such network may include multiple repeating networks configured as such.
  • IB shows an embodiment of well-plate 100 with a series network of four (4) traps 102 with associated bypass channels 104.
  • the well-plate with such network may include multiple repeating networks configured as such.
  • FIG. 1C shows an embodiment of well-plate 100 with a single trap 102 with associated bypass channels 104.
  • the well-plate may include repeating single trap networks.
  • FIG. ID shows an embodiment with 176 traps 102 with associated bypass channels 104 connected in a series network. This last embodiment illustrates that the number of traps can be chosen and configured to meet requirements based on the application.
  • the microfluidic serial dilution platform based well-plate designs shown herein may be situated on a chip or other suitable substrate.
  • the well-plates may be made from, for example, poly dimethyl siloxane (PDMS), cyclic olefin copolymer (COC), poly carbonate (PC), or similar materials.
  • PDMS poly dimethyl siloxane
  • COC cyclic olefin
  • an embodiment includes a fluidic inlet channel 106 connected to traps 102 and associated bypass channels 104 (each trap 102 and bypass channel 104 together forming a well 108) in parallel arrangement.
  • Fluidic inlet channel 106 includes an interface for pipettor, pipette or other fluid driving mechanism.
  • the embodiment shown further includes main channel 110, including straight channel portion 112, connecting individual wells 108 together in parallel circuit as shown, and hydrophilic capillary constriction channels 114 with, e.g., 40 pm width (small constriction inlet) connecting main channel 110 directly to traps 102.
  • square fluidic traps 102 have, e.g., 1 mm x 1 mm sides and bypass channels 104 have, e.g., 200 pm width.
  • main channel extension 116 connects traps 102 to fluidic outlet 118.
  • Each trap 102 is an enclosed chamber with openings where main channel 110 and hydrophilic capillary constriction channels 114 connect with trap 102.
  • the traps 102 shown in FIGS. 1A-1D are square traps, embodiments may include any variety of shaped traps, including circular or semi-circular traps.
  • covers cover that cover the entire well-plate and the network of fluidic traps 102 on the well-plate (see FIG. 10 for an example of a cover). The cover encloses each trap 102, as well as the various channels, creating the enclosed chamber.
  • the cover is also hydrophilic in nature.
  • an embodiment includes fluidic inlet channel 106 with an interface for pipettor, pipette or other fluid driving mechanism, straight channel portion 112 of main channel 110 extending from inlet 106 and, with rest of main channel 110, connecting inlet 106 to fluidic traps 102 and associated bypass channels 104 (together forming a well 108) in a series circuit with each other, and hydrophilic capillary constriction channels 114 with, e.g., 40 pm width (small constriction inlet), connecting main channel 110 directly to traps 102.
  • Bypass channels 104 may be fabricated with a, e.g., 200 pm width, and fluidic traps 102 may be fabricated as square, e.g., 1 mm x 1 mm, fluidic traps 102.
  • Embodiment may include enlarged main channel portions 115 to optimize a reduction of air invading into the fluidic trap 102 and main channel extension 116 connecting traps 102 to fluidic outlet 118.
  • FIG. 1C shown is an embodiment with a fluidic inlet channel 106 with an interface for pipettor, pipette or other fluid driving mechanism, main channel 110 connecting fluidic trap 102 to inlet, hydrophilic capillary constriction channel 114 with, e.g., 40 pm width (small constriction inlet), connecting main channel 110 to trap 102, enlarged channel 115 to minimize invasion of air into the fluidic trap 102, and main channel 110 connecting well or trap 102 to fluidic outlet 118.
  • a fluidic inlet channel 106 with an interface for pipettor, pipette or other fluid driving mechanism
  • main channel 110 connecting fluidic trap 102 to inlet
  • hydrophilic capillary constriction channel 114 with, e.g., 40 pm width (small constriction inlet)
  • main channel 110 connecting well or trap 102 to fluidic outlet 118.
  • each trap 102 and bypass channel 104 together form well 108 and adjacent trap 102 and bypass channel 104 combinations are connected by main channel 110 and various portions or extensions thereof.
  • FIG. IE shown is an entire well-plate 100 with a uniform network of ninety-six fluidic traps. Visible is cover 180, fluidic inlets 106 and fluidic outlets 118 for each fluidic trap network. Fluidic inlets 106 and fluidic outlets 118 extend through cover 180.
  • FIGS. 2A-2C shown are schematic diagrams illustrating a fluid trapping process using embodiments of a microfluidic serial dilution platform based well-plate using an oil-free immiscible phase driven by manual or electronic pipettors.
  • fluid 200 first enters the bypass channel 204, through main channel 210 from direction of fluidic inlet (not shown), enhancing or increasing the hydrodynamic resistance in the bypass channel 204, and stops at the larger constriction of the main channel 210 and unfilled fluidic square trap 202.
  • unfilled hydrophilic capillary constriction channel 214 is also shown in FIG. 2A.
  • fluid 200 is shown now filling the fluidic square trap 202 through the smaller constriction (hydrophilic capillary constriction channel 214) connected upstream to square trap 202.
  • Fluid 200 in bypass channel 204 now stops at mouth of the trap 202.
  • air 220 is then passed through the network of fluidic traps 202.
  • the air 220 passes through bypass channel 204, removing remaining excess fluid 200 from the bypass channel 204 into main channel 210 and leaving a fragmented droplet of fluid 200 trapped in the hydrodynamic trap 202.
  • Air 220 will continue to pass through main channel 210 to next well (not shown), removing excess fluid 200 from bypass channel of next well, and so on through network of traps 202 towards fluidic outlet (now shown).
  • FIG. 3 shown are a series of images illustrating the trapping process described above and illustrated in FIGS. 2A-2C.
  • FIG. 3 shown are a series of micrograph images 1-6 of the series of events that leads to the fragmentation of the long fluid slug and the trapping of fluid in the square trap.
  • Pipettor 330 connected to fluidic inlet channel (e.g., see fluidic inlet channel 106 in FIGS. 1A-D) with an interface for pipettor 330, pipette or other fluid driving mechanism is shown in these images.
  • FIGS. 4A-D shown are schematic diagrams illustrating a serial dilution process using an embodiment of microfluidic serial dilution platform based well-plate using an oil-free immiscible phase driven by manual or electronic pipettors. Steps shown in FIGS. 4A-4D take place after the fluid trapping process described above. Together, the fluid trapping process and serial dilution process, shown in FIGS. 2A-2C and 4A-4D, comprise a significant portion of the operation of the microfluidic serial dilution platform based well-plate using an oil-free immiscible phase driven by manual or electronic pipettors.
  • diluting stream or fluid (white) 425 first displaces air 420 and enters the main channel 410, then enters the constriction (hydrophilic capillary constriction channel) 414 upstream of the network, invading a part of a first fluid-filled trap 402A, diluting the fluid 400 in the trap 402.
  • Fluid 400 is ejected from the trap 402A into the main channel 410 due to the displacement of fluid 400 from the trap 402A by the diluting fluid 425.
  • the portion of fluid 400 that exited the first trap 402A now enters the second trap 402B and causes a portion of fluid 400 to leave the second trap 402B.
  • trap 402A filled with diluted fluid 400’, ejected fluid 400 in main channel 410, ejected fluid 400 from first trap 402A that has entered second trap 402B, connected in series, through hydrophilic capillary constriction channel 414 of second trap 402B, and fluid ejected from second trap 402B into main channel 410.
  • diluting fluid 425 As an increasing amount of diluting fluid 425 enters the upper section of the first trap 402A a portion of the diluting stream 425 now enters the second trap 402B and a series of micro-droplets are formed that enter successive traps causing a serial dilution.
  • diluted fluid 400’ in first trap 402A diluting fluid 425 filling upper section of first trap 402A and entering second trap 402B, diluting fluid 425 filing capillary section 414 of the second trap 402B, and as air is injected into device following the diluting plug, causing fluidic droplets 435 in air phase to form.
  • air is pumped into the channel 410 following the diluting stream, excess diluting fluid 425 is carried away from the channel into the outlet.
  • FIG. 4D shown is air-filled bypass channel 404 as air 420 is driven into bypass channels 404 after the diluting plug, the diluted fluid 400’ in first trap 402A, the diluted fluid 400’ in second trap 402B and main channel 410 with excess fluid 425 flushed out with air phase.
  • FIG. 5 shown are a series of images illustrating the serial dilution process described above with reference FIGS. 4A-4D. Shown in FIG. 5, are five (5) micrograph images of the series of events that leads to serial dilution of the trapped droplets.
  • image 2 ejected fluid from first trap enters 1 second trap connected in series, bypass channel 2 is filled with air, and fluid is ejected 3 from second trap.
  • image 3 diluting fluid enters 4 capillary section of first trap, fluid in first trap 5 is now diluted, ejected fluid from second trap forms a fluid drop 6 in air phase.
  • first trap 10 has the highest amount of diluting fluid
  • second trap 11 has a comparatively lower amount of diluting fluid compared to first trap
  • a third trap 12 has the lowest amount of diluting fluid compared to first trap and second trap.
  • Embodiments enable dilution of different magnitudes carried out in a trapping network.
  • embodiments enable cell cultures to be carried out in the traps, such as breast cancer cells cultures in a matrigel environment in the traps.
  • Embodiments provide a new method for the trapping and dilution of nano to pico liter droplets stored in microfluidic networks.
  • the fluid is pumped in through capillary action and the applied pressure drop of a pipettor. The fluid is driven into the channel in the direction where the smaller constriction of the trap is upstream (as opposed to the conventional system where fluid enters the trap through the larger constriction).
  • the fluidic slug then fills the entire trap by flowing through this constriction (see FIGS. 2 and 3). Consecutive traps in the network are also filled in this manner. Air is then used as the immiscible phase to fragment the long fluidic slug and remove excess fluid contained in the bypass channels.
  • an immiscible oil phase which can cause adverse results in some applications, although if required an immiscible oil phase can also be used to fragment the fluidic slug in the trap by flowing it through the network at a lower pre-defined flow rate.
  • Embodiments of the method utilized by embodiments described herein allows for the slug to be trapped and fragmented using larger pressure drops (which are typical for off-the shelf pipetting systems) compared to currently available solutions that require optimization of flow rates or additional external pumping systems (such as syringe pumps).
  • Embodiments also dilute fluids stored in the traps using a novel dilution method that produces fluidic drops in-air, in-situ in the device. This method with optimization can prevent cross-contamination between compositions of fluids in the various stationary traps.
  • Embodiments of the device described herein can also be used for the three-dimensional culture of cells in the hydrodynamic traps using an appropriate polymer matrix. These cultured cells can then be serially diluted and screened against drugs in an HTS fashion.
  • a hydrophilic channel microfluidic based network with square (or other shaped) storage traps to store and dilute nano-liter droplets.
  • These droplets are produced in-situ in these square traps by flowing a fluidic slug through the fluidic network in a direction where with the smaller capillary junction is upstream of the large entrance channel at the traps.
  • This injection of fluid into the channels is achieved at high flow rates using a commercially available pipetting system.
  • This is followed by fragmenting the long slug of fluid using an immiscible air-phase that removes excess fluid from the channels causing nano to pico liter droplets of fluid to be contained in the square traps (see FIGS. 2 and 3).
  • the need for an immiscible oil-phase is, therefore, completely eliminated.
  • Embodiments of the method for dilution causes the diluting stream to directly enter into part of the square ( or other shaped) trap ( amount can be varied based on volume, size of trap and flow rate of the diluting stream) (see FIGS. 4 and 5).
  • the injection of the diluting stream into the trap causes part of the reagent in the trap to be displaced, which in turn causes the formation of a fluid droplet in the air filled channels (see FIG. 4).
  • This droplet then enters the second trap (where composition is the same as first trap) and causes another fluid-air drop to be produced (see FIG. 5).
  • This mechanism therefore, can produce serial dilutions without causing contamination of the diluting stream or of the reagents in the traps downstream.
  • Both the trapping and serial dilution of the droplets in the device are performed using conventional pipetting systems without the need for precise fluid control or lower flow rates.
  • FIGS. 6A-6B shown are schematic diagrams that illustrate trapping using this such an embodiment. These diagrams again illustrate only a portion of a well-plate and a portion of the network of traps on the well-plate.
  • the fluid is first trapped by injecting it into the channel towards the larger mouth of the hydrodynamic trap that is filled initially with air.
  • the channels are hydrophobic while the base cover used to enclose these channels is hydrophilic in nature.
  • the fluidic slug fills the trap while not entering the hydrophobic capillary section that has a larger hydrodynamic resistance than the fluidic trap and is filled with air. This capillary section filled with air, therefore, acting as an air valve.
  • the hydrodynamic resistance of the trap is enhanced and excess fluid from the trap then moves into the bypass channel. This fluid subsequently enters other traps in the network and fills them in the same method as described previously.
  • an outlet for fluid 618 fluid filled first hydrodynamic trap 602, bypass channel of fluidic network 604, capillary section of hydrodynamic trap filled with air 614, inlet for fluid driven by pipette or other fluid driving mechanism 606, structure of the fluidic network that is hydrophobic in nature and base 650 of the fluidic network, that is used to cover the hydrophobic structure, which is hydrophilic in nature.
  • FIG. 6B shown is an outlet for fluid 618, diluted filled first hydrodynamic trap 602, diluting fluid injected from the inlet 606, diluting fluid coalescing with fluid trapped in hydrodynamic trap 602, inlet for fluid driven by pipette or other fluid driving mechanism 606, structure of the fluidic network that is hydrophobic in nature and hydrophilic base 650 of the fluidic network that is used to cover the microfluidic hydrophobic structure.
  • the various features described herein with reference to the hydrophilic embodiments may be incorporated into the hydrophobic embodiment described in FIGS. 6A-6B.
  • FIGS. 7A-7C shown are graphs illustrating data from dilutions carried out in the hydrophilic design of FIG. 1C using a MatrixTM sixteen (16) channel electronic pipettor from Thermofisher Scientific.
  • the amount of dilution in the microfluidic chambers can be varied by varying either: (a) the volume of the diluting fluid stream, with the results shown in FIG. 7A; (b) the number of diluting plugs, with the results shown in FIG. 7B and 7C.
  • the co-efficient of variation (CV) of the dilution is typically ⁇ 5%.
  • FIGS. 8A-8B shown are graphs illustrating data from dilutions carried out in a hydrophobic design of FIG. 1C using a MatrixTM sixteen (16) channel electronic pipettor from Thermofisher Scientific.
  • the graph in FIG. 8A illustrates the varying amount of dilutions that can be accomplished using varying volumes of diluting plugs and varying numbers of such diluting plugs.
  • the graph in FIG. 8B illustrates the varying amounts of dilutions that can be accomplished using varying volumes of diluting plugs.
  • FIGS. 9A-9C tables and diagrams are shown illustrating the embodiments of a microfluidic serial dilution platform based well-plate that may also be used as a hemocytometer.
  • the embodiment shown is a hydrophobic design (e.g., see FIGS. 6A-6B).
  • FIG. 9A a table is shown illustrating cell counts made with a standard hemocytometer as well as an embodiment of a microfluidic serial dilution platform based wellplate.
  • the table illustrates two cell counting experiments: (1) an experiment performed with a standard hemocytometer diluted with trypan blue, a dye used to determine between live/dead cells, and a microfluidic serial dilution platform based well-plate without dilution by trypan blue and (2) an experiment performed with a standard hemocytometer diluted with trypan blue and a microfluidic serial dilution platform based well-plate with dilution by trypan blue.
  • the cell counting formula used is a common protocol associated when using a hemocytometer, where the cell count is multiplied by both the dilution factor and the conversion factor.
  • a cell suspension may be loaded using either a manual or electronic pipette into a gridded microfluidic trap.
  • the cells within the traps were counted and used to calculate the total population.
  • the cell count using a standard hemocytometer with trypan blue took six minutes and twenty -two seconds (6:22) and produced counts of 180, 182, 225, and 83 totaling to 670.
  • the count became 670e 4 which is the same as 6.7xl0 6 cells/ml.
  • the total count from the standard gridded hemocytometer resulted in 20.1x10 6 total cells.
  • the count using an implementation of microfluidic serial dilution platform based well-plate 900 with traps gridded into quadrants took only thirty seconds (0:30). Within six traps, the quadrants totaled to 681, 659, 667, 610, 641, and 734, producing an average of 665 cells/0.1 pl, which converts to 6653 cells/pl, equaling 6.65xl0 6 cells/ml. With the same suspension volume, this method calculated to a total of 19.9x10 6 cells. The results for the second experiment were obtained using the same methods and produced values that were equally close.
  • microfluidic serial dilution platform based well-plate shows excellent reproducibility and presents further advantages over conventionally used hemocytometers one such being the time required, as illustrated in FIG. 9C.
  • microfluidic serial dilution platform based well-plate may perform various assays completely on-chip (i.e., on a chip or other suitable substrate containing (how many traps within a given chip. For example, experiments showed Clenbuterol ELISA assays may be performed completely on-chip using an electronic pipette.
  • ELIS A-based assays with embodiments of the present invention include: (a) reduced time to conduct tests (nearly one-third the time compared to conventional methods; (b) higher sensitivity due to an increased surface to volume ratio; and (c) increased accuracy due to a conserved volume that does not change.
  • FIGS. 10A-C shown is an embodiment of microfluidic serial dilution platform based well-plate that controls the evaporation of fluid from the fluidic traps. If evaporation of fluid from the traps needs to be controlled as is the case when performing cell based assays the device is configured as shown.
  • FIG. 10A shown is a top view of this configuration which includes a hole 1100 drilled into each trap 1002 of the microfluidic network (specifically, hole 1100 is drilled through cover enclosing trap 1002). In this manner, trap 1002 is not fully enclosed by cover.
  • this hole 1100 is covered at all times while microfluidic serial dilution platform based well-plate is in use by a material different than the cover.
  • cover e.g., cover 1200
  • hole 1100 which extends through cover
  • the covered hole maintains humidity in the trap to prevent evaporation of fluid in the trap.
  • the fluidic trap 1002 shown in FIG. 10A is not square; rather trap 1002 has a rounded or semi-circular bottom.
  • FIG. 10B shown is a perspective view of this embodiment of microfluidic serial dilution platform based well-plate 1000.
  • a reservoir 1150 situated on well-plate 1000 and filled with fluid, such as water, at a fixed pressure, surrounds the microfluidic network.
  • fluid such as water
  • a cover 1200 is placed over the microfluidic serial dilution platform based well-plate covering the inlet 1006, outlet 1018, the hole 1100 and the reservoir 1150 (note cover 1200 is shown in suspended above microfluidic serial dilution platform based well-plate; in use, it would be directly in contact and actually cover microfluidic network).
  • FIG. 10C shown is a graph depicting the amount of evaporation in the well after various time points using the embodiment illustrated in FIGS. 10A-B. As can be seen the maximum evaporation is less than fifteen percent (15%) after a time period of seventy -two (72) hrs.
  • FIG. 11 shown is a diagram of an embodiment of a microfluidic serial dilution platform based well-plate 2000 of the disclosed invention, which can be driven by electronic pipettors.
  • the well-plate 2000 may be formed of wells 2010a, 2010b, 2010c that are connected in series.
  • Well 2010a includes a bypass channel 2003a, a fluidic trap 2004a, and a capillary constriction channel 2005a.
  • the well-plate 2000 includes a plurality of inlets 2001a, 2001b.
  • the well 2010a is connected to the inlets 2001a, 2001b through a main channel 2002a, and may be connected to another well 2010b downstream or outlet 2006 through a main channel 2002b.
  • Capillary constriction channel 2005a is connected to the fluidic trap 2004a in series.
  • the capillary constriction channel 2005a is connected to an outlet side of the fluidic trap 2005a, but in another embodiment, the capillary constriction channel 2005a may be connected to an inlet side (toward the inlets 2001a, 2001b) of the fluidic trap 2005a.
  • Main channels 2002a, 2002b, 2002c, 2002d with a plurality of portions connect the inlets 2001a, 2001b to the plurality of fluidic traps 2004a, 2004b, 2004c, associated hydrophilic capillary constriction channels 2005a, 2005b, 2005c and associated bypass channels 2003a, 2003b, 2003c, and the outlet 2006.
  • the fluidic traps 2004a, 2004b, 2004c have larger widths than the associated bypass channels 2003a, 2003b, 2003c to trap fluid in said each fluidic trap while the fluid is removed from the associated bypass channel.
  • the constriction channels 2005a, 2005b, 2005c have smaller widths than the associated fluidic traps 2004a, 2004b, 2004c and the associated bypass channels 2003a, 2003b, 2003c.
  • the constriction channels 2005a, 2005b, 2005c are hydrophilic or hydrophobic channels.
  • the bypass channels 2003a, 2003b, 2003c and the associated fluidic trap 2004a, 2004b, 2004c are connected in parallel.
  • the constriction channels 2005a, 2005b, 2005c and the associated fluidic trap 2004a, 2004b, 2004c are connected in series.
  • FIG. 11 shows three wells 2010a, 2010b, 2010c, but the number of wells are not limited. As shown in FIG. ID, a plurality of wells may be connected in series to form a network of the wells.
  • the well-plate 2000 has two inlets 2001a, 2001b that allow simultaneous flow of two fluid streams into the well-plate 2000.
  • FIG. 11 shows two inlets 2001a, 2001b.
  • the well-plate 2000 of the disclosed invention may have more than two inlets based on applications to allow multiple fluid streams to enter the well-plate 2000 simultaneously.
  • This structure of the embodiment shown in FIG. 11 allows the two or more fluids that enter into the well-plate 2000 to mix more efficiently than compared to when fluids mixing under similar hydraulic diameter channels. This can be useful to form nanoparticles that encapsulate gene delivery vehicles such as sRNA, mRNA under much lower shear stress/pressure-drop/shear rate conditions compared to other methods which might cause the mRNA to degrade at harsh mixing conditions.
  • one stream of fluid can carry alcohol along with dissolved polymer or other encapsulating agent, and another stream of fluid can be aqueous fluid containing load or drug.
  • another stream of fluid can be aqueous fluid containing load or drug.
  • the lengths of the hydrophilic or hydrophobic constriction channels can be made shorter or longer, and the widths of the hydrophilic or hydrophobic constriction channels can be different. In other words, the lengths and/or widths of some or all of the constriction channels 2005a, 2005b, 2005c may be different from each other.
  • the fluidic trap 2004a may have a recess 2007 at a bottom of the fluidic trap 2004a. With reference to FIGS. 17A-17B, shown are a top view of the fluidic trap and a cross-sectional view of section A-A’ of FIG. 17A, respectively, showing an exemplary structure of the recess 2007.
  • the recesses 2007 may formed at bottoms of other fluidic traps 2004a, 2004b, 2004c.
  • the multiplexed well-plate 2100 includes a plurality of microfluidic serial dilution platform based well-plates 2102a, 2102b, 2102c connected in parallel.
  • Each serial platform 2102a, 2102b or 2102c may include one or more wells 2010a connected in series.
  • Each well 2010a includes fluidic trap 2004a and associated bypass channel 2003a and associated capillary constriction channel 2005a.
  • the multiplexed array of wellplates 2102a, 2102b, 2102c are connected to an central input channel 2101 that may include one or more inlets to introduce fluid streams sequentially or simultaneously into the multiplexed well-plate 2100.
  • Wells 2010a in well-plates 2102a, 2102b, 2102c may have different configurations.
  • capillary constrictions channels 2005a may have different lengths and/or widths
  • fluidic traps 2004a may have different sizes.
  • the trap in order to achieve high throughput screening of nanoparticle delivery vehicles using low sample volumes, the trap maybe first filled with the drug/therapeutic to be delivered followed by flowing the non-aqueous stream containing the enclosing polymer.
  • the traps can be “multiplexed” using a central splitting network to conduct high throughput studies with samples trapped in wells ranging in volume from nano-liters to a few microliters. This maybe particularly important in designing delivery vehicles for gene therapy (e.g. mRNA).
  • FIGS. 13A-13D shown are embodiments on in-vitro screening of cells against drugs.
  • the cells are loaded in the fluidic traps, when the associated capillary constriction channels are filled with air (FIG. 13A), and are allowed to attach and culture in the fluidic traps (FIG. 13B).
  • the constriction channels work as valves when they are filled with air due to the large surface tension at the micro scale.
  • the capillary constriction channels may be hydrophobic.
  • Dissolvable beads are loaded into the traps after cells are cultured (FIG. 13C).
  • Dissolvable beads containing the drug can be loaded by sieving when the valve is closed (while the constriction channels are filled with fluid), allowing one bead per chamber (fluidic trap), as shown in FIG. 13D.
  • the dissolvable beads can be prepared using the method described referring to FIG. 12.
  • the traps are isolated after passing an immiscible phase. Each trap then is independent of the others in series since beads contain different compounds.
  • the polymer concentration of the beads can be tailored to have a pharmacokinetic (PK) like profile allowing high throughput screening of drugs such as protein degraders whose pharmacological effects differ on the time course of the reaction.
  • PK pharmacokinetic
  • FIG. 14 shown is trapped culture of suspension cells with flow after fluidic constriction is filled with fluid.
  • Arrow refers to suspension cells in a recessed part of the trap.
  • the recessed part allows fluid to flow over the cells filled in the recessed part. Allowing constant perfusion of suspension cells for kinetic drug screening.
  • the traps after they are formed eventually close e.g. for cell culture such that when fluid is re-introduced it flows over the adherent cells or suspension cells that are first introduced and is trapped where the trap has recess 2007 in the middle allowing the suspension cells to settle after any fluid introduced into it flows “over it” as it is in the recess (as shown in FIG. 14).
  • 3D culture of cells is also possible with commercially available supports like Matrigel.
  • the method is particularly suited for screening degraders (Proteolysis Targeting Chimeras), for example, when there is a pharmacokinetics and pharmacodynamics (PK-PD) disconnect and washout is required to determine the catalytic activity of the drug degrading the proteome of interest which could be labelled through clustered regularly interspaced short palindromic repeats (CRISPR) based methods in order to identify rate of degradation.
  • PK-PD pharmacokinetics and pharmacodynamics
  • a first fluid and a second fluid are simultaneously introduced into a first inlet and a second inlet, respectively, block 2201.
  • the first and second fluids are caused to enter into a bypass channel associated with a fluidic trap, block 2202.
  • the bypass channel and the associated fluidic trap are connected in parallel.
  • the first and second fluids are caused to enter into the fluidic trap until the fluidic trap is filled with the first and second fluids, block 2203.
  • the first and second fluids are mixed in the fluidic trap, block 2204.
  • the first fluid may include alcohol with dissolved polymer or encapsulating agent and the second fluid may be an aqueous fluid containing load or drug.
  • the polymer or encapsulating agent from the first fluid and the load or drug from the second fluid may be self-assembled in the fluidic trap forming nanoparticles with drug or load encapsulated.
  • the first fluid may include media and the second fluid may include drug. The method may further includes controlling flowrates of the first fluid and the second fluid while introducing the first and second fluids into the first and second inlets, respectively, to control a concentration of the drug in the media.
  • FIG. 16 shown is a flowchart for a method 2300 of operating a microfluidic serial dilution platform based well-plate of the disclosed invention for in-vitro screening of cells against drugs.
  • Cells are introduced in fluidic traps connected in series, block 2301. The cells are loaded in the fluidic traps while capillary constriction channels associated with the fluid traps are closed, block 2302.
  • Cell culture is performed for the cells loaded in the fluidic traps, block 2303.
  • Dissolved beads containing drugs are introduced into the fluidic traps, block 2304. The dissolved beads are loaded in the fluidic traps, block 2305.
  • the fluidic traps containing the beads are isolated, block 2306.
  • the fluidic traps may be constructed to have recesses formed at bottoms of the fluidic traps and the cells are loaded in the recesses of the fluidic traps.
  • the capillary constriction channels are closed by filling the capillary constriction channel with air.
  • the fluidic traps may be isolated by filling the bypass channels with air.

Abstract

L'invention concerne une plaque à puits basée sur une plateforme de dilution en série microfluidique faisant appel à une phase immiscible exempte d'huile entraînée par des pipetteurs manuels ou électroniques. La plaque à puits comprend une pluralité de pièges fluidiques (2004a-2004c), une pluralité de canaux de constriction capillaires hydrophiles (2005a-2005c) et une pluralité de canaux de dérivation (2003a-2003c). Chacun des canaux de dérivation est associé à l'un des pièges fluidiques, chacun des canaux de constriction capillaires hydrophiles est associé à l'un desdits pièges fluidiques, et chacun des multiples pièges fluidiques est associé à l'un desdits canaux de dérivation et à l'un desdits canaux de constriction capillaires hydrophiles. La plaque à puits comprend en outre un orifice d'entrée (2001a, 2001b), un orifice de sortie (2006) et un canal principal (2002a-2002d) comportant une pluralité de parties qui relient l'orifice d'entrée à la pluralité de pièges fluidiques, aux canaux de constriction capillaires hydrophiles associés et aux canaux de dérivation associés et à l'orifice de sortie.
PCT/US2021/064512 2020-12-28 2021-12-21 Plaque à puits basée sur une plateforme de dilution en série microfluidique faisant appel à une phase immiscible exempte d'huile entraînée par des pipetteurs manuels ou électroniques et procédé de fonctionnement WO2022146770A1 (fr)

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US17/134,737 US20210114022A1 (en) 2015-01-23 2020-12-28 Microfluidic serial dilution platform based well-plate using an oil-free immiscible phase driven by manual or electronic pipettors

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US11759781B2 (en) 2017-11-10 2023-09-19 Unchained Labs Integrated fluidic circuit and device for droplet manipulation and methods thereof
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