Patent Application
20190143328
This specification generally relates to microfluidic systems.
Individual particles, such as cells, within a fluid sample can be difficult to analyze within high-throughput microfluidic systems when large number of cells are included in the sample. In addition, individual cells must initially be isolated from the fluid sample to properly analyze cellular contents such as DNA, RNA, and/or proteins, depending on the type of test performed. In some instances, individual cells can also need to be isolated in pre-defined geometric arrangements to enable automated processing and analysis. Common isolation techniques often include diluting a fluid sample in a manner such that only a single cell can coincide with a single micro-well of a micro-well-plate. However, such techniques lack sufficient accuracy and speed, and primarily rely upon statistics, reducing the chances of obtaining repeatable results.
Although high-throughput microfluidic systems have been proposed to overcome challenges associated with single cell analysis, such systems still have various limitations. For instance, while various geometric arrangements of micro-wells can be used to increase capture of individual cells, these techniques are often incapable of capturing both individual cells and cell clusters within a single fluid sample. In addition, designs of such systems are often incapable of capturing rare cells with relatively low concentrations in a fluid. Another limitation impacting the use of these systems is that they are often unable to allow access to captured cells, preventing the ability to directly manipulate captured cells without risk of reducing cell viability.
The systems and techniques described herein can be used in many scientific and clinical studies of disease conditions where analyzing individual cells separately is critical to understand and detect cell-to-cell variations. For instance, the systems and techniques can be used to improve studies of cancers that have tumor heterogeneity, which can often require identifying the presence and nature of multiple tumors. As an example, if multiple cells are combined and lysed, then their genetic contents will mix and information pertaining to cell-to-cell variations will be compromised and/or lost. However, if they can be isolated, captured, and analyzed separately using the systems and techniques described herein, information relating to cell-to-cell variations can be retained for analysis. This applies to cells obtained from fluids (e.g. blood, urine, and saliva) and also cells obtained by grinding solid tissues, e.g., tumor tissue, chemically or mechanically.
Accordingly, the innovative aspects described throughout this disclosure include devices, systems, and methods that are capable of capturing individual particles, e.g., cells, cell clusters, and/or other types of particles, generally “target entities,” within a fluid sample that is flowed across or introduced onto a micro-well array device (also referred to herein as a “micro-well chip”), e.g., arranged in, or as a part of, a microfluidic chamber. The micro-well chip includes a substrate, e.g., a thin plate, having a surface with one or more arrays of micro-wells in which the micro-wells have a size selected to enable a particular size of target entity to enter the micro-wells. In one implementation, all of the micro-wells are in one array and all have approximately the same size, e.g., within plus or minus five percent of a selected size. In other implementations the micro-well chip can have two or more arrays of micro-wells in which the micro-wells in a given array are all approximately the same size, but the micro-wells in one array have a different size from the micro-wells in another array.
As used herein, the term “size,” when referring to a micro-well, can be any one or more of a diameter, cross-sectional area, depth, shape, and/or total volume of the micro-well.
For example, a micro-well chip can have two arrays of micro-wells in which a first array of smaller micro-wells is located on the surface of the substrate near a first location, e.g., a first end, of the surface, e.g., closer to an inlet port of a microfluidic chamber, to capture individual target entities, e.g., cells, and in which a second array that includes relatively larger micro-wells is located on the surface closer to a second location, e.g., a second end (e.g., “downstream” of the first array) and closer to an outlet port of a microfluidic chamber, to capture larger cells or cell clusters that do not fit into the upstream smaller micro-wells.
The systems can also include a magnet component that can be used to apply a flow-independent variable magnetic force to direct and control the movement of target entities that are magnetic or made to be magnetic. For example, the magnet component is used to move target entities into the micro-wells and/or to hold the target entities in the micro-wells, without a need to use a wash step to avoid false-positive detection of non-specific target entities, e.g., cells, which can often lead to unintended loss of specific target entities.
As used herein, the term “magnetic” when referring to target entities means either inherently magnetic, paramagnetic, or superparamagnetic, or made to be magnetic, paramagnetic, or superparamagnetic, by the application of a magnetic or electric force. The term magnetic when referring to target entities also refers to target entities that are, or are made to be, magnetic, paramagnetic, or superparamagnetic by being attached, i.e., linked, to a bead or particle that is itself magnetic, paramagnetic, or superparamagnetic.
In different implementations, the magnitude of the magnetic force is modulated to increase or decrease the target entity, e.g., cell, settling rate, and the direction of the applied magnetic field can be adjusted to cause magnetically induced target entity movement along one or two dimensions of the surface of the micro-well chip. In this regard, the micro-well arrangement of the plate and the application of the variable magnetic field can be used to more efficiently capture magnetized cells and cell clusters with higher accuracy and consistency.
In one implementation, target entities and particles (e.g., smaller and larger cells or cell clusters) in a sample fluid initially encounter a first array with smaller micro-wells before encountering one or more additional arrays with larger micro-wells. For example, smaller target entities can enter into the micro-wells of the first array, but larger target entities cannot, because they are too large to pass into the openings of micro-wells in the first array. During a typical capture operation using this implementation, a magnet is moved or swept, e.g., horizontally, beneath the micro-well chip to direct the larger target entities that have not been captured across the surface of the micro-well chip towards the second array with larger micro-wells. In some implementations, the remaining target entities that are too large to be situated in the micro-wells of the second array are then directed toward the micro-wells of a third array by moving the magnet downstream in a similar manner. To achieve this, target entities can be flowed into the chamber while the magnet is substantially underneath the first array, so as to place all target entities on the first array. The flow can then be stopped or reduced significantly to prevent smaller entities from accidentally reaching the larger micro-wells of subsequent arrays. Once small target entities are captured in the micro-wells of the first array, flow can be restarted or increased to assist the magnet in moving the remaining larger target entities into the next array with larger wells downstream, and so on.
The target entities, e.g., cells, can be inherently magnetic, paramagnetic, or superparamagnetic, or can be made magnetic, paramagnetic, or superparamagnetic by attaching to the target entity one or more beads or particles that are themselves magnetic, paramagnetic, or superparamagnetic. Thus, the combined complex of target entity and beads or particles is then magnetic, paramagnetic, or superparamagnetic, and can be manipulated with a magnet arranged adjacent to the micro-well chip, e.g., below, on the sides, or above the micro-well chip, as described in further detail herein.
In a first general aspect, the disclosure features a micro-well array device for capturing target entities that are, or are made to be, magnetic. The first micro-well array device includes a substrate including a surface comprising a plurality of micro-wells arranged in one or more arrays on the surface where a first array of micro-wells is arranged at a first location on the surface. Second and subsequent arrays, if present, are arranged sequentially on the surface at second and subsequent locations, where when a liquid sample is added onto the substrate and caused to flow, the liquid sample will flow across the first array first and then flow across the second and subsequent arrays in sequential order. The micro-wells in the first array each have a size that permits entry of only one target entity into the micro-well and wherein each micro-well in the first array has approximately the same size. The micro-wells in the second and subsequent arrays, if present, each have a size that is at least 10 percent larger than the size of the micro-wells in the previously adjacent array and wherein each micro-well in a given subsequent array has approximately the same size. The plurality of micro-wells all have a size sufficient such that after target entities enter the micro-wells, at least one target entity remains within a micro-well when fluid flows across the surface or when a magnetic force is applied to the target entities in the micro-wells or both fluid flows and a magnetic force is applied.
In certain implementations, the micro-well array device includes a magnet component arranged adjacent to the surface. The magnet component is arranged and configured to generate a magnetic force sufficient to attract the target entities into the one or more arrays of micro-wells after target entities enter the micro-wells and to hold at least one target entity in at least one of the micro-wells when fluid flows across the surface.
In some implementations, the magnet component is adjustably arranged adjacent to the surface. In such implementations, the magnet component is arranged and configured to generate a magnetic force sufficient to hold at least one target entity in at least one of the micro-wells when the magnet is moved, e.g., horizontally, adjacent the surface.
In some implementations, the substrate is a polygon, e.g., a rectangle, having first and second ends. In such implementations, the first array of micro-wells is arranged at a first end of the substrate, and second and subsequent arrays are arranged further away from the first end of the substrate than the previously adjacent array.
In some implementations, the substrate is radially symmetric, e.g., circular or octagonal, and the first array of micro-wells includes one or more concentric circles of micro-wells arranged around a central location of the substrate that is devoid of micro-wells. The substrate includes second and subsequent arrays each including one or more concentric circles of micro-wells arranged further away from the central location of the substrate than the previously adjacent array.
In a second general aspect, the disclosure features a microfluidic system for capturing target entities that are, or are made to be, magnetic. The microfluidic system includes a body including a chamber having an inlet, an outlet, and is configured to contain the micro-well array device described above. The microfluidic system also includes a magnet component adjustably arranged adjacent to the surface. The magnet component is arranged and configured to generate a magnetic force sufficient to move target entities sized to fit into the micro-wells in the first array along, e.g., horizontally on, the surface and into the micro-wells in the first array and to move larger target entities along, e.g., horizontally on, the surface and into second and subsequent arrays. The magnetic force is sufficient such that after target entities enter the micro-wells, at least one target entity remains within a micro-well when fluid flows across the surface or when a magnetic force is applied to the target entities, or both fluid flows and the magnetic force is applied.
In some implementations, the microfluidic system further includes a detector configured to analyze optical properties of the target entities.
In some implementations, the magnet component is configured to be moved along at least one, e.g., two, axes, e.g., horizontal axes, relative to the surface.
In some implementations, a portion of the body, e.g., a transparent portion, above the chamber is detachable from the body of the microfluidic system, e.g., to allow access to the micro-well array device once target entities have been captured and retained.
In some implementations, the micro-well array device is an integral part of the body and the surface of the micro-well array device forms one wall, e.g., a floor, of the chamber. Alternatively, the micro-well array device can be in the form of a separate micro-chip that can be inserted into and/or removed from the microfluidic chamber.
In certain implementations, the microfluidic system includes a pump for flowing the fluid from the inlet of the chamber to the outlet of the chamber at a flow rate sufficient to permit target entities to reach the micro-well arrays.
In certain implementations, the microfluidic system includes a target entity extraction module configured to extract target entities from at least one of the plurality of micro-wells. In such implementations, the microfluidic system includes a second magnet component adjustably arranged relative to the target entity extraction module opposite the plurality of micro-wells. The second magnet component is configured to generate a variable magnetic force sufficient to attract a target entity that is, or is made to be, magnetic from a micro-well into an entrance channel of the target entity extraction module.
In some implementations, the target entity extraction module includes a micropipette, and the second magnet component includes a magnetic ring placed on a tip of the micropipette.
In some implementations, the surface includes a base layer, and a micro-well array device in the form of a micro-well array layer arranged on top of and contacting the base layer. The micro-well array layer includes a plurality of through holes that form the plurality of micro-wells. Alternatively, the micro-well array layer can simply be the micro-well array device with micro-wells that are not through holes, and is arranged to form one wall of the chamber.
In some implementations, the base layer or the micro-wells in one or more of the arrays are functionalized with one or more binding moieties to enhance binding of the target entities to the base layer or to inner walls of the micro-wells.
In some implementations, the micro-wells in the second array each have a size that permits entry of a second target entity into the micro-well. In such implementations, the second target entities are larger than the first target entities, and micro-wells in the first array each have a size that does not permit entry of the second target entity into the micro-well.
In some implementations, the size of the micro-well is any one or more of diameter, cross-sectional area, depth, shape, and total volume.
In some implementations, the size of the micro-wells that is varied between arrays is a diameter, volume, or cross-sectional area, while a depth of the plurality of micro-wells is approximately the same in all arrays.
In some implementations, the microfluidic system includes a set of magnetic beads comprising on their surfaces one or more binding moieties that specifically bind to a molecule on the surface of the target entities.
In a third general aspect, the disclosure features a method of capturing target entities. The method includes adding a fluid sample containing magnetic target entities into a chamber of the microfluidic system of the micro-well array device described above. The method also includes applying, using the magnet component adjustably arranged underneath the surface, a variable magnetic force to the chamber, and adjusting the position of the magnet component relative to the surface such that the applied variable magnetic force attracts the target entities into the first and/or second array of micro-wells. In certain implementations, the method includes analyzing, using a detector component, a property of the target entities.
In some implementations, the property to be analyzed includes quantity, size, sequence and/or conformation of molecules, DNA, RNA, proteins, small molecules, and enzymes contained inside the target entities, or molecular markers contained on surfaces of target entities, or molecules secreted from target entities.
In certain implementations, after adjusting the position of the magnet component relative to the surface, the method includes detaching a lid of the body of the microfluidic system, and extracting a target entity from at least one of the plurality of micro-wells.
In some implementations, extracting the target entity from at least one of the plurality of micro-wells includes transporting the extracted target entity to a container outside the microfluidic system.
In some implementations, analyzing includes detecting fluorescence emitted by the target entities. In some implementations, adjusting the position of the magnet component includes moving the magnet component along one, two, or three axes, e.g., horizontal axes, relative to the surface. In some implementations, after adjusting the placement of the magnet component relative to the surface, the method further includes providing a turbulent flow into the microfluidic device, and extracting a magnetized target entity from at least one of the plurality of micro-wells. In some implementation, adjusting the placement of the magnet component relative to the surface includes moving the magnet component in a pattern that causes the target entities to follow the pattern along the surface. In some implementations, adding the fluid sample containing magnetic target entities into the chamber includes flowing the fluid sample from the inlet to the outlet over the surface comprising the plurality of micro-wells.
In some implementations, adding the fluid sample containing magnetic target entities into the chamber includes dispensing the fluid sample onto the surface of the chamber comprising the plurality of micro-wells. In some implementations, the variable magnetic force is applied to the chamber while the fluid sample is being placed into the chamber of the microfluidic chamber.
In a fourth general aspect, the disclosure features a micro-well array device for capturing target entities that are, or are made to be, magnetic. The micro-well array device includes a substrate including a surface comprising a plurality of micro-wells arranged in one or more arrays on the surface. A first array of micro-wells is arranged adjacent to a first end of the surface, and a second array, if present, is arranged further away from the first end of the surface than the first array and any additional arrays are arranged sequentially such that each subsequent array is arranged further away from the first end of the surface than a neighboring array. The micro-wells in the first array each have a size that permits entry of only one target entity into the micro-well and wherein each micro-well in the first array has approximately the same size. The micro-wells in the second array, if present, each have a size that is at least 10 percent larger than the size of the micro-wells in the first array. The plurality of micro-wells all have a depth sufficient such that after target entities enter the micro-wells, at least one target entity remains within a micro-well when fluid flows across the surface.
In some implementations, the substrate includes a plurality of micro-wells arranged in two or more arrays on the surface. In certain implementations, substrate includes a plurality of micro-wells arranged in one array on the surface. In some implementations, the size is a diameter, volume, cross-sectional area.
In a fifth general aspect, the disclosure features a microfluidic system for capturing target entities that are, or are made to be magnetic. The microfluidic system includes a body including a chamber having an inlet, an outlet, and a surface extending from the inlet to the outlet. The surface includes a plurality of micro-wells that all have a depth that is at least 1 times the size of the smallest target entity that, after target entities enter the micro-wells, at least one target entity remains within a micro-well when fluid flows through the chamber. The microfluidic system also includes a magnet component adjustably arranged adjacent to the surface, wherein the magnet component is arranged and configured to generate a magnetic force sufficient to attract the target entities into the array of micro-wells that after target entities enter the micro-wells, at least one target entity remains within the micro-wells when the magnet is moved, e.g., horizontally.
In certain implementations, the microfluidic system includes a detector configured to analyze optical properties of the target entities. In some implementations, the magnet component is configured to be moved along one or two exes, e.g., horizontal axes, relative to the surface. In some implementations, the depth of the plurality of micro-wells allows the target entities to be carried out of the plurality of micro-wells by a turbulent flow of liquid in the chamber. In some implementations, the plurality of micro-wells are sufficiently spaced apart such that a target entity in a first micro-well adjacent to a second micro-well remains within the first micro-well when a suction force by a pipette is applied nearby the second micro-well.
In some implementations, a portion of the body above the chamber is detachable from the body of the microfluidic system such that at least a portion of the plurality of micro-wells is accessible by a tip of a micropipette once the portion of the body has been detached
The various micro-well array devices described throughout can include a substrate that includes only one, two, three, four, five, six, ten, or even many more arrays, e.g., arrays in the form of columns or concentric circles of micro-wells. The micro-well array devices can be simply inserted into a chamber, e.g., a glass or plastic or other chamber, container, or cuvette, and then the sample fluid is applied to the surface, either as a droplet that spreads across the device or a flow of the sample across the surface from one end to the other. The magnet component can be used to direct the target entities by moving the magnet component underneath the device until most or all of the target entities have entered a micro-well. Thereafter, the magnet component can be secured to or sufficiently near the bottom of the device to ensure that the target entities remain in the micro-wells while other assay steps are performed on the micro-well assay device, e.g., washing steps, labeling steps, incubation steps, or analysis steps. Alternatively, this can be achieved by using one or multiple electromagnets arranged in the vicinity of the cell array. In such implementations, the electromagnets can be stationary and their magnetic fields can be controlled and/or turned on or off. By turning the electromagnets on and off in sequence, a “moving” magnetic force can be created to cause the motion of the magnetized target entities, (e.g., particles or cells) without having to move the magnets physically.
The micro-well array devices can be used, e.g., to separately capture and isolate individual cells and clusters of cells on the same device, or to separately capture and isolate different sized cells on the same device.
The micro-well array devices (micro-well chips) as well as the microfluidic cell analysis systems described herein allow for increased capture efficiencies of target entities of varying sizes based on the magnitude of the magnetic force applied, the dimensions of the micro-wells placed on the surface of the micro-well chip, and the flow rate of the liquid flowing over the micro-well chip, e.g., through a microfluidic chamber that encloses the surface of a micro-well chip. The micro-well chips can be used to capture both individual cells, e.g., cells of different sizes, as well as cell clusters that can be present within a fluid sample, because the arrays of micro-wells placed on the surface of the micro-well chip vary by size (e.g., diameter, cross-sectional area, depth, shape, and/or total volume) from one array to another. In addition, the magnetic force can be applied in a manner that is independent of the rate of flow and volume of fluid flowing through the microfluidic chamber and independent of gravity such that cell settling is not necessary to capture cells within the micro-wells of the micro-well chip. This removes the need for a wash step after sample injection into the microfluidic chamber, which reduces the likelihood of losing target cells and improves testing speed.
As described herein, “target entities” or “target particles” within a fluid sample are either inherently magnetic, paramagnetic, or superparamagnetic, or are magnetized (e.g. made magnetic, paramagnetic, or superparamagnetic), at least temporarily, using different techniques, e.g., as described herein. The target entities or particles can be cells (e.g., human or animal blood cells, mammalian cells (e.g., human or animal fetal cells, e.g., in a maternal blood sample, human or animal tumor cells, e.g., circulating tumor cells (CTC), epithelial cells, stems cells, B-cells, T-cells, dendritic cells, granulocytes, innate lymphoid cells, senescent cells (and other cells that are related to idiopathic pulmonary fibrosis), megakaryocytes, monocytes/macrophages, myeloid-derived suppressor cells, natural killer cells, platelets, red blood cells, thymocytes, neural cells) bacterial cells (e.g., Streptococcus pneumonia, E. coli, Salmonella, Listeria, and other bacteria such as those that lead to sepsis including methicillin-resistant Staphylococcus aureus (MRSA)).
The target entities or particles can also be plant cells (e.g., cells of pollen grains, leaves, flowers and vegetables, parenchyma cells, collenchyma cells, xylem cells and plant epidermal cells) or various biomolecules (e.g., DNA, RNA, or peptides), proteins (e.g., antigens and antibodies), or contaminants in environmental (e.g., sewage, burkholderia pseudomallei, cryptosporidium parvum, giardia lamblia and parasitic worms) or industrial samples (e.g., detergents, disinfection by-products, insecticides, herbicides, volatile organic compounds, petroleum and its byproducts, solvent including chlorinated solvents and drugs). The target entities that are cells can have a minimum diameter between one hundred nanometers to one micron and range up to about 20, 30, or 40 microns or more. The clusters of target entities can be larger and range up to 100 μm or 1 mm in size (e.g., 250, 500, or 750 μm). Although this disclosure in described in reference to the capture of cells or cell clusters, the systems and methods described herein can also be to capture or isolate other types of target entities or particles from liquid samples. For example, the target entities can be exosomes or other extracellular vesicles with sizes that can be as small as 30 nanometers or less.
Unless otherwise defined, all technical and scientific terms used herein have the same meaning as commonly understood by one of ordinary skill in the art to which this invention belongs. Although methods and materials similar or equivalent to those described herein can be used in the practice or testing of the present invention, suitable methods and materials are described below. All publications, patent applications, patents, and other references mentioned herein are incorporated by reference in their entirety. In case of conflict, the present specification, including definitions, will control. In addition, the materials, methods, and examples are illustrative only and not intended to be limiting.
The details of one or more implementations are set forth in the accompanying drawings and the description below. Other potential features and advantages will become apparent from the description, the drawings, and the claims.
In the drawings, like reference numbers represent corresponding parts throughout.
In general, this disclosure describes cell analysis systems and methods that are capable of capturing and isolating both individual particles, such as cells, e.g., cells of different sizes, and clusters of particles, such as cell clusters, suspended in a fluid sample flowing across a micro-well chip, e.g., through a microfluidic chamber that encloses a micro-well chip, or in which a micro-well patterned surface is formed into the bottom wall. The bottom surface of the chamber includes a portion of the floor or a separate micro-well chip that has a micro-well arrangement, e.g., a single array of micro-wells in which all of the micro-wells are approximately the same size, or two or more arrays, e.g., in which arrays of smaller micro-wells are located closer to an inlet port of the microfluidic chamber to capture individual cells, e.g., smaller cells, and arrays with larger micro-wells are located further from the inlet port (and closer to an outlet port) to capture larger cells or cell clusters. The micro-wells can be arranged in multiple arrays, e.g., wherein the micro-wells in each array are the same size or approximately the same size (e.g., all of the micro-wells within one array have a size, e.g., diameter, or cross-sectional area, or depth, or shape, and/or total volume, that is plus or minus 5% of the selected size for the micro-wells in the array), but the size (e.g., diameter, or cross-sectional area, or depth, or shape, and/or total volume) of the micro-wells in different arrays are different from the size in the first array (e.g., by at least 10, 20, 30, 40, or 50 percent, e.g., by at least 75, 100, 125, 150, 200, 500, 750, or even 1000 percent). For example, the wells in a third array can be larger than those in the second array by the same percentages. Similarly, the wells of each array can be larger than those in the preceding array by the same percentages as above.
Even though for some applications it may be sufficient to keep the depths of all wells in all arrays the same, and only change their diameter, it may also be necessary to increase the depths of wells in subsequent arrays as well as their diameters to account for entities and clusters that are larger in up to 3 dimensions. In one implementation, the area occupied by each array may be similar or equal. In other implementations, the areas occupied by arrays may be different from each other (e.g. by 25, 50 or 100%). For example, the first array may occupy 50% to 75% of the entire area covered by all arrays. This implementation may help ensure that in the presence of fluid flow across the micro-well chip surface, all target entities first land on the first array and help minimize the possibility of small target entities reaching other arrays downstream.
In some implementations, the micro-wells can be arranged in columnar arrays, in which the micro-wells are arranged in columns (e.g., each array is a column of micro-wells) perpendicular to a central axis of the micro-well chip from one end to another, e.g., from the inlet to the outlet of a microfluidic chamber if the micro-well chip is arranged within, or is a part of, a chamber. The micro-wells in the column closest to the inlet can have the smallest size, e.g., diameter, cross-sectional area, depth, shape, and/or total volume, and the micro-wells in the column closest to the outlet have the largest size, e.g., diameter. In all implementations, the depth of all of the micro-wells in one, some, or all arrays (e.g., columns) can be the same or different, but each micro-well must be sufficiently deep to enclose and “trap” a cell or cluster of cells and keep the cells in the micro-wells even when liquid is flowing over the top of the micro-well or when the magnet is moved, e.g., horizontally, to lead target entities into the subsequent wells.
In some implementations, the diameters and depths of all micro-wells in one column are the same or approximately the same. Other than instances in which the extraction of the target entities from the micro-wells is intended, it is generally desirable that once target entities are captured in micro-wells, all of them remain in the micro-wells even under the influence of fluid flow and/or a motion, e.g., a horizontal motion, of the magnet. In some implementations it may be necessary to keep 100% of the target entities (e.g. cells) in the micro-wells, while in other implementations it may be sufficient to keep 90%, 80%, 50% or as low as 10%, or even just 1% of the target entities or a single target entity in the micro-wells, even if the rest are unintentionally extracted from the micro-wells.
In certain implementations, the depth of a micro-well can be limited to prevent unintended stacking of multiple cells on top of each other. In these implementations, the micro-well depth could be slightly larger than the nominal diameter of a cell to help prevent the stacking of a second cell. Alternatively, the micro-well depth can be slightly smaller than the nominal diameter of the cell as long as the cell is still prevented or inhibited from moving out of the micro-well prematurely. In this implementation, a part of the cell can protrude above the surface surrounding the micro-well. Alternatively, this implementation can also take advantage of the flexibility of the cells, which under the application of a vertical downward force will compress in the vertical direction, ultimately making a cell's height smaller than its nominal diameter. In this case, a cell can remain entirely inside the micro-well.
In one implementation, a second micro-well chip with the same micro-well diameters, but greater depths, can be placed on top of the micro-well chip 110 in a manner that aligns the entrances of all of the micro-wells, so that an external magnetic force can extract the cells from the micro-wells of micro-well chip 110 and move them into the micro-wells of the secondary chip. This implementation will effectively change the depth of the micro-well in which a cell is located.
In some implementations, the second micro-well chip can have micro-wells that have different diameters than those of the first micro-well chip.
The systems are also capable of applying a flow-independent variable attractive force to direct movement of magnetic, paramagnetic, or superparamagnetic cells of interest without a need to use a wash step to avoid false-positive detection of non-specific cells. For instance, the magnitude of the applied flow-independent attractive force can be manipulated to increase or decrease the cell-settling rate, and the direction of the applied magnetic field can be adjusted to cause magnetically induced cell movement along two dimensions of the plate surface. In this regard, the micro-well arrangement on the plate and the application of the variable magnetic field can be used to efficiently capture cells and cell clusters with high accuracy and consistency.
The “magnetic beads” as described herein for use in the systems and methods described herein can be magnetic, paramagnetic, or superparamagnetic particles that can have any shape, and are not limited to spherical shapes. Such magnetic beads are commercially available or can be specifically designed for use in the methods and systems described herein. For example, Dynabeads® are magnetic or superparamagnetic and come in various diameters (1.05 μm, 2.8 μm and 4.5 μm). Sigma provides paramagnetic beads (1 μm, 3 μm, 5 μm, and 10 μm). Pierce provides superparamagnetic beads, e.g., 1 μm. Thermo Scientific MagnaBind® Beads are superparamagnetic and come in various diameters (1 μm to 4 μm). Bangs Lab sells magnetic and paramagnetic beads (0.36, 0.4, 0.78, 0.8, 0.87, 0.88, 0.9, 2.9, 3.28, 5.8, and 7.9 μm). R&D Systems MagCellect® Ferrofluid contains superparamagnetic nanoparticles (150 nanometers in diameter). Bioclone sells magnetic beads (1 μm and 5 μm). In addition, PerkinElmer provides (Chemagen) superparamagnetic beads (e.g., 0.5-1 μm and 1-3 μm). The magnetic beads are particles that can range in size, for example, from 10 nanometers to 100 micrometers, e.g., 50, 100, 250, 500, or 750 nanometers or 1, 5, 10, 25, 50, or 75 micrometers.
If a cell is traveling in a fluidic chamber under the influence of a substantially horizontal fluidic flow and a downward magnetic force, its contact with the surface depends on a balance between the fluidic drag force and the downward magnetic force which depends on the magnetic field, as well as the properties and the number of the beads on the cell surface. The fluidic drag force depends on the average flow velocity, which is related is represented by the following equation: Q=V*A, where Q is the flow rate, V is the average fluid velocity, and A is the cross-sectional area of the flow chamber.
Investigators have demonstrated that when a tumor cell, e.g., a circulating tumor cell (CTC), is bound to at least 7 superparamagnetic beads (with 1 μm average diameter, e.g., from Sigma), the cell has a 90% probability in encountering a solid surface if the average fluid velocity is on the order of 4.4 mm/s (i.e., 2 ml/min flow rate with a cross-sectional area of about 7.6 mm2). See, Lab chip, 2015, 15, 1677-1688. In the study, the magnet used was a neodymium permanent magnet (K&J Magnetics, grade N52) with 0.4 to 1.5 T of flux density and a gradient of 160 to 320 T/m in the vicinity of the surface of the magnet, which was placed some 650 micrometers below the surface of a chip. Under these conditions, even a cell that has a single magnetic bead can be attracted to the chip surface, albeit with a lower probability.
In some implementations, the flow rates and velocities can be reduced significantly in order to maximize the probability of capturing cells. Higher flow rates (ml/min) can result in higher velocities (mm/s) which may introduce risk of cells escaping the surface. Alternatively, higher flow rates can still be used with larger cross-sectional areas so as to prevent the average velocity from increasing. In these implementations, “cross-sectional area” refers to that of the fluidic chamber that is perpendicular to the fluid flow. Alternatively, stronger magnets or beads with higher magnetic susceptibility (e.g. higher iron-oxide content) can also be used. In some other variations, higher affinity antibodies can be coupled on the beads surface. This will result in greater number of beads binding to the surface of a cell, and hence a greater overall magnetic force.
In some implementations, the fluidic flow rate and speed can also be increased without causing cells captured in the micro-wells to escape from the surface of the micro-well chip. For example, in one implementation, the volumetric flow rate and the cross-sectional area are configured to enable average flow velocities that range from 0.01 mm/s to 50 mm/s, e.g., 0.1, 0.5, 1.0, 2.5, 5.0, 7.5, 10.0, 12.5, 15, 20, 25, 30, 35, 40, or 45 mm/s.
Most magnetic beads typically have an iron oxide core in their center with a polymeric shell. The beads can also come pre-coated with a surface that can be easily functionalized, e.g., a surface coating of streptavidin, biotin, dextran, carboxyl, NHS, or amines.
In various implementations, magnetic beads are bound or linked to specific antigens expressed on the surfaces of the target cells within the fluid sample. In these implementations, the magnetic beads are functionalized in any one or more ways, e.g., new, conventional, or commercially available, ways to include one or more binding moieties or one or more different types of binding moieties, e.g., appropriate monoclonal or polyclonal antibodies including, but not limited to, antibodies against EpCAM, EGFR, Vimentin, HER2, progesterone receptor, estrogen receptor, PSMA, CEA, folate receptor, or with other binding moieties such as aptamers, or short peptides that can bind to specific target entities.
In specific examples or functionalization techniques, low molecular weight ligands (e.g. 2-[3-(1, 3-dicarboxy propyl)-ureido] pentanedioic acid (“DUPA”) for prostate cancer cells, and folic acid for ovarian cancer cells or other cancer cells that over-express the folate receptor on their surfaces including lung, colon, renal and breast cancers) are used to promote binding to certain cells. Specifically, low molecular weight ligands (e.g., DUPA and folate) can be bound to a functional group (amino, n-hydroxy succinamide (NHS), or biotin depending on the functional group on the magnetic bead to be used) with a linker group, e.g., with a polyethylene glycol (PEG) chain, in between the low molecular weight ligand and the functional group to suppress nonspecific binding to the beads.
In other instances, magnetic particles are internalized by the target cells by exposing the fluid sample to droplets of magnetic particles, fluid flow of the magnetic particles, or with the use of a magnetophoretic flow to the micro-well chip. For example, the target cells can be incubated in a fluid that contains the magnetic, paramagnetic or superparamagnetic particles, typically nanoparticles having a size of about 1 nm to a micrometer, under conditions and for a time sufficient for the cells to internalize the magnetic particles. In one implementation, the size of the magnetic particles is several micrometers as long as the particles are sufficiently smaller than the size of the cells so that that they can be internalized by the cells. In one implementation, the cells are blood cells or tumor cells with sizes that range from 5 micrometers to 20 micrometers.
The micro-well chip 110 can include multiple surfaces that form a microfluidic chamber where the fluid sample flows between an inlet port and an outlet port. The bottom surface of the microfluidic chamber either includes or contains a plate that includes an array of micro-wells (also referred to herein as “wells”) that is designed to capture individual cells or cell clusters that are suspended in the fluid sample. The dimensions of the micro-wells (e.g., diameter, depth, shape, etc.) and the micro-well array pattern can be varied based on the target entity, e.g., target cell, to be captured using the micro-well chip 110. In some instances, the micro-well chip 110 can also include an arrangement with multiple arrays of micro-wells in which all the micro-wells in each array (or group of arrays) have the same dimensions, but the dimensions of the micro-wells in different arrays (or groups of arrays) are different to simultaneously capture individual cells and cell clusters within a single sample run through the chamber.
In an alternative implementation, the micro-well chip 110 functions without a fluidic chamber or any inlet and outlet ports or a fluid control device. In this implementation, the sample fluid containing magnetized cells are exposed to the top surface of the micro-well chip 110 in the form of a droplet, using conventional methods such as pipetting. For example, a cuvette type fluidic chamber (with an open top) can be configured to accommodate the micro-well chip 110. This cuvette can be accessed directly from above directly by pipettes or inlet and outlet tubing. Alternatively, the cuvette can also be configured to have a fluidic inlet and a fluidic outlet.
The fluid control device 120 can be any type of fluid delivery device used to introduce a sample fluid into a fluidic circuit. For instance, the fluid control device 120 can be either a peristaltic pump, a syringe pump, a pressure controller with a flow meter, or a pressure controller with a matrix valve. The fluid control device 120 can be configured to tubing that attaches to the inlet port of the micro-well chip 110 to introduce the sample fluid into the microfluidic chamber of the micro-well chip 110. In some instances, the fluid control device 120 is also capable of adjusting the flow rate of the sample fluid introduced into the microfluidic chamber according to a predetermined program. This predetermined program can be based on a specific sequence that involves flowing the sample fluid that contains cells for a certain period of time at certain speeds and then introducing certain dyes to stain the cells and certain molecules and enzymes to bind to or interact with the cells.
The fluid control device 120 can be placed in different locations of a fluidic circuit associated with the micro-well chip 110. In some implementations, the fluid control device 120 is located upstream of the micro-well chip 110 (e.g., before the inlet port of the micro-well chip 110 within the fluidic circuit). In such implementations, the fluid control device 120 can be used to exert a force that “pushes” a volume of fluid from a sample chamber (e.g., a cuvette) into a chamber containing the micro-well chip 110. In other implementations, the fluid control device 120 can be located downstream of the micro-well chip 110 (e.g., after the outlet port of the micro-well chip 110 within the fluidic circuit). In such implementations, the fluid control device 120 can instead be used to exert a force, e.g., a suction force that “pulls” fluid from the sample container into the chamber containing the micro-well chip 110. The flow rate used by the fluid control device 120 in either the downstream or the upstream configuration can range between, for example, 0-100 mL/minute, or 0.1-3 mL/minute, e.g., 10, 20, 30, 40, 50, 60, 70, 80, or 90 mL/minute, or 0.25, 0.5, 0.75, 1.0, 1.5, 2.0, 2.5, or 3.0 mL/minute.
The magnet 130 is generally situated underneath the chip 100 and is calibrated relative to the magnetic beads linked to the target entities to exert a magnetic force sufficient to pull the target entities towards the entrances of the micro-wells in the surface of the micro-well chip 110, and to retain the target entities within the micro-wells once the target entities have passed through the entrances of the micro-wells. The magnetic force is also sufficiently strong to pull the target entities out of the fluid flow through the microfluidic chamber that tends to pull the target entities in a flow path parallel to the surface of the micro-well chip 110. As an example, the magnet 130 can be an NdFeB Cube Magnet (about 5×5×5 mm) with a measured surface flux density and computed gradient of 0.4 T to 2 T and 100 to 400 T/m (depending on the exact location of the measurement), respectively. In other examples, other magnets including, but not limited to, larger or smaller permanent magnets made of various materials, and electromagnets that are commercially available or manufactured using standard or microfabrication procedures and that are capable of generating time-varying magnetic fields, can also be used. The magnetic flux density and the gradients can range from 0.01 to 10 T/m, 10 to 100 T/m, 100 to 100 T/m, and 1 to 1000 T/m, respectively.
The magnet 130 can have different shapes and dimensions based on a particular application. For example, the shape of the magnet 130 can be, but is not limited to, a cubic shape, rectangular prism-like shape, a ring shape, a circular or elliptical shape, or a combination thereof. In addition, multiple magnets can be used. The size of the magnet 130 can vary such that its minimum dimension can be between 0.1-30 cm. In some implementations, the magnet 130 is a ring-shaped magnet that is used to cause and/or help dispersing of aggregates of magnetic particles or magnetized target entities. For example, a ring-shaped magnet can be placed around an aggregate of target entities to help dispersing of individual target entities towards a perimeter of the magnet 130.
The magnet 130 can be housed within a cavity formed in the bottom half of a housing that includes the micro-well chip 110 or can be attached to an outer surface of the housing without the need for a cavity. The magnet 130 can be affixed to or supported relative to the outside of the micro-well chip 110 provided that it is oriented or positioned in a manner to attract the target entities toward the surface of the micro-well chip 110, and to adjust the movement of cells on the surface of the chamber in a controlled manner. For instance, the magnet 130 can be used to guide cells on the surface along a path defined by the movement of the magnet 130 underneath the micro-well chip 110. In other implementations, the magnet or magnets can be secured within a receiving chamber in a system into which a microfluidic device as described herein, e.g., in the form of a cartridge or cuvette, can be inserted. Such systems can also include the required pumps, controllers (e.g., computers or microprocessors), fluid conduits, reservoirs for fluids to be passed through the microfluidic devices, and analysis systems and equipment as described herein.
Movement of the magnet 84 can be accomplished manually, by a motor, and/or can be provided with a controller that allows selection of a particular sweep pattern for the magnet. The magnet 130 can be electromagnets that can be activated or deactivated as desired. Moreover, the electromagnets can be configured to reverse polarities as part of a technique for controlling movement of the magnetic beads and ligand-bound entities. In addition, the orientation of the magnet 130 can be changed to selectively control the magnitude and direction of the attractive force applied.
In some implementations, multiple magnets, e.g., electromagnets, can be used and controlled, for example, in tandem or in sequence, to generate magnetic fields that vary with respect to time and space. For example, two or more electromagnets situated in the vicinity (e.g. below) the micro-well chip 110 can be controlled to generate a moving magnetic force that is used to move magnetic entities along the surface of the micro-well chip 110.
The magnitude of the attractive force applied by the magnet 130 can be adjusted based on the magnetic properties of the particles attached to the cells, the strength of the magnet 130, and/or the placement of the magnet 130 relative to the micro-well chip 110. For example, the magnet 130 can be associated with an external body so that the distance of the magnet from the micro-well chip 110 can be varied to thereby vary the magnetic force applied to the target entities in the microfluidic chamber. The magnetic force applied can then be calibrated to a particular type of target entity or a particular type of functionalized magnetic beads used. In addition, the magnet 130 can be moved to remove the magnetic force entirely according to a protocol for the system 100. Removal of the magnetic force can be used to facilitate removal of the captured target entities within the micro-wells so that the target entities can then be transported or flushed to a separate collection vessel. In one implementation, the magnet 130, or another magnet, can be placed on top of the chip to help extract the cells out of the micro-wells. The magnet 130 that is placed on the top can then be moved sideways for sequential extraction of cells in micro-well arrays.
In some implementations, the magnet 130 includes an array of electromagnets placed underneath the micro-well chip 110 in a manner that covers a portion of the micro-well chip 110. One or more electromagnets within the array can then be selectively powered in certain sequences to apply attractive forces to cause motion of the cells along specified pathways along the surface of the micro-well chip 110.
The analyzer device 140 can be configured to use optical techniques to analyze the cells that are captured within the micro-wells of the chamber surface. For instance, the analyzer device 140 can be configured to use various microscopic techniques based on fluorescence, bright field, dark field, Nomarski, mass spectroscopy, Raman spectroscopy, surface plasmon resonance, among other known techniques.
The analyzer device 140 can include a CCD camera and a computerized image acquisition and analysis system. The CCD camera can be large enough to cover the size of the entire area of the micro-well chip 110 in a manner to acquire images from all micro-wells in the micro-well chip 110. Alternatively, the CCD camera can be able to analyze a smaller field of view that contains only one micro-well or a group of micro-wells. In such implementations, the CCD camera or the chip 100 can be moved manually or using a translation stage or other computer controlled modalities to sequentially align the CCD camera with other micro-wells and acquire their images.
The analyzer device 140 can be used to analyze various aspects cell capture process using the micro-well chip 110. For example, the analyzer device 140 can be used to analyze cells that have been extracted from micro-wells of the micro-well chip 110. Alternatively, the analyzer device 140 can additionally or alternatively be used to visualize and/or confirm cell capture within micro-wells of the micro-well chip 110 prior to cell extraction.
The cell analysis system 100 can optionally include a controller 150. The controller 150 can be used to automate actions performed on the micro-well chip 110 for various steps of the methods described herein, e.g., sample fluid injection, cell capture, extraction of captured cells, and/or analysis of captured cells. In one example, the controller 150 can be used to adjust the position of a translation stage that adjusts the position of the micro-well chip 110 relative to the field-of-view of the analyzer device 140 to record images of the contents of each micro-well or relative to a micro-pipette for extraction of captured cells. In another example, the controller 150 is capable of generating computer-implemented instructions that adjust the location of the magnet 130 and the magnitude of the generated attracted force to customize the cell capture technique for a specific type of sample fluid.
The controller 150 can be a microprocessor configured to follow a controlled flow protocol to a particular target entity, recognition element, and sample size. The controller 150 can incorporate a reader to read indicia associated with a particular sample or samples, and automatically upload and execute a predetermined flow protocol associated with the particular sample. The controller 150 can also modulate the magnetic field during a detection cycle to facilitate capturing the target entities and drawing the unbound magnetic beads into the array of micro-wells.
The controller 150 can also be configured to allow user-controlled operation. For instance, the flow rate for a particular target cell-magnetic bead combination can be determined by increasing the flow rate of a bound target cell sample until it is no longer possible to attract beads to the surface of the micro-well chip 110. The continuous operation of the system 100 can be directly observed through a visualization window to determine whether a flow bypass is required or whether the detection process is complete. The controller 150 can also cause the micro-well chip 110 to move to enable the analyzer device 140 to scan and obtain images on various sections of the micro-well chip 110. These images can then be used to reconstruct an image of the entire or a part of the surface of the micro-well chip 110.
The size of the entrance of the micro-wells 102a, 102b, and 102c on the surface of the micro-well chip 110 can be configured such that either only a single cell or a cell cluster is captured within the micro-well. The micro-wells 102a, 102b, and 102c also have a sufficient depth such that once a single cell or cell cluster is captured within the micro-wells, the captured cells remain within the micro-wells even as the fluid sample continues to flow through the microfluidic chamber from the inlet port to the outlet port, or in the absence of the attractive force applied by the magnet 130.
In one implementation, the depth of each micro-well is limited to prevent stacking of multiple cells. The depth of a micro-well can be between the nominal diameter of a targeted cell and less than 2 times the nominal diameter of a targeted cell. As an example, a circulating tumor cell's diameter is about 15 micrometers. The depth of the micro-well can be between 15 and 30 micrometers. As another example, the size of a bacterium is about 1 micrometer and the depth of a micro-well can be between 1 and 2 micrometers. In another embodiment, the depth of the micro-well can be equal to or even 5, 10, 20 or 50% less than the nominal diameter of a cell given the possibility that once a cell is inside the micro-well and under the influence of a downward magnetic force, its thickness can reduce, while its width can increase. For these cases, the depth of the micro-well can be configured so that when a first cell is already in the micro-well, another second cell that coincides on top of the first cell has a part of it exposed outside the micro-well, so that it can be washed away by flow or a sideways magnetic force while the first cell will be prevented from being washed away. For the example of a 15-micrometer circulating tumor cell (CTC), the depth of the micro-well can be between 1 micrometer and 15 micrometers. It should be appreciated that the depth of the micro-wells need to be configured depending on the nominal size of the target cell or the cell cluster sought to be captured/isolated and hence specific depths of micro-wells in micrometers in an actual device can be different from those that are mentioned here. In addition, in some implementations, the depths of micro-wells are fabricated to differ from array to array or within the same array.
In one implementation, the magnetic force as well as the spacing between the micro-wells is adjusted to minimize the possibility of magnetized entities aggregating and hence the possibility of multiple magnetic entities entering into the same micro-well.
In one implementation, the dimensions of the micro-wells are configured such that captured cells can be released from the micro-wells upon the application of a turbulent flow through the microfluidic chamber. For example, the flow rate of the sample fluid, the micro-well depth, and the magnitude of the attractive force applied by the magnet 130 can be carefully selected and controlled such that the cells that are captured in the micro-wells can be extracted in a controlled manner by either adjusting the attractive force applied or the fluidic flow rate of the sample fluid. In some implementations, an individual cell, or a cell cluster, is retrieved by means of a pipette, either manually or in a computer-controlled fashion, in the presence or absence of fluid flow.
As an example, if the cells to be captured in the micro-well chip 110 are white blood cells with 10-20 micrometer diameters, the entrance of the micro-well 102a on the surface of the micro-well chip 110 can be 15-30 micrometers. Alternatively, in other instances, the size of the entrance can be equal to or 5 to 20% smaller than the cell diameter so that the cell is squeezed into the micro-well by the attractive force applied by the magnet 130. As another example, the captured cells can be circulating tumor cells with 10-20 micrometer diameters and the entrance of the micro-well of 102a on the surface of the micro-well chip 110 can be 10-35 micrometers. As another example, the captured cells can be red blood cells with 6-8 micrometer diameters. In this case, the entrance of the micro-well of 102 on the surface of the micro-well chip 110 can be 6 to 10 micrometers. As another example, the captured cells can be bacteria with an approximately 1-micrometer diameter and the entrance of the micro-well of 102a on the surface of the micro-well chip 110 can be 1 to 2 micrometers. Yet as another example, the captured cells can be exosomes with diameters ranging from 50 to 100 nanometers, and the entrance of the well of 102a on the surface of the micro-well chip 110 can be larger than 50 nm.
In the example depicted in
In some implementations, the bottoms of the micro-wells include one or more micro-pores or openings that are capable of passing liquids and unbound magnetic beads out of the micro-wells, while retaining the captured cells. In such implementations, once cells have been captured within the micro-wells, fluids can be introduced through the micro-wells to wash the captured cells. In one example, a wash step can be used to sieve free unbound magnetic beads and other small entities captured within the micro-well through the micro-pores.
In some implementations with many micro-well arrays, which require the length of the micro-well chip to be disproportionally larger than its width, the micro-well arrays, instead of being arranged in a linear manner can be arranged in a meandering pattern, which can enable packing more micro-wells on a rectangular surface.
In one implementation, the target entities can be introduced by a fluid flow through the inlet port and the fluid flow can be stopped or reduced while target entities are substantially located on the first array, so as to prevent the smaller target entities from escaping downstream and accidentally entering into larger wells of subsequent arrays. The magnet can be moved, e.g. horizontally, in an oscillatory fashion to ensure entry of small target entities (or individual cells) into the wells of the first array. Then the magnet can be moved downstream to lead larger entities (or clusters) into the larger wells of the next array. This process could be assisted by restarting or increasing fluid flow or alternatively without using any fluid flow. Once the process of capturing entities in the wells is completed, a wash process can be performed if necessary. In one implementation, the inlet and the outlet ports can inherently be parts of the micro-well chip 110.
The magnet can be moved underneath the micro-well chip 110 along two dimensions beneath the micro-well chip (e.g., along the x-axis and y-axis as depicted in
As described herein, the magnitude of the attractive force 212 can also be adjusted to increase or decrease the magnetically-induced movement of the cells 202a, the small cell clusters 202b, and the large cell clusters 202c into the micro-wells. For instance, the magnet 130 can be moved or controlled to apply a smaller attractive force to induce individual cells 202a to be captured within micro-wells, and moved or controlled to apply a larger attractive force to induce cell clusters to be captured within the micro-wells due to the greater size of the cell clusters. In some instances, the magnitude of the attractive force 212 can be specifically modulated to selectively capture cells and/or cell clusters of a particular size or shape (e.g., selectively capturing small cell clusters 202b, but not large cell clusters 202c). For example, if the magnet 130 is a permanent magnet, the magnet 130 can moved closer to from the microfluidic chamber to increase the magnitude of the magnetic force applied and moved further away from the microfluidic chamber to decrease the magnitude of the magnetic force applied. In one implementation the distance between the magnet and the bottom of the chip surface can be between 10 micrometers and 2 centimeters, or more narrowly between 0.5 to 2 mm. In other examples, where the magnet 130 is an electromagnet, the amount of energy supplied to the magnet 130 can be increased or decreased to similarly increase to result in a corresponding increase or decrease in the magnitude of the magnetic force applied. In one embodiment the force exerted on a single magnetic, paramagnetic or superparamagnetic particle can be between 0.1 pN to 1 nN or more narrowly between 1 to 100 pN.
In some implementations, the surface of the micro-well chip 110 is capable of generating an electric field within the microfluidic chamber to adjust the movement of captured cells within the micro-wells. For example, the micro-well chip 110 can have an embedded modality (e.g., an electromagnet or an electric generator) that generates an electric field on the bottom surface of the micro-wells that repels negatively charged cells that are captured within the micro-wells to cause the captured cells to exit the micro-wells. The magnitude of the generated electric field can be modulated to perform specific operations on the captured cells. For example, a low magnitude electric field can be generated to adjust the placement of the cells within the micro-wells (e.g., can vibrate or agitate the cells in the micro-well) to enhance mixing with chemicals such as dyes, stains, lysates, etc., that are introduced into the micro-wells after capture. In another example, a high magnitude electric field can be generated to displace the cells from the micro-well and collect the cells through the outlet port of the microfluidic chamber. In some implementations, the particles or beads that are used to bind to the target entities can bear a negative or positive charge in a manner that helps attract or repel the target entities by means of an external electric field. In some embodiments, the magnitude of the force that results from the electric field on a target entity can be between 0.01 pN to 1 nN.
In contrast, chip 220 shown in
A flow of the target entities in a fluid sample can be created by a pump and/or vacuum arranged at the inlet and/or outlets of the system, or a flow can be created by rotating the symmetrical, e.g., circular or octagonal substrate. For example, the diameter of the substrate can range from 3 mm to 30 cm, e.g., from 2 cm to 10 cm (e.g., 3, 4, 5, 6, 7, 8, 9, 10, 15, 20, 25, 30, 40, 50, 75, or 100 mm or 1, 2, 3, 4, 5, 6, 7, 8, 9, 10, 15, 20, 25, or 30 cm). In one implementation the rotational speed of the substrate can range from 0.0001 rpm to 1000 rpm, e.g., from 0.01 rpm to 20 rpm (e.g., 0.0001, 0.0005, 0.001, 0.005, 0.01, 0.05, 0.1, 0.5, 1.0, 2.5, 5, 7.5, 10, 12.5, 15, 17.5, 20, 25, 30, 40, 50, 75, 100, 200, 250, 250, 500, 750, or 1000 rpm).
In this implementation, the arrays of micro-wells are arranged as concentric circles with the circle (or circles) of the smallest micro-wells 266 arranged closest to the center of the device, and the circle (or circles) of the largest micro-wells 264 arranged furthest from the center of the device. One magnet can be arranged below the substrate to cause magnetic target entities to enter the micro-wells and be held in the micro-wells. Alternatively, one or more magnets can be arranged adjacent, e.g., below, the substrate and configured and controlled to be move to cause the target entities to move, e.g., radially outwardly, towards subsequent circular arrays of micro-wells. In some embodiments, electromagnets, e.g., a circular electromagnet or a series of circular electromagnets can be arranged, e.g., below the substrate, and triggered in sequence to provide a magnetic force in a radially outward direction to move the target entities on the surface of the device.
The micro-well chip 110 can include various features to enable the capture of target entities such as cells within a fluid sample flowing over the micro-well chip, e.g., flowing through a microfluidic chamber that contains the micro-well chip either as a separate and removable plate at the bottom of the microfluidic chamber, or formed as part of the bottom wall of the chamber. For instances, the micro-well chip 110 can include structural features that adjust the flow of the fluid sample to enable the capture of cells within a particular location of the microfluidic chamber. As an example, the micro-well chip 110 can include fluidic circuits with bifurcations and/or valves in a predetermined arrangement that assist in segregation of fluid from cellular components. In other instances, the surfaces of the micro-well chip 110 can be functionalized to enhance cell capture using receptor-ligand binding between particular chemicals used to functionalize the surfaces of the micro-well chip and the receptors expressed on the surfaces of the target cells. In some instances, the micro-wells can be selectively functionalized to recognize specific types of cells and molecules. For example, the inner walls of the micro-wells can be coated and/or functionalized with binding moieties as described herein to aid in retaining the target entities within the micro-wells. In some implementations, a combination of structural features (e.g., channel dimensions and channel arrangement) and functional features (e.g., binding moieties bound to surfaces of channels and/or inner surfaces of the micro-wells) are used to enhance cell capture within the micro-well chip 110.
The micro-well chip 110 can be fabricated using commonly used microfabrication techniques for silicon such as photolithography and etching. In some instances, the micro-well chip 110 is a single surface structure that is situated inside a fluidic chamber that has a transparent upper surface that allows for viewing and analysis of captured cells. In other instances, the micro-well chip 110 is constructed by combining multiple pre-fabricated layers where the top layer (and in some implementations the bottom layer) is made of, or includes a window of, a transparent material such as glass, quartz, or plastic (e.g., acrylic, polyvinyl chloride, polypropylene, or polystyrene). In such instances, the micro-well chip 110 can include a bottom layer that includes an arrangement of micro-wells as depicted in
In some implementations, micro-wells of the micro-well chip 110 are constructed by initially forming holes in a polydimethylsiloxane (PDMS) film and then applying the film to a surface of a solid material such as glass. In such implementations, the PDMS film can be placed on the solid surface to “cap” the through holes on the bottom of the solid material so as to form micro-wells to be used for capturing cells.
In one implementation, the micro-well chip 110 can be made out of a metal such as aluminum or stainless steel to enable efficient conduction for temperature control for applications that include polymerase chain reaction (PCR). The micro-well chip can be coated or patterned with gold or platinum or a similar material that enables functionalization with other molecules including thiols.
In some implementations the surface area of the micro-well chip 110 can range from 100 μm2 to 1000 cm2 or more narrowly from 0.01 mm2 to 100 mm2. In one implementation the size of the micro-well chip 110 can be 15 cm by 10 cm so that it is comparable to the size of an adult human hand. The micro-well chip 110 can be composed of micro-wells that have 30 micrometer entrance diameters with 40 micrometers of center-to-center spacing. In this implementation the micro-well chip can have approximately 6 million micro-wells. In another implementation the micro-well chip 110 can have dimensions of 20 cm by 15 cm, and can therefore contain 12 million of the same micro-wells.
In other implementations, the separation between the micro-wells can be different and range from 1 micrometer (edge-to-edge) to 200 micrometers center-to-center (or 170 micrometers from edge-to-edge for a micro-well with a 30 micrometer entrance diameter). The number of micro-wells that are packed onto the surface of the micro-well chip 110 can then vary accordingly. For example, about 1 billion micro-wells can be present in a 11 cm by 3.7 cm micro-well chip 110 if a micro-well's entrance diameter is 1 micrometer and if micro-wells are spaced by 1 micrometer (edge-to-edge) from each other. As another example, 100 million micro-wells can be present in a 17.7 cm by 6 cm micro-well chip 110 if the micro-wells' entrance diameter as well as edge-to-edge spacing are 5 micrometers. In some implementations, the diameter of the entrance of a micro-well can range from 10 nm to 500 μm.
In one implementation, a “cartridge” or a housing that contains the micro-well chip can be made out of injection molded plastic. The plastic can contain a transparent observation window. In another implementation the housing can be made out of acrylic or metals or wood.
In one implementation the length and width of the housing can be 1 millimeter to 5 cm larger than those of the micro-well chip 110. The thickness of the housing can vary between 1 millimeter to 5 centimeters.
In general, once cells have been captured within the micro-wells of the micro-well chip 110, the captured cells can be viewed, imaged, or accessed for further analysis or processing using different techniques. In some implementations, the fluid flow through the microfluidic chamber and/or the magnitude of the attractive force applied by the magnet can be adjusted to remove the captured cells from the micro-wells. In some implementations, one or more surfaces of micro-well chip 110 are disassembled to directly view or access the captured cells as depicted in
The extracted cells can be further analyzed with a different system (e.g., fluorescence analysis, polymerase chain reaction (PCR) modules, next generation DNA or RNA sequencing modules, plate readers, 2 or 3 dimensional cell culturing modules, high-content analysis devices like Opera etc.), collected to be transported out of the micro-well chip 110, or accessed to be cultured on the micro-well chip 110. As described more particularly below, various implementations include structural features that provide such functionalities.
The microfluidic chamber is attached to an inlet 302a, which enables the fluid sample to enter the microfluidic chamber, and an outlet 302b, which enables the fluid sample to exit the microfluidic chamber. The fluid sample includes individual cells 202a and cell clusters 202c to be captured in the micro-wells of the base 310 using techniques described previously with respect to
In the example depicted, once the cells 202a and cell clusters 202c have been captured within the micro-wells of the base surface 310, the spacer 320 and the top plate 330 can be detached from the base 310 to enable direct access to the captured cells. For instance, the captured cells can be accessed visually for optical analysis and/or accessed physically for extraction. After detachment, fluid media 312 in the microfluidic chamber can remain within the micro-wells so that the captured cells do not dry out after detachment. This is accomplished by configuring the micro-wells with a sufficient depth such that the capillary forces from the top plate 330 on the fluid media 312 do not remove all of the fluid media within the micro-wells. Furthermore, the surface of the micro-wells can be configured to possess a certain degree of hydrophilicity to retain as much water as possible. In an alternative implementation, the micro-wells can be shallower but as soon as the top plate 330 is removed, more fluid 312 can be added to prevent drying of the cells, or the removal of the top plate 330 can be accomplished while the entire device is submerged in a bath of liquid 312. A magnet can be present underneath the base 310 so as to prevent the escaping of the cells from the micro-wells during the detachment of the top plate 330.
Referring now to
In some implementations, the surface of base 340 are functionalized with molecules that promote cell adhesion to improve capture efficiency of the cells 202a. Once the cells 202a are immobilized to the surface of base 340, the porous layer 350 can be removed to provide direct access to the immobilized cells. The base 340 with the immobilized cells can be immersed in a fluid bath or placed in a fluidic chamber for additional analysis (e.g., fluorescence microscopy).
In other implementations, instead of being a functionalized surface, the surface of base 340 can instead be a free surface or a surface that is blocked with a non-fouling agent such as bovine serum albumin (BSA), polyethylene glycol (PEG), zwitterionic materials or other materials that block non-specific binding. In such implementations, an attractive force can be applied by the magnet 130 underneath the base 340 to inhibit cell movement when the porous layer 350 is detached from the base surface 340.
The system 300 includes a housing 350 that holds a micro-well chip 360 with multiple micro-wells placed on its surface. A spacer 370 is placed between the micro-well chip 360 and a transparent sheet 380 to form a chamber where a fluid sample containing target entities is introduced for a cell extraction operation. The fluid sample enters the chamber through the inlet 302a and exits the chamber through the outlet 302b in a similar manner as discussed above with respect to
In a particular implementation, the housing 350 is constructed from acrylic, the spacer 370 is constructed from PDMS, and the transparent sheet 352 can be constructed from glass or any other suitable transparent (or opaque) material to allow the transmission of light into the chamber. The layer 352 can be a PDMS film that is capable of being peeled off the top surface of the transparent sheet 352. In other implementations, other suitable materials can be used as replacements to construct the system 300.
During a typical cell capture operation, the layer 352 is initially affixed to the top surface of the transparent sheet 380 to provide a sealed chamber that enables liquid flow with minimal leakage. A fluid sample containing target entities is then introduced into the sealed chamber through the inlet 302a. As the fluid sample flows from the inlet 302a to the outlet 302b, target entities and/or cell clusters are captured in the micro-wells of the chip 360 as described above. The layer 352 can then be removed as shown in
Various techniques can be employed to ensure that the layer 352 is sufficient to sustain a leakage-free fluid flow as the sample fluid is introduced into chamber through the inlet 302a. For example, in some implementations, the structure of the system 300 can be reinforced by mechanical pressure applied by a plastic structure (e.g., acrylic) that is placed on top of the layer 352 as fluid flows through the chamber.
Referring now to
The tunnel extraction module 410 can have an entrance that has a diameter larger than the diameter of the entrance of a micro-well on the surface of the micro-well chip 110. In addition, the diameter of the entrance of the tunnel extraction module 410 can be configured such that the entrance can be used to extract a captured cell 202a from only a single micro-well without overlapping with the entrance of another micro-well. In some instances, the tunnel extraction module 410 is constructed with a flexible rubber-like material, e.g., polymers such as PDMS, to form a seal with the surface of the micro-well chip 110 around the entrance of the micro-well. Alternatively, the extraction module 410 can be made from plastic or metals such as stainless steel and be configured to have a sheet of polymeric material such as PDMS on the bottom surface of it to form a seal around a micro-well. In addition, the tunnel extraction module 410 can also be filled with liquid (e.g., media fluid) to accommodate the captured cell 202a during the extraction process. In such instances, the bottom of the micro-well includes one or more entrances to allow the passage of liquid through the micro-well for suction force applied by the tunnel extraction module 410.
In the example depicted in
Referring now to
In the example depicted in
In another implementation, the extraction module 420 can be configured to have the collection chamber 420, but not the narrow entrance 424.
In one implementation, the chamber 422 and the tunnel 202a are fluidly accessed from the outside to deliver liquid and establish a fluid connection with a micro-well that contains a cell. This can be achieved by drilling a hole into the extraction module 410 or 420. In another implementation, the extraction module 420 can be fabricated to have a connection from the outside to the chamber 422. This cancan be achieved by using PDMS as the material for the extraction module and placing a tube into the PDMS during the fabrication process before the PDMS cures. Once the curing is completed, the PDMS will have solidified around the tube resulting in a connection to the chamber 422 from the outside. Similarly, the extraction module 410 can be fabricated to have the entrance of the tunnel 202a but not the longer, horizontal portion of the tunnel that established connection to the outside. The entrance of the tunnel can then be fluidly accessed from the outside by puncturing the extraction module with a needle or drilling a hole into the extraction module and inserting a tube into the hole.
In various other configurations, the transfer operation can be performed in other directions. For example, the micro-well chips 110 and 430 can be placed on the side to transfer, e.g., horizontally transfer, the captured target entities between the micro-wells. In another example, the micro-wells chips 110 and 430 can be placed such that the micro-well chip 110 is placed on top of the micro-well chip 430 such that a gravitational force can be used to transfer the target entities from the micro-wells of the micro-well chip 110 to the micro-wells of the micro-well chip 430.
In some implementations, the transfer operation can be conducted after immersing the micro-wells of micro-well chips 110 and 4320 in liquid to, for example, provide a fluid interface for transfer, hydrate the target entities, among other purposes. In some implementations, the micro-well chips 110 and 430 can have micro-wells of different well depths. Alternatively, in other implementations, the micro-well chips 110 and 430 can have micro-wells that have the same well depth.
In some instances, the micropipette 510 can be configured to apply a suction force to facilitate the motion of the single cell 202a into the tip of the micropipette 510. In such instances, the suction force is initially used to assist the single cell 202a to enter the tip of the micropipette 510, and then migrate up the micropipette 510 based on the attractive force applied by the magnetic ring 520. The suction force can be controlled manually or automatically with the use of a computer-controlled robotic manipulator.
As described herein with respect to the magnet 130, the magnitude of the attractive force applied by the magnetic ring 520 can be modulated (e.g., moving the location of the magnetic ring 520 along a vertical location on the pipette 510, adjusting the current applied to a magnetic ring 520 that is an electromagnet) to control the migration of the single cell 202a up the tip of the micropipette 510. In some instances, the magnitude of the attractive force can be set to a particular value such that single cell 202a remains within a vicinity of the magnetic ring 520 after reaching a certain distance from the magnetic ring 520. For example, the magnitude of the magnetic force applied by the magnetic ring 520 can configured such that the cell 202a is stuck to the side of the micropipette 510 in the presence of a liquid flow out of the tip of the micropipette 510. In such instances, the micropipette 510 can then be used to transport the extracted cell to a precise location by using an outward hydraulic force from the micropipette 510 of a greater magnitude than the attractive force applied by the magnetic ring 520.
In one implementation, the magnetic ring can be an electromagnet whose strength could be adjusted or switched on and off to hold magnetized entities inside the tip or help ejecting them from the tip.
In one implementation, the magnetic ring is replaced with one or multiple magnets with cubic or rectangular shapes that are placed on one or multiple sides of the micropipette at a specific distance from the tip. The magnetic fields strength can be localized so as to prevent perturbation of other cells.
In a different implementation for cell extraction, the micro-well chip is accessed directly by conventional micropipettes that have tips that are small enough to enter into the micro-wells. The micropipettes can be connected to computer-controlled translation stages and fluidic flow control modules to fluidly extract the cells. Such implementations can be particularly useful for applications wherein the micro-well chip, after capturing of the cells only contains liquid in its micro-wells but not on its entire surface. This implementation can also be useful for applications that involve delivering a specific chemical or fluid into an individual micro-well without cross-contamination of other micro-wells. In this implementation, a magnetic force provided from below can hold the cell in place while a wash step is performed by injection using the pipette.
In one implementation, the pipette that is used has a tip that is larger than the entrance diameter of a micro-well. This implementation can be particularly useful when the micro-well chip is placed in a fluid in such a manner that the same fluid contacts most of the micro-wells. The fluidic suction created by a pump that is connected to the pipette can then be configured to be sufficient to extract the contents of a micro-well without perturbing the contents of other micro-wells. In one instance, the fluidic pressure and the spacing between the micro-wells can be configured to be large enough to prevent such perturbation. Alternatively, the spacing and the fluidic suction pressure can be controlled to cause extraction from a number of neighboring micro-wells without perturbing others.
In one implementation, a pump or syringe is configured to create a droplet of liquid extend from the tip of a pipette without completely detaching from the tip of the pipette. This droplet can then be used to form a fluid connection between the pipette and the liquid inside a micro-well. This fluid connection can then enable ‘sucking’ the cell out of the micro-well by means of a pump or a syringe that is connected to the pipette through a tube. This implementation can be particularly useful for applications where the micro-well chip is not placed in fluid in its entirety but contains liquid in its micro-wells.
In one implementation, the micro-well chip is accessed by micropipettes that are bent so as to prevent obstruction of microscopic viewing of the micro-well chip from above.
In one implementation, the magnetic field applied from underneath the micro-well chip is adjusted, instead of being completely turned off, to a level that will permit extraction of a magnetized entity using pipetting.
In more detail, the process 600 can include injecting a fluid containing magnetized cells into a microfluidic system (610). For instance, the sample fluid including target cells 202a can be injected into the microfluidic chamber of the micro-well chip 110 using the fluid control device 120.
The process 600 can include applying a variable magnetic force to a chamber of the microfluidic system using a magnet component (620). For instance, the magnet 130 can be used to generate the attractive force 212 beneath the micro-well chip 110 such that the target cells 202a are captured within the micro-wells on the surface of the micro-well chip 110. In some instances, the magnitude of the attractive force 212 can be modulated to increase or decrease the force applied on the target cells 202a.
The process 600 can include adjusting placement of the magnet component relative to the chamber of the microfluidic system (630). For instance, the magnet 130 can be moved along the x-axis and the y-axis of the surface of the micro-well chip 110 such that different portions of the micro-well chip 110 are exposed to the attractive force 212. As described previously, the adjustment can be made in certain patterns (e.g., circular, zigzag, raster, or sigmoidal) to improve the capture efficiency of the micro-wells.
The process 600 can include analyzing optical properties of the magnetized cells (640). For instance, the analyzer device 140 can be used to assess or analyze the target cells 202a that are captured in the micro-wells of the micro-well chip 110. In some instances, the analyzer device 140 can be a microscope that uses various types of imaging modalities to collect images of the captured cells as described herein.
The invention is further described in the following examples, which do not limit the scope of the invention described in the claims.
In one example, the micro-well chip is a silicon wafer with an array of micro-wells that are eight micrometers in diameter and approximately 10 micrometers in depth that were formed using an etching technique. In this example, no cells were tested, but 2.8 micrometer streptavidin-coated magnetic beads conjugated with biotinylated-FITC for fluorescence measurements were tested as a proof-of-concept. A PDMS spacer was placed around the micro-well chip so as to form a cuvette (i.e., without using a closed fluidic chamber) that can hold approximately 200 microliters of fluid.
During a preliminary experiment, a 200-microliter phosphate buffered saline-tween (PBST) buffer containing a 50 microliter bead suspension (approximately 350,000 magnetic beads) was initially placed on the micro-well chip as a droplet using a micropipette. A magnet was then swept underneath the micro-well chip to capture the magnetic beads into the 8 micrometer micro-wells. The micro-well chip was then placed underneath a bright field microscope and a fluorescent microscope was used to analyze the capture efficiency of the magnetic beads on the micro-well chip.
A first bright field image and a fluorescent image of the same array of micro-wells were captured prior to the magnet sweep and utilized as a control measurement for cell capture within the micro-wells. After performing a magnet sweep, a second bright field image and fluorescent image of the array of micro-wells were captured to determine the impact of the attractive force on the capture efficiency by the micro-wells. Comparisons of the captured images indicate that the magnet sweep improved the capture efficiency of the micro-wells (indicated by the increased fluorescence detected within the array of micro-wells), which suggests that a greater number of magnetic beads were captured by the micro-wells.
In this example, the micro-well chip is a silicon wafer with an array of micro-wells that are 30 micrometers in diameter and approximately 40 micrometers in depth with 200-micrometer center-to-center spacing that was formed using photolithography and a deep reactive ion etching technique. The micro-well chip surface was blocked with a PBST buffer that contains BSA (bovine serum albumin) to prevent or minimize sticking of cells onto the chip surface or the micro-wells.
A feasibility experiment was conducted to verify the capability of directing magnetized cells into micro-wells as well as extracting them using a pipette. A PDMS spacer/frame was placed on the micro-well chip in a manner that surrounds the area that contained the micro-wells. The PDMS frame served for the purposed of a “cuvette” that was capable of maintaining a maximum fluid volume of 200 microliters. A 100-microliter sample fluid with approximately 1000 KB cells (cultured tumor cells) that were previously labeled with both anti-folate-receptor antibody conjugated magnetic beads, and FITC-conjugated folate were introduced into the cuvette. (The beads were 1-micrometer streptavidin coated superparamagnetic beads that were conjugated with biotinylated antibodies against folate receptor).
A magnet was then placed underneath the microfluidic chamber and swept across from one side of the micro-well chip to the opposite side of the micro-well chip for about 10 seconds to apply an attractive force across the micro-well chip during the sweep of the magnet to capture the cultured tumor cells into the micro-wells of the micro-well chip. The micro-well chip was then imaged using both bright field as well as fluorescent microscopy for analysis. The magnet was swept from side to side, but can also be moved in a circular or sinusoidal pattern.
In the experiment, the presence of cells was verified by fluorescence microcopy (
In some implementations, this optical effect illustrated in
In some implementations, one or more computer algorithms are used to recognize the presence of one or more target entities in micro-wells, determine locations of identified target entities, and assign specific coordinates for each micro-well of a micro-well chip. In these implementations, location and coordinate information is used to extract the contents of micro-wells (e.g., captured target entities) in a substantially automatic computer-implemented manner (e.g., without human intervention). For example, an actuating device can be used to move a pipette to a coordinate location of a particular micro-well and then operate the pipette to extract the contents of the particular micro-well without the need to use microscopy to visualize and/or identify the location of the particular micro-well. In addition, assigned coordinate locations of micro-wells can also be used to standardize extraction techniques such that the contents of a particular micro-well chip can examined in different experimental laboratories with the use of an assigned coordinate location.
Results depicted in
An experiment was performed to verify if a single cell could be extracted from a micro-well chip without perturbing cells that were captured in nearby micro-wells. In this experiment, the chip included micro-wells that captured different kinds of fluorescently tagged cells (magnetized KB cells, and magnetized MCF-7 cells). The fluorescence signals produced was used as an indicator of a cell being captured in a micro-well, and visual confirmation that a cell had been extracted from the micro-well after applying a suction force using a micropipette. The KB cells were labeled with FITC-tagged magnetic beads baring anti-folate receptor antibodies that emit a green fluorescence signal. The MCF-7 cells were labeled with PE-tagged magnetic beads baring anti-EpCAM antibodies that emit a red fluorescence signal.
Fluorescent images were captured during an extraction procedure for a single KB cell (green) to determine if the extraction affected cells captured in nearby micro-wells. A first set of images were captured prior to extraction to use a green fluorescence signal produced by the KB cell to verify that it was captured in a micro-well. These images were also used to verify that a MCF-7 cell (red) was not captured even though it was in a nearby micro-well. A second set of images were captured during the extraction procedure to identify movement of the KB cell after being exposed to a suction force applied by a micropipette placed above the micro-well where the KB cell was captured. A third set of images were captured after completing the extraction procedure to characterize the impacts of the extraction procedure on nearby cells such as the MCF-7 cell.
Results from the collected images indicated that a suction force applied by a micropipette caused the KB cell to travel inside a tip of the micropipette after a suction force was applied above a micro-well where the cell was captured. Once the extraction operation was completed, results indicated that the MCF-7 cell was still present in its location (determined based on comparing the presence of a fluorescence signal in images collected prior to and after the extraction procedure). These results illustrate the benefit of using a micro-well chip to separate rare cell populations into individual micro-wells, where the number of cells in a fluid sample is significantly less than the number of micro-wells on the surface of the micro-well chip.
An experiment was performed to determine the impact of having multiple cell populations within a single substrate on the capturing ability of micro-wells on the surface of a micro-well chip. The substrate included two kinds of fluorescently tagged cells (magnetized KB cells, and magnetized MCF-7 cells). The KB cells were labeled with FITC-tagged magnetic beads baring anti-folate receptor antibodies that emit a green fluorescence signal. The MCF-7 cells were labeled with PE-tagged magnetic beads baring anti-EpCAM antibodies that emit a red fluorescence signal.
During the experiment, the micro-well chip was placed in a closed fluidic chamber and the mixture was initially distributed over the micro-wells by a laminar fluid flow. The flow was then stopped and a magnetic sweep was performed to attract the magnetized cell populations towards the surface of the micro-well chip to induce cell capture within micro-wells. Fluorescent images of the surface of the micro-well chip were then captured to identify cell capture based on the presence of fluorescent signals within the micro-wells. To determine whether cell capture was localized to a particular regions of the micro-well chip, various fields of views were captured and stitched together to reconstruct a high field-of-view image that collectively represented a large area of the surface of the micro-well chip.
Results indicated that over 1000 cells were captured in the micro-wells of the micro-well chip. Results also indicated that both types of cells (e.g., KB cells and MCF-7 cells) were captured within the micro-wells, indicating that the presence of different cell types did not cause preferential cell capture within the micro-wells.
In another example, a micro-well chip can be used to detect and analyze multiple target entities such as different types of viruses or molecules within a single microfluidic chamber. In this example, the micro-well chip 110 can be constructed to have a micro-well arrangement pattern that includes a set of micro-well entrance sizes on the surface of the micro-well chip 110 corresponding to a set of individual magnetic beads that are each associated with a different target entity.
For instance, each group of magnetic beads, with each group having a different size, can initially be functionalized to recognize and bind specifically to (e.g., with the use of an antibody) one type of target molecule. The magnetic beads can then be exposed to the fluid sample containing different types of target molecules. After the magnetic beads have been bound to the respective target molecules, the fluid sample can be introduced into the microfluidic chamber of the micro-well chip 110 and the different micro-well entrance sizes corresponding to the various magnetic beads can be used to separate the capture of target molecules by magnetic bead size (e.g., smaller magnetic beads with corresponding target entities being captured upstream). The micro-well chip 110 can then be used with single color fluorescence detection to obtain readouts using single-color fluorescent microscopes or inexpensive plate readers. In this implementation, the types of target entities that can be detected include DNA, RNA, proteins, antibodies, enzymes, viruses, extracellular vesicles, exosomes, nucleosomes, small molecules and peptides.
A number of implementations have been described. Nevertheless, it will be understood that various modifications can be made without departing from the spirit and scope of the invention. In addition, the logic flows depicted in the figures do not require the particular order shown, or sequential order, to achieve desirable results. In addition, other steps can be provided, or steps can be eliminated, from the described flows, and other components can be added to, or removed from, the described systems. Accordingly, other implementations are within the scope of the following claims.
This application claims priority to U.S. Provisional Application No. 62/326,405, filed on Apr. 22, 2016 and entitled “HIGH-THROUGHPUT PARTICLE CAPTURE AND ANALYSIS,” the entire disclosure of which is incorporated herein by reference.
| Filing Document | Filing Date | Country | Kind |
|---|---|---|---|
| PCT/US2017/029202 | 4/24/2017 | WO | 00 |
| Number | Date | Country | |
|---|---|---|---|
| 62326405 | Apr 2016 | US |
