Patent Application
20200299351
Immunotherapy offers a potentially powerful approach to treating cancers successfully. T lymphocyte activation by antigen presenting dendritic cells is one aspect of preparing tumor-targeting cytotoxic T lymphocytes for use in immunotherapy. Activation by dendritic cells may be improved by using more reproducible and better characterizable technologies. Some embodiments of the present invention include modified surfaces configured to activate T lymphocytes, related methods of using such modified surfaces to activate T lymphocytes, and compositions containing such activated T lymphocytes.
In a first aspect, an antigen-presenting surface for activating a T lymphocyte (T cell) is provided, comprising: a plurality of primary activating molecular ligands, wherein each primary activating molecular ligand comprises a major histocompatibility complex (MHC) Class I molecule configured to bind to a T cell receptor (TCR) of the T cell; and, a plurality of co-activating molecular ligands each comprising a TCR co-activating molecule or an adjunct TCR activating molecule, wherein each of the plurality of primary activating molecular ligands and the plurality of co-activating molecular ligands is specifically bound to the antigen presenting surface. In some embodiments, the plurality of co-activating molecular ligands comprise TCR co-activating molecules and an adjunct TCR activating molecules. In some embodiments, the ratio of the TCR co-activating molecules to the adjunct TCR activating molecule may be about 10:1 to about 1:20. In some embodiments, the plurality of primary activating molecular ligands may be disposed upon at least a portion of the antigen-presenting surface at a density from about 4×102 to about 3×104 molecules per square micron. In other embodiments, the plurality of primary activating molecular ligands is disposed upon at least a portion of a surface of the antigen-presenting surface at a density from about 5×103 to about 3×104 molecules per square micron. In any of these embodiments, the antigen-presenting surface can be the surface of a bead. In any of these embodiments, the antigen-presenting surface can be the surface of a wafer. In any of these embodiments, the antigen-presenting surface can be at least one inner surface of a microfluidic device. In any of these embodiments, the antigen-presenting surface can be an inner surface of a tube.
In another aspect, a method of preparing an antigen-presenting surface for activating a T lymphocyte (T cell) is provided, comprising: reacting a plurality of primary activating molecules, each comprising a major histocompatibility complex (MHC) Class I molecule configured to bind to a T cell receptor of the T cell, with a first plurality of binding moieties of a covalently functionalized surface, wherein each of the first plurality of binding moieties is configured for binding the primary activating molecule; and reacting a plurality of co-activating molecules, each comprising: a T cell receptor (TCR) co-activating molecule; or an adjunct TCR activating molecule, with a second plurality of binding moieties of the covalently functionalized surface configured for binding the co-activating molecule, thereby providing a plurality of specifically bound primary activating molecular ligands and a plurality of specifically bound co-activating molecular ligands on the antigen-presenting surface. In any of these embodiments, the antigen-presenting surface can be the surface of a bead. In any of these embodiments, the antigen-presenting surface can be the surface of a wafer. In any of these embodiments, the antigen-presenting surface can be at least one inner surface of a microfluidic device. In any of these embodiments, the antigen-presenting surface can be an inner surface of a tube.
In another aspect, a kit is provided for preparing an antigen-presenting synthetic surface for activating a T lymphocyte (T cell), including: a. any covalently functionalized synthetic surface as described herein, which includes a plurality of noncovalently or covalently associated first coupling agents; and a first modification reagent including a plurality of major histocompatibility complex (MHC) I molecules configured to bind with a T cell receptor of the T cell, and further wherein the MHC molecules are configured to bind to one of a first subset of the plurality of noncovalently or covalently associated first coupling agents of the covalently functionalized synthetic surface. In some embodiments, the first coupling agents may be a biotin-binding agent. The biotin-binding agent may be streptavidin. In some embodiments, each of the plurality of MHC molecules may further include at least one biotin functionality. In some embodiments, the kit further includes a reagent comprising a plurality of co-activating molecules, each configured to bind one of a second subset of the noncovalently or covalently associated first coupling agents of the covalently functionalized synthetic surface. In some embodiments, the co-activating molecules may be T cell receptor (TCR) co-activating molecules, adjunct TCR activating molecules, or any combination thereof. The co-activating molecules may further include at least one biotin functionality.
In yet another aspect, a method of preparing a covalently functionalized surface comprising a plurality of streptavidin or biotin functionalities and at least a first plurality of surface-blocking molecular ligands, wherein the method comprises: reacting at least a first subset of reactive moieties of an intermediate reactive synthetic surface with a plurality of linking reagents, each linking reagent of the plurality comprising streptavidin or biotin; and reacting at least a second subset of reactive moieties of the intermediate reactive synthetic surface with a plurality of surface-blocking molecules, thereby providing the covalently functionalized synthetic surface comprising at the least one plurality of streptavidin or biotin functionalities and at the least first plurality of surface-blocking molecular ligands. In some embodiments, if the linking reagents comprise biotin, the method optionally further comprises noncovalently associating streptavidin with the biotin functionalities.
In another aspect, a method of activating T lymphocytes (T cells) is provided, comprising: contacting a plurality of T cells with an antigen-presenting synthetic surface comprising: a plurality of primary activating molecular ligands, each comprising a major histocompatibility (MHC) Class I molecule configured to bind to a T cell receptor of the T cell; and a plurality of co-activating molecular ligands each comprising a T cell receptor (TCR) co-activating molecule or an adjunct TCR activating molecule; and culturing the plurality of T cells in contact with the antigen-presenting synthetic surface, thereby converting at least a portion of the plurality of T cells to activated T cells. The antigen-presenting synthetic surface may be any antigen-presenting synthetic surface described herein, e.g., an antigen-presenting bead, antigen-presenting wafer, antigen-presenting tube, or antigen-presenting microfluidic device described herein or a product of any one of the methods described herein. In some embodiments, the T cells comprise CD8+ T cells. In some embodiments, the method further comprises contacting the plurality of T cells with a plurality of growth stimulatory molecular ligands. In some embodiments, each of the growth stimulatory molecular ligands comprises a growth factor receptor ligand. In some embodiments, the growth factor receptor ligand comprises IL-21 or a fragment thereof.
In another aspect, a method of performing an antigen-specific cytotoxicity assay is provided, comprising: loading one or more target cells in a sequestration pen of a microfluidic device; loading one or more T cells in the sequestration pen, such that the one or more T cells can contact the one or more target cells; contacting the target cells with a detectable marker that labels apoptotic cells; and detecting whether the target cells become apoptotic. In certain embodiments, the microfluidic device further comprises a microfluidic channel, and the sequestration pen comprises an opening which opens to the microfluidic channel such that the sequestration pen is fluidically connected to the microfluidic channel. In certain embodiments, a plurality of target cells are loaded into the sequestration pen. In other embodiments, a single target cell is loaded into the sequestration pen. In certain embodiments, a single T cell is loaded into the sequestration pen. In other embodiments, a plurality of T cells are loaded into the sequestration pen. In certain embodiments, the target cell(s) and/or T cell(s) are loaded into the sequestration pen by flowing them into the microfluidic channel, then tilting the microfluidic chip and allowing gravity to pull the target cell(s) and/or T cell(s) into the sequestration pen. In certain embodiments, the microfluidic device comprises a DEP configuration and DEP force is used to load the target cell(s) and/or T cell(s) into the sequestration pen. In certain embodiments, the DEP force is activated by structured light. In certain embodiments, the detectable marker is provided in a solution that is flowed through the microfluidic channel, whereupon the detectable marker can diffuse from the microfluidic channel into the sequestration pen and contact the target cells. In certain embodiments, the detectable marker is a enzymatic substrate, such as a Caspase 3 substrate. In other embodiments, the detectable marker is a labeled antibody that specifically binds to apoptotic cells and/or apoptotic bodies. In certain embodiments, detecting whether the target cells become apoptotic is determined 2 or more hours (e.g., 3, 4, 5, 6, 7, or more hours) after contacting the target cell(s) with the detectable marker. In certain embodiments, the target cell(s) are cancer cells, such as cells from a cancer cell line. In certain embodiments, the target cell(s) are cells from a cell line that express a cancer-associated or cancer-specific antigen. In certain embodiments, the target cell(s) express an antigen associated with melanoma, breast cancer, or lung cancer. In certain embodiments, the T cells express a chimeric antigen receptor (CAR). For example, the T cells can be CAR T cells. In other embodiments, the T cells do not express a chimeric antigen receptor. For example, the T cells can be therapeutic endogenous T cells (ETCs).
In another aspect, a method of treating a subject in need of treating a cancer is provided; comprising: obtaining a plurality of T lymphocytes (T cells) from the subject; contacting the plurality of T cells with an antigen-presenting synthetic surface comprising a plurality of major histocompatibility complex (MHC) I molecules configured to bind to a T cell receptor of each of the plurality of T cells, wherein the MHC molecules comprise an antigen specific for the cancer of the subject and wherein the antigen-presenting synthetic surface is an antigen-presenting surface described herein or is produced according to a method as described herein; producing a plurality of activated T cells, wherein the activation is configured to be specific against the cancer of the subject; separating the plurality of specific activated T cells from unactivated cells; and, introducing the plurality of antigen-specific activated T cells into the subject. In some embodiments, the antigen-presenting surface is an antigen-presenting bead, an antigen-presenting wafer, an antigen-presenting tube, or an antigen-presenting microfluidic device as described herein.
In another aspect, a kit for activating T lymphocytes (T cells) is provided, comprising: an antigen-presenting surface described herein. In some embodiments, the antigen-presenting surface is an antigen-presenting bead, an antigen-presenting wafer, an antigen-presenting tube, or an antigen-presenting microfluidic device as described herein.
In another aspect, a kit for performing an antigen-specific cytotoxicity assay is provided, comprising: a microfluidic device (e.g., a microfluidic device having a microfluidic channel and a sequestration pen); and a reagent for detecting apoptosis. In certain embodiments, the microfluidic device is an antigen-presenting microfluidic device. The microfluidic device or antigen-presenting microfluidic device can be any microfluidic device or antigen-presenting microfluidic device described herein. In certain embodiments, the reagent for detecting apoptosis is a substrate for a caspase enzyme, such as Caspase 3. In certain embodiments, the reagent for detecting apoptosis specifically binds to apoptotic cells, such as an apoptosis-specific antibody.
In a further aspect, a covalently functionalized synthetic surface is provided, comprising at least one plurality of streptavidin functionalities and at least one plurality of surface-blocking molecular ligands, wherein the plurality of surface-blocking molecular ligands are covalently attached to the covalently functionalized synthetic surface, and the streptavidin functionalities are (i) covalently attached to the covalently functionalized synthetic surface or (ii) noncovalently attached to the covalently functionalized synthetic surface through a biotin moiety covalently attached to the covalently functionalized synthetic surface. In some embodiments, the covalently functionalized synthetic surface may be a covalently functionalized bead, a covalently functionalized wafer, or a covalently functionalized microfluidic device, as described herein.
This specification describes exemplary embodiments and applications of the disclosure. The disclosure, however, is not limited to these exemplary embodiments and applications or to the manner in which the exemplary embodiments and applications operate or are described herein. Moreover, the figures may show simplified or partial views, and the dimensions of elements in the figures may be exaggerated or otherwise not in proportion. In addition, as the terms “on,” “attached to,” “connected to,” “coupled to,” or similar words are used herein, one element (e.g., a material, a layer, a substrate, etc.) can be “on,” “attached to,” “connected to,” or “coupled to” another element regardless of whether the one element is directly on, attached to, connected to, or coupled to the other element or there are one or more intervening elements between the one element and the other element. Also, unless the context dictates otherwise, directions (e.g., above, below, top, bottom, side, up, down, under, over, upper, lower, horizontal, vertical, “x,” “y,” “z,” etc.), if provided, are relative and provided solely by way of example and for ease of illustration and discussion and not by way of limitation. In addition, where reference is made to a list of elements (e.g., elements a, b, c), such reference is intended to include any one of the listed elements by itself, any combination of less than all of the listed elements, and/or a combination of all of the listed elements. The term “or” is used in an inclusive sense, i.e., equivalent to “and/or,” unless the context dictates otherwise. It is noted that, as used in this specification and the appended claims, the singular forms “a,” “an,” and “the,” and any singular use of any word, include plural referents unless expressly and unequivocally limited to one referent. As used herein, the terms “comprise,” “include,” and grammatical variants thereof are intended to be non-limiting, such that recitation of items in a list is not to the exclusion of other like items that can be substituted or added to the listed items. Section divisions in the specification are for ease of review only and do not limit any combination of elements discussed. In case of any contradiction or conflict between material incorporated by reference and the expressly described content provided herein, the expressly described content controls.
Where dimensions of microfluidic features are described as having a width or an area, the dimension typically is described relative to an x-axial and/or y-axial dimension, both of which lie within a plane that is parallel to the substrate and/or cover of the microfluidic device. The height of a microfluidic feature may be described relative to a z-axial direction, which is perpendicular to a plane that is parallel to the substrate and/or cover of the microfluidic device. In some instances, a cross sectional area of a microfluidic feature, such as a channel or a passageway, may be in reference to a x-axial/z-axial, a y-axial/z-axial, or an x-axial/y-axial area.
For the purposes of this specification and appended claims, unless otherwise indicated, all numbers expressing quantities, percentages, or proportions, and other numerical values used in the specification and claims, are to be understood as being modified in all instances by the term “about,” to the extent they are not already so modified. “About” indicates a degree of variation that does not substantially affect the properties of the described subject matter, e.g., within 10%, 5%, 2%, or 1%. Accordingly, unless indicated to the contrary, the numerical parameters set forth in the following specification and attached claims are approximations that may vary depending upon the desired properties sought to be obtained. At the very least, and not as an attempt to limit the application of the doctrine of equivalents to the scope of the claims, each numerical parameter should at least be construed considering the number of reported significant digits and by applying ordinary rounding techniques.
As used herein, “substantially” means sufficient to work for the intended purpose. The term “substantially” thus allows for minor, insignificant variations from an absolute or perfect state, dimension, measurement, result, or the like such as would be expected by a person of ordinary skill in the field but that do not appreciably affect overall performance. When used with respect to numerical values or parameters or characteristics that can be expressed as numerical values, “substantially” means within ten percent.
The term “ones” means more than one. As used herein, the term “plurality” can be 2, 3, 4, 5, 6, 7, 8, 9, 10, or more.
As used herein, “alkyl” refers to a straight or branched hydrocarbon chain radical consisting solely of carbon and hydrogen atoms, containing no unsaturation, having from one to six carbon atoms (e.g., C1-C6 alkyl). Whenever it appears herein, a numerical range such as “1 to 6” refers to each integer in the given range; e.g., “1 to 6 carbon atoms” means that the alkyl group may consist of 1 carbon atom, 2 carbon atoms, 3 carbon atoms, etc., up to and including 6 carbon atoms, although the present definition also covers the occurrence of the term “alkyl” where no numerical range is designated. In some embodiments, it is a C1-C3 alkyl group. Typical alkyl groups include, but are in no way limited to, methyl, ethyl, propyl, isopropyl, n-butyl, iso-butyl, sec-butyl isobutyl, tertiary butyl, pentyl, isopentyl, neopentyl, hexyl, and the like. The alkyl is attached to the rest of the molecule by a single bond, for example, methyl (Me), ethyl (Et), n-propyl, 1-methylethyl (iso-propyl), n-butyl, n-pentyl, 1,1-dimethylethyl (t-butyl); hexyl, and the like.
Unless stated otherwise specifically in the specification, an alkyl group may be optionally substituted by one or more substituents which independently are: aryl, arylalkyl, heteroaryl, heteroarylalkyl, hydroxy, halo, cyano, trifluoromethyl, trifluoromethoxy, nitro, trimethylsilanyl, —OR′, —SR′, —OC(O)—R′, —C(O)R′, —C(O)OR′, —OC(O)N(R′)2, —C(O)N(R)2, —N(R′)C(O)OR′, —N(R′)C(O)R′, —N(R′)C(O)N(R′)2, N(R′)C(NR′)N(R′)2, —N(R′)S(O)tR′ (where t is 1 or 2), —S(O)tOR′ (where t is 1 or 2), —S(O)tN(R)2 (where t is 1 or 2), or PO3(R′)2 where each R′ is independently hydrogen, alkyl, fluoroalkyl, aryl, aralkyl, heterocycloalkyl, or heteroaryl.
As referred to herein, a fluorinated alkyl moiety is an alkyl moiety having one or more hydrogens of the alkyl moiety replaced by a fluoro substituent. A perfluorinated alkyl moiety has all hydrogens attached to the alkyl moiety replaced by fluoro substituents.
As referred to herein, a “halo” moiety is a bromo, chloro, or fluoro moiety.
As referred to herein, an “olefinic” compound is an organic molecule which contains an “alkene” moiety. An alkene moiety refers to a group consisting of at least two carbon atoms and at least one carbon-carbon double bond. The non-alkene portion of the molecule may be any class of organic molecule, and in some embodiments, may include alkyl or fluorinated (including but not limited to perfluorinated) alkyl moieties, any of which may be further substituted.
As used herein, “air” refers to the composition of gases predominating in the atmosphere of the earth. The four most plentiful gases are nitrogen (typically present at a concentration of about 78% by volume, e.g., in a range from about 70-80%), oxygen (typically present at about 20.95% by volume at sea level, e.g. in a range from about 10% to about 25%), argon (typically present at about 1.0% by volume, e.g. in a range from about 0.1% to about 3%), and carbon dioxide (typically present at about 0.04%, e.g., in a range from about 0.01% to about 0.07%). Air may have other trace gases such as methane, nitrous oxide or ozone, trace pollutants and organic materials such as pollen, diesel particulates and the like. Air may include water vapor (typically present at about 0.25%, or may be present in a range from about 10 ppm to about 5% by volume). Air may be provided for use in culturing experiments as a filtered, controlled composition and may be conditioned as described herein.
As used herein, the term “plurality” can be 2, 3, 4, 5, 6, 7, 8, 9, 10, or more.
As used herein, the term “disposed” encompasses within its meaning “located.”
As used herein, a “microfluidic device” or “microfluidic apparatus” is a device that includes one or more discrete microfluidic circuits configured to hold a fluid, each microfluidic circuit comprised of fluidically interconnected circuit elements, including but not limited to region(s), flow path(s), channel(s), chamber(s), and/or pen(s), and at least one port configured to allow the fluid (and, optionally, micro-objects suspended in the fluid) to flow into and/or out of the microfluidic device. Typically, a microfluidic circuit of a microfluidic device will include a flow region, which may include a microfluidic channel, and at least one chamber, and will hold a volume of fluid of less than about 1 mL, e.g., less than about 750, 500, 250, 200, 150, 100, 75, 50, 25, 20, 15, 10, 9, 8, 7, 6, 5, 4, 3, or 2 μL. In certain embodiments, the microfluidic circuit holds about 1-2, 1-3, 1-4, 1-5, 2-5, 2-8, 2-10, 2-12, 2-15, 2-20, 5-20, 5-30, 5-40, 5-50, 10-50, 10-75, 10-100, 20-100, 20-150, 20-200, 50-200, 50-250, or 50-300 μL. The microfluidic circuit may be configured to have a first end fluidically connected with a first port (e.g., an inlet) in the microfluidic device and a second end fluidically connected with a second port (e.g., an outlet) in the microfluidic device.
As used herein, a “nanofluidic device” or “nanofluidic apparatus” is a type of microfluidic device having a microfluidic circuit that contains at least one circuit element configured to hold a volume of fluid of less than about 1 μL, e.g., less than about 750, 500, 250, 200, 150, 100, 75, 50, 25, 20, 15, 10, 9, 8, 7, 6, 5, 4, 3, 2, 1 nL or less. A nanofluidic device may comprise a plurality of circuit elements (e.g., at least 2, 3, 4, 5, 6, 7, 8, 9, 10, 15, 20, 25, 50, 75, 100, 150, 200, 250, 300, 400, 500, 600, 700, 800, 900, 1000, 1500, 2000, 2500, 3000, 3500, 4000, 4500, 5000, 6000, 7000, 8000, 9000, 10,000, or more). In certain embodiments, one or more (e.g., all) of the at least one circuit elements is configured to hold a volume of fluid of about 100 μL to 1 nL, 100 μL to 2 nL, 100 μL to 5 nL, 250 μL to 2 nL, 250 μL to 5 nL, 250 μL to 10 nL, 500 μL to 5 nL, 500 μL to 10 nL, 500 μL to 15 nL, 750 μL to 10 nL, 750 μL to 15 nL, 750 μL to 20 nL, 1 to 10 nL, 1 to 15 nL, 1 to 20 nL, 1 to 25 nL, or 1 to 50 nL. In other embodiments, one or more (e.g., all) of the at least one circuit elements are configured to hold a volume of fluid of about 20 nL to 200 nL, 100 to 200 nL, 100 to 300 nL, 100 to 400 nL, 100 to 500 nL, 200 to 300 nL, 200 to 400 nL, 200 to 500 nL, 200 to 600 nL, 200 to 700 nL, 250 to 400 nL, 250 to 500 nL, 250 to 600 nL, or 250 to 750 nL.
A microfluidic device or a nanofluidic device may be referred to herein as a “microfluidic chip” or a “chip”; or “nanofluidic chip” or “chip”.
A “microfluidic channel” or “flow channel” as used herein refers to flow region of a microfluidic device having a length that is significantly longer than both the horizontal and vertical dimensions. For example, the flow channel can be at least 5 times the length of either the horizontal or vertical dimension, e.g., at least 10 times the length, at least 25 times the length, at least 100 times the length, at least 200 times the length, at least 500 times the length, at least 1,000 times the length, at least 5,000 times the length, or longer. In some embodiments, the length of a flow channel is about 100,000 microns to about 500,000 microns, including any value therebetween. In some embodiments, the horizontal dimension is about 100 microns to about 1000 microns (e.g., about 150 to about 500 microns) and the vertical dimension is about 25 microns to about 200 microns, (e.g., from about 40 to about 150 microns). It is noted that a flow channel may have a variety of different spatial configurations in a microfluidic device, and thus is not restricted to a perfectly linear element. For example, a flow channel may be, or include one or more sections having, the following configurations: curve, bend, spiral, incline, decline, fork (e.g., multiple different flow paths), and any combination thereof. In addition, a flow channel may have different cross-sectional areas along its path, widening and constricting to provide a desired fluid flow therein. The flow channel may include valves, and the valves may be of any type known in the art of microfluidics. Examples of microfluidic channels that include valves are disclosed in U.S. Pat. Nos. 6,408,878 and 9,227,200, each of which is herein incorporated by reference in its entirety.
As used herein, the term “obstruction” refers generally to a bump or similar type of structure that is sufficiently large so as to partially (but not completely) impede movement of target micro-objects between two different regions or circuit elements in a microfluidic device. The two different regions/circuit elements can be, for example, a microfluidic sequestration pen and a microfluidic channel, or a connection region and an isolation region of a microfluidic sequestration pen.
As used herein, the term “constriction” refers generally to a narrowing of a width of a circuit element (or an interface between two circuit elements) in a microfluidic device. The constriction can be located, for example, at the interface between a microfluidic sequestration pen and a microfluidic channel, or at the interface between an isolation region and a connection region of a microfluidic sequestration pen.
As used herein, the term “transparent” refers to a material which allows visible light to pass through without substantially altering the light as is passes through.
As used herein, the term “micro-object” refers generally to any microscopic object that may be isolated and/or manipulated in accordance with the present disclosure. Non-limiting examples of micro-objects include: inanimate micro-objects such as microparticles; microbeads (e.g., polystyrene beads, Luminex™ beads, or the like); magnetic beads; microrods; microwires; quantum dots, and the like; biological micro-objects such as cells; biological organelles; vesicles, or complexes; synthetic vesicles; liposomes (e.g., synthetic or derived from membrane preparations); lipid nanorafts, and the like; or a combination of inanimate micro-objects and biological micro-objects (e.g., microbeads attached to cells, liposome-coated micro-beads, liposome-coated magnetic beads, or the like). Beads may include moieties/molecules covalently or non-covalently attached, such as fluorescent labels, proteins, carbohydrates, antigens, small molecule signaling moieties, or other chemical/biological species capable of use in an assay. Lipid nanorafts have been described, for example, in Ritchie et al. (2009) “Reconstitution of Membrane Proteins in Phospholipid Bilayer Nanodiscs,” Methods Enzymol., 464:211-231.
As used herein, the term “cell” is used interchangeably with the term “biological cell.” Non-limiting examples of biological cells include eukaryotic cells, plant cells, animal cells, such as mammalian cells, reptilian cells, avian cells, fish cells, or the like, prokaryotic cells, bacterial cells, fungal cells, protozoan cells, or the like, cells dissociated from a tissue, such as muscle, cartilage, fat, skin, liver, lung, neural tissue, and the like, immunological cells, such as T cells, B cells, natural killer cells, macrophages, and the like, embryos (e.g., zygotes), oocytes, ova, sperm cells, hybridomas, cultured cells, cells from a cell line, cancer cells, infected cells, transfected and/or transformed cells, reporter cells, and the like. A mammalian cell can be, for example, from a human, a mouse, a rat, a horse, a goat, a sheep, a cow, a primate, or the like.
A colony of biological cells is “clonal” if all of the living cells in the colony that are capable of reproducing are daughter cells derived from a single parent cell. In certain embodiments, all the daughter cells in a clonal colony are derived from the single parent cell by no more than 10 divisions. In other embodiments, all the daughter cells in a clonal colony are derived from the single parent cell by no more than 14 divisions. In other embodiments, all the daughter cells in a clonal colony are derived from the single parent cell by no more than 17 divisions. In other embodiments, all the daughter cells in a clonal colony are derived from the single parent cell by no more than 20 divisions. The term “clonal cells” refers to cells of the same clonal colony.
As used herein, a “colony” of biological cells refers to 2 or more cells (e.g. about 2 to about 20, about 4 to about 40, about 6 to about 60, about 8 to about 80, about 10 to about 100, about 20 to about 200, about 40 to about 400, about 60 to about 600, about 80 to about 800, about 100 to about 1000, or greater than 1000 cells).
As used herein, the term “maintaining (a) cell(s)” refers to providing an environment comprising both fluidic and gaseous components and, optionally a surface, that provides the conditions necessary to keep the cells viable and/or expanding.
As used herein, the term “expanding” when referring to cells, refers to increasing in cell number.
As referred to herein, “gas permeable” means that the material or structure is permeable to at least one of oxygen, carbon dioxide, or nitrogen. In some embodiments, the gas permeable material or structure is permeable to more than one of oxygen, carbon dioxide and nitrogen and may further be permeable to all three of these gases.
A “component” of a fluidic medium is any chemical or biochemical molecule present in the medium, including solvent molecules, ions, small molecules, antibiotics, nucleotides and nucleosides, nucleic acids, amino acids, peptides, proteins, sugars, carbohydrates, lipids, fatty acids, cholesterol, metabolites, or the like.
As used herein in reference to a fluidic medium, “diffuse” and “diffusion” refer to thermodynamic movement of a component of the fluidic medium down a concentration gradient.
The phrase “flow of a medium” means bulk movement of a fluidic medium primarily due to any mechanism other than diffusion. For example, flow of a medium can involve movement of the fluidic medium from one point to another point due to a pressure differential between the points. Such flow can include a continuous, pulsed, periodic, random, intermittent, or reciprocating flow of the liquid, or any combination thereof. When one fluidic medium flows into another fluidic medium, turbulence and mixing of the media can result.
The phrase “substantially no flow” refers to a rate of flow of a fluidic medium that, when averaged over time, is less than the rate of diffusion of components of a material (e.g., an analyte of interest) into or within the fluidic medium. The rate of diffusion of components of such a material can depend on, for example, temperature, the size of the components, and the strength of interactions between the components and the fluidic medium.
As used herein in reference to different regions within a microfluidic device, the phrase “fluidically connected” means that, when the different regions are substantially filled with fluid, such as fluidic media, the fluid in each of the regions is connected so as to form a single body of fluid. This does not mean that the fluids (or fluidic media) in the different regions are necessarily identical in composition. Rather, the fluids in different fluidically connected regions of a microfluidic device can have different compositions (e.g., different concentrations of solutes, such as proteins, carbohydrates, ions, or other molecules) which are in flux as solutes move down their respective concentration gradients and/or fluids flow through the device.
As used herein, a “flow path” refers to one or more fluidically connected circuit elements (e.g. channel(s), region(s), chamber(s) and the like) that define, and are subject to, the trajectory of a flow of medium. A flow path is thus an example of a swept region of a microfluidic device. Other circuit elements (e.g., unswept regions) may be fluidically connected with the circuit elements that comprise the flow path without being subject to the flow of medium in the flow path.
As used herein, “isolating a micro-object” confines a micro-object to a defined area within the microfluidic device.
A microfluidic (or nanofluidic) device can comprise “swept” regions and “unswept” regions. As used herein, a “swept” region is comprised of one or more fluidically interconnected circuit elements of a microfluidic circuit, each of which experiences a flow of medium when fluid is flowing through the microfluidic circuit. The circuit elements of a swept region can include, for example, regions, channels, and all or parts of chambers. As used herein, an “unswept” region is comprised of one or more fluidically interconnected circuit element of a microfluidic circuit, each of which experiences substantially no flux of fluid when fluid is flowing through the microfluidic circuit. An unswept region can be fluidically connected to a swept region, provided the fluidic connections are structured to enable diffusion but substantially no flow of media between the swept region and the unswept region. The microfluidic device can thus be structured to substantially isolate an unswept region from a flow of medium in a swept region, while enabling substantially only diffusive fluidic communication between the swept region and the unswept region. For example, a flow channel of a micro-fluidic device is an example of a swept region while an isolation region (described in further detail below) of a microfluidic device is an example of an unswept region.
As used herein, a “non-sweeping” rate of fluidic medium flow means a rate of flow in a flow region, such as a microfluidic channel, which is sufficient to permit components of a second fluidic medium in an isolation region of the sequestration pen to diffuse into the first fluidic medium in the flow region and/or components of the first fluidic medium to diffuse into the second fluidic medium in the isolation region; and further wherein the first medium does not substantially flow into the isolation region.
As used herein, “synthetic surface” refers to an interface between a support structure and a gaseous/liquid medium, where the synthetic surface is prepared by non-biological processes. The synthetic surface may have biologically derived materials connected to it, e.g., primary and co-activating molecules as described herein, to provide an antigen-presenting synthetic surface, provided that the synthetic surface is not expressed by a biological organism. Typically, the support structure is solid, such as the non-surface exposed portions of a bead, a wafer, or a substrate, cover or circuit material of a microfluidic device and does not enclose a biological nucleus or organelle.
As used herein, “co-activating” refers to a binding interaction between a biological macromolecule, fragment thereof, or synthetic or modified version thereof and a T cell, other than the primary T cell receptor/antigen:MHC binding interaction, that enhances a productive immune response to produce activation of the T cell. Co-activating interactions are antigen-nonspecific interactions, e.g., between a T-cell surface protein able to engage in intracellular signaling such as CD28, CD2, ICOS, etc., and an agonist thereof. “Co-activation” and “co-activating” as used herein is equivalent to the terms co-stimulation and co-stimulating, respectively.
As used herein, a “TCR co-activating molecule” is a biological macromolecule, fragment thereof, or synthetic or modified version thereof that binds to one or more co-receptors on a T Cell that activate distal signaling molecules which amplify and/or complete the response instigated by antigen specific binding of the TCR. In one example, signaling molecules such as transcription factors Nuclear Factor kappa B (NF kB) and Nuclear factor of activated T cells (NFAT) are activated by the TCR co-activating molecule. The TCR co-activating molecule can be, for example, an agonist of the CD28 receptor, which signals through the phosphoinositide 3 kinase (PI3K)/Akt pathway. See
As used herein, “CD28high” refers to a phenotype of high CD28 surface expression in a T cell. Those skilled in the art are familiar with the CD28high phenotype and appropriate ways of identifying CD28high T cells. Unless otherwise indicated, CD28high T cells include T cells that meet any of the following criteria. In some embodiments, a CD28high T cell is a T cell that expresses higher levels of CD28 than a resting CD8+ T cell. A CD28high T cell may also express higher levels of CD28 than an irrelevant non-antigen specific T cell. In some embodiments, CD28high T cells are a population in which the level of surface CD28 which can be measured by FACS is equal to or greater than the level of surface CD28 present on circulating memory T cells which can be measured by FACS. In some embodiments, a CD28high T cell has a level of surface CD28 equal to or greater than the level of surface CD28 present on circulating memory T cells from the same sample or individual. Expression of surface CD28 can be determined by FACS and the mean (e.g., geometric mean) or median level of surface CD28 present on circulating memory T cells can be used for determining whether a given T cell is CD28high. In some embodiments, a CD28high T cell is a T cell that expresses CD28 at a significantly higher level than expression typical of naïve CD8 T cells from the same sample or individual, e.g., higher than 75%, 80%, 85%, 87.5%, 90%, 92.5%, or 95% of the naïve T cells. Naïve CD8 T cells can be identified and characterized by known methods, e.g., flow cytometrically, as CD8+ cells expressing detectable CD28 and minimal or no CD45RO.
As used herein, a “TCR adjunct activating molecule” stimulates classes of signaling molecules which amplify the antigen-specific TCR interaction and are distinct from the TCR co-activating molecules. For example, TCR proximal signaling by phosphorylation of the TCR proximal signaling complex is one route by which TCR adjunct activating molecules can act. The TCR adjunct activating molecule may be, for example, an agonist of the CD2 receptor. See
As used herein, an “activated T cell” is a T cell that has experienced antigen (or a descendant thereof) and is capable of mounting an antigen-specific response to that antigen. Activated T cells are generally positive for at least one of CD28, CD45RO, CD127, and CD197.
Overview.
Immunotherapy for cancer is a promising development, but requires specifically activated T lymphocytes which are compatible with the subject of the therapy. However, the current use of antigen presenting dendritic cells to activate T lymphocytes presents several disadvantageous aspects. Dendritic cells must be obtained from donor sources, limiting throughput. Dendritic cells must be matured for each sequence of T lymphocyte activation, which requires a lead time of about 7 days. Irradiation of dendritic cells is also required, which limits where such processing can be performed.
Replacing the use of autologous antigen presenting dendritic cells with antigen presenting synthetic surfaces for activating T lymphocytes may afford greater reproducibility to stimulate and expand T lymphocytes for a therapeutically relevant population. Antigen presenting synthetic surfaces may be engineered for antigen-specific activation of T lymphocytes, providing more controllable, characterizable, reproducible and/or more rapid development of populations of activated T lymphocytes having desirable phenotypes for treatment of cancer. Antigen-presenting synthetic surfaces can also allow for more control and selectivity over T cell activation, including more precise targeting of desired T cell phenotypes following activation, e.g., enrichment of particular forms of memory T cells. Furthermore, antigen-presenting synthetic surfaces can also exploit economies of scale and/or provide reproducibility to a greater degree than using autologous antigen presenting dendritic cells. As such, this technology can make cellular therapies available to patients in need thereof in greater numbers and/or in less time. Providing T cells useful for cellular therapies more rapidly can be especially important for patients with advanced disease. The structure of such antigen-presenting synthetic surfaces and their methods of preparation and use are described herein. In some embodiments, the antigen-presenting synthetic surfaces comprise primary activating ligands in combination with TCR co-activating molecules and/or adjunct TCR activating molecules, which together serve to activate T cells. Surface density ranges for these components and ratios of one to another that can further improve efficacy are also disclosed herein. In some embodiments, the antigen-presenting synthetic surfaces and their methods of preparation and use provide one or more of the foregoing advantages, or at least provide the public with a useful choice.
Antigen-Presenting Synthetic Surface for T Cell Activation.
An antigen-presenting synthetic surface is provided herein for activating a T lymphocyte (T cell) comprising: a plurality of primary activating molecular ligands, and a plurality of co-activating molecular ligands each comprising a T cell receptor (TCR) co-activating molecule or an adjunct TCR activating molecule, wherein each of the plurality of primary activating molecular ligands and the plurality of co-activating molecular ligands is specifically bound to the antigen presenting synthetic surface. Each primary activating molecular ligand can comprise a major histocompatibility complex (MHC) molecule configured to bind to a T cell receptor of the T cell. In some embodiments, the MHC molecule is an MHC Class 1 molecule. In some other embodiments, the MHC molecule is an MHC Class II molecule. In some embodiments, the primary activating molecular ligand comprises an antigenic peptide (e.g., covalently or non-covalently bound to an MHC molecule). In some embodiments, the plurality of co-activating molecular ligands comprises a plurality of T cell receptor (TCR) co-activating molecules and a plurality of adjunct TCR activating molecules. In some embodiments, the T cell receptor (TCR) co-activating molecules and the adjunct TCR activating molecules are present in a ratio of about 1:100 to about 100:1, e.g., about 20:1 to about 1:20, or about 10:1 to about 1:20. In some embodiments, one or more of the plurality of co-activating molecular ligands is a TCR co-activating molecule which can activate signaling molecules such as transcription factors Nuclear Factor kappa B (NF kB) and Nuclear factor of activated T cells (NFAT). In some embodiments, the TCR co-activating molecule is an agonist of the CD28 receptor, which signals through the phosphoinositide 3 kinase (PI3K)/Akt pathway. In some embodiments, one or more of the plurality of co-activating molecular ligands is a TCR adjunct activating molecule which activates TCR proximal signaling, e.g., by phosphorylation of the TCR proximal signaling complex. The TCR adjunct activating molecule may be, for example, an agonist of the CD2 receptor. Exemplary pathways that can be activated through the CD28 and CD2 receptors (and additional details) are shown in
In various embodiments, the antigen-presenting synthetic surface is configured to activate a T lymphocyte in vitro. The primary activating molecular ligand may comprise a MHC molecule having an amino acid sequence and may be connected covalently to the surface of the antigen-presenting synthetic surface via a C-terminal connection. The MHC molecule may present a N-terminal portion of the MHC molecule oriented away from the surface, thereby facilitating specific binding of the MHC molecule with the TCR of a T lymphocyte disposed upon the surface. The MHC molecule may include a MHC peptide. Clusters of at least four of the MHC molecules may be disposed at locations upon the antigen-presenting synthetic surface such that when the surface is exposed to an aqueous environment, a MHC tetramer may be formed.
In some embodiments, each of the plurality of primary activating molecular ligands may be covalently connected to the antigen presenting synthetic surface via a linker. In some embodiments, an MHC molecule of a primary activating molecular ligand may be connected to the antigen-presenting synthetic surface through a covalent linkage. Covalent linkages can be formed, for example, using Click chemistry and an appropriate Click reagent pair. Likewise, other ligands described herein, such as co-activating molecular ligands (comprising TCR co-activating molecules and/or adjunct TCR activating molecules), growth stimulatory molecular ligands, and additional stimulatory molecular ligands may be covalently connected to the surface of the antigen presenting synthetic surface via a linker, and the linkage can be formed using Click chemistry and an appropriate Click reagent pair.
In other embodiments, the MHC molecule may be connected to the antigen presenting synthetic surface noncovalently through a coupling group (CG), such as a biotin/streptavidin binding pair interaction. In some embodiments, one member of the coupling group is covalently associated with the surface (e.g., streptavidin). Further examples of coupling groups include, but are not limited to biotin/avidin, biotin/NeutrAvidin, and digoxygenin/anti-digoxygenin. Streptavidin, avidin, and NeutrAvidin represent examples of biotin-binding agents. Likewise, other ligands described herein, such as co-activating molecular ligands (comprising TCR co-activating molecules and/or adjunct TCR activating molecules), growth stimulatory molecular ligands, and additional stimulatory molecular ligands may be noncovalently coupled to the antigen presenting synthetic surface, and the coupling group may include biotin or digoxygenin.
In some embodiments, one member of the CG binding pair may itself be covalently bound to the surface, e.g., through one or more linkers. The covalent linkange to the surface can be through a series of about 15, 20, 25, 30, 35, 40, 45, 50, 55, 60, 65, 70, 75, 80, 85, 95, 100, 200 bond lengths, or any number of bond lengths therebetwteen. In some embodiments, the member of the CG binding pair covalently bound to the surface is bound through a Click reagent pair. This may also be true for CG binding pair members involved in associating other ligands described herein (such as co-activating molecular ligands, TCR co-activating molecules, adjunct TCR activating molecules, growth stimulatory molecules, and additional stimulatory molecules) with the surface. Further, since some binding pair members such as streptavidin have multiple binding sites (e.g., four in streptavidin), a primary activating molecular ligand may be coupled to the antigen presenting synthetic surface by a biotin/streptavidin/biotin linkage. Again, this may also be true for CG binding pair members involved in associating other ligands described herein (such as co-activating molecular ligands, TCR co-activating molecules, adjunct TCR activating molecules, growth stimulatory molecules, and additional stimulatory molecules) with the surface.
In some embodiments, a first member of the CG binding pair is covalently associated with the primary activating molecular ligand and a second member of the CG binding pair is non-covalently associated with the surface. For example, the first member of the CG binding pair can be a biotin covalently associated with the primary activating molecular ligand; and the second member of the CG binding pair can be a streptavidin non-covalently associated with the surface (e.g., through an additional biotin, wherein the additional biotin is covalently associated with the surface). In some embodiments, the biotin covalently associated with the surface is linked to the surface through a series of about 15, 20, 25, 30, 35, 40, 45, 50, 55, 60, 65, 70, 75, 80, 85, 95, 100, 200 bond lengths, or any number of bond lengths therebetwteen. For example, the biotin covalently associated with the surface may be linked to the surface through a series of one or more linkers having a total length as described. Again, this may also be true for CG binding pair members involved in associating other ligands described herein (such as co-activating molecular ligands, TCR co-activating molecules, adjunct TCR activating molecules, growth stimulatory molecules, and additional stimulatory molecules) with the surface. Noncovalently associating the second member of the CG binding pair, such as streptavidin, with the surface may facilitate loading ligands such as primary activating molecular ligands, co-activating molecular ligands, TCR co-activating molecules, and adjunct TCR activating molecules at greater densities than if the second member of the CG binding pair is covalently associated with the surface.
The primary activating molecular ligand (e.g., comprising a MHC molecule) may further include an antigenic peptide that comprises a tumor associated antigen. The tumor associated antigen may be noncovalently associated with the primary activating molecular ligand (e.g., MHC molecule). The tumor associated antigen may be presented by the primary activating molecular ligand (e.g., MHC molecule) in an orientation which can initiate activation of a T lymphocyte. The tumor associated antigen may be a peptide. Some non-limiting examples of tumor associated antigens include MART1 (peptide sequence ELAGIGILTV), for melanoma, NYESO1 (peptide sequence SLLMWITQV), involved in melanoma and some carcinomas, SLC45A2, TCL1, and VCX3A, but the disclosure is not so limited. Additional examples of tumor antigens include peptides comprising a segment of amino acid sequence from a protein expressed on the surface of a tumor cell such as CD19, CD20, CLL-1, TRP-2, LAGE-1, HER2, EphA2, FOLR1, MAGE-A1, mesothelin, SOX2, PSM, CA125, T antigen, etc. The peptide can be from an extracellular domain of the tumor associated antigen. An antigen is considered tumor associated if it is expressed at a higher level on a tumor cell than on a healthy cell of the type from which the tumor cell was derived. The T cell which recognizes this tumor associated antigen is an antigen specific T cell. Any tumor associated antigen may be utilized in the antigen presenting surface described herein. In some embodiments, the tumor associated antigen is a neoantigenic peptide, e.g., encoded by a mutant gene in a tumor cell. For detailed discussion of neoantigenic peptides, see, e.g., US 2011/0293637.
The antigen presenting synthetic surface includes a plurality of co-activating molecular ligands each comprising a TCR co-activating molecule or an adjunct TCR activating molecule. In some embodiments, the plurality of co-activating molecular ligands include a plurality of TCR co-activating molecules. In some embodiments, the plurality of co-activating molecular ligands include a plurality of adjunct TCE activating molecules. In other embodiments, the plurality of co-activating molecular ligands may include TCR co-activating molecules and adjunct TCR activating molecules. The TCR co-activating molecules and the adjunct TCR activating molecules can be present in a ratio of one to the other such as 100:1 to 1:100, 10:1 to 1:20, 5:1 to 1:5, 3:1 to 1:3, 2:1 to 1:2, or the like, wherein each of the foregoing values can be modified by “about.” In some embodiments, the plurality of co-activating molecular ligands may include TCR co-activating molecules and adjunct TCR activating molecules in a ratio ranging from about 3:1 to about 1:3.
The TCR co-activating molecule or adjunct TCR activating molecule may include a protein, e.g., an antibody or a fragment thereof. In some embodiments, the TCR co-activating molecule may be a CD28 binding molecule (e.g., including a CD80 molecule) or a fragment thereof which retains binding ability to CD28. In some embodiments, the TCR co-activating molecule may be a CD28 binding molecule (e.g., including a CD80 molecule) or a fragment thereof which specifically binds to CD28. In some embodiments, the TCR co-activating molecule may be a CD28 binding molecule (e.g., including a CD80 molecule) or a CD28-binding fragment thereof. In some embodiments, the TCR co-activating molecule may include an anti-CD28 antibody or a fragment thereof (e.g., a CD28-binding fragment).
In some embodiments, each of the plurality of co-activating molecular ligands may be covalently connected to the antigen-presenting synthetic surface via a linker. In other embodiments, each of the plurality of co-activating molecular ligands may be noncovalently bound to a linker covalently bound to the antigen-presenting synthetic surface. The TCR co-activating molecule or adjunct TCR activating molecule may be connected to the covalently modified surface noncovalently through a CG, such as a biotin/streptavidin binding pair interaction. For example, the TCR co-activating molecule or adjunct TCR activating molecule may further comprise a site-specific C-terminal biotin moiety that interacts with a streptavidin, which may be associated covalently or noncovalently with the surface as described herein. A site-specific C-terminal biotin moiety can be added to a TCR co-activating molecule or adjunct TCR activating molecule using known methods, e.g., using a biotin ligase such as the BirA enzyme. See, e.g., Fairhead et al., Methods Mol Biol 1266:171-184, 2015. Further examples of coupling groups include biotin/avidin, biotin/NeutrAvidin, and digoxygenin/anti-digoxygenin. In some embodiments, one of the CG binding pair may itself be covalently bound to the surface, e.g., through a linker, as described above. See the examples for exemplary TCR co-activating molecules or adjunct TCR activating molecules.
In some other embodiments, the co-activating molecular ligands of the antigen-presenting synthetic surface may include a plurality of adjunct TCR activating molecules, e.g., in addition to or instead of a TCR co-activating molecule as described herein. In some further embodiments, there may be additional co-activating molecular ligands. In some embodiments, the adjunct TCR activating molecules or additional co-activating molecular ligands comprise one or more of a CD2 agonist, a CD27 agonist, or a CD137 agonist. For example, the adjunct TCR activating molecule may be a CD2 binding protein or a fragment thereof, where the fragment retains binding ability with CD2. In some embodiments, the adjunct TCR activating molecule may be CD58 or a fragment thereof which retains binding ability with CD2. The adjunct TCR activating molecule may be a CD2 binding protein (e.g., CD58) or a fragment thereof, where the fragment specifically binds CD2. The adjunct TCR activating molecule may be a CD2 binding protein (e.g., CD58) or a CD2-binding fragment thereof. The adjunct TCR activating molecules or additional co-activating molecular ligands may each be an antibody to CD2, CD27, or CD137, or there may be any combination of such antibodies. The adjunct TCR activating molecules or additional co-activating molecular ligands may alternatively each be a fragment of an antibody to CD2, CD27, or CD137, or any combination thereof. Varlilumab (CDX-1127) is an exemplary anti-CD27 antibody. Utomilumab (PF-05082566) is an exemplary anti-CD137 antibody. CD70 or an extracellular portion thereof may also be used as a CD27 agonist. TNFSF9, also known as CD137L, or an extracellular portion thereof may also be used as a CD137 agonist. In some embodiments, the adjunct TCR activating molecules comprise an agonist of CD2, such as an anti-CD2 antibody. In some embodiments, each of the adjunct TCR activating molecules may be covalently connected to the surface via a linker. In other embodiments, each of the adjunct TCR activating molecules may be noncovalently bound to a linker covalently bound to the surface, e.g., through a CG, such as a biotin/streptavidin binding pair interaction. For example, the adjunct TCR activating molecules may comprise a site-specific C-terminal biotin moiety as discussed above that interacts with a streptavidin, which may be associated covalently or noncovalently with the surface as described herein. Further examples of coupling groups include biotin/avidin, biotin/NeutrAvidin, and digoxygenin/anti-digoxygenin. In some embodiments, one of the CG binding pair may itself be covalently bound to the surface, e.g., through a linker.
The antigen-presenting synthetic surface may further include at least one growth stimulatory molecular ligand. The growth stimulatory molecular ligand may be a protein or peptide. The growth stimulatory protein or peptide may be a cytokine or fragment thereof. The growth stimulatory protein or peptide may be a growth factor receptor ligand. The growth stimulatory molecular ligand may comprise IL-21 or a fragment thereof. In some embodiments, the growth stimulatory molecular ligand may be connected to the antigen-presenting synthetic surface via a covalent linker. In other embodiments, the growth stimulatory molecular ligand may be connected to the antigen-presenting synthetic surface through a CG, such as a biotin/streptavidin binding pair interaction. Further examples of coupling groups include biotin/avidin, biotin/NeutrAvidin, and digoxygenin/anti-digoxygenin. In some embodiments, one of the CG binding pair may itself be covalently bound to the surface, e.g., through a linker. In other embodiments, the growth stimulatory molecular ligand may be attached to a surface either covalently or via a biotin/streptavidin binding interaction, where the surface is not the same surface as the antigen-presenting synthetic surface having MHC molecules connected thereto. For example, the surface to which the growth stimulatory molecular ligand is attached can be a second surface of a microfluidic device also comprising a first, antigen-presenting synthetic surface.
In yet other embodiments, there may be additional growth stimulatory molecular ligands, which may be one or more cytokines, or fragments thereof. In some embodiments, additional stimulatory molecular ligands including, but not limited to IL-2 or IL-7 may be connected to a the antigen-presenting synthetic surface or to another surface that is not the antigen-presenting synthetic surface, as discussed above with respect to growth stimulatory molecular ligands.
In some embodiments, the antigen-presenting synthetic surface comprises an adhesion stimulatory molecular ligand, which is a ligand for a cell adhesion receptor including an ICAM protein sequence.
The additional stimulatory molecular ligands and/or adhesion stimulatory molecular ligands may be covalently connected to a surface or may be noncovalently connected to a surface through a CG, such as a biotin/streptavidin binding pair interaction. Further examples of coupling groups include biotin/avidin, biotin/NeutrAvidin, and digoxygenin/anti-digoxygenin. In some embodiments, one of the CG binding pair may itself be covalently bound to the surface, e.g., through a linker via a biotin/streptavidin binding interaction.
In some embodiments, the antigen-presenting synthetic surface comprises a plurality of surface-blocking molecular ligands, which may include a linker and a terminal surface-blocking group. The linker can include a linear chain of 6 or more atoms (e.g., 7, 8, 9, 10, 11, 12, 13, 14, 15, 20, 25, 30, 35, 40, 45, 50, 75, 100, or more atoms) covalently linked together. Optionally, the linker has a linear structure. The terminal surface-blocking group may be a hydrophilic moiety, an amphiphilic moiety, a zwitterionic moiety, or a negatively charged moiety. In some embodiments, the terminal blocking group comprises a terminal hydroxyl group. In some embodiments, the terminal blocking group comprises a terminal carboxyl group. In some embodiments, the terminal blocking group comprises a terminal zwitterionic group. The plurality of surface-blocking molecular ligands may have all the same terminal surface-blocking group or may have a mixture of terminal surface-blocking groups. Without being bound by theory, the terminal surface-blocking group as well as a hydrophilic linker of the surface-blocking molecular ligand may interact with water molecules in the aqueous media surrounding the antigen-presenting synthetic surface to create a more hydrophilic surface overall. This enhanced hydrophilic nature may render the contact between the antigen-presenting synthetic surface and a cell more compatible and more similar to natural intercellular interactions and/or cell-extracellular fluidic environment in-vivo. The linker can comprise, for example, a polymer. The polymer may include a polymer including alkylene ether moieties. A wide variety of alkylene ether containing polymers may be suitable for use on the surfaces described herein. One class of alkylene ether containing polymers is polyethylene glycol (PEG Mw<100,000 Da), which are known in the art to be biocompatible. In some embodiments, a PEG may have an Mw of about 88 Da, 100 Da, 132 Da, 176 Da, 200 Da, 220 Da, 264 Da, 308 Da, 352 Da, 396 Da, 440 Da, 500 Da, 600 Da, 700 Da, 800 Da, 900 Da, 1000 Da, 1500 Da, 2000 Da, 5000 Da, 10,000 Da or 20,000 Da, or may have a Mw that falls within a range defined by any two of the foregoing values. In some embodiments, the PEG polymer has a polyethylene moiety repeat of about 3, 4, 5, 10, 15, 25 units, or any value therebetween. In some embodiments, the PEG is a carboxyl substituted PEG moiety. In some embodiments, the PEG is a hydroxyl substituted PEG moiety. In some embodiments, each of the plurality of surface-blocking molecular ligands may have a linker having the same length as the linkers of the other ligands of the plurality. In other embodiments, the linkers of the plurality of surface-blocking molecular ligands may have varied lengths. In some embodiments, the surface-blocking group and the length of the linker may be same for each of the plurality of surface-blocking molecular ligands. Alternatively, the surface blocking group and the length of the linker may vary within the plurality of the surface-blocking molecular ligands and may include 2, 3, or 4 different surface-blocking groups and/or 2, 3, 4, or more different lengths, chosen in any combination. In general, the surface-blocking molecular ligands have a length and/or structure that is sufficiently short so as not to sterically hinder the binding and/or function of the primary activating molecular ligands and the co-activating molecular ligands. For example, in some embodiments, the length of the surface-blocking molecular ligands is equal to or less than the length of the other linkers bound to the surface (e.g., linkers that connect coupling groups, primary activating molecular ligands, co-stimulating molecular ligands, or other ligands). In some embodiments, the length of the surface-blocking molecular ligands is about 1 or more angstroms (e.g., about 2, 3, 4, 5, 10, 15, 20, 25, 30, 35, 40, 45, 50, 75, 100, or more angstroms) less than the length of the other linkers bound to the surface (e.g., linkers that connect coupling groups, primary activating molecular ligands, co-stimulating molecular ligands, or other ligands). In some embodiments, the length of the surface-blocking molecular ligands is about 1 to about 100 angstroms (e.g., about 2 to about 75, about 3 to about 50, about 4 to about 40, or about 5 to about 30 angstroms) less than the length of the other linkers bound to the surface. When the surface-blocking molecular ligands have a length that is the same or somewhat less than the length of the other linkers bound to the surface, the resulting surface effectively presents the ligands attached to the other linkers in a manner that is readily available for coupling and/or interacting with cells. With respect to antigen-presenting beads, it has been found that including a surface-blocking molecular ligand such as a hydrophilic polymer, e.g., a PEG or PEO polymer and/or ligands comprising terminal hydroxyl or carboxyl groups, can beneficially reduce aggregation of the beads through hydrophobic interactions. The surface-blocking molecular ligands can be attached to the surface after the primary and other (e.g., coactivating, adjunct, etc.) ligands discussed above or may be introduced before any of the activating or co-activating species are attached to the surface, as set forth in any embodiments disclosed herein.
The antigen-presenting synthetic surface may comprise glass, metal, a polymer, or a metal oxide. In some embodiments, the antigen-presenting synthetic surface is a surface of a wafer having any kind of configuration, a surface of a bead, at least one inner surface of a fluidic circuit containing device (e.g., microfluidic device) configured to contain a plurality of cells, or an inner surface of a tube (e.g., glass or polymer tube). In some embodiments, the wafer having a antigen-presenting synthetic surface configured to activate T lymphocytes may be sized to fit within a well of a standard 48, 96 or 384 wellplate. In various embodiments, beads having a antigen-presenting synthetic surface configured to activate T lymphocytes may be disposed for use within a wellplate or within a fluidic circuit containing device. In some embodiments, the density of the plurality of primary activating molecular ligands on the antigen-presenting synthetic surface (or in each portion or sub-region where it is attached) may be from about 50 to about 500 molecules per square micron; about 4×102 to about 2×103 molecules per square micron; about 1×103 to about 2×104 molecules per square micron; about 5×103 to about 3×104 molecules per square micron; about 4×102 to about 3×104 molecules per square micron; about 4×102 to about 2×103 molecules per square micron; about 2×103 to about 5×103 molecules per square micron; about 5×103 to about 2×104 molecules per square micron; about 1×104 to about 2×104 molecules per square micron; or about 1.25×104 to about 1.75×104 molecules per square micron.
In some embodiments, the density of the plurality of co-activating molecular ligands on the antigen-presenting synthetic surface (or in each portion or sub-region where it is attached) is from about 20 to about 250 molecules per square micron; about 2×102 to about 1×103 molecules per square micron; about 500 to about 5×103 molecules per square micron; about 1×103 to about 1×104 molecules per square micron; about 5×102 to about 2×104 molecules per square micron; about 5×102 to about 1.5×104 molecules per square micron; about 5×103 to about 2×104 molecules per square micron, about 5×103 to about 1.5×104 molecules per square micron, about 1×104 to about 2×104 per square micron, about 1×104 to about 1.5×104 per square micron, about 1.25×104 to about 1.75×104, or about 1.25×104 to about 1.5×104 per square micron.
Without wishing to be bound by any particular theory, certain experiments have indicated that it may be advantageous to provide and use beads for T cell activation that have relatively defined surface-area to volume ratios. Such beads may present the relevant ligands in a more accessible way so that they interact more efficiently with T cells during activation. Such beads may provide a desired degree of T cell activation with fewer ligands needed than beads with higher surface-area to volume ratios and/or may provide a higher degree of T cell activation or more T cells with desired features (e.g., antigen specificity and/or marker phenotypes described herein) than beads with higher surface-area to volume ratios. An ideally spherical solid has the lowest possible surface-area to volume ratio. Accordingly, in some embodiments, the bead surface-area is within 10% of the surface-area of a sphere of an equal size (volume or diameter), and is referred to herein as “substantially spherical.” For example, for a bead with a 2.8 μm diameter (1.4 μm radius), the corresponding ideal sphere would have a surface area of 4πr2=24.63 μm2. A substantially spherical 2.8 μm diameter bead with a surface-area within 10% of the surface-area of an ideal sphere of an equal volume or diameter would therefore have a surface-area less than or equal to 27.093 μm2. It is noted that certain commercially available beads are reported as having higher surface areas; for example, Dynabeads M-270 Epoxy are described in their product literature as having a specific surface area of 2-5 m2/g and a 2.8 μm diameter, and the literature also indicates that 1 mg of beads is 6-7×107 beads. Multiplying the specific surface area by 1 mg/6-7×107 beads gives a surface area per bead of 28 to 83 μm2 per bead, which is more than 10% greater than the surface-area of an ideal sphere with a 2.8 μm diameter. Polymer beads having a surface area more than 10% greater than the surface-area of an ideal sphere are referred to herein as a “convoluted bead.” In some embodiments, a polymer bead may be either substantially spherical or convoluted. In some embodiments, the polymer bead is not convoluted, but is substantially spherical.
Unpatterned Surface.
In various embodiments, the antigen-presenting synthetic surface may be a unpatterned surface having a plurality of primary activating molecular ligands distributed evenly thereon. The primary activating molecular ligands can comprise MHC molecules, each of which may include a tumor associated antigen. The unpatterned surface may further include a plurality of co-activating molecular ligands (e.g., TCR co-activating molecules and/or adjunct TCR activating molecules) distributed evenly thereon. The co-activating molecular ligands may be as described above for antigen-presenting surfaces, in any combination. The density of the primary activating molecular ligands and the co-activating molecular ligands may the same ranges as described above for antigen-presenting surfaces. The unpatterned antigen-presenting synthetic surface may further include additional growth stimulatory, adhesive, and/or surface-blocking molecular ligands, as described above for antigen-presenting surfaces, each of which (if present) can be evenly distributed on the upatterned surface. For example, the unpatterned surface can include an adjunct stimulatory molecule such as IL-21 connected to the surface. The primary activating molecular ligands, co-activating molecular ligands, and/or additional ligands may be linked to the surface as described above for the antigen-presenting surfaces. As used herein, a surface having a ligand “distributed evenly” thereon is characterized in that no portion of the surface having a size of 10% the total surface area, or greater, has a statistically significant higher concentration of ligand as compared to the average ligand concentration of the total surface area of the surface.
Patterned Surface.
In various embodiments, the antigen-presenting synthetic surface may be patterned and may have a plurality of regions, each region including a plurality of the primary activating molecular ligands comprising MHC molecules, where the plurality of regions is separated by a region configured to substantially exclude the primary activating molecular ligands. The antigen-presenting synthetic surface may be a planar surface. In some embodiments, each of the plurality of regions including the at least a plurality of the primary activating molecular ligands may further include a plurality of the co-activating molecular ligands, e.g., a TCR co-activating molecule and/or an adjunct TCR activating molecule. The co-activating molecular ligands may be any of the co-activating molecular ligands as described above and in any combination. The primary activating molecular ligands and/or co-activating molecular ligands may be linked to the surface as described above for the antigen-presenting surfaces. The density of the primary activating molecular ligands and/or the co-activating molecular ligands in each of the regions containing the primary activating molecular ligands and/or the co-activating molecular ligands may be in the same range as the densities described above for antigen-presenting surfaces. In some embodiments, each of the plurality of regions comprising at least the plurality of the primary activating molecular ligands has an area of about 0.10 square microns to about 4.0 square microns. In other embodiments, the area of each of the plurality of regions may be about 0.20 square microns to about 0.8 square microns. The plurality of regions may be separated from each other by about 2 microns, about 3 microns, about 4 microns, or about 5 microns. The pitch between each region of the plurality and its neighbor may be about 2 microns, about 3 microns, about 4 microns, about 5 microns, or about 6 microns. See
In various embodiments, the region configured to substantially exclude the primary activating molecular ligands comprising MHC molecules may also be configured to substantially exclude TCR co-activating molecules and/or adjunct TCR activating molecules.
In some embodiments, the region configured to substantially exclude the primary activating molecular ligands and optionally the TCR co-activating molecules and/or adjunct TCR activating molecules may also be configured to include one or more of surface-blocking molecular ligands, growth stimulatory molecules, additional stimulatory molecules, and adhesion stimulatory molecular ligands. In some embodiments, the growth stimulatory molecules and/or additional stimulatory molecules include a cytokine or fragment thereof, and may further include IL-21 or fragment thereof. In some embodiments, the region configured to substantially exclude the primary activating molecular ligands and optionally the TCR co-activating molecules and/or adjunct TCR activating molecules may further be configured to include one or more supportive moieties. The supportive moieties may provide adhesive motifs to support T lymphocyte growth or may provide hydrophilic moieties providing a generally supportive environment for cell growth. The moiety providing adhesive support may include a peptide sequence including a RGD motif. In other embodiments, the moiety providing adhesive support may be an ICAM sequence. A moiety providing hydrophilicity may be a moiety such as a PEG moiety or carboxylic acid substituted PEG moiety.
Microfluidic Device.
In some embodiments, a microfluidic device comprises a patterned antigen-presenting synthetic surface having a plurality of regions according to any of the foregoing embodiments. While the antigen-presenting surface of microfluidic device may be any microfluidic (or nanofluidic) device as described herein, the disclosure is not so limited. Other classes of microfluidic devices, including but not limited to microfluidic devices including microwells or microchambers such as described in WO2014/153651, WO2016/115337, or WO2017/124101, may be modified to either incorporate an antigen presenting surface as described in this section, or may be used in combination with the antigen-presenting beads or antigen-presenting wafers as described herein in the methods described in this disclosure.
In some embodiments, the antigen-presenting synthetic surface is an inner surface of a microfluidic device comprising one or more sequestration pens and a channel. At least part of a surface within one or more such sequestration pens may comprise a plurality of primary activating molecular ligands and a plurality of co-activating molecular ligands, e.g., comprising TCR co-activating molecules and/or adjunct TCR activating molecules. The primary activating molecular ligands and the co-activating molecular ligands may be any described above for antigen-presenting surfaces, and may be present in any concentration or combination as described above. The nature of the ligands attachment to the surface of the microfluidic device may be any described above as for antigen-presenting surfaces. In some embodiments, this surface within the one or more such sequestration pens can further comprise one or more of surface-blocking molecular ligands, growth stimulatory molecular ligands, additional stimulatory molecular ligands, and adhesion stimulatory molecular ligands. At least part of a surface of the channel may comprise surface-blocking molecular ligands, e.g., any of the regions configured to substantially exclude the primary activating molecular ligands described herein. In some embodiments, the surface of the channel comprises surface-blocking molecular ligands and optionally other non-stimulatory ligands, but is substantially free of other ligands present on the surface of the sequestration pen, e.g., primary activating molecular ligands and co-activating molecular ligands.
Modulation of Cell-to-Surface Adhesion.
In some embodiments, it can be useful to modulate the capacity for cells to adhere to surfaces within the microfluidic device. A surface that has substantially hydrophilic character may not provide anchoring points for cells requiring mechanical stress of adherence to grow and expand appropriately. A surface that presents an excess of such anchoring moieties may prevent successfully growing adherent cells from being exported from within a sequestration pen and out of the microfluidic device. In some embodiments, a covalently bound surface modification comprises surface contact moieties to help anchor adherent cells. The structures of the surfaces described herein and the methods of preparing them provide the ability to select the amount of anchoring moieties that may be desirable for a particular use. A very small percentage of adherent type motifs may be needed to provide a sufficiently adhesion enhancing environment. In some embodiments, the adhesion enhancing moieties are prepared before cells are introduced to the microfluidic device. Alternatively, an adhesion enhancing modified surface may be provided before introducing cells, and a further addition of another adhesion enhancing moiety may be made, which is designed to attach to the first modified surface either covalently or non-covalently (e.g., as in the base of biotin/streptavidin binding).
In some embodiments, adhesion enhancing surface modifications may modify the surface in a random pattern of individual molecules of a surface modifying ligand. In some other embodiments, a more concentrated pattern of adhesion enhancing surface modifications may be introduced by using polymers containing multiple adhesion enhancing motifs such as positively charged lysine side chains, which can create small regions of surface modification surrounded by the remainder of the surface, which may have hydrophilic surface modifications to modulate the adhesion enhancement. This may be further elaborated by use of dendritic polymers, having multiple adhesion enhancing ligands. A dendritic polymer type surface modifying compound or reagent may be present in a very small proportion relative to a second surface modification having only hydrophilic surface contact moieties, while still providing adhesion enhancement. Further a dendritic polymer type surface modifying compound or reagent may itself have a mixed set of end functionalities which can additionally modulate the behavior of the overall surface.
In some embodiments, it may be desirable to provide regioselective introduction of surfaces. For example, in the context of a microfluidic device comprising a microfluidic channel and sequestration pens, it may be desirable to provide a first type of surface within the microfluidic channel while providing a surface within the sequestration pens opening off of the channel that provides the ability to both culture adherent-type cells successfully as well as easily export them (e.g., using dielectrophoretic or other forces) when desired. In some embodiments, the adhesion enhancing modifications may include cleavable moieties. The cleavable moieties may be cleavable under conditions compatible with the cells being cultured within, such that at any desired timepoint, the cleavable moiety may be cleaved and the nature of the surface may alter to be less enhancing for adhesion. The underlying cleaved surface may be usefully non-fouling such that export is enhanced at that time. While the examples discussed herein focus on modulating adhesion and motility, the use of these regioselectively modified surfaces are not so limited. Different surface modifications for any kind of benefit for cells being cultured therein may be incorporated into the surface having a first and a second surface modification according to the disclosure.
Exemplary adherent motifs that may be used include poly-L-lysine, amine and the like, and the tripeptide sequence RGD, which is available as a biotinylated reagent and is easily adaptable to the methods described herein. Other larger biomolecules that may be used include fibronectin, laminin or collagen, amongst others. A surface modification having a structure of Formula XXVI as defined in WO2017/205830, including a polyglutamic acid surface contact moiety, can induce adherent cells to attach and grow viably. Another motif that may assist in providing an adherent site is an Elastin Like Peptide (ELP), which includes a repeat sequence of VPGXG, where X is a variable amino acid which can modulate the effects of the motif.
In some embodiments, in the context of a microfluidic device comprising a microfluidic channel and sequestration pens, a surface of the flow region (e.g., microfluidic channel) may be modified with a first covalently bound surface modification and a surface of the at least one sequestration pen may be modified with a second covalently bound surface modification, wherein the first and the second covalently bound surface modification have different surface contact moieties, different reactive moieties, or a combination thereof. The first and the second covalently bound surface modifications may be selected from any of Formula XXX, Formula V, Formula VII, Formula XXXI, Formula VIII, and/or Formula IX, all of which are as defined in WO2017/205830. When the first and the second covalently bound surface modifications both include functionalized surface of Formula XXX, Formula V, or Formula VII as defined in WO2017/205830, then orthogonal reaction chemistries are selected for the choice of the first reactive moiety and the second reactive moiety. In various embodiments, all the surfaces of the flow region may be modified with the first covalent surface modification and all the surfaces of the at least one sequestration pen may be modified with the second covalent modification.
Methods of Preparing an Antigen-Presenting Synthetic Surface; Covalently Functionalized Surface
Turning to
The intermediate reactive surface is then treated with functionalizing reagents including binding moieties BM, where the functionalizing reagents react with the reactive moieties RM to introduce binding moiety BM ligands. The binding moieties so introduced may be any binding moiety BM described herein. The binding moiety BM may be streptaviding or biotin. In some embodiments, the binding moiety BM is streptavidin which is covalently attached via a linker to the covalently functionalized surface, through a reaction with a reactive moiety RM. In some other embodiments, the covalently functionalized surface may introduce a streptavidin binding moiety non-covalently, in a two part structure. This two part structure is introduced by contacting the intermediate reactive surface with a first functionalizing reagent to introduce a biotin moiety covalently attached via a linker through reaction with the reactive moieties RM. Subsequent introduction of streptavidin, as a second functionalizing reagent, provides the covalently functionalized surface wherein the binding moiety BM, streptavidin, is non-covalently attached to a biotin moiety which itself is covalently attached to the surface. Surface-blocking molecular ligands SB′ may be introduced at the same time as the introduction of the binding moieties or may be introduced to the covalently functionalized surface subsequent to the introduction of the binding moieties. The surface-blocking molecular ligands SB′ may be any surface-blocking molecular ligand as described herein and may be the same as or different from surface-blocking molecular ligands SB, if surface-blocking molecular ligands SB are present. In some embodiments, surface-blocking molecular ligands SB may be present and there may be no surface-blocking molecular ligands SB′. Alternatively, there may be surface-blocking molecular ligands SB′ but no surface-blocking molecular ligands SB. In some embodiments, both surface-blocking molecular ligands SB and SB′ are present. Without being bound by theory, there may be some reactive moieties RM left unreacted upon the covalently functionalized surface but there are insufficient numbers of reactive moieties RM present to prevent the product antigen presenting synthetic surface from functioning. Primary activating ligands MHC and Co-Activating Ligands Co-A1 and Co-A2 are introduced by reacting the binding moieties BM, of the covalently functionalized surface, with appropriate activating ligand reagents, providing the antigen-presenting synthetic surface. Co-A1 and Co-A2 may be the same or different co-activating ligands. For example, Co-A1 and Co-A2 can comprise one, the other, or collectively both of a TCR co-activating molecule and a TCR adjunct activating molecule. Co-A1 and/or Co-A2, may be any combination of TCR co-activating molecule and a TCR adjunct activating molecule as described herein. In some embodiments, the primary activating ligand MHC may be introduced to the covalently functionalized surface, before the covalently functionalized surface is contacted with the co-activating ligands Co-A1 and/or Co-A2. In other embodiments, the primary activating ligand MHC may be introduced to the covalently functionalized surface concurrently with or subsequently to the introduction of the Co-Activating ligands Co-A1 and Co-A2. In some embodiments, not shown in
Methods of Preparing an Antigen-Presenting Synthetic Surface
A method of preparing an antigen-presenting synthetic surface for activating a T lymphocyte (T cell), is provided, comprising: reacting a plurality of primary activating molecules, with a first plurality of binding moieties of a covalently functionalized synthetic surface comprising binding moieties (e.g., a biotin-binding agent such as streptavidin, or biotin moieties that are noncovalently associated with a biotin-binding agent such as streptavidin), wherein each of the first plurality of binding moieties is configured for binding the primary activating molecule; and reacting a plurality of co-activating molecules, each comprising: a T cell receptor (TCR) co-activating molecule; or an adjunct TCR activating molecule, with a second plurality of binding moieties of the covalently functionalized synthetic surface, wherein each of the second plurality of binding moieties is configured for binding the co-activating molecule, thereby providing a plurality of specifically bound primary activating molecular ligands and a plurality of specifically bound co-activating molecular ligands on the antigen-presenting synthetic surface.
Also provided is a covalently functionalized synthetic surface comprising binding moieties (e.g., a biotin-binding agent such as streptavidin, or biotin moieties that are noncovalently associated with a biotin-binding agent such as streptavidin) and at least a first plurality of surface-blocking molecular ligands. To the extent that the following discussion describes features of a covalently functionalized synthetic surface, it applies both to embodiments of the covalently functionalized synthetic surface and to embodiments of methods of preparing an antigen-presenting surface in which a covalently functionalized synthetic surface is used.
The covalently functionalized synthetic surface may be any of the surface types described herein, e.g., a bead, wafer, inner surface of a microfluidic device, or tube (e.g., glass or polymer tube). The surface material may comprise, e.g., metal, glass, ceramic, polymer, or a metal oxide. The microfluidic device may be any microfluidic device as described herein, and may have any combination of features. The bead can be a bead with a surface-area that is within 10% of the surface-area of a sphere of an equal volume or diameter, as discussed herein in the section regarding antigen-presenting synthetic surfaces. In some embodiments, the bead may be a bead having a surface area that exceeds 10% of the surface area of a sphere of an equal volume or diameter, as discussed herein for antigen presenting surfaces. In some embodiments, the bead is not a bead that has a surface area that exceeds 10% of the surface area of a sphere of an equal volume or diameter, as discussed herein for antigen presenting surfaces.
The primary activating molecules and co-activating molecules may each be any such molecule described herein, and any combination thereof may be used. Thus, a primary activating molecule can comprise an MHC molecule and, optionally, an antigenic peptide; and a co-activating molecule can comprise any of the TCR co-activating molecules described herein or any of the adjunt TCR activating molecules described herein.
In some embodiments, reacting a plurality of primary activating molecules with a first plurality of binding moieties of a covalently functionalized synthetic surface comprising binding moieties comprises forming a noncovalent association between the primary activating molecules and the binding moieties. For example, the primary activating molecules can comprise biotin and the binding moieties can comprise a biotin-binding agent such as streptavidin (e.g., which may be covalently bound to the surface or which may be non-covalently bound to a second biotin which itself is covalently bound to the surface). In some embodiments, the biotin-binding agent such as streptavidin is linked to the surface through a series of about 15, 20, 25, 30, 35, 40, 45, 50, 55, 60, 65, 70, 75, 80, 85, 95, 100, 200 bond lengths, or any number of bond lengths therebetwteen. For example, the biotin-binding agent may be linked to the surface through a series of one or more linkers having a selected length as described. In another example, both the binding moieties and the primary activating molecules can comprise biotin and a free, multivalent biotin-binding agent, such as streptavidin, can be used as a noncovalent linking agent. Any other suitable noncovalent binding pair, such as those described elsewhere herein, can also be used.
Alternatively, reacting a plurality of primary activating molecules with a first plurality of binding moieties of a covalently functionalized synthetic surface comprising binding moieties can comprise forming a covalent bond. For example, an azide-alkyne reaction (such as any of those described elsewhere herein) can be used to form the covalent bond, where the primary activating molecules and the binding moieties comprise, respectively, an azide and an alkyne, or an alkyne and an azide. Other reaction pairs may be used, as is known in the art, including but not limited to maleimide and sulfides. More generally, exemplary functionalities useful for forming covalent bonds include azide, carboxylic acid and active esters thereof, succiniimide ester, maleimide, keto, sulfonyl halides, sulfonic acid, dibenzocyclooctyne, alkene, alkyne, and the like. Skilled artisans are familiar with appropriate combinations and reaction conditions for forming covalent bonds using such moieties.
Where the covalently functionalized synthetic surface comprises a covalently associated biotin, the surface can further comprise noncovalently associated biotin-binding agent (e.g., streptavidin), such that the surface can be reacted with primary activating molecules and co-activating molecules that comprise biotin moieties. In some embodiments, the method of preparing an antigen-presenting synthetic surface comprises reacting a covalently functionalized synthetic surface comprising a covalently associated biotin with a biotin-binding agent (e.g., streptavidin), and then with primary activating molecules and co-activating molecules comprising biotin moieties. In some embodiments, the biotin of the covalently functionalized surface is linked to the surface through a series of about 15, 20, 25, 30, 35, 40, 45, 50, 55, 60, 65, 70, 75, 80, 85, 95, 100, 200 bond lengths, or any number of bond lengths therebetween.
In some embodiments, the reaction provides any of the densities described herein of primary activating molecular ligands on the surface, such as about 4×102 to about 3×104, 4×102 to about 2×103, about 5×103 to about 3×104, about 5×103 to about 2×104, or about 1×104 to about 2×104 molecules per square micron.
In some embodiments, reacting a plurality of co-activating molecules, each comprising: a T cell receptor (TCR) co-activating molecule; or an adjunct TCR activating molecule, with a second plurality of binding moieties of the covalently functionalized synthetic surface comprises forming a noncovalent association between the co-activating molecules and the binding moieties. Any of the embodiments described above or set forth in any embodiments disclosed herein with respect to primary activating molecules involving noncovalent binding pairs such as biotin and a biotin-binding agent such as streptavidin may be used.
Alternatively, reacting a plurality of co-activating molecules with a second plurality of binding moieties of the covalently functionalized synthetic surface can comprise forming a covalent bond. For example, an azide-alkyne reaction (such as any of those described elsewhere herein) can be used to form the covalent bond, where the primary activating molecules and the binding moieties comprise, respectively, an azide and an alkyne, or an alkyne and an azide.
In some embodiments, the reaction provides any of the densities described herein of co-activating molecular ligands on the surface, such as from about 4×102 to about 3×104, 4×102 to about 2×103, about 5×103 to about 3×104, about 5×103 to about 2×104, or about 1×104 to about 2×104 molecules per square micron.
In some embodiments, the reaction provides TCR co-activating molecules and adjunct TCR activating molecules on the surface in any of the ratios described herein, such as 100:1 to 1:100, 10:1 to 1:20, 5:1 to 1:5, or 3:1 to 1:3, wherein each of the foregoing values can be modified by “about.”
In some embodiments, the reactions described above or set forth in any embodiments disclosed herein provide primary activating molecular ligands and co-activating molecular ligands on the surface in any of the ratios described herein, such as about 1:1 to about 2:1; about 1:1; or about 3:1 to about 1:3.
In some embodiments, a method of preparing an antigen-presenting surface further comprises reacting a plurality of surface-blocking molecules with a third plurality of binding moieties of the covalently functionalized surface, wherein each of the binding moieties of the third plurality is configured for binding the surface-blocking molecule. Any surface-blocking molecule described elsewhere herein may be used. Any of the reaction approaches described herein for forming noncovalent associations or a covalent bond may be used.
In some embodiments, a method of preparing an antigen-presenting surface further comprises reacting a plurality of adhesion stimulatory molecular ligands, wherein each adhesion stimulatory molecular ligand includes a ligand for a cell adhesion receptor including an ICAM protein sequence, with a fourth plurality of binding moieties of the covalently functionalized bead, wherein each of the binding moieties of the fourth plurality is configured for binding with the cell adhesion receptor ligand molecule. Any of the reaction approaches described herein for forming noncovalent associations or a covalent bond may be used.
In some embodiments, a method of preparing an antigen-presenting surface further comprises producing the intermediate reactive surface. This can include, e.g., reacting at least a first portion of surface-exposed moieties disposed at a surface of a synthetic reactive surface with a plurality of intermediate preparation molecules including reactive moieties, thereby producing the intermediate reactive surface. Methods of preparing a covalently functionalized surface, which can be used as the intermediate reactive surface, are described in detail elsewhere herein. Producing the intermediate reactive surface can comprise any of the features described herein with respect to methods of preparing a covalently functionalized surface.
In some embodiments, the methods further comprise modulating the capacity for cells to adhere to surfaces within the microfluidic device, e.g., by providing anchoring points for cells requiring mechanical stress of adherence to grow and expand appropriately. This can be accomplished by introducing a covalently bound surface modification comprising surface contact moieties to help anchor adherent cells. Any of the surface contact moieties described elsewhere herein can be used.
The covalently functionalized synthetic surface can comprise moieties suitable for use in any of the reactions described herein.
Methods of Preparing a Covalently Functionalized Surface
Also provided is a method of preparing a covalently functionalized surface including a plurality of streptavidin or biotin functionalities and at least a first plurality of surface-blocking molecular ligands, wherein the method includes: reacting at least a first subset of reactive moieties of an intermediate reactive synthetic surface with a plurality of linking reagents, each linking reagent including streptavidin or biotin; and reacting at least a second subset of reactive moieties of the intermediate reactive synthetic surface with a plurality of surface-blocking molecules, thereby providing the covalently functionalized synthetic surface including at the least one plurality of streptavidin or biotin functionalities and at the least first plurality of surface-blocking molecular ligands. Generally only one or the other of a linking reagent including streptavidin or a linking reagent including biotin is used. The intermediate reactive synthetic surface may be any of the surface types described herein, e.g., a bead, wafer, inner surface of a microfluidic device, or tube (e.g., glass or polymer tube). The surface material may comprise, e.g., metal, glass, ceramic, polymer, or a metal oxide. The antigen-presenting microfluidic device may be any microfluidic device as described herein, and may have any combination of features. The bead can be a bead with a surface-area is within 10% of the surface-area of a sphere of an equal volume or diameter, as discussed herein in the section regarding antigen-presenting synthetic surfaces.
In embodiments in which the linking reagents include biotin, the method can further comprise noncovalently associating streptavidin with the biotin. In such embodiments, with reference to
In some embodiments, the reactive moieties of an intermediate reactive synthetic surface are linked to the surface through a series of 5, 10, 11, 12, 13, 14, 15, 16, 17, 18, 19, 20, or, in some embodiments, greater numbers of bonds. For example, the reactive moieties can be linked through a series of 15 bonds, e.g., using (11-(X)undecyl)trimethoxy silane, where X is the reactive moiety (e.g., X can be azido). With respect to linking reagents including biotin, biotin can then be covalently associated using a linking reagent such as one having the general structure DBCO-PEG4-biotin (commercially available from BroadPharm). In some embodiments, the biotin is linked to the surface through a series of about 15, 20, 25, 30, 35, 40, 45, 50, 55, 60, 65, 70, 75, 80, 85, 95, 100, 200 bond lengths, or any number of bond lengths therebetwteen. With respect to linking reagents including streptavidin, streptavidin can then be covalently associated using a linking reagent such as one having the general structure DBCO-PEG13-succinimide, followed by reaction of streptavidin with the succinimide. In some embodiments, the streptavidin is linked to the surface through a series of about 15, 20, 25, 30, 35, 40, 45, 50, 55, 60, 65, 70, 75, 80, 85, 95, 100, 200 bond lengths, or any number of bond lengths therebetwteen. The number of bonds through which a moiety is linked to a surface can be varied, e.g., by using reagents similar to those mentioned above but with alkylene and/or PEG chains of different lengths.
In some embodiments, the reactive moieties of at least first region of the intermediate reactive synthetic surface include azide moieties. In some embodiments, covalent bonds are formed through an azide-alkyne reaction, such as any azide-alkyne reaction described elsewhere herein.
In some embodiments, the covalently functionalized synthetic surface includes a second region wherein the plurality of streptavidin functionalities is excluded. In some embodiments, the at least first plurality of surface-blocking molecular ligands are disposed in the second region of the covalently functionalized synthetic surface.
In some embodiments, a method further includes reacting a second plurality of surface-blocking molecules with a second subset of reactive moieties in the at least first region of the intermediate reactive synthetic surface.
In some embodiments, the reacting of the plurality of streptavidin functionalities and the reacting of the at least first plurality of surface-blocking molecules is performed at a plurality of sub-regions of the at least first region of the covalently prepared synthetic surface including reactive moieties.
In some embodiments, the second portion of the reactive synthetic surface includes surface exposed moieties configured to substantially not react with the pluralities of the primary activating and co-activating molecules.
In some embodiments, a method further includes preparing the intermediate reactive synthetic surface, including: reacting at least a first surface preparing reagent including azide reactive moieties with surface-exposed moieties disposed at at least a first region of a reactive synthetic surface.
In some embodiments, the surface-exposed moieties are nucleophilic moieties. In some embodiments, the nucleophilic moiety of the surface is a hydroxide, amino or thiol. In some other embodiments, the nucleophilic moiety of the surface may be a hydroxide.
In some embodiments, the surface-exposed moieties are displaceable moieties.
In some embodiments, where two modifying reagents are used, the reaction of the first modifying reagent and the reaction of the second modifying reagent with the surface may occur at random locations upon the surface. In other embodiments, the reaction of the first modifying reagent may occurs within a first region of the surface and reaction of the second modifying reagent may occur within a second region of the surface abutting the first region. For example, the surfaces within the channel of a microfluidic device may be selectively modified with a first surface modification and the surfaces within the sequestration pen, which abut the surfaces within the channel, may be selectively modified with a second, different surface modification.
In yet other embodiments, the reaction of the first modifying reagent may occurs within a plurality of first regions separated from each other on the at least one surface, and the reaction of the second modifying reaction may occur at a second region surrounding the plurality of first regions separated from each other.
In various embodiments, modification of one or more surfaces of a microfluidic device to introduce a combination of a first surface modification and a second surface modification may be performed after the microfluidic device has been assembled. For one nonlimiting example, the first and second surface modification may be introduced by chemical vapor deposition after assembly of the microfluidic device. In another nonlimiting example, a functionalized surface having a first surface modification having a first reactive moiety and a second surface modification having a second, orthogonal reactive moiety may be introduced. Differential conversion to two different surface modifying ligands having two different surface contact moieties can follow.
In some embodiments, at least one of the combination of first and second surface modification may be performed before assembly of the microfluidic device. In some embodiments, modifying the at least one surface may be performed after assembly of the microfluidic device.
In some embodiments, a covalently functionalized surface is prepared comprising a binding agent. In some embodiments, the distribution of the plurality of binding agent (e.g., plurality of multivalent binding agent, such as a tetravalent binding agent, e.g., streptavidin functionalities, which may be covalently associated or noncovalently associated with a covalently bound biotin) on the covalently functionalized synthetic surface is from about 6×102 to about 5×103 molecules per square micron, in each region where it is attached. In some embodiments, the distribution of the plurality of binding agent (e.g., plurality of multivalent binding agent, such as a trivalent binding agent) is about about 1.5×103 to about 1×104, about 1.5×103 to about 7.5×103, or about 3×103 to about 7.5×103 molecules per square micron, in each region where it is attached. In some embodiments, the distribution of the plurality of binding agent (e.g., plurality of multivalent binding agent, such as a divalent binding agent) is about 2.5×103 to about 1.5×104, about 2.5×103 to about 1×104, or about 5×103 to about 1×104 molecules per square micron, in each region where it is attached. In some embodiments, the distribution of the plurality of binding agent (e.g., plurality of monovalent binding agent) is about 5×103 to about 3×104, about 5×103 to about 2×104, or about 1×104 to about 2×104 molecules per square micron, in each region where it is attached.
In some embodiments, a covalently functionalized surface is prepared comprising a binding agent, in which the distribution of the plurality of binding agent (e.g., streptavidin functionalities, which may be covalently associated or noncovalently associated with a covalently bound biotin) on the covalently functionalized synthetic surface is from about 1×104 to about 1×106 molecules per square micron, in each region where it is attached.
In some embodiments, a combined method comprising preparing a covalently functionalized surface and then preparing an antigen-presenting synthetic surface is provided. As such, any suitable combination of steps for preparing the covalently functionalized surface and steps for preparing the antigen-presenting synthetic surface may be used.
Additional Aspects of Surface Preparation and Covalently Functionalized Surfaces.
Any method of preparing a surface described herein, including methods of preparing an antigen-presenting synthetic surface and methods of preparing a covalently functionalized surface, may further comprise one or more of the following aspects. A covalently functionalized surface may further comprise one or more of the following aspects applicable to such surfaces, such as reactive groups.
Azide-Alkyne Reactions.
In some embodiments, covalent bonds are formed by reacting an alkyne, such as an acyclic alkyne, with an azide. For example, a “Click” cyclization reaction may be performed, which is catalyzed by a copper (I) salt. When a copper (I) salt is used to catalyze the reaction, the reaction mixture may optionally include other reagents which can enhance the rate or extent of reaction. When an alkyne, e.g., of a surface modifying reagent or a functionalized surface is a cyclooctyne, the “Click” cyclization reaction with an azide of the corresponding functionalized surface or the surface modifying reagent may be copper-free. A “Click” cyclization reaction can thereby be used to couple a surface modifying ligand to a functionalized surface to form a covalently modified surface.
Copper Catalysts.
Any suitable copper (I) catalyst may be used. In some embodiments, copper (I) iodide, copper (I) chloride, copper (I) bromide or another copper (I) salt. In other embodiments, a copper (II) salt may be used in combination with a reducing agent such as ascorbate to generate a copper (I) species in situ. Copper sulfate or copper acetate are non-limiting examples of a suitable copper (II) salt. In other embodiments, a reducing agent such as ascorbate may be present in combination with a copper (I) salt to ensure sufficient copper (I) species during the course of the reaction. Copper metal may be used to provide Cu(I) species in a redox reaction also producing Cu(II) species. Coordination complexes of copper such as [CuBr(PPh3)3], silicotungstate complexes of copper, [Cu(CH3CN)4]PF6, or (Eto)3P CuI may be used. In yet other embodiments, silica supported copper catalyst, copper nanoclusters or copper/cuprous oxide nanoparticles may be employed as the catalyst.
Other Reaction Enhancers.
As described above, reducing agents such as sodium ascorbate may be used to permit copper (I) species to be maintained throughout the reaction, even if oxygen is not rigorously excluded from the reaction. Other auxiliary ligands may be included in the reaction mixture, to stabilize the copper (I) species. Triazolyl containing ligands can be used, including but not limited to tris(benzyl-1H-1,2,3-triazol-4-yl) methylamine (TBTA) or 3 [tris(3-hydroxypropyltriazolylmethyl)amine (THPTA). Another class of auxiliary ligand that can be used to facilitate reaction is a sulfonated bathophenanthroline, which is water soluble, as well, and can be used when oxygen can be excluded. Other chemical couplings as are known in the art may be used to couple a surface modifying reagent to a functionalized surface.
Cleaning the Surface.
The surface to be modified may be cleaned before modification to ensure that the nucleophilic moieties on the surface are freely available for reaction, e.g., not covered by oils or adhesives. Cleaning may be accomplished by any suitable method including treatment with solvents including alcohols or acetone, sonication, steam cleaning and the like. Alternatively, or in addition, such pre-cleaning can include cleaning (e.g., of the cover, the microfluidic circuit material, and/or the substrate in the context of components of a microfluidic device) in an oxygen plasma cleaner, which can remove various impurities, while at the same time introducing an oxidized surface (e.g. oxides at the surface, which may be covalently modified as described herein). Alternatively, liquid-phase treatments, such as a mixture of hydrochloric acid and hydrogen peroxide or a mixture of sulfuric acid and hydrogen peroxide (e.g., piranha solution, which may have a ratio of sulfuric acid to hydrogen peroxide from about 3:1 to about 7:1) may be used in place of an oxygen plasma cleaner. This can advantageously provide more sites for modification on the surface, thereby providing a more closely packed modified surface layer.
Components of Microfluidic Devices.
A surface of a material that may be used as a component of a microfluidic device may be modified before assembly thereof. Alternatively, a partially or completely constructed microfluidic device may be modified such that all surfaces that will contact biomaterials including biomolecules and/or micro-objects (which may include biological micro-objects) are modified at the same time. In some embodiments, the entire interior of a device and/or apparatus may be modified, even if there are differing materials at different surfaces within the device and/or apparatus. This discussion also applies to the methods of preparing an antigen-presenting synthetic surface described herein.
When an interior surface of a microfluidic device reacted with a surface modifying reagent, the reaction may be performed by flowing a solution of the surface modifying reagent into and through the microfluidic device.
Surface Modifying Reagent Solutions and Reaction Conditions.
In various embodiments, the surface modifying reagent may be used in a liquid phase surface modification reaction, e.g., wherein the surface modifying reagent is provided in solution, such as an aqueous solution. Other useful solvents include aqueous dimethyl sulfoxide (DMSO), DMF, acetonitrile, or an alcohol may be used. For example, surfaces activated with tosyl groups or labeled with epoxy groups can be modified in liquid phase reactions. Reactions to couple biotin or proteins such as antibodies, MHCs, or streptavidin to a binding moiety can also be performed as liquid phase reactions.
The reaction may be performed at room temperature or at elevated temperatures. In some embodiments, the reaction is performed at a temperature in a range from about 15° C. to about 60° C.; about 15° C. to about 55° C.; about 15° C. to about 50° C.; about 20° C. to about 45° C. In some embodiments, the reaction to convert a functionalized surface of a microfluidic device to a covalently modified surface is performed at a temperature of about 15° C., 20° C., 25° C., 30° C., 35° C., 40° C., 45° C., 50° C., 55° C., or about 60° C.
Alternatively, a surface modifying reagent may be used in a vapor phase surface modification reaction. For example, silica surfaces and other surfaces comprising hydroxyl groups can be modified in a vapor phase reaction. In some embodiments, a surface (e.g., a silicon surface) is treated with plasma (e.g., using an oxygen plasma cleaner; see the Examples for exemplary treatment conditions). In some embodiments, a surface, such as a plasma treated and/or silicon surface, is reacted under vacuum with a preparing reagent, e.g., comprising a methoxysilane and an azide, such as (11-azidoundecyl) trimethoxy silane. The preparing reagent can be provided initially in liquid form in a vessel separate from the surface and can be vaporized to render it available for reaction with the surface. A water source such as a hydrated salt, e.g., magnesium sulfate heptahydrate can also be provided, e.g., in a further separate vessel. For example, foil boat(s) in the bottom of a vacuum reactor can be used as the separate vessel(s). Exemplary reaction conditions and procedures include pumping the chamber to about 750 mTorr using a vacuum pump and then sealing the chamber. The vacuum reactor can then be incubated at a higher-than ambient temperature for an appropriate length of time, e.g., by placing it within an oven heated at 110° C. for 24-48 h. Following the reaction period, the chamber can be allowed to cool and an inert gas such as argon can be introduced to the evacuated chamber. The surface can be rinsed with one or more appropriate liquids such as acetone and/or isopropanol, and then dried under a stream of inert gas such as nitrogen. Confirmation of introduction of the modified surface can be obtained using techniques such as ellipsometry and contact angle goniometry.
Additional modified surfaces, surface-modifying reagents, and related methods that can be employed in accordance with this disclosure are described in WO2017/205830, published Nov. 30, 2017, which is incorporated herein by reference for all purposes.
Methods of Activating a T Lymphocyte.
A method of activating T lymphocytes is provided, comprising: contacting a plurality of T lymphocytes with a antigen-presenting synthetic surface including: a plurality of primary activating molecular ligands, each including a major histocompatibility (MHC) molecule configured to bind to a T cell receptor of the T cell; and a plurality of co-activating molecular ligands each including a T cell receptor (TCR) co-activating molecule or an adjunct TCR activating molecule; and, culturing the plurality of T lymphocytes in contact with the antigen-presenting synthetic surface, thereby converting at least a portion of the plurality of T Lymphocytes to activated T lymphocytes. The antigen-presenting surface may be any antigen-presenting surface as described herein. In some embodiments, the MHC molecule is an MHC Class 1 molecule. Any of the antigen-presenting synthetic surfaces described herein can be used. In various embodiments, the plurality of MHC molecules may each include an amino acid sequence, and further may be connected to the antigen-presenting synthetic surface via a C-terminal connection of the amino acid sequence. Alternatively, the MHC molecule can be connected to the antigen-presenting synthetic surface through a noncovalent association. Any noncovalent association can be used, e.g., biotinylation of the MHC and binding thereof to streptavidin on the surface. In various embodiments, the MHC molecule may further include an antigen molecule, such as a tumor associated antigen, e.g., any of the tumor associated antigens described herein. In some embodiments, the antigen molecule may be MART1, NYESO1, SLC45A2, TCL1, or VCX3A.
In some embodiments, the co-activating molecules may be connected to the antigen-presenting synthetic surface, as described herein. The T cell receptor (TCR) co-activating molecule or an adjunct TCR activating molecule of the plurality of co-activating molecules may be any TCR co-activating molecule or any adjunct TCR activating molecule as described herein and may be provided in any ratio described herein.
In various embodiments the method may further include contacting the plurality of T lymphocytes with a plurality of growth stimulatory molecular ligands. In some embodiments, each of the growth stimulatory molecular ligands may includes a growth factor receptor ligand. In some embodiments, contacting the plurality of T lymphocytes with the plurality of growth stimulatory molecular ligands may be performed after a first period of culturing of at least one day. In some embodiments, the plurality of growth stimulatory molecular ligands may include IL-21 or a fragment thereof. In various embodiments, the plurality of growth stimulatory molecular ligands may be connected to the antigen-presenting synthetic surface. In some embodiments, the plurality of growth stimulatory molecular ligands may be connected to a surface (e.g., of a bead) that is a different surface than the antigen-presenting synthetic surface including the biomolecules including MHC molecules. In some embodiments, the plurality of growth stimulatory molecular ligands may be connected to the antigen-presenting synthetic surface including MHC molecules.
In various embodiments, the method may include using antigen presenting surfaces on beads. When beads having antigen presenting surfaces are used, the ratio of beads to T lymphocytes may be about 1:1; about 3:1; about 5:1; about 7:1 or about 10:1. The beads may have antigen presenting MHC molecules and anti-CD28 antibodies attached thereto in any method as described herein. In some embodiments, IL-21 may also be attached to the antigen presenting surface of the bead. In other embodiments, IL-21 may be attached to a second bead that has IL-21 as the only biomolecule contributing to activation.
In other embodiments, the method may be performed using a planar surface which may be patterned or unpatterned.
In various embodiments, a first period of culturing may be performed for 4, 5, 6, 7, or 8 days. During the first period of culturing, growth stimulatory molecules such as IL-21, IL-2, and/or IL-7 may be added in solution or may be added on bead to feed the T lymphocytes.
At the end of a first period of culture, the population of cells may include a mixture of unactivated and activated T lymphocytes. Flow cytometry using multiple cell surface markers can be performed to determine the extent of activation and the phenotype of the cells analyzed.
A second period of culture can be performed. If the antigen presenting surfaces are beads, a second aliquot of beads containing the primary activating molecular ligand including the MHC molecule, which includes the tumor associated antigen and co-activating molecules (e.g., TCR co-activating molecules and/or adjunct TCR activating molecules, such as anti-CD28 antibodies and/or anti-CD2 antibodies, respectively) may be provided to the T lymphocytes, e.g., by addition to the wellplate, chamber of the fluidic circuit containing device, or microfluidic device having sequestration pens as described herein. The antigen presenting beads may further include additional growth stimulatory molecules, e.g., IL-21, connected thereto. The antigen presenting beads may be added to the cells being cultured in about a 1:1; about 3:1, about 5:1; or about 10:1 ratio to the cells. In some embodiments, a second aliquot of IL-21 may be added as a second set of beads having IL-21 connected thereto, or further, may be added as a solution. IL-2 and IL-7 may also be added during the second period of culturing to activate additional numbers of T lymphocytes.
When a patterned or unpatterned wafer, inner surface of a fluidic circuit containing device, inner surface of a tube, or inner surface of a microfluidic device having sequestration pens is used, a second period of culturing may be accomplished by continuing to culture in contact with same antigen presenting surface. Alternatively, a new antigen presenting surface may be brought into contact with the T lymphocytes resultant from the first period of culturing. In other embodiments, antigen presenting beads, like any described above or set forth in any embodiments disclosed herein, may be added to the wells or interior chamber of a fluidic circuit containing device or the sequestration pens of a microfluidic device. Growth stimulatory molecules such as IL-21, IL-2, IL-7, or a combination thereof may be added in solution or on beads. In some embodiments, IL-2 and IL-7 are added.
At the conclusion of the second culturing period, flow cytometry analysis can be performed to determine the extent of activation and to determine the phenotype of the further activated T lymphocytes present at that time.
In some embodiments, a third period of culturing may be included. The third period may have any of the features described herein with respect to the second period. In some embodiments, the third period is performed in the same way as the second period. For example, and all of the actions employed in the second period of culturing may be repeated to further activate T lymphocytes in the wells of the wellplate, in a tube, or in the chamber of a fluidic circuit containing device or a microfluidic device having sequestration pens.
In some embodiments, the T lymphocytes being activated comprise CD8+ T lymphocytes, such as naïve CD8+ T lymphocytes. In some embodiments, the T lymphocytes being activated are enriched for CD8+ T lymphocytes, such as naïve CD8+ T lymphocytes. Alternatively, in some embodiments, the T lymphocytes being activated comprise CD4+ T lymphocytes, such as naïve CD4+ T lymphocytes. In some embodiments, the T lymphocytes being activated are enriched for CD4+ T lymphocytes, such as naïve CD4+ T lymphocytes. CD4+ T lymphocytes can be used, e.g., if T cells specific for a Class II-restricted antigen are desired.
In some embodiments, the method produces activated T lymphocytes that are CD45RO+. In some embodiments, the method produces activated T lymphocytes that are CD28+. In some embodiments, the method produces activated T lymphocytes that are CD28+CD45RO+. In some embodiments, the method produces activated T lymphocytes that are CD197+. In some embodiments, the method produces activated T lymphocytes that are CD127+. In some embodiments, the method produces activated T lymphocytes that are positive for CD28, CD45RO, CD127 and CD197, or at least any combination of three of the foregoing markers, or at least any combination of two of the foregoing markers. The activated T lymphocytes with any of the foregoing phenotypes can further be CD8+. In some embodiments, any of the foregoing phenotypes that is CD28+ comprises a CD28high phenotype.
In some embodiments, the method produces a population of T cells comprising antigen-specific T cells, wherein at least 65%, 70%, 75%, 80%, 85%, 86%, 87%, 88%, 89%, 90%, 91%, 92%, 93%, 94%, 95%, 96%, 97%, or 98% of the antigen-specific T cells are CD45RO+/CD28High cells, wherein each of the foregoing values can be modified by “about.” Alternatively or in addition, in some embodiments, the method produces a population of T cells wherein at least 1%, 1.5%, 2%, 3,%, 4%, 5%, 6%, 7%, 8%, 9%, or 10% of the T cells are antigen-specific T cells; or wherein 1%-2%, 2%-3%, 3%-4%, 4%-5%, 5%-6%, 6%-7%, 7%-8%, 8%-9%, 9%-10%, 10%-11%, or 11%-12% of the T cells are antigen-specific T cells, wherein each of the foregoing values can be modified by “about.” The content of the population of T cells can be determined on the “crude” product of the method following contact with the antigen-presenting surface and optionally further expansion steps, i.e., before/without enriching or separating product T cells having a particular phenotype. The determination of antigen-specificity and/or T cell marker phenotype can exclude dead cells.
In some embodiments, the method provides a population of T cells in which the fraction of T cells that are antigen-specific is increased relative to the starting population.
Cells and Compositions.
An activated T lymphocyte produced by any method described herein is provided.
In some embodiments, the activated T lymphocytes are CD45RO+. In some embodiments, the activated T lymphocytes are CD28+. In some embodiments, the activated T lymphocytes are CD28+CD45RO+. In some embodiments, the activated T lymphocytes are CD197+. In some embodiments, the activated T lymphocytes are CD127+. In some embodiments, the activated T lymphocytes are positive for CD28, CD45RO, CD127 and CD197, at least any combination of three of the foregoing markers, or at least any combination of two of the foregoing markers. The activated T lymphocytes with any of the foregoing phenotypes can further be CD8+. In some embodiments, any of the foregoing phenotypes that is CD28+ comprises a CD28high phenotype.
In some embodiments, a population of T cells comprising activated T cells produced by any method described herein is provided. The population can have any of the features described above for T cell populations.
In some embodiments, a microfluidic device is provided comprising a population of T cells provided herein. The microfluidic device can be any of the antigen-presenting microfluidic devices or other microfluidic devices (e.g., for performing an antigen-specific cytotoxicity assay) described herein.
In some embodiments, a pharmaceutical composition is provided comprising a population of T cells provided herein. The pharmaceutical composition can further comprise, e.g., saline, glucose, and/or Human Serum Albumin The composition may be an aqueous composition and can be provided in frozen or liquid form. A pharmaceutical composition can be provided as a single dose, e.g., within a syringe, and can comprise 10 million, 100 million, 1 billion, or 10 billion cells. The number of cells administered is indication specific, patient specific (e.g., size of patient), and will also vary with the purity and phenotype of the administered cells.
Methods of Performing an Antigen-Specific Cytotoxicity Assay.
Provided herein is a method of performing an antigen-specific cytotoxicity assay, comprising: loading one or more target cells into a sequestration pen of a microfluidic device;
loading one or more T cells in the sequestration pen, such that the one or more T cells can contact the one or more target cells;
contacting the target cells with a detectable marker that labels apoptotic cells; and
detecting whether the target cells become apoptotic.
The microfluidic device can be any device described herein. The microfluidic device included in a kit for performing an antigen-specific cytotoxicity assay need not comprise an antigen-presenting synthetic surface. The one or more T cells can be produced or activated according to any method described herein for producing or activating such cells. Any type of CD8+ T cell described herein can be used. In some embodiments, the one or more T cells express a chimeric antigen receptor (CAR). In some embodiments, the one or more T cells do not express a CAR.
The target cells can express a tumor antigen, such as any of the tumor antigens described herein. In some embodiments, the T cell is specific for the antigen expressed by the target cells. In some embodiments, the target cells are from an immortal cell line and/or are derived from a cancer such as a melanoma, breast cancer, or lung cancer.
In some embodiments, a single target cell and/or a single T cell is loaded into the sequestration pen. In some embodiments, a plurality of target cells and/or a plurality of T cells are loaded into the sequestration pen. In some embodiments, the plurality of T cells is a clonal population. In some embodiments, a single T cell and plurality of target cells are loaded into the sequestration pen.
Loading cells into the sequestration pen may be performed using gravity, e.g., by tilting the microfluidic device so that cells are pulled gravitationally into the pen. Alternatively, with a microfluidic device having a dielectrophoresis (DEP) configuration, DEP force can be used to load the cells. In some embodiments, the DEP force is activated by structured light.
Any suitable marker that labels apoptotic cells can be used. Markers that label apoptotic cells include those that label dead cells distinguishably from live cells, e.g., dyes that do not cross live cell membranes but do cross compromised dead cell membranes, and labels that are dependent on an apoptosis-associated protein or enzymatic activity (e.g., an apoptosis-associated protease) for labeling. In some embodiments, the marker comprises a nucleic acid-binding moiety. In some embodiments, the marker is a fluorogenic or cleavable marker that is activated by cleavage by a protease, such as an apoptosis-associated protease, such as a caspase, e.g., caspase-3. In some embodiments, the marker comprises a binding agent (e.g., antibody) that specifically binds to apoptotic cells and/or apoptotic bodies; the binding agent can further comprise a detectable moiety, such as a fluorophore.
The method can comprise detecting whether target cells have become apoptotic one time or periodically, e.g., two, three, or more times. The method can comprise detecting whether target cells have become apoptotic 2 or more hours after contacting the cells with the marker and/or the T cell(s).
Kits for Performing an Antigen-Specific Cytotoxicity Assay.
Also provided herein are kits for performing an antigen-specific cytotoxicity assay. In some embodiments, the kit comprises a microfluidic device. The microfluidic device can be any of the microfluidic devices described herein. In some embodiments, the microfluidic device is as described above in the section regarding methods for performing an antigen-specific cytotoxicity assay or as set forth in any embodiments disclosed herein. The microfluidic device included in a kit for performing an antigen-specific cytotoxicity assay need not comprise an antigen-presenting synthetic surface. In some embodiments, the kit comprises a reagent for detecting apoptotic cells. In some embodiments, the reagent for detecting apoptotic cells is a detectable marker that labels apoptotic cells as described above in the section regarding methods for performing an antigen-specific cytotoxicity assay or as set forth in any embodiments disclosed herein.
Methods of Treatment.
Provided herein is a method of treating a subject in need of treating a cancer; including: obtaining a sample comprising T lymphocytes from the subject; separating the T lymphocytes from other cells in the sample; contacting the T lymphocytes with a antigen-presenting synthetic surface including MHC molecules according to any method described herein, where the MHC molecules include an antigen specific for the cancer of the subject; producing a plurality of T lymphocytes activated to be specific against the cancer of the subject; separating the plurality of specific activated T lymphocytes from non-activated T lymphocytes; and, introducing the plurality of specific activated T lymphocytes into the subject. Also provided herein is a plurality of specific activated T lymphocytes for use in treating a cancer, wherein the plurality is prepared by a method including: obtaining a sample comprising T lymphocytes from the subject; separating the T lymphocytes from other cells in the sample; contacting the T lymphocytes with a antigen-presenting synthetic surface including MHC molecules according to any method described herein, where the MHC molecules include an antigen specific for the cancer of the subject; producing a plurality of T lymphocytes activated to be specific against the cancer of the subject; and separating the plurality of specific activated T lymphocytes from non-activated T lymphocytes. Also provided herein is the use of a plurality of specific activated T lymphocytes for the manufacture of a medicament for treating a cancer, wherein the plurality is prepared by a method including: obtaining a sample comprising T lymphocytes from the subject; separating the T lymphocytes from other cells in the sample; contacting the T lymphocytes with a antigen-presenting synthetic surface including MHC molecules according to any method described herein, where the MHC molecules include an antigen specific for the cancer of the subject; producing a plurality of T lymphocytes activated to be specific against the cancer of the subject; and separating the plurality of specific activated T lymphocytes from non-activated T lymphocytes.
Also provided is a method of treating a subject in need of treating a cancer; including introducing a plurality of specific activated T lymphocytes into the subject, wherein the plurality of specific activated T lymphocytes were produced by a method described herein. Also provided is a method of treating a subject in need of treating a cancer, including introducing a population of specific activated T lymphocytes described herein into the subject. Such methods can further comprise separating activated T lymphocytes from non-activated T lymphocytes. Also provided is a plurality of specific activated T lymphocytes for use in treating a subject in need of treating a cancer, wherein the plurality of specific activated T lymphocytes were produced by a method described herein. Also provided is a population of specific activated T lymphocytes described herein for use in treating a subject in need of treating a cancer. Also provided is a use of a plurality of specific activated T lymphocytes for the manufacture of a medicament for treating a subject in need of treating a cancer, wherein the plurality of specific activated T lymphocytes were produced by a method described herein. Also provided is a use of a population of specific activated T lymphocytes described herein for the manufacture of a medicament for treating a subject in need of treating a cancer. Such a plurality or population of specific activated T lymphocytes can be further prepared by separating activated T lymphocytes from non-activated T lymphocytes.
In some embodiments, separating the plurality of specific activated T lymphocytes may further include detecting surface biomarkers of the specific activated T lymphocytes.
In some embodiments, the specific activated T lymphocytes are autologous (i.e., derived from the subject to which they are to be administered).
In various embodiments, the methods or the preparation of the plurality or population of specific activated T lymphocytes may further include rapidly expanding the activated T lymphocytes to provide an expanded population of activated T lymphocytes. In some embodiments, the rapid expansion may be performed after separating the specific activated T lymphocytes from the non-activated T lymphocytes. The generation of sufficient levels of T lymphocytes may be achieved using rapid expansion methods described herein or known in the art. See, e.g., the Examples below; Riddell, U.S. Pat. No. 5,827,642; Riddell et al., U.S. Pat. No. 6,040,177, and Yee and Li, PCT Patent App. Pub. No. WO2009/045308 A2.
Uses of T cells in treatment of human subjects (e.g., for adoptive cell therapy) are known in the art. T cells prepared according to the methods described herein can be used in such methods. For example, adoptive cell therapy using tumor-infiltrating lymphocytes including MART-1 antigen specific T cells have been tested in the clinic (Powell et al., Blood 105:241-250, 2005). Also, administration of T cells coactivated with anti-CD3 monoclonal antibody and IL-2 was described in Chang et al., J. Clinical Oncology 21:884-890, 2003. Additional examples and/or discussion of T cell administration for the treatment of cancer are provided in Dudley et al., Science 298:850-854, 2002; Roszkowski et al., Cancer Res 65(4): 1570-76, 2005; Cooper et al., Blood 101: 1637-44, 2003; Yee, US Patent App. Pub. No. 2006/0269973; Yee and Li, PCT Patent App. Pub. No. WO2009/045308 A2; Gruenberg et al., US Patent App. Pub. No. 2003/0170238; Rosenberg, U.S. Pat. No. 4,690,915; and Alajez et al., Blood 105:4583-89, 2005.
In some embodiments, the cells are formulated by first harvesting them from their culture medium, and then washing and concentrating the cells in a medium and container system suitable for administration (a “pharmaceutically acceptable” carrier) in a treatment-effective amount. Suitable infusion medium can be any isotonic medium formulation, typically normal saline, Normosol R (Abbott) or Plasma-Lyte A (Baxter), but also 5% dextrose in water or Ringer's lactate can be utilized. The infusion medium can be supplemented with human serum albumin.
In some embodiments, the number of cells in the composition is at least 109, or at least 1019 cells. In some embodiments, a single dose can comprise at least 10 million, 100 million, 1 billion, or 10 billion cells. The number of cells administered is indication specific, patient specific (e.g., size of patient), and will also vary with the purity and phenotype of the administered cells. The number of cells will depend upon the ultimate use for which the composition is intended as will the type of cells included therein. For example, if cells that are specific for a particular antigen are desired, then the population will contain greater than 70%, generally greater than 80%, 85% and 90-95% of such cells. For uses provided herein, the cells are generally in a volume of a liter or less, can be 500 mls or less, even 250 mls or 100 mls or less. Hence the density of the desired cells may be greater than 106 cells/ml, greater than 107 cells/ml, or 108 cells/ml or greater. The clinically relevant number of immune cells can be apportioned into multiple infusions that cumulatively equal or exceed 109, 1010 or 1011 cells.
In some embodiments, T lymphocytes described herein or prepared according to a method described herein of the invention may be used to confer immunity to individuals against a tumor or cancer cells. By “immunity” is meant a lessening of one or more physical symptoms associated with cancer cells or a tumor against an antigen of which the lymphocytes have been activated. The cells may be administered by infusion, with each infusion in a range of at least 106 to 1010 cells/m2, e.g., in the range of at least 107 to 109 cells/m2. The clones may be administered by a single infusion, or by multiple infusions over a range of time. However, since different individuals are expected to vary in responsiveness, the type and amount of cells infused, as well as the number of infusions and the time range over which multiple infusions are given are determined by the attending physician, and can be determined by examination.
Following the transfer of cells back into patients, methods may be employed to maintain their viability by treating patients with cytokines that could include IL-21 and IL-2 (Bear et al., Cancer Immunol. Immunother. 50:269-74, 2001; and Schultze et al., Br. J. Haematol. 113:455-60, 2001). In another embodiment, cells are cultured in the presence of IL-21 before administration to the patient. See, e.g., Yee, US Patent App. Pub. No. 2006/0269973. IL-21 can increase T cell frequency in a population comprising activated T cells to levels that are high enough for expansion and adoptive transfer without further antigen-specific T cell enrichment. Accordingly, such a step can further decrease the time to therapy and/or obviate a need for further selection and/or cloning.
Kits for Preparing an Antigen-Presenting Synthetic Surface.
A kit is also provided for preparing an antigen-presenting synthetic surface for activating a T lymphocyte (T cell), including: a. any covalently functionalized synthetic surface as described herein, which includes a plurality of noncovalently or covalently associated first coupling agents; and a first modification reagent including a plurality of major histocompatibility complex (MHC) I molecules configured to bind with a T cell receptor of the T cell, and further wherein the MHC molecules are configured to bind to one of a first subset of the plurality of noncovalently or covalently associated first coupling agents of the covalently functionalized synthetic surface. In some embodiments, the first coupling agents may be a biotin-binding agent. The biotin-binding agent may be streptavidin. In some embodiments, each of the plurality of MHC molecules may further include at least one biotin functionality. Other coupling chemistries may be used, as is known in the art, wherein other site specific protein tags may be attached to the MHC protein, which are configured to covalently attach to recognition protein based species attached to the bead. These coupling strategies can provide the equivalent site specific and specifically orienting attachment of the MHC molecule as provided by C-terminal biotinylation of the MHC molecule. The covalently functionalized synthetic surface may be a wafer, a bead, at least one inner surface of a microfluidic device, or a tube.
The kit may further include a reagent including a plurality of co-activating molecules, each configured to bind one of a second subset of the plurality of noncovalently or covalently associated biotin-binding agents of the covalently functionalized synthetic surface. In some embodiments, each of the plurality of co-activating molecules may include a biotin functionality. Each of the co-activating molecules may include a T cell receptor (TCR) co-activating molecule, an adjunct TCR activating molecule, or any combination thereof. In some embodiments, the reagent is provided in individual containers containing the T cell receptor (TCR) co-activating molecule and/or an adjunct TCR activating molecule. Alternatively, the reagent including the plurality of co-activating molecules may be provided in one container containing the TCR co-activating molecules and/or the adjunct TCR activating molecules of the plurality of co-activating molecular ligands in a ratio from about 100:1 to 1:100. In some embodiments the reagent including the plurality of co-activating molecules includes a mixture of TCR co-activating molecules and adjunct TCR activating molecules wherein the ratio of the TCR co-activating molecules to the adjunct TCR activating molecules of the plurality of co-activating molecular ligands is 100:1 to 90:1, 90:1 to 80:1, 80:1 to 70:1, 70:1 to 60:1, 60:1 to 50:1, 50:1 to 40:1, 40:1 to 30:1, 30:1 to 20:1, 20:1 to 10:1, 10:1 to 1:1, 1:1 to 1:10, 1:10 to 1:20, 1:20 to 1:30, 1:30 to 1:40, 1:40 to 1:50, 1:50 to 1:60, 1:60 to 1:70, 1:70 to 1:80, 1:80 to 1:90, or 1:90 to 1:100, wherein each of the foregoing values is modified by “about”. In some embodiments, the reagent including a plurality of co-activating molecules contains the TCR co-activating molecules and the adjunct TCR activating molecules of the plurality of co-activating molecular ligands in a ratio from about 20:1 to about 1:20.
In some embodiments, the kit for preparing an antigen presenting synthetic surface may further include a reagent including adhesion stimulatory molecules, wherein each adhesion stimulatory molecule includes a ligand for a cell adhesion receptor including an ICAM protein sequence configured to react with a third subset of the plurality of noncovalently or covalently associated biotin-binding agent functionalities of the covalently functionalized synthetic surface. In some embodiments, the adhesion stimulatory molecule may include a biotin functionality.
In some embodiments, the kit for preparing an antigen presenting synthetic surface may further include a reagent including growth stimulatory molecules, wherein each growth stimulatory molecule may include a growth factor receptor ligand. In some embodiments, the growth factor receptor ligand may include a cytokine or a fragment thereof. In some embodiments, the cytokine may include IL-21 or a fragment thereof. In some embodiments, the growth stimulatory molecule may be attached to a covalently modified bead.
In some embodiments, the kit for preparing an antigen presenting synthetic surface may further include a reagent including one or more additional growth-stimulatory molecules. In some embodiments, the one or more additional growth-stimulatory molecules include IL2 and/or IL7, or fragments thereof. In some embodiments, the growth stimulatory molecule may be attached to a covalently modified bead.
Kits for Activating T Lymphocytes.
Also provided is a kit for activating T lymphocytes, including an antigen-presenting synthetic surface as described herein. The kit can further comprise growth stimulatory molecules, wherein each growth stimulatory molecule may include a growth factor receptor ligand. The growth stimulatory molecules can be provided as free molecules, attached to the antigen presenting synthetic surface (in the same or a different region than the primary activating molecular ligand), or attached to a different covalently modified synthetic surface. For example, the kit can further comprise a plurality of covalently modified beads comprising an adjunct stimulatory molecule. In some embodiments, the growth factor receptor ligand molecule may include a cytokine or a fragment thereof. In some embodiments, the growth factor receptor ligand may include IL-21. In other embodiments, the kit may include one or more additional (e.g., a second or second and third) growth stimulatory molecules). In some embodiments, the one or more additional growth stimulatory molecules may include IL-2 and/or IL-7, or fragments thereof. Additional growth stimulatory molecules can be provided as a free molecule, attached to the antigen presenting synthetic surface (in the same or a different region than the primary activating molecular ligand), or attached to a different covalently modified synthetic surface, such as a bead.
Additional Aspects of Microfluidic Device Structure, Loading, and Operation; Related Systems
Microfluidic devices and uses thereof described herein may have any of the following features, and can be used in conjunction with systems described below.
Methods of Loading.
Loading of biological micro-objects or micro-objects such as, but not limited to, beads, can involve the use of fluid flow, gravity, a dielectrophoresis (DEP) force, electrowetting, a magnetic force, or any combination thereof as described herein. The DEP force can be generated optically, such as by an optoelectronic tweezers (OET) configuration and/or electrically, such as by activation of electrodes/electrode regions in a temporal/spatial pattern. Similarly, electrowetting force may be provided optically, such as by an opto-electro wetting (OEW) configuration and/or electrically, such as by activation of electrodes/electrode regions in a temporal spatial pattern.
Microfluidic Devices and Systems for Operating and Observing Such Devices.
As generally illustrated in
The support structure 104 can be at the bottom and the cover 110 at the top of the microfluidic circuit 120 as illustrated in
The support structure 104 can comprise one or more electrodes (not shown) and a substrate or a plurality of interconnected substrates. For example, the support structure 104 can comprise one or more semiconductor substrates, each of which is electrically connected to an electrode (e.g., all or a subset of the semiconductor substrates can be electrically connected to a single electrode). The support structure 104 can further comprise a printed circuit board assembly (“PCBA”). For example, the semiconductor substrate(s) can be mounted on a PCBA.
The microfluidic circuit structure 108 can define circuit elements of the microfluidic circuit 120. Such circuit elements can comprise spaces or regions that can be fluidly interconnected when microfluidic circuit 120 is filled with fluid, such as flow regions (which may include or be one or more flow channels), chambers, pens, traps, and the like. In the microfluidic circuit 120 illustrated in
The microfluidic circuit material 116 can be patterned with cavities or the like to define circuit elements and interconnections of the microfluidic circuit 120. The microfluidic circuit material 116 can comprise a flexible material, such as a flexible polymer (e.g. rubber, plastic, elastomer, silicone, polydimethylsiloxane (“PDMS”), or the like), which can be gas permeable. Other examples of materials that can compose microfluidic circuit material 116 include molded glass, an etchable material such as silicone (e.g. photo-patternable silicone or “PPS”), photo-resist (e.g., SU8), or the like. In some embodiments, such materials—and thus the microfluidic circuit material 116—can be rigid and/or substantially impermeable to gas. Regardless, microfluidic circuit material 116 can be disposed on the support structure 104 and inside the frame 114.
The cover 110 can be an integral part of the frame 114 and/or the microfluidic circuit material 116. Alternatively, the cover 110 can be a structurally distinct element, as illustrated in
In some embodiments, the cover 110 can comprise a rigid material. The rigid material may be glass or a material with similar properties. In some embodiments, the cover 110 can comprise a deformable material. The deformable material can be a polymer, such as PDMS. In some embodiments, the cover 110 can comprise both rigid and deformable materials. For example, one or more portions of cover 110 (e.g., one or more portions positioned over sequestration pens 124, 126, 128, 130) can comprise a deformable material that interfaces with rigid materials of the cover 110. In some embodiments, the cover 110 can further include one or more electrodes. The one or more electrodes can comprise a conductive oxide, such as indium-tin-oxide (ITO), which may be coated on glass or a similarly insulating material. Alternatively, the one or more electrodes can be flexible electrodes, such as single-walled nanotubes, multi-walled nanotubes, nanowires, clusters of electrically conductive nanoparticles, or combinations thereof, embedded in a deformable material, such as a polymer (e.g., PDMS). Flexible electrodes that can be used in microfluidic devices have been described, for example, in U.S. 2012/0325665 (Chiou et al.), the contents of which are incorporated herein by reference. In some embodiments, the cover 110 can be modified (e.g., by conditioning all or part of a surface that faces inward toward the microfluidic circuit 120) to support cell adhesion, viability and/or growth. The modification may include a coating of a synthetic or natural polymer. In some embodiments, the cover 110 and/or the support structure 104 can be transparent to light. The cover 110 may also include at least one material that is gas permeable (e.g., PDMS or PPS).
The electrical power source 192 can provide electric power to the microfluidic device 100 and/or tilting device 190, providing biasing voltages or currents as needed. The electrical power source 192 can, for example, comprise one or more alternating current (AC) and/or direct current (DC) voltage or current sources. The imaging device 194 (part of imaging module 164, discussed below) can comprise a device, such as a digital camera, for capturing images inside microfluidic circuit 120. In some instances, the imaging device 194 further comprises a detector having a fast frame rate and/or high sensitivity (e.g. for low light applications). The imaging device 194 can also include a mechanism for directing stimulating radiation and/or light beams into the microfluidic circuit 120 and collecting radiation and/or light beams reflected or emitted from the microfluidic circuit 120 (or micro-objects contained therein). The emitted light beams may be in the visible spectrum and may, e.g., include fluorescent emissions. The reflected light beams may include reflected emissions originating from an LED or a wide spectrum lamp, such as a mercury lamp (e.g. a high pressure mercury lamp) or a Xenon arc lamp. As discussed with respect to
System 150 further comprises a tilting device 190 (part of tilting module 166, discussed below) configured to rotate a microfluidic device 100 about one or more axes of rotation. In some embodiments, the tilting device 190 is configured to support and/or hold the enclosure 102 comprising the microfluidic circuit 120 about at least one axis such that the microfluidic device 100 (and thus the microfluidic circuit 120) can be held in a level orientation (i.e. at 0° relative to x- and y-axes), a vertical orientation (i.e. at 90° relative to the x-axis and/or the y-axis), or any orientation therebetween. The orientation of the microfluidic device 100 (and the microfluidic circuit 120) relative to an axis is referred to herein as the “tilt” of the microfluidic device 100 (and the microfluidic circuit 120). For example, the tilting device 190 can tilt the microfluidic device 100 at 0.1°, 0.2°, 0.3°, 0.4°, 0.5°, 0.6°, 0.7°, 0.8°, 0.9°, 1°, 2°, 3°, 4°, 5°, 10°, 15°, 20°, 25°, 30°, 35°, 40°, 45°, 50°, 55°, 60°, 65°, 70°, 75°, 80°, 90° relative to the x-axis or any degree therebetween. The level orientation (and thus the x- and y-axes) is defined as normal to a vertical axis defined by the force of gravity. The tilting device can also tilt the microfluidic device 100 (and the microfluidic circuit 120) to any degree greater than 90° relative to the x-axis and/or y-axis, or tilt the microfluidic device 100 (and the microfluidic circuit 120) 180° relative to the x-axis or the y-axis in order to fully invert the microfluidic device 100 (and the microfluidic circuit 120). Similarly, in some embodiments, the tilting device 190 tilts the microfluidic device 100 (and the microfluidic circuit 120) about an axis of rotation defined by flow path 106 or some other portion of microfluidic circuit 120.
In some instances, the microfluidic device 100 is tilted into a vertical orientation such that the flow path 106 is positioned above or below one or more sequestration pens. The term “above” as used herein in the context of microfluidic devices denotes that the flow path 106 is positioned higher than the one or more sequestration pens on a vertical axis defined by the force of gravity (i.e. an object in a sequestration pen above a flow path 106 would have a higher gravitational potential energy than an object in the flow path). The term “below” as used herein in the context of microfluidic devices denotes that the flow path 106 is positioned lower than the one or more sequestration pens on a vertical axis defined by the force of gravity (i.e. an object in a sequestration pen below a flow path 106 would have a lower gravitational potential energy than an object in the flow path).
In some instances, the tilting device 190 tilts the microfluidic device 100 about an axis that is parallel to the flow path 106. Moreover, the microfluidic device 100 can be tilted to an angle of less than 90° such that the flow path 106 is located above or below one or more sequestration pens without being located directly above or below the sequestration pens. In other instances, the tilting device 190 tilts the microfluidic device 100 about an axis perpendicular to the flow path 106. In still other instances, the tilting device 190 tilts the microfluidic device 100 about an axis that is neither parallel nor perpendicular to the flow path 106.
System 150 can further include a media source 178. The media source 178 (e.g., a container, reservoir, or the like) can comprise multiple sections or containers, each for holding a different fluidic medium 180. Thus, the media source 178 can be a device that is outside of and separate from the microfluidic device 100, as illustrated in
The master controller 154 can comprise a control module 156 and a digital memory 158. The control module 156 can comprise, for example, a digital processor configured to operate in accordance with machine executable instructions (e.g., software, firmware, source code, or the like) stored as non-transitory data or signals in the memory 158. Alternatively, or in addition, the control module 156 can comprise hardwired digital circuitry and/or analog circuitry. The media module 160, motive module 162, imaging module 164, tilting module 166, and/or other modules 168 can be similarly configured. Thus, functions, processes acts, actions, or steps of a process discussed herein as being performed with respect to the microfluidic device 100 or any other microfluidic apparatus can be performed by any one or more of the master controller 154, media module 160, motive module 162, imaging module 164, tilting module 166, and/or other modules 168 configured as discussed above. Similarly, the master controller 154, media module 160, motive module 162, imaging module 164, tilting module 166, and/or other modules 168 may be communicatively coupled to transmit and receive data used in any function, process, act, action or step discussed herein.
The media module 160 controls the media source 178. For example, the media module 160 can control the media source 178 to input a selected fluidic medium 180 into the enclosure 102 (e.g., through an inlet port 107). The media module 160 can also control removal of media from the enclosure 102 (e.g., through an outlet port (not shown)). One or more media can thus be selectively input into and removed from the microfluidic circuit 120. The media module 160 can also control the flow of fluidic medium 180 in the flow path 106 inside the microfluidic circuit 120. For example, in some embodiments media module 160 stops the flow of media 180 in the flow path 106 and through the enclosure 102 prior to the tilting module 166 causing the tilting device 190 to tilt the microfluidic device 100 to a desired angle of incline.
The motive module 162 can be configured to control selection, trapping, and movement of micro-objects (not shown) in the microfluidic circuit 120. As discussed below with respect to
The imaging module 164 can control the imaging device 194. For example, the imaging module 164 can receive and process image data from the imaging device 194. Image data from the imaging device 194 can comprise any type of information captured by the imaging device 194 (e.g., the presence or absence of micro-objects, droplets of medium, accumulation of label, such as fluorescent label, etc.). Using the information captured by the imaging device 194, the imaging module 164 can further calculate the position of objects (e.g., micro-objects, droplets of medium) and/or the rate of motion of such objects within the microfluidic device 100.
The tilting module 166 can control the tilting motions of tilting device 190. Alternatively, or in addition, the tilting module 166 can control the tilting rate and timing to optimize transfer of micro-objects to the one or more sequestration pens via gravitational forces. The tilting module 166 is communicatively coupled with the imaging module 164 to receive data describing the motion of micro-objects and/or droplets of medium in the microfluidic circuit 120. Using this data, the tilting module 166 may adjust the tilt of the microfluidic circuit 120 in order to adjust the rate at which micro-objects and/or droplets of medium move in the microfluidic circuit 120. The tilting module 166 may also use this data to iteratively adjust the position of a micro-object and/or droplet of medium in the microfluidic circuit 120.
In the example shown in
The microfluidic circuit 120 may comprise any number of microfluidic sequestration pens. Although five sequestration pens are shown, microfluidic circuit 120 may have fewer or more sequestration pens. As shown, microfluidic sequestration pens 124, 126, 128, and 130 of microfluidic circuit 120 each comprise differing features and shapes which may provide one or more benefits useful for maintaining, isolating, assaying or culturing biological micro-objects. In some embodiments, the microfluidic circuit 120 comprises a plurality of identical microfluidic sequestration pens.
In the embodiment illustrated in
However, other embodiments may contain multiple channels 122, each configured to comprise a flow path 106. The microfluidic circuit 120 further comprises an inlet valve or port 107 in fluid communication with the flow path 106 and fluidic medium 180, whereby fluidic medium 180 can access channel 122 via the inlet port 107. In some instances, the flow path 106 comprises a single path. In some instances, the single path is arranged in a zigzag pattern whereby the flow path 106 travels across the microfluidic device 100 two or more times in alternating directions.
In some instances, microfluidic circuit 120 comprises a plurality of parallel channels 122 and flow paths 106, wherein the fluidic medium 180 within each flow path 106 flows in the same direction. In some instances, the fluidic medium within each flow path 106 flows in at least one of a forward or reverse direction. In some instances, a plurality of sequestration pens is configured (e.g., relative to a channel 122) such that the sequestration pens can be loaded with target micro-objects in parallel.
In some embodiments, microfluidic circuit 120 further comprises one or more micro-object traps 132. The traps 132 are generally formed in a wall forming the boundary of a channel 122, and may be positioned opposite an opening of one or more of the microfluidic sequestration pens 124, 126, 128, 130. In some embodiments, the traps 132 are configured to receive or capture a single micro-object from the flow path 106. In some embodiments, the traps 132 are configured to receive or capture a plurality of micro-objects from the flow path 106. In some instances, the traps 132 comprise a volume approximately equal to the volume of a single target micro-object.
The traps 132 may further comprise an opening which is configured to assist the flow of targeted micro-objects into the traps 132. In some instances, the traps 132 comprise an opening having a height and width that is approximately equal to the dimensions of a single target micro-object, whereby larger micro-objects are prevented from entering into the micro-object trap. The traps 132 may further comprise other features configured to assist in retention of targeted micro-objects within the trap 132. In some instances, the trap 132 is aligned with and situated on the opposite side of a channel 122 relative to the opening of a microfluidic sequestration pen, such that upon tilting the microfluidic device 100 about an axis parallel to the microfluidic channel 122, the trapped micro-object exits the trap 132 at a trajectory that causes the micro-object to fall into the opening of the sequestration pen. In some instances, the trap 132 comprises a side passage 134 that is smaller than the target micro-object in order to facilitate flow through the trap 132 and thereby increase the likelihood of capturing a micro-object in the trap 132.
In some embodiments, dielectrophoretic (DEP) forces are applied across the fluidic medium 180 (e.g., in the flow path and/or in the sequestration pens) via one or more electrodes (not shown) to manipulate, transport, separate and sort micro-objects located therein. For example, in some embodiments, DEP forces are applied to one or more portions of microfluidic circuit 120 in order to transfer a single micro-object from the flow path 106 into a desired microfluidic sequestration pen. In some embodiments, DEP forces are used to prevent a micro-object within a sequestration pen (e.g., sequestration pen 124, 126, 128, or 130) from being displaced therefrom. Further, in some embodiments, DEP forces are used to selectively remove a micro-object from a sequestration pen that was previously collected in accordance with the embodiments of the current disclosure. In some embodiments, the DEP forces comprise optoelectronic tweezer (OET) forces.
In other embodiments, optoelectrowetting (OEW) forces are applied to one or more positions in the support structure 104 (and/or the cover 110) of the microfluidic device 100 (e.g., positions helping to define the flow path and/or the sequestration pens) via one or more electrodes (not shown) to manipulate, transport, separate and sort droplets located in the microfluidic circuit 120. For example, in some embodiments, OEW forces are applied to one or more positions in the support structure 104 (and/or the cover 110) in order to transfer a single droplet from the flow path 106 into a desired microfluidic sequestration pen. In some embodiments, OEW forces are used to prevent a droplet within a sequestration pen (e.g., sequestration pen 124, 126, 128, or 130) from being displaced therefrom. Further, in some embodiments, OEW forces are used to selectively remove a droplet from a sequestration pen that was previously collected in accordance with the embodiments of the current disclosure.
In some embodiments, DEP and/or OEW forces are combined with other forces, such as flow and/or gravitational force, so as to manipulate, transport, separate and sort micro-objects and/or droplets within the microfluidic circuit 120. For example, the enclosure 102 can be tilted (e.g., by tilting device 190) to position the flow path 106 and micro-objects located therein above the microfluidic sequestration pens, and the force of gravity can transport the micro-objects and/or droplets into the pens. In some embodiments, the DEP and/or OEW forces can be applied prior to the other forces. In other embodiments, the DEP and/or OEW forces can be applied after the other forces. In still other instances, the DEP and/or OEW forces can be applied at the same time as the other forces or in an alternating manner with the other forces.
Examples of microfluidic devices having pens in which biological micro-objects can be placed, cultured, and/or monitored have been described, for example, in US 2014/0116881 (application Ser. No. 14/060,117, filed Oct. 22, 2013), US 2015/0151298 (application Ser. No. 14/520,568, filed Oct. 22, 2014), and US 2015/0165436 (application Ser. No. 14/521,447, filed Oct. 22, 2014), each of which is incorporated herein by reference in its entirety. U.S. application Ser. Nos. 14/520,568 and 14/521,447 also describe exemplary methods of analyzing secretions of cells cultured in a microfluidic device. Each of the foregoing applications further describes microfluidic devices configured to produce dielectrophoretic (DEP) forces, such as optoelectronic tweezers (OET) or configured to provide opto-electro wetting (OEW). For example, the optoelectronic tweezers device illustrated in FIG. 2 of US 2014/0116881 is an example of a device that can be utilized in embodiments of the present disclosure to select and move an individual biological micro-object or a group of biological micro-objects.
Microfluidic Device Motive Configurations.
As described above, the control and monitoring equipment of the system can comprise a motive module for selecting and moving objects, such as micro-objects or droplets, in the microfluidic circuit of a microfluidic device. The microfluidic device can have a variety of motive configurations, depending upon the type of object being moved and other considerations. For example, a dielectrophoresis (DEP) configuration can be utilized to select and move micro-objects in the microfluidic circuit. Thus, the support structure 104 and/or cover 110 of the microfluidic device 100 can comprise a DEP configuration for selectively inducing DEP forces on micro-objects in a fluidic medium 180 in the microfluidic circuit 120 and thereby select, capture, and/or move individual micro-objects or groups of micro-objects. Alternatively, the support structure 104 and/or cover 110 of the microfluidic device 100 can comprise an electrowetting (EW) configuration for selectively inducing EW forces on droplets in a fluidic medium 180 in the microfluidic circuit 120 and thereby select, capture, and/or move individual droplets or groups of droplets.
One example of a microfluidic device 200 comprising a DEP configuration is illustrated in
As seen in
In certain embodiments, the microfluidic device 200 illustrated in
With the power source 212 activated, the foregoing DEP configuration creates an electric field gradient in the fluidic medium 180 between illuminated DEP electrode regions 214a and adjacent dark DEP electrode regions 214, which in turn creates local DEP forces that attract or repel nearby micro-objects (not shown) in the fluidic medium 180. DEP electrodes that attract or repel micro-objects in the fluidic medium 180 can thus be selectively activated and deactivated at many different such DEP electrode regions 214 at the inner surface 208 of the region/chamber 202 by changing light patterns 218 projected from a light source 216 into the microfluidic device 200. Whether the DEP forces attract or repel nearby micro-objects can depend on such parameters as the frequency of the power source 212 and the dielectric properties of the medium 180 and/or micro-objects (not shown).
The square pattern 220 of illuminated DEP electrode regions 214a illustrated in
In some embodiments, the electrode activation substrate 206 can comprise or consist of a photoconductive material. In such embodiments, the inner surface 208 of the electrode activation substrate 206 can be featureless. For example, the electrode activation substrate 206 can comprise or consist of a layer of hydrogenated amorphous silicon (a-Si:H). The a-Si:H can comprise, for example, about 8% to 40% hydrogen (calculated as 100*the number of hydrogen atoms/the total number of hydrogen and silicon atoms). The layer of a-Si:H can have a thickness of about 500 nm to about 2.0 μm. In such embodiments, the DEP electrode regions 214 can be created anywhere and in any pattern on the inner surface 208 of the electrode activation substrate 206, in accordance with the light pattern 218. The number and pattern of the DEP electrode regions 214 thus need not be fixed, but can correspond to the light pattern 218. Examples of microfluidic devices having a DEP configuration comprising a photoconductive layer such as discussed above have been described, for example, in U.S. Pat. No. RE 44,711 (Wu et al.) (originally issued as U.S. Pat. No. 7,612,355), the entire contents of which are incorporated herein by reference.
In other embodiments, the electrode activation substrate 206 can comprise a substrate comprising a plurality of doped layers, electrically insulating layers (or regions), and electrically conductive layers that form semiconductor integrated circuits, such as is known in semiconductor fields. For example, the electrode activation substrate 206 can comprise a plurality of phototransistors, including, for example, lateral bipolar phototransistors, each phototransistor corresponding to a DEP electrode region 214. Alternatively, the electrode activation substrate 206 can comprise electrodes (e.g., conductive metal electrodes) controlled by phototransistor switches, with each such electrode corresponding to a DEP electrode region 214. The electrode activation substrate 206 can include a pattern of such phototransistors or phototransistor-controlled electrodes. The pattern, for example, can be an array of substantially square phototransistors or phototransistor-controlled electrodes arranged in rows and columns, such as shown in
Examples of microfluidic devices having electrode activation substrates that comprise phototransistors have been described, for example, in U.S. Pat. No. 7,956,339 (Ohta et al.) (see, e.g., device 300 illustrated in
In some embodiments of a DEP configured microfluidic device, the top electrode 210 is part of a first wall (or cover 110) of the enclosure 102, and the electrode activation substrate 206 and bottom electrode 204 are part of a second wall (or support structure 104) of the enclosure 102. The region/chamber 202 can be between the first wall and the second wall. In other embodiments, the electrode 210 is part of the second wall (or support structure 104) and one or both of the electrode activation substrate 206 and/or the electrode 210 are part of the first wall (or cover 110). Moreover, the light source 216 can alternatively be used to illuminate the enclosure 102 from below.
With the microfluidic device 200 of
In other embodiments, the microfluidic device 200 can have a DEP configuration that does not rely upon light activation of DEP electrodes at the inner surface 208 of the electrode activation substrate 206. For example, the electrode activation substrate 206 can comprise selectively addressable and energizable electrodes positioned opposite to a surface including at least one electrode (e.g., cover 110). Switches (e.g., transistor switches in a semiconductor substrate) may be selectively opened and closed to activate or inactivate DEP electrodes at DEP electrode regions 214, thereby creating a net DEP force on a micro-object (not shown) in region/chamber 202 in the vicinity of the activated DEP electrodes. Depending on such characteristics as the frequency of the power source 212 and the dielectric properties of the medium (not shown) and/or micro-objects in the region/chamber 202, the DEP force can attract or repel a nearby micro-object. By selectively activating and deactivating a set of DEP electrodes (e.g., at a set of DEP electrodes regions 214 that forms a square pattern 220), one or more micro-objects in region/chamber 202 can be trapped and moved within the region/chamber 202. The motive module 162 in
As yet another example, the microfluidic device 200 can have an electrowetting (EW) configuration, which can be in place of the DEP configuration or can be located in a portion of the microfluidic device 200 that is separate from the portion which has the DEP configuration. The EW configuration can be an opto-electrowetting configuration or an electrowetting on dielectric (EWOD) configuration, both of which are known in the art. In some EW configurations, the support structure 104 has an electrode activation substrate 206 sandwiched between a dielectric layer (not shown) and the bottom electrode 204. The dielectric layer can comprise a hydrophobic material and/or can be coated with a hydrophobic material, as described below. For microfluidic devices 200 that have an EW configuration, the inner surface 208 of the support structure 104 is the inner surface of the dielectric layer or its hydrophobic coating.
The dielectric layer (not shown) can comprise one or more oxide layers, and can have a thickness of about 50 nm to about 250 nm (e.g., about 125 nm to about 175 nm). In certain embodiments, the dielectric layer may comprise a layer of oxide, such as a metal oxide (e.g., aluminum oxide or hafnium oxide). In certain embodiments, the dielectric layer can comprise a dielectric material other than a metal oxide, such as silicon oxide or a nitride. Regardless of the exact composition and thickness, the dielectric layer can have an impedance of about 10 kOhms to about 50 kOhms.
In some embodiments, the surface of the dielectric layer that faces inward toward region/chamber 202 is coated with a hydrophobic material. The hydrophobic material can comprise, for example, fluorinated carbon molecules. Examples of fluorinated carbon molecules include perfluoro-polymers such as polytetrafluoroethylene (e.g., TEFLON®) or poly(2,3-difluoromethylenyl-perfluorotetrahydrofuran) (e.g., CYTOP™). Molecules that make up the hydrophobic material can be covalently bonded to the surface of the dielectric layer. For example, molecules of the hydrophobic material can be covalently bound to the surface of the dielectric layer by means of a linker such as a siloxane group, a phosphonic acid group, or a thiol group. Thus, in some embodiments, the hydrophobic material can comprise alkyl-terminated siloxane, alkyl-termination phosphonic acid, or alkyl-terminated thiol. The alkyl group can be long-chain hydrocarbons (e.g., having a chain of at least 10 carbons, or at least 16, 18, 20, 22, or more carbons). Alternatively, fluorinated (or perfluorinated) carbon chains can be used in place of the alkyl groups. Thus, for example, the hydrophobic material can comprise fluoroalkyl-terminated siloxane, fluoroalkyl-terminated phosphonic acid, or fluoroalkyl-terminated thiol. In some embodiments, the hydrophobic coating has a thickness of about 10 nm to about 50 nm. In other embodiments, the hydrophobic coating has a thickness of less than 10 nm (e.g., less than 5 nm, or about 1.5 to 3.0 nm).
In some embodiments, the cover 110 of a microfluidic device 200 having an electrowetting configuration is coated with a hydrophobic material (not shown) as well. The hydrophobic material can be the same hydrophobic material used to coat the dielectric layer of the support structure 104, and the hydrophobic coating can have a thickness that is substantially the same as the thickness of the hydrophobic coating on the dielectric layer of the support structure 104. Moreover, the cover 110 can comprise an electrode activation substrate 206 sandwiched between a dielectric layer and the top electrode 210, in the manner of the support structure 104. The electrode activation substrate 206 and the dielectric layer of the cover 110 can have the same composition and/or dimensions as the electrode activation substrate 206 and the dielectric layer of the support structure 104. Thus, the microfluidic device 200 can have two electrowetting surfaces.
In some embodiments, the electrode activation substrate 206 can comprise a photoconductive material, such as described above. Accordingly, in certain embodiments, the electrode activation substrate 206 can comprise or consist of a layer of hydrogenated amorphous silicon (a-Si:H). The a-Si:H can comprise, for example, about 8% to 40% hydrogen (calculated as 100*the number of hydrogen atoms/the total number of hydrogen and silicon atoms). The layer of a-Si:H can have a thickness of about 500 nm to about 2.0 μm. Alternatively, the electrode activation substrate 206 can comprise electrodes (e.g., conductive metal electrodes) controlled by phototransistor switches, as described above. Microfluidic devices having an opto-electrowetting configuration are known in the art and/or can be constructed with electrode activation substrates known in the art. For example, U.S. Pat. No. 6,958,132 (Chiou et al.), the entire contents of which are incorporated herein by reference, discloses opto-electrowetting configurations having a photoconductive material such as a-Si:H, while U.S. Patent Publication No. 2014/0124370 (Short et al.), referenced above, discloses electrode activation substrates having electrodes controlled by phototransistor switches.
The microfluidic device 200 thus can have an opto-electrowetting configuration, and light patterns 218 can be used to activate photoconductive EW regions or photoresponsive EW electrodes in the electrode activation substrate 206. Such activated EW regions or EW electrodes of the electrode activation substrate 206 can generate an electrowetting force at the inner surface 208 of the support structure 104 (i.e., the inner surface of the overlaying dielectric layer or its hydrophobic coating). By changing the light patterns 218 (or moving microfluidic device 200 relative to the light source 216) incident on the electrode activation substrate 206, droplets (e.g., containing an aqueous medium, solution, or solvent) contacting the inner surface 208 of the support structure 104 can be moved through an immiscible fluid (e.g., an oil medium) present in the region/chamber 202.
In other embodiments, microfluidic devices 200 can have an EWOD configuration, and the electrode activation substrate 206 can comprise selectively addressable and energizable electrodes that do not rely upon light for activation. The electrode activation substrate 206 thus can include a pattern of such electrowetting (EW) electrodes. The pattern, for example, can be an array of substantially square EW electrodes arranged in rows and columns, such as shown in
Regardless of the configuration of the microfluidic device 200, a power source 212 can be used to provide a potential (e.g., an AC voltage potential) that powers the electrical circuits of the microfluidic device 200. The power source 212 can be the same as, or a component of, the power source 192 referenced in FIG. 1. Power source 212 can be configured to provide an AC voltage and/or current to the top electrode 210 and the bottom electrode 204. For an AC voltage, the power source 212 can provide a frequency range and an average or peak power (e.g., voltage or current) range sufficient to generate net DEP forces (or electrowetting forces) strong enough to trap and move individual micro-objects (not shown) in the region/chamber 202, as discussed above, and/or to change the wetting properties of the inner surface 208 of the support structure 104 (i.e., the dielectric layer and/or the hydrophobic coating on the dielectric layer) in the region/chamber 202, as also discussed above. Such frequency ranges and average or peak power ranges are known in the art. See, e.g., U.S. Pat. No. 6,958,132 (Chiou et al.), U.S. Pat. No. RE44,711 (Wu et al.) (originally issued as U.S. Pat. No. 7,612,355), and US Patent Application Publication Nos. US2014/0124370 (Short et al.), US2015/0306598 (Khandros et al.), and US2015/0306599 (Khandros et al.).
Sequestration Pens.
Non-limiting examples of generic sequestration pens 224, 226, and 228 are shown within the microfluidic device 230 depicted in
The sequestration pens 224, 226, and 228 of
The microfluidic channel 122 can thus be an example of a swept region, and the isolation regions 240 of the sequestration pens 224, 226, 228 can be examples of unswept regions. As noted, the microfluidic channel 122 and sequestration pens 224, 226, 228 can be configured to contain one or more fluidic media 180. In the example shown in
As is known, a flow 242 of fluidic medium 180 in a microfluidic channel 122 past a proximal opening 234 of sequestration pen 224 can cause a secondary flow 244 of the medium 180 into and/or out of the sequestration pen 224. To isolate micro-objects 246 in the isolation region 240 of a sequestration pen 224 from the secondary flow 244, the length Lcon of the connection region 236 of the sequestration pen 224 (i.e., from the proximal opening 234 to the distal opening 238) should be greater than the penetration depth Dp of the secondary flow 244 into the connection region 236. The penetration depth Dp of the secondary flow 244 depends upon the velocity of the fluidic medium 180 flowing in the microfluidic channel 122 and various parameters relating to the configuration of the microfluidic channel 122 and the proximal opening 234 of the connection region 236 to the microfluidic channel 122. For a given microfluidic device, the configurations of the microfluidic channel 122 and the opening 234 will be fixed, whereas the rate of flow 242 of fluidic medium 180 in the microfluidic channel 122 will be variable. Accordingly, for each sequestration pen 224, a maximal velocity Vmax for the flow 242 of fluidic medium 180 in channel 122 can be identified that ensures that the penetration depth Dp of the secondary flow 244 does not exceed the length Lcon of the connection region 236. As long as the rate of the flow 242 of fluidic medium 180 in the microfluidic channel 122 does not exceed the maximum velocity Vmax, the resulting secondary flow 244 can be limited to the microfluidic channel 122 and the connection region 236 and kept out of the isolation region 240. The flow 242 of medium 180 in the microfluidic channel 122 will thus not draw micro-objects 246 out of the isolation region 240. Rather, micro-objects 246 located in the isolation region 240 will stay in the isolation region 240 regardless of the flow 242 of fluidic medium 180 in the microfluidic channel 122.
Moreover, as long as the rate of flow 242 of medium 180 in the microfluidic channel 122 does not exceed Vmax, the flow 242 of fluidic medium 180 in the microfluidic channel 122 will not move miscellaneous particles (e.g., microparticles and/or nanoparticles) from the microfluidic channel 122 into the isolation region 240 of a sequestration pen 224. Having the length Lcon of the connection region 236 be greater than the maximum penetration depth Dp of the secondary flow 244 can thus prevent contamination of one sequestration pen 224 with miscellaneous particles from the microfluidic channel 122 or another sequestration pen (e.g., sequestration pens 226, 228 in
Because the microfluidic channel 122 and the connection regions 236 of the sequestration pens 224, 226, 228 can be affected by the flow 242 of medium 180 in the microfluidic channel 122, the microfluidic channel 122 and connection regions 236 can be deemed swept (or flow) regions of the microfluidic device 230. The isolation regions 240 of the sequestration pens 224, 226, 228, on the other hand, can be deemed unswept (or non-flow) regions. For example, components (not shown) in a first fluidic medium 180 in the microfluidic channel 122 can mix with a second fluidic medium 248 in the isolation region 240 substantially only by diffusion of components of the first medium 180 from the microfluidic channel 122 through the connection region 236 and into the second fluidic medium 248 in the isolation region 240. Similarly, components (not shown) of the second medium 248 in the isolation region 240 can mix with the first medium 180 in the microfluidic channel 122 substantially only by diffusion of components of the second medium 248 from the isolation region 240 through the connection region 236 and into the first medium 180 in the microfluidic channel 122. In some embodiments, the extent of fluidic medium exchange between the isolation region of a sequestration pen and the flow region by diffusion is greater than about 90%, 91%, 92%, 93%, 94% 95%, 96%, 97%, 98%, or greater than about 99% of fluidic exchange. The first medium 180 can be the same medium or a different medium than the second medium 248. Moreover, the first medium 180 and the second medium 248 can start out being the same, then become different (e.g., through conditioning of the second medium 248 by one or more cells in the isolation region 240, or by changing the medium 180 flowing through the microfluidic channel 122).
The maximum penetration depth Dp of the secondary flow 244 caused by the flow 242 of fluidic medium 180 in the microfluidic channel 122 can depend on a number of parameters, as mentioned above. Examples of such parameters include: the shape of the microfluidic channel 122 (e.g., the microfluidic channel can direct medium into the connection region 236, divert medium away from the connection region 236, or direct medium in a direction substantially perpendicular to the proximal opening 234 of the connection region 236 to the microfluidic channel 122); a width Wch (or cross-sectional area) of the microfluidic channel 122 at the proximal opening 234; and a width Wcon (or cross-sectional area) of the connection region 236 at the proximal opening 234; the velocity V of the flow 242 of fluidic medium 180 in the microfluidic channel 122; the viscosity of the first medium 180 and/or the second medium 248, or the like.
In some embodiments, the dimensions of the microfluidic channel 122 and sequestration pens 224, 226, 228 can be oriented as follows with respect to the vector of the flow 242 of fluidic medium 180 in the microfluidic channel 122: the microfluidic channel width Wch (or cross-sectional area of the microfluidic channel 122) can be substantially perpendicular to the flow 242 of medium 180; the width Wcon (or cross-sectional area) of the connection region 236 at opening 234 can be substantially parallel to the flow 242 of medium 180 in the microfluidic channel 122; and/or the length Lcon of the connection region can be substantially perpendicular to the flow 242 of medium 180 in the microfluidic channel 122. The foregoing are examples only, and the relative position of the microfluidic channel 122 and sequestration pens 224, 226, 228 can be in other orientations with respect to each other.
As illustrated in
As illustrated in
The microfluidic device 250 of
Each sequestration pen 266 can comprise an isolation structure 272, an isolation region 270 within the isolation structure 272, and a connection region 268. From a proximal opening 274 at the microfluidic channel 264 to a distal opening 276 at the isolation structure 272, the connection region 268 fluidically connects the microfluidic channel 264 to the isolation region 270. Generally, in accordance with the above discussion of
As illustrated in
As illustrated in
In various embodiments of sequestration pens (e.g. 124, 126, 128, 130, 224, 226, 228, or 266), the isolation region (e.g. 240 or 270) is configured to contain a plurality of micro-objects. In other embodiments, the isolation region can be configured to contain only one, two, three, four, five, or a similar relatively small number of micro-objects. Accordingly, the volume of an isolation region can be, for example, at least 1×106, 2×106, 4×106, 6×106 cubic microns, or more.
In various embodiments of sequestration pens, the width Wch of the microfluidic channel (e.g., 122) at a proximal opening (e.g. 234) can be about 50-1000 microns, 50-500 microns, 50-400 microns, 50-300 microns, 50-250 microns, 50-200 microns, 50-150 microns, 50-100 microns, 70-500 microns, 70-400 microns, 70-300 microns, 70-250 microns, 70-200 microns, 70-150 microns, 90-400 microns, 90-300 microns, 90-250 microns, 90-200 microns, 90-150 microns, 100-300 microns, 100-250 microns, 100-200 microns, 100-150 microns, or 100-120 microns. In some other embodiments, the width Wch of the microfluidic channel (e.g., 122) at a proximal opening (e.g. 234) can be about 200-800 microns, 200-700 microns, or 200-600 microns. The foregoing are examples only, and the width Wch of the microfluidic channel 122 can be any width within any of the endpoints listed above. Moreover, the Wch of the microfluidic channel 122 can be selected to be in any of these widths in regions of the microfluidic channel other than at a proximal opening of a sequestration pen.
In some embodiments, a sequestration pen has a height of about 30 to about 200 microns, or about 50 to about 150 microns. In some embodiments, the sequestration pen has a cross-sectional area of about 1×104-3×106 square microns, 2×104-2×106 square microns, 4×104-1×106 square microns, 2×104-5×105 square microns, 2×104-1×105 square microns or about 2×105-2×106 square microns.
In various embodiments of sequestration pens, the height Ho of the microfluidic channel (e.g., 122) at a proximal opening (e.g., 234) can be a height within any of the following heights: 20-100 microns, 20-90 microns, 20-80 microns, 20-70 microns, 20-60 microns, 20-50 microns, 30-100 microns, 30-90 microns, 30-80 microns, 30-70 microns, 30-60 microns, 30-50 microns, 40-100 microns, 40-90 microns, 40-80 microns, 40-70 microns, 40-60 microns, or 40-50 microns. The foregoing are examples only, and the height Ho of the microfluidic channel (e.g., 122) can be a height within any of the endpoints listed above. The height Hch of the microfluidic channel 122 can be selected to be in any of these heights in regions of the microfluidic channel other than at a proximal opening of a sequestration pen.
In various embodiments of sequestration pens a cross-sectional area of the microfluidic channel e.g., 122) at a proximal opening (e.g., 234) can be about 500-50,000 square microns, 500-40,000 square microns, 500-30,000 square microns, 500-25,000 square microns, 500-20,000 square microns, 500-15,000 square microns, 500-10,000 square microns, 500-7,500 square microns, 500-5,000 square microns, 1,000-25,000 square microns, 1,000-20,000 square microns, 1,000-15,000 square microns, 1,000-10,000 square microns, 1,000-7,500 square microns, 1,000-5,000 square microns, 2,000-20,000 square microns, 2,000-15,000 square microns, 2,000-10,000 square microns, 2,000-7,500 square microns, 2,000-6,000 square microns, 3,000-20,000 square microns, 3,000-15,000 square microns, 3,000-10,000 square microns, 3,000-7,500 square microns, or 3,000 to 6,000 square microns. The foregoing are examples only, and the cross-sectional area of the microfluidic channel (e.g., 122) at a proximal opening (e.g., 234) can be any area within any of the endpoints listed above.
In various embodiments of sequestration pens, the length Lcon of the connection region (e.g., 236) can be about 1-600 microns, 5-550 microns, 10-500 microns, 15-400 microns, 20-300 microns, 20-500 microns, 40-400 microns, 60-300 microns, 80-200 microns, or about 100-150 microns. The foregoing are examples only, and length Lcon of a connection region (e.g., 236) can be in any length within any of the endpoints listed above.
In various embodiments of sequestration pens the width Wcon of a connection region (e.g., 236) at a proximal opening (e.g., 234) can be about 20-500 microns, 20-400 microns, 20-300 microns, 20-200 microns, 20-150 microns, 20-100 microns, 20-80 microns, 20-60 microns, 30-400 microns, 30-300 microns, 30-200 microns, 30-150 microns, 30-100 microns, 30-80 microns, 30-60 microns, 40-300 microns, 40-200 microns, 40-150 microns, 40-100 microns, 40-80 microns, 40-60 microns, 50-250 microns, 50-200 microns, 50-150 microns, 50-100 microns, 50-80 microns, 60-200 microns, 60-150 microns, 60-100 microns, 60-80 microns, 70-150 microns, 70-100 microns, or 80-100 microns. The foregoing are examples only, and the width Wcon of a connection region (e.g., 236) at a proximal opening (e.g., 234) can be different than the foregoing examples (e.g., any value within any of the endpoints listed above).
In various embodiments of sequestration pens, the width Wcon of a connection region (e.g., 236) at a proximal opening (e.g., 234) can be at least as large as the largest dimension of a micro-object (e.g., biological cell which may be a T cell, or B cell) that the sequestration pen is intended for. The foregoing are examples only, and the width Wcon of a connection region (e.g., 236) at a proximal opening (e.g., 234) can be different than the foregoing examples (e.g., a width within any of the endpoints listed above).
In various embodiments of sequestration pens, the width Wcon of a proximal opening of a connection region may be at least as large as the largest dimension of a micro-object (e.g., a biological micro-object such as a cell) that the sequestration pen is intended for. For example, the width Wpr may be about 50 microns, about 60 microns, about 100 microns, about 200 microns, about 300 microns or may be about 50-300 microns, about 50-200 microns, about 50-100 microns, about 75-150 microns, about 75-100 microns, or about 200-300 microns.
In various embodiments of sequestration pens, a ratio of the length Lcon of a connection region (e.g., 236) to a width Wcon of the connection region (e.g., 236) at the proximal opening 234 can be greater than or equal to any of the following ratios: 0.5, 1.0, 1.5, 2.0, 2.5, 3.0, 3.5, 4.0, 4.5, 5.0, 6.0, 7.0, 8.0, 9.0, 10.0, or more. The foregoing are examples only, and the ratio of the length Lcon of a connection region 236 to a width Wcon of the connection region 236 at the proximal opening 234 can be different than the foregoing examples.
In various embodiments of microfluidic devices 100, 200, 23, 250, 280, 290, Vmax can be set around 0.2, 0.5, 0.7, 1.0, 1.3, 1.5, 2.0, 2.5, 3.0, 3.5, 4.0, 4.5, 5.0, 5.5, 6.0, 6.7, 7.0, 7.5, 8.0, 8.5, 9.0, 10, 11, 12, 13, 14, or 15 microliters/sec.
In various embodiments of microfluidic devices having sequestration pens, the volume of an isolation region (e.g., 240) of a sequestration pen can be, for example, at least 5×105, 8×105, 1×106, 2×106, 4×106, 6×106, 8×106, 1×107, 5×107, 1×108, 5×108, or 8×108 cubic microns, or more. In various embodiments of microfluidic devices having sequestration pens, the volume of a sequestration pen may be about 5×105, 6×105, 8×105, 1×106, 2×106, 4×106, 8×106, 1×107, 3×107, 5×107, or about 8×107 cubic microns, or more. In some other embodiments, the volume of a sequestration pen may be about 1 nanoliter to about 50 nanoliters, 2 nanoliters to about 25 nanoliters, 2 nanoliters to about 20 nanoliters, about 2 nanoliters to about 15 nanoliters, or about 2 nanoliters to about 10 nanoliters.
In various embodiment, the microfluidic device has sequestration pens configured as in any of the embodiments discussed herein where the microfluidic device has about 5 to about 10 sequestration pens, about 10 to about 50 sequestration pens, about 100 to about 500 sequestration pens; about 200 to about 1000 sequestration pens, about 500 to about 1500 sequestration pens, about 1000 to about 2000 sequestration pens, about 1000 to about 3500 sequestration pens, about 3000 to about 7000 sequestration pens, about 5000 to about 10,000 sequestration pens, about 9,000 to about 15,000 sequestration pens, or about 12,000 to about 20,000 sequestration pens. The sequestration pens need not all be the same size and may include a variety of configurations (e.g., different widths, different features within the sequestration pen).
As illustrated in
Typically, the electrical signal generation subsystem 304 will include a waveform generator (not shown). The electrical signal generation subsystem 304 can further include an oscilloscope (not shown) and/or a waveform amplification circuit (not shown) configured to amplify a waveform received from the waveform generator. The oscilloscope, if present, can be configured to measure the waveform supplied to the microfluidic device 320 held by the socket 302. In certain embodiments, the oscilloscope measures the waveform at a location proximal to the microfluidic device 320 (and distal to the waveform generator), thus ensuring greater accuracy in measuring the waveform actually applied to the device. Data obtained from the oscilloscope measurement can be, for example, provided as feedback to the waveform generator, and the waveform generator can be configured to adjust its output based on such feedback. An example of a suitable combined waveform generator and oscilloscope is the Red Pitaya™.
In certain embodiments, the nest 300 further comprises a controller 308, such as a microprocessor used to sense and/or control the electrical signal generation subsystem 304. Examples of suitable microprocessors include the Arduino™ microprocessors, such as the Arduino Nano™. The controller 308 may be used to perform functions and analysis or may communicate with an external master controller 154 (shown in
In some embodiments, the nest 300 can comprise an electrical signal generation subsystem 304 comprising a Red Pitaya™ waveform generator/oscilloscope unit (“Red Pitaya unit”) and a waveform amplification circuit that amplifies the waveform generated by the Red Pitaya unit and passes the amplified voltage to the microfluidic device 100. In some embodiments, the Red Pitaya unit is configured to measure the amplified voltage at the microfluidic device 320 and then adjust its own output voltage as needed such that the measured voltage at the microfluidic device 320 is the desired value. In some embodiments, the waveform amplification circuit can have a +6.5V to −6.5V power supply generated by a pair of DC-DC converters mounted on the PCBA 322, resulting in a signal of up to 13 Vpp at the microfluidic device 100.
As illustrated in
In some embodiments, the nest 300 can include a thermal control subsystem 306 with a feedback circuit that is an analog voltage divider circuit (not shown) which includes a resistor (e.g., with resistance 1 kOhm+/−0.1%, temperature coefficient +/−0.02 ppm/C0) and a NTC thermistor (e.g., with nominal resistance 1 kOhm+/−0.01%). In some instances, the thermal control subsystem 306 measures the voltage from the feedback circuit and then uses the calculated temperature value as input to an on-board PID control loop algorithm. Output from the PID control loop algorithm can drive, for example, both a directional and a pulse-width-modulated signal pin on a Pololu™ motor drive (not shown) to actuate the thermoelectric power supply, thereby controlling the Peltier thermoelectric device.
The nest 300 can include a serial port 324 which allows the microprocessor of the controller 308 to communicate with an external master controller 154 via the interface 310 (not shown). In addition, the microprocessor of the controller 308 can communicate (e.g., via a Plink tool (not shown)) with the electrical signal generation subsystem 304 and thermal control subsystem 306. Thus, via the combination of the controller 308, the interface 310, and the serial port 324, the electrical signal generation subsystem 304 and the thermal control subsystem 306 can communicate with the external master controller 154. In this manner, the master controller 154 can, among other things, assist the electrical signal generation subsystem 304 by performing scaling calculations for output voltage adjustments. A Graphical User Interface (GUI) (not shown) provided via a display device 170 coupled to the external master controller 154, can be configured to plot temperature and waveform data obtained from the thermal control subsystem 306 and the electrical signal generation subsystem 304, respectively. Alternatively, or in addition, the GUI can allow for updates to the controller 308, the thermal control subsystem 306, and the electrical signal generation subsystem 304.
As discussed above, system 150 can include an imaging device 194. In some embodiments, the imaging device 194 comprises a light modulating subsystem 330 (See
In certain embodiments, the imaging device 194 further comprises a microscope 350. In such embodiments, the nest 300 and light modulating subsystem 330 can be individually configured to be mounted on the microscope 350. The microscope 350 can be, for example, a standard research-grade light microscope or fluorescence microscope. Thus, the nest 300 can be configured to be mounted on the stage 344 of the microscope 350 and/or the light modulating subsystem 330 can be configured to mount on a port of microscope 350. In other embodiments, the nest 300 and the light modulating subsystem 330 described herein can be integral components of microscope 350.
In certain embodiments, the microscope 350 can further include one or more detectors 348. In some embodiments, the detector 348 is controlled by the imaging module 164. The detector 348 can include an eye piece, a charge-coupled device (CCD), a camera (e.g., a digital camera), or any combination thereof. If at least two detectors 348 are present, one detector can be, for example, a fast-frame-rate camera while the other detector can be a high sensitivity camera. Furthermore, the microscope 350 can include an optical train configured to receive reflected and/or emitted light from the microfluidic device 320 and focus at least a portion of the reflected and/or emitted light on the one or more detectors 348. The optical train of the microscope can also include different tube lenses (not shown) for the different detectors, such that the final magnification on each detector can be different.
In certain embodiments, imaging device 194 is configured to use at least two light sources. For example, a first light source 332 can be used to produce structured light (e.g., via the light modulating subsystem 330) and a second light source 334 can be used to provide unstructured light. The first light source 332 can produce structured light for optically-actuated electrokinesis and/or fluorescent excitation, and the second light source 334 can be used to provide bright field illumination. In these embodiments, the motive module 164 can be used to control the first light source 332 and the imaging module 164 can be used to control the second light source 334. The optical train of the microscope 350 can be configured to (1) receive structured light from the light modulating subsystem 330 and focus the structured light on at least a first region in a microfluidic device, such as an optically-actuated electrokinetic device, when the device is being held by the nest 300, and (2) receive reflected and/or emitted light from the microfluidic device and focus at least a portion of such reflected and/or emitted light onto detector 348. The optical train can be further configured to receive unstructured light from a second light source and focus the unstructured light on at least a second region of the microfluidic device, when the device is held by the nest 300. In certain embodiments, the first and second regions of the microfluidic device can be overlapping regions. For example, the first region can be a subset of the second region. In other embodiments, the second light source 334 may additionally or alternatively include a laser, which may have any suitable wavelength of light. The representation of the optical system shown in
In
In some embodiments, the second light source 334 emits blue light. With an appropriate dichroic filter 346, blue light reflected from the sample plane 342 is able to pass through dichroic filter 346 and reach the detector 348. In contrast, structured light coming from the light modulating subsystem 330 gets reflected from the sample plane 342, but does not pass through the dichroic filter 346. In this example, the dichroic filter 346 is filtering out visible light having a wavelength longer than 495 nm. Such filtering out of the light from the light modulating subsystem 330 would only be complete (as shown) if the light emitted from the light modulating subsystem did not include any wavelengths shorter than 495 nm. In practice, if the light coming from the light modulating subsystem 330 includes wavelengths shorter than 495 nm (e.g., blue wavelengths), then some of the light from the light modulating subsystem would pass through filter 346 to reach the detector 348. In such an embodiment, the filter 346 acts to change the balance between the amount of light that reaches the detector 348 from the first light source 332 and the second light source 334. This can be beneficial if the first light source 332 is significantly stronger than the second light source 334. In other embodiments, the second light source 334 can emit red light, and the dichroic filter 346 can filter out visible light other than red light (e.g., visible light having a wavelength shorter than 650 nm).
Coating solutions and coating agents. Without intending to be limited by theory, maintenance of a biological micro-object (e.g., a biological cell) within a microfluidic device (e.g., a DEP-configured and/or EW-configured microfluidic device) may be facilitated (i.e., the biological micro-object exhibits increased viability, greater expansion and/or greater portability within the microfluidic device) when at least one or more inner surfaces of the microfluidic device have been conditioned or coated so as to present a layer of organic and/or hydrophilic molecules that provides the primary interface between the microfluidic device and biological micro-object(s) maintained therein. In some embodiments, one or more of the inner surfaces of the microfluidic device (e.g. the inner surface of the electrode activation substrate of a DEP-configured microfluidic device, the cover of the microfluidic device, and/or the surfaces of the circuit material) may be treated with or modified by a coating solution and/or coating agent to generate the desired layer of organic and/or hydrophilic molecules.
The coating may be applied before or after introduction of biological micro-object(s), or may be introduced concurrently with the biological micro-object(s). In some embodiments, the biological micro-object(s) may be imported into the microfluidic device in a fluidic medium that includes one or more coating agents. In other embodiments, the inner surface(s) of the microfluidic device (e.g., a DEP-configured microfluidic device) are treated or “primed” with a coating solution comprising a coating agent prior to introduction of the biological micro-object(s) into the microfluidic device.
In some embodiments, at least one surface of the microfluidic device includes a coating material that provides a layer of organic and/or hydrophilic molecules suitable for maintenance and/or expansion of biological micro-object(s) (e.g. provides a conditioned surface as described below). In some embodiments, substantially all the inner surfaces of the microfluidic device include the coating material. The coated inner surface(s) may include the surface of a flow region (e.g., channel), chamber, or sequestration pen, or a combination thereof. In some embodiments, each of a plurality of sequestration pens has at least one inner surface coated with coating materials. In other embodiments, each of a plurality of flow regions or channels has at least one inner surface coated with coating materials. In some embodiments, at least one inner surface of each of a plurality of sequestration pens and each of a plurality of channels is coated with coating materials.
Coating Agent/Solution.
Any convenient coating agent/coating solution can be used, including but not limited to: serum or serum factors, bovine serum albumin (BSA), polymers, detergents, enzymes, and any combination thereof.
Polymer-Based Coating Materials.
The at least one inner surface may include a coating material that comprises a polymer. The polymer may be covalently or non-covalently bound (or may be non-specifically adhered) to the at least one surface. The polymer may have a variety of structural motifs, such as found in block polymers (and copolymers), star polymers (star copolymers), and graft or comb polymers (graft copolymers), all of which may be suitable for the methods disclosed herein.
The polymer may include a polymer including alkylene ether moieties. A wide variety of alkylene ether containing polymers may be suitable for use in the microfluidic devices described herein. One non-limiting exemplary class of alkylene ether containing polymers are amphiphilic nonionic block copolymers which include blocks of polyethylene oxide (PEO) and polypropylene oxide (PPO) subunits in differing ratios and locations within the polymer chain. Pluronic® polymers (BASF) are block copolymers of this type and are known in the art to be suitable for use when in contact with living cells. The polymers may range in average molecular mass Mw from about 2000 Da to about 20 KDa. In some embodiments, the PEO-PPO block copolymer can have a hydrophilic-lipophilic balance (HLB) greater than about 10 (e.g. 12-18). Specific Pluronic® polymers useful for yielding a coated surface include Pluronic® L44, L64, P85, and F127 (including F127NF). Another class of alkylene ether containing polymers is polyethylene glycol (PEG Mw<100,000 Da) or alternatively polyethylene oxide (PEO, Mw>100,000). In some embodiments, a PEG may have an Mw of about 88 Da, 100 Da, 132 Da, 176 Da, 200 Da, 220 Da, 264 Da, 308 Da, 352 Da, 396 Da, 440 Da, 500 Da, 600 Da, 700 Da, 800 Da, 900 Da, 1000 Da, 1500 Da, 2000 Da, 5000 Da, 10,000 Da or 20,000 Da, or may have a Mw that falls within a range defined by any two of the foregoing values.
In other embodiments, the coating material may include a polymer containing carboxylic acid moieties. The carboxylic acid subunit may be an alkyl, alkenyl or aromatic moiety containing subunit. One non-limiting example is polylactic acid (PLA). In other embodiments, the coating material may include a polymer containing phosphate moieties, either at a terminus of the polymer backbone or pendant from the backbone of the polymer. In yet other embodiments, the coating material may include a polymer containing sulfonic acid moieties. The sulfonic acid subunit may be an alkyl, alkenyl or aromatic moiety containing subunit. One non-limiting example is polystyrene sulfonic acid (PSSA) or polyanethole sulfonic acid. In further embodiments, the coating material may include a polymer including amine moieties. The polyamino polymer may include a natural polyamine polymer or a synthetic polyamine polymer. Examples of natural polyamines include spermine, spermidine, and putrescine.
In other embodiments, the coating material may include a polymer containing saccharide moieties. In a non-limiting example, polysaccharides such as xanthan gum or dextran may be suitable to form a material which may reduce or prevent cell sticking in the microfluidic device. For example, a dextran polymer having a size about 3 kDa may be used to provide a coating material for a surface within a microfluidic device.
In other embodiments, the coating material may include a polymer containing nucleotide moieties, i.e. a nucleic acid, which may have ribonucleotide moieties or deoxyribonucleotide moieties, providing a polyelectrolyte surface. The nucleic acid may contain only natural nucleotide moieties or may contain unnatural nucleotide moieties which comprise nucleobase, ribose or phosphate moiety analogs such as 7-deazaadenine, pentose, methyl phosphonate or phosphorothioate moieties without limitation.
In yet other embodiments, the coating material may include a polymer containing amino acid moieties. The polymer containing amino acid moieties may include a natural amino acid containing polymer or an unnatural amino acid containing polymer, either of which may include a peptide, a polypeptide or a protein. In one non-limiting example, the protein may be bovine serum albumin (BSA) and/or serum (or a combination of multiple different sera) comprising albumin and/or one or more other similar proteins as coating agents. The serum can be from any convenient source, including but not limited to fetal calf serum, sheep serum, goat serum, horse serum, and the like. In certain embodiments, BSA in a coating solution is present in a concentration from about 1 mg/mL to about 100 mg/mL, including 5 mg/mL, 10 mg/mL, 20 mg/mL, 30 mg/mL, 40 mg/mL, 50 mg/mL, 60 mg/mL, 70 mg/mL, 80 mg/mL, 90 mg/mL, or more or anywhere in between. In certain embodiments, serum in a coating solution may be present in a concentration of about 20% (v/v) to about 50% v/v, including 25%, 30%, 35%, 40%, 45%, or more or anywhere in between. In some embodiments, BSA may be present as a coating agent in a coating solution at 5 mg/mL, whereas in other embodiments, BSA may be present as a coating agent in a coating solution at 70 mg/mL. In certain embodiments, serum is present as a coating agent in a coating solution at 30%. In some embodiments, an extracellular matrix (ECM) protein may be provided within the coating material for optimized cell adhesion to foster cell growth. A cell matrix protein, which may be included in a coating material, can include, but is not limited to, a collagen, an elastin, an RGD-containing peptide (e.g. a fibronectin), or a laminin. In yet other embodiments, growth factors, cytokines, hormones or other cell signaling species may be provided within the coating material of the microfluidic device.
In some embodiments, the coating material may include a polymer containing more than one of alkylene oxide moieties, carboxylic acid moieties, sulfonic acid moieties, phosphate moieties, saccharide moieties, nucleotide moieties, or amino acid moieties. In other embodiments, the polymer conditioned surface may include a mixture of more than one polymer each having alkylene oxide moieties, carboxylic acid moieties, sulfonic acid moieties, phosphate moieties, saccharide moieties, nucleotide moieties, and/or amino acid moieties, which may be independently or simultaneously incorporated into the coating material.
In addition, in embodiments in which a covalently modified surface is used in conjunction with coating agents, the anions, cations, and/or zwitterions of the covalently modified surface can form ionic bonds with the charged portions of non-covalent coating agents (e.g. proteins in solution) that are present in a fluidic medium (e.g. a coating solution) in the enclosure.
Further details of appropriate coating treatments and modifications may be found at U.S. application Ser. No. 15/135,707, filed on Apr. 22, 2016, and is incorporated by reference in its entirety.
Additional System Components for Maintenance of Viability of Cells within the Sequestration Pens of the Microfluidic Device.
In order to promote growth and/or expansion of cell populations, environmental conditions conducive to maintaining functional cells may be provided by additional components of the system. For example, such additional components can provide nutrients, cell growth signaling species, pH modulation, gas exchange, temperature control, and removal of waste products from cells.
General Materials and Methods.
System and Microfluidic Device:
An OptoSelect chip, a microfluidic (or nanofluidic) device manufactured by Berkeley Lights, Inc. and controlled by an optical instrument which was also manufactured by Berkeley Lights, Inc. The instrument included: a mounting stage for the chip coupled to a temperature controller; a pump and fluid medium conditioning component; and an optical train including a camera and a structured light source suitable for activating phototransistors within the chip. The OptoSelect™ chip included a substrate configured with OptoElectroPositioning (OEP™) technology, which provides a phototransistor-activated OET force. The chip also included a plurality of microfluidic channels, each having a plurality of NanoPen™ chambers (or sequestration pens) fluidically connected thereto. The volume of each sequestration pen was around 1×106 cubic microns.
Priming Solution:
Complete growth medium containing 0.1% Pluronic® F127 ((Life Technologies® Cat # P6866).
Preparation for culturing: The microfluidic device having a modified surface was loaded onto the system and purged with 100% carbon dioxide at 15 psi for 5 min. Immediately following the carbon dioxide purge, the priming solution was perfused through the microfluidic device at 5 microliters/sec for 8 min. Culture medium was then flowed through the microfluidic device at 5 microliters/sec for 5 min.
Priming Regime.
250 microliters of 100% carbon dioxide was flowed in at a rate of 12 microliters/sec. This was followed by 250 microliters of PBS containing 0.1% Pluronic® F27 (Life Technologies® Cat # P6866), flowed in at 12 microliters/sec. The final step of priming included 250 microliters of PBS, flowed in at 12 microliters/sec. Introduction of the culture medium follows.
Perfusion regime.
The perfusion method was either of the following two methods:
1. Perfuse at 0.01 microliters/sec for 2 h; perfuse at 2 microliters/sec for 64 sec; and repeat.
2. Perfuse at 0.02 microliters/sec for 100 sec; stop flow 500 sec; perfuse at 2 microliters/sec for 64 sec; and repeat.
A silicon wafer (780 microns thick, 1 cm by 1 cm) was treated in an oxygen plasma cleaner (Nordson Asymtek) for 5 min, using 100 W power, 240 mTorr pressure and 440 sccm oxygen flow rate. The plasma treated silicon wafer was treated in a vacuum reactor with (11-azidoundecyl) trimethoxy silane (300 microliters) in a foil boat in the bottom of the vacuum reactor in the presence of magnesium sulfate heptahydrate (0.5 g, Acros Cat. #10034-99-8), as a water reactant source in a separate foil boat in the bottom of the vacuum reactor. The chamber was then pumped to 750 mTorr using a vacuum pump and then sealed. The vacuum reactor was placed within an oven heated at 110° C. for 24-48 h. This introduced a modified surface to the wafer, where the modified surface had a structure of Formula I:
After cooling to room temperature and introducing argon to the evacuated chamber, the wafer was removed from the reactor. The wafer was rinsed with acetone, isopropanol, and dried under a stream of nitrogen. Confirmation of introduction of the modified surface was made by ellipsometry and contact angle goniometry.
Alternatively, the silicon wafer was cut to size to fit within the bottom of a flat bottomed wellplate before introducing the functionalized surface of Formula I upon it, and a plurality of the formatted silicon wafers were functionalized at the same time.
The product silicon wafer from Example 1, having a surface of Formula I as described above, was treated with dibenzylcyclooctynyl (DBCO) Streptavidin (SAV), Nanocs, Cat. # SV1-DB-1, where there are 2-7 DBCO for each molecule of SAV) by contacting the silicon wafer with an aqueous solution containing a 2 micromolar solution of the commercially available DBCO-SAV. The reaction was allowed to proceed at room temperature for at least 1 h. The unpatterned silicon wafer having a modified surface of Formula II was then rinsed with 1×PBS.
5 mg of lyophilized SAV (ThermoFisher PN # S888) was dissolved into 1 mL of 1×PBS (Gibco) and 1 mL of 2 mM Na2CO3 (Acros) in 1×PBS. 10 mg of neat DBCO-PEG13-NHS (Compound 2, Click Chemistry Tools PN #1015-10) was dissolved into 0.4 mL of dry DMSO. 16 uL of the DBCO-PEG13-NHS solution was added to the SAV solution and mixed at 400 RPM at 25° C. for 4 h on an Eppendorf ThermoMixer. The labeled SAV (Compound 1) was purified from the DBCO-PEG13-NHS by passing the reaction mixture through Zeba size exclusion chromatography spin columns (ThermoFisher PN #89882), and used without further purification.
The product silicon wafer from Example 1, having a surface of Formula I as described above, was treated with Compound 1 (DBCO linked Streptavidin (SAV), product of Example 3, having a PEG 13 linker, where there are 2-7 DBCO for each molecule of SAV) by contacting the silicon wafer with an aqueous solution containing 2 micromolar Compound 1. The reaction was allowed to proceed at room temperature for at least 1 h. The unpatterned silicon wafer having a streptavidin covalently functionalized surface including a PEG 13 linker was then rinsed with 1×PBS.
Comparison of the SAV modified surfaces was made by ellipsometry and contact angle goniometry after each step of introduction of reactive azide moieties (Example 1); introduction of respective SAV layers; followed by introduction of biotinylated anti-CD28, where the concentrations of reagents and reaction conditions were the same. Sample 2, using the DBCO SAV reagent having a linker including a PEG13 moiety, clearly provided a more robust functionalization of SAV than that of Sample 1, and subsequently, more robust functionalization by biotinylated anti-CD2 binding to the SAV binding sites.
Without being bound by theory, it was shown that a linker having a length of at least 5 PEG repeat units up to about 20 PEG repeat units (alternatively, a linker having a length from about 20 Angstroms to about 100 Angstroms) may provide superior levels of coupling to the reactive moieties on this reactive surface of the silicon wafer. This is further demonstrated by the additional thickness of the layer of anti-CD28 introduced in Sample Wafer 2, as more SAV binding sites were available.
Indium tin oxide (ITO) wafers were fabricated to have a patterned plurality of regions of amorphous silicon upon the ITO. The regions were a.) 1 micron diameter round amorphous silicon regions separated by three microns from each other or b.) 2 micron square amorphous silicon regions separated by 2 microns from each other.
The patterned wafers were cleaned prior to functionalization by sonication for 10 minutes in acetone, rinsed with deionized water, and dried (Step 1 of
A Schematic Representation of the Functionalization Process is Shown in
The indium tin oxide base layer of the wafer was functionalized by reaction with 40 mM undecynyl phosphonic acid (Sikemia Catalog # SIK7110-10) in 50% N-methylpyrrolidine (NMP)/water solution (Step 2 of
A. Biotinylation of the ITO Region of the Patterned Surface.
The alkyne functionalized ITO region was further covalently modified by reaction with 1.5 mM biotin linked to an azido reactive moiety (azide-S-S-biotin, Broadpharm Catalog # BP-2877), 0.5 mM sodium ascorbate; and 1 mM Cu(II)SO4/THPTA in water (Step 3 of
B. Covalent Modification of the Surfaces of the Plurality of Amorphous Silicon Regions of the Patterned Wafer.
The patterned wafers having biotinylated surface within the ITO region of the wafer was treated in a vacuum reactor with (11-azidoundecyl) trimethoxy silane (Compound 3, 300 microliters) in a foil boat in the bottom of the vacuum reactor in the presence of magnesium sulfate heptahydrate (0.5 g, Acros Cat. #10034-99-8), as a water reactant source in a separate foil boat in the bottom of the vacuum reactor (Step 4 of
After cooling to room temperature and introducing argon to the evacuated chamber, the wafer was removed from the reactor. The wafer was rinsed with acetone, isopropanol, and dried under a stream of nitrogen. Metrology showed that the biotinylated ITO region of the patterned wafer did not have substantial amounts of contamination of the functionalizing ligands of Formula I; 10% or less contaminant was found.
C. Covalent Modification of the Biotin-Modified ITO Region of the Patterned Wafer to Provide Supportive Moieties.
The patterned wafers having a plurality of undecyl azido modified amorphous silicon regions separated by a biotin modified ITO region was reacted with a solution of streptavidin (SAV, 3.84 micromolar) in PBS containing 0.02% sodium azide and allowed to incubate for 30 min (Step 5 of
The streptavidin modified surface of the ITO region of the patterned wafers is then modified by reaction with a 200 micromolar solution of biotin-RGD (Anaspec Catalog # AS-62347) in PBS containing 0.02% sodium azide, thereby providing adhesive moieties for general improvement in viability of the T lymphocytes when cultured upon these surfaces (Step 6 of
Further Generalization.
The streptavidin modified surface of the ITO region of the patterned wafers may alternatively be modified by reaction with a 200 micromolar solution of biotin-PEG-5K (Jenkem Catalog # M-BIOTIN-5000) to provide hydrophilic moieties within this non-activating region of the patterned surface. Further the streptavidin surface may be modified by a mixture of the adhesive and hydrophilic moieties by reacting the streptavidin surface with a mixture of 200 micromolar stock solutions of the biotinylated moieties, in any ratio, e.g., 1:1: 1:10; 10:1 or any ration therebetween.
D.
Providing a secondary functionalized surface to the plurality of azido functionalized amorphous silicon regions of the patterned wafers. A solution of DBCO-SAV (Nanocs Catalog # SV1-DB-1, 2 micromolar) in PBS containing 0.02% sodium azide was contacted with the patterned wafer having a plurality of azido-functionalized amorphous silicon regions separated by a region of ITO having supportive moieties (e.g., adhesive motifs such as RGD, or hydrophilic moieties such as PEG-5K) covalently attached thereupon, for an incubation period of 30 min, providing a plurality of amorphous regions having a streptavidin functionalized surface separated by the region of supportively modified ITO surface (Step 7 of
E.
Functionalization of streptavidin modified surfaces of the amorphous silicon regions of the patterned wafer (Step 8 of
The product patterned wafer of Example 6 was sized for placement within the bottom of a well of a 48-well plate. Two different patterned surfaces were used, the first having circular regions having a diameter of 1 micron, such as shown in
After the first period of stimulation is complete, the resultant T cells are restimulated for Days 7-14, and optionally for Days 14-21 within the same well of the well plate, adding the cytokine additions as above. Alternatively, on Day 7 and/or Day 14, the resultant T lymphocytes may be moved to a new well having a fresh patterned wafer, and the protocol of Example 12 continued. At the end of the desired repetitions of stimulation, a portion of the cells may be stained and examined by flow cytometry to determine the extent of activation. It is expected that the patterned surface wafers stimulate T cell activation as readily as bead-based activation or activation by antigen presenting Dendritic cells.
A microfluidic device (Berkeley Lights, Inc.) as described in the general experimental section above, having a first silicon electrode activation substrate and a second ITO substrate on the opposite wall, and photopatterned silicone microfluidic circuit material separating the two substrates, was treated in an oxygen plasma cleaner (Nordson Asymtek) for 1 min, using 100 W power, 240 mTorr pressure and 440 sccm oxygen flow rate. The plasma treated microfluidic device was treated in a vacuum reactor with 3-azidoundecyl) trimethoxy silane (300 microliters) in a foil boat in the bottom of the vacuum reactor in the presence of magnesium sulfate heptahydrate (0.5 g, Acros), as a water reactant source in a separate foil boat in the bottom of the vacuum reactor. The chamber was then pumped to 750 mTorr using a vacuum pump and then sealed. The vacuum reactor was placed within an oven heated at 110° C. for 24-48 h. This introduced a modified surface to the microfluidic device, where the modified surface had a structure of Formula I:
After cooling to room temperature and introducing argon to the evacuated chamber, the microfluidic device was removed from the reactor. The microfluidic device having the functionalized surface was rinsed with at least 250 microliters of deionized water, and was ready for further use.
A.
The internal surfaces of an OptoSelect microfluidic device were covalently modified to include azido moieties as in Example 8 (Formula I). To functionalize the surface with streptavidin, the OptoSelect microfluidic device is first flushed repeatedly with 100% carbon dioxide, and then loaded with DBCO-streptavidin solution having a concentration from about 0.5 to about 2 micromolar, as produced in Example 4. After incubation for 15-30 minutes, during which the DBCO and azide groups coupled, the OptoSelect microfluidic device is washed repeatedly with 1×PBS to flush unbound DBCO-modified streptavidin.
This streptavidin surface is then further modified with biotinylated pMHC, and a selection of biotinylated anti CD28, biotinylated anti CD2 or any combination thereof. These molecules are suspended in PBS with 2% Bovine Serum Albumin at concentrations of about 1-10 micrograms/mL, in a ratio of pMHC molecules to antiCD28/antiCD2 from about 2:1 to about 1:2. This solution is perfused through the OptoSelect microfluidic device having streptavidin functionalized surfaces, facilitating conjugation to the surface. After one hour of incubation, the OptoSelect microfluidic device is flushed with PBS or media prior to loading cells.
B.
Alternatively, biomolecules of interest are conjugated via biotin modification of the biomolecules to streptavidin prior to reaction with the azido-modified surfaces of the OptoSelect microfluidic device. DBCO-streptavidin and biotinylated biomolecule are prepared separately in PBS solution at concentrations in the range of 0.5-2 micromolar, then mixed at any desired ratio, as described below. After allowing the biotinylated biomolecules to conjugate to the streptavidin for at least 15 minutes, this complex is used to modify the surface of an azido-modified OptoSelect microfluidic device as described above.
Cells may be imported into the microfluidic device having at least one antigen-presenting inner surface and activated during periods of culturing similarly as described for activation of T cells with antigen-presenting beads of Example 19.
10A. Silica Beads Having Covalent PEG 3 Disulfide Biotin Linked to Streptavidin
Spherical silica beads (2.5 micron, G biosciences Catalog #786-915, having a substantially simple spherical volume, e.g. the surface area of the bead is within the range predicted by the relationship 4πr2+/−no more than 10%) were dispersed in isopropanol, and then dried. The dried beads were treated in an oxygen plasma cleaner (Nordson Asymtek) for 5 min, using 100 W power, 240 mTorr pressure and 440 sccm oxygen flow rate. The cleaned beads were treated in a vacuum reactor with (11-azidoundecyl) trimethoxy silane (300 microliters) in a foil boat in the bottom of the vacuum reactor in the presence of magnesium sulfate heptahydrate (0.5 g, Acros Cat. #10034-99-8), as a water reactant source in a separate foil boat in the bottom of the vacuum reactor. The chamber was then pumped to 750 mTorr using a vacuum pump and then sealed. The vacuum reactor was placed within an oven heated at 110° C. for 24-48 h. This introduced a covalently modified surface to the beads, where the modified surface had an azide functionalized structure of Formula I:
After cooling to room temperature and introducing argon to the evacuated chamber, the covalently modified beads were removed from the reactor. The beads having a covalently modified surface functionalized with azide reactive moieties were rinsed with acetone, isopropanol, and dried under a stream of nitrogen. The covalently modified azide functionalized beads were dispersed at a concentration of 1 mg/20 microliters in a 5.7 mM DMSO solution of dibenzylcyclooctynyl (DBCO)S-S biotin modified-PEG3 (Broadpharm, Cat. # BP-22453) then incubated at 90° C./2000 RPM in a thermomixer for 18 hours. The biotin modified beads were washed three times each in excess DMSO, then rinsed with PBS. The biotin modified beads in PBS were dispersed in PBS solution containing approximately 30 micromoles/700 microliter concentration streptavidin. The reaction mixture was shaken at 30° C./2000 RPM in a thermomixer for 30 minutes. At the completion of the reaction period, the covalently modified beads presenting streptavidin were washed three times in excess PBS. FTIR analysis determined that SAV was added to the surface (Data not shown). The disulfide containing linker may be particularly useful if cleavage from the surface may be desirable. The disulfide linker is susceptible to cleavage with dithiothreitol at concentrations that were found to be compatible with T lymphocyte viability (Data not shown).
10B. Silica Beads Having Covalent PEG4 Biotin Linked to Streptavidin Diluted with PEG5-Carboxylic Acid Surface-Blocking Molecular Ligands.
Beads having a covalently modified surface functionalized with azide reactive moieties of Formula 1, prepared as above in Example 10A, were rinsed with acetone, isopropanol, and dried under a stream of nitrogen. The covalently modified azide functionalized beads were dispersed at a concentration of 1 mg/10 microliters in a DMSO solution of 0.6 mM dibenzylcyclooctynyl (DBCO)-modified-PEG4-biotin (Broadpharm, Cat. # BP-22295), 5.4 mM dibenzylcyclooctynyl (DBCO)-modified-PEG5-carboxylic acid (Broadpharm, Cat. # BP-22449), and 100 mM sodium iodide then incubated at 30° C./1,000 RPM in a thermomixer for 18 hours. The biotin modified beads were washed three times each in excess DMSO, then rinsed with PBS. The biotin modified beads in PBS were dispersed in PBS solution containing approximately 10 nanomoles/1 milliliter concentration streptavidin. The reaction mixture was shaken at 30° C./1000 RPM in a thermomixer for 30 minutes. At the completion of the reaction period, the covalently modified beads presenting streptavidin were washed three times in excess PBS. FTIR analysis determined that SAV was added to the surface (Data not shown).
Streptavidin functionalized (covalently coupled) convoluted spherical polymeric beads (e.g., the actual surface area of the bead is greater than the relationship surface area=4πr2+/−no more than 10%, DynaBeads™ (ThermoFisher Catalog #11205D, bead stock at 6.67e8/mL)) were delivered (15 microliters; 1e7 beads) to a 1.5 mL microcentrifuge tube with 1 mL of Wash Buffer (DPBS (No Magnesium+2, No Calcium+2, 244 mL); EDTA (1 ml, final concentration 2 mM); and BSA (5 ml of 5%, final concentration 0.1%), and separated using a magnetic DynaBead rack. The wash/separation with 1 mL of the Wash Buffer was repeated, and a further 200 microliters of Wash Buffer was added with subsequent pulse centrifugation. Supernatant Wash Buffer was removed.
Wash Buffer (600 microliters) containing 1.5 micrograms biotinylated Monomer MHC (HLA-A*02:01 MART-1 (MBL International Corp., Catalog No. MR01008, ELAGIGILTV) was dispensed into the microcentrifuge tube, and the beads were resuspended by pipetting up and down. The monomer was allowed to bind for 30 min at 4° C. After 15 minutes, the mixture was pipetted up and down again. The tube was pulse centrifuged and the supernatant liquid removed, and the tube was placed within the magnetic rack to remove more supernatant without removing beads.
A solution of biotinylated anti-CD28 (Miltenyi Biotec, Catalog #130-100-144, 22.5 microliters) in 600 microliters Wash Buffer was added to the microcentrifuge tube. The beads were resuspended by pipetting up and down. The beads were incubated at 4° C. for 30 min, resuspending after 15 min with another up and down pipetting. At the end of the incubation period, the tube was briefly pulse centrifuged. After placing back into the magnetic rack, and allowing separation for 1 min, the Buffer solution was aspirated away from the functionalized beads. The MHC monomer/anti-CD28 antigen presenting beads were resuspended in 100 microliters Buffer Wash, stored at 4° C., and used without further manipulation. The 1e7 2.80 micron diameter functionalized DynaBeads have a nominal (ideal predicted surface area of a sphere) surface area of about 24e6 square microns available for contact with T lymphocyte cells. However, the convolutions of this class of polymeric bead which are not necessarily accessible by T lymphocyte cells, are also functionalized in this method. Total ligand count may not reflect what is available to contact and activate T lymphocyte cells.
The MHC monomer/anti-CD28 antigen presenting beads were characterized by staining with Alexa Fluor 488-conjugated Rabbit anti Mouse IgG (H+L) Cross-adsorbed secondary antibody (Invitrogen Catalog # A-11059) and APC-conjugated anti-HLA-A2 antibody (Biolegend Catalog #343307), and characterized by flow cytometry.
Cells: CD8+ T lymphocytes were enriched in a medium including RPMI plus 10% fetal bovine serum (FBS) from commercially available PBMCs following manufacturers directions for EasySep™ Human CD8 Positive Selection Kit II, commercially available kit from StemCell Technologies Canada Inc. (Catalog #17953), by negative selection.
Dendritic cells: were generated from autologous PBMCs. Autologous PBMCs (10-50 e6) were thawed into 10 mL of pre-warmed RPMI media including 10% FBS. Cells were pelleted by centrifuging for 5 mins at 400×g. Cells were resuspended in RPMI and counted.
The cells were enriched for monocytes using negative bead isolation (EasySep™ Human Monocyte Isolation Kit, StemCell Technologies, Catalog #19359), according to manufacturers instructions. The resulting monocytes were counted, providing about a 5% yield, and then plated at 1.5-3 e6 cells per 3 mL per well in AIM-V® Medium (ThermoFisher Catalog #12055091) containing 17 ng/mL IL-4 and 53 ng/mL Human Granulocyte Macrophage Colony-Stimulating Fact (GM-CSF, ThermoFisher Catalog # PHC2013)). The cells were incubated for a total of 6 days at 37° C. At Day 2 and Day 4, 100 microliters of feeding media (AIM-V® Medium plus IL-4 (167 U/mL) and GM-CSF (540 ng/mL)) was added to each well, and incubation was continued.
On Day 6, 0.5 mL of a maturation cocktail was added to each well. The maturation cocktail included 10 ng/mL TNF-alpha; 2 ng/mL IL-1B; 1000 U/mL IL-6, 1000 ng/mL PGE2; 167 U/mL IL-4 and 267 U/mL GM-CSF in AIM-V® Medium. The cells were incubated for a further 24 h at 37° C. Mature DCs were then collected from the maturation medium, counted, and prepared for further use. The DCs were characterized by staining for CD3 (BD Catalog #344828), DC-SIGN (CD209, Biolegend Catalog #330104), CD14 (Biolegend Catalog #325608), CD86 (BD Catalog #560359), Fc Block (BioLegend Catalog #422302), and viability (BD Catalog #565388); suspended in FACS buffer; and examined by FACS flow cytometry.
Dendritic cells presenting antigen were prepared by plating at a concentration of 2e6/mL in 1% HSA, and pulsing with antigen (MART1 peptide, Anaspec, custom synthesis, 40 micrograms/mL) and beta2-microglobulin (Sigma Aldrich Catalog # M4890, 3 micrograms/mL), and then culturing with agitation for 4 h. The pulsed DCs were irradiated in a Faxitron CellRad® x-ray cell irradiator for 30 min before use, with a target dose of 50 greys.
Culture medium and diluent for reagent additions: Advanced RPMI (ThermoFisher Catalog #12633020, 500 mL); 1× GlutaMAX (ThermoFisher Catalog #35050079, 5 mL); 10% Human AB serum (zen-bio, Catalog # HSER-ABP 100 mL, 50 mL); and 50 nM beta-mercaptoethanol (ThermoFisher Catalog #31350010, 50 nm stock, 0.5 mL, final conc 50 micromolar).
Experimental Setup: For each activating species, a single 96-well tissue-culture treated plate (VWR Catalog #10062-902) was used (wellplate 1 (DCs); wellplate 2 (Antigen presenting beads)). CD8+ T lymphocytes (2e5) (80-90% pure) were added to each individual well.
Pulsed DCs were added at 5e3 for each well in wellplate 1, yield a 1:40 ratio of DCs: CD8+ T lymphocytes.
Antigen presenting surface polymeric beads (2e5), prepared as in Example 11, presenting pMHC including MART1 and anti-CD28 antibody, were added to each of the wells in wellplate 2. pMHC was loaded at 1.5 micrograms/1e7 beads. Anti-CD 28 antibody was loaded on the beads at three different levels: 0.25 micrograms/1e7 beads; 0.75 micrograms/1e7 beads; and 2.25 micrograms/1e7 beads.
Each wellplate was cultured at 37° C. On day 0, IL-21 (150 ng/milliliter) in CTL media, was added to each well of wellplates 1 and 2, providing a final concentration in each well of 30 ng/mL. On day 2, IL21 was added to each well of the wellplates, to a final concentration of 30 ng/mL. Culturing was continued to day 7.
Day 7. A subset of wells from each wellplate was individually stained for MHC tetramer (Tetramer PE, MBL Catalog # T02000, 1 microliter/well), CD4 (Biolegend Catalog #300530, 0.5 microliters/well); CD8 (Biolegend Catalog #301048, 0.5 microliters/well); CD28 (Biolegend Catalog #302906, 0.31 microliters/well); CD45RO (Biolegend Catalog #304210, 0.63 microliters/well); CCR7 (CD197, Biolegend Catalog #353208, 0.5 microliters/well); and viability (BD Catalog #565388, 0.125 microliters/well). Each well was resuspended with 150 microliters FACS buffer and 10 microliters of Countbright™ beads (ThermoFisher Catalog # C36950). FACS analysis was performed on a FACSCelesta™ flow cytometer (BD Biosciences).
Day 7. Restimulation. A second aliquot of pulsed DCs or antigen presenting beads, respectively, was delivered to each occupied well in wellplate 1 and wellplate 2. IL21 was added to each well of the wellplate to a final concentration of 30 ng/mL. Culturing was continued.
Day 8. Addition of 50 microliters of IL-2 (50 IU/mL) and IL-7 (25 ng/mL) was made to each well in wellplate 1 and wellplate 2 to provide a final concentration of 10 IU/mL and 5 ng/mL respectively. Culturing was continued.
Day 9. Addition of 50 microliters of IL-21(150 ng/mL) was made to each occupied well of wellplate 1 and wellplate 2 to a final concentration of 30 ng/mL. Culturing was continued.
Day 14. A second subset of wells from each wellplate was individually stained and FACS sorted as described for the analysis on Day 7. The flow cytometry results are shown in
Third Period of Culturing.
In another experiment, where antigen presenting surfaces on beads were used as described in the immediately preceding paragraphs, but where comparison was not made with DCs, a third period of stimulation and culturing was performed. Day 14 to Day 21. Restimulation and feeding was performed as above for Day 7-Day 14, during continuation of culture conditions until Day 21. On Day 21, a last subset of wells from each wellplate was individually stained and FACS sorted as described for the analysis on Day 7. Additional activation was observed for the extended third stimulation sequence (Data not shown).
Silica beads (2.5 micron, G biosciences Catalog #786-915, having a substantially simple spherical surface, e.g. the surface area of the bead is within the range predicted by the relationship 4πr2+/−no more than 10%) were dispersed in isopropanol, and then dried. The dried beads were treated in an oxygen plasma cleaner (Nordson Asymtek) for 5 min, using 100 W power, 240 mTorr pressure and 440 sccm oxygen flow rate. The cleaned beads were treated in a vacuum reactor with (11-azidoundecyl) trimethoxy silane (300 microliters) in a foil boat in the bottom of the vacuum reactor in the presence of magnesium sulfate heptahydrate (0.5 g, Acros Cat. #10034-99-8), as a water reactant source in a separate foil boat in the bottom of the vacuum reactor. The chamber was then pumped to 750 mTorr using a vacuum pump and then sealed. The vacuum reactor was placed within an oven heated at 110° C. for 24-48 h. This introduced a covalently linked surface presenting reactive azide moieties to the beads, where the modified surface has a structure of Formula I.
After cooling to room temperature and introducing argon to the evacuated chamber, the intermediate reactive azide presenting beads were removed from the reactor and were rinsed with acetone, isopropanol, and dried under a stream of nitrogen. The azide presenting reactive beads (50 mg) were dispersed in 500 microliters DMSO with vigorous vortexing/brief sonication. The beads were pelleted, and 450 microliters of the DMSO were aspirated away from the beads. The pellet, in the remaining 50 microliters DMSO was vortexed vigorously to disperse. DBCO-SAV (52 microliters of 10 micromolar concentration, Compound 1) as synthesized in Example 3, having a PEG13 linker, was added. The beads were dispersed by tip mixing, followed by vortexing. 398 microliters of PBS with 0.02% sodium azide solution was added, followed by additional vortexing. The reaction mixture was incubated overnight on a thermomixer at 30° C., 1000 RPM.
After 16 hrs, 10 microliters of 83.7 mM DBCO-PEG5-acid were added to each sample and they were incubated an additional 30 minutes at 30° C./1,000 RPM. The beads were washed 3X in PBS/azide, then suspended in 500 microliters of the same.
These covalently functionalized beads are modified to introduce primary activating molecules and co-activating molecules as described below in Example 18.
Divinylbenzene-crosslinked polystyrene beads (14-20 micron, Cospheric Catalog #786-915) were dispersed in isopropanol, and then dried in a glass petri dish. The dried beads were treated in an oxygen plasma cleaner (Nordson Asymtek) for 40 seconds, using 100 W power, 240 mTorr pressure and 440 sccm oxygen flow rate. The cleaned beads were treated in a vacuum oven with (11-azidoundecyl) trimethoxy silane (Compound 5, 900 microliters) in a foil boat on the shelf of the oven in the presence of magnesium sulfate heptahydrate (1 g, Acros Cat. #10034-99-8), as a water reactant source in a separate foil boat on the same shelf of the oven. The oven was then pumped to 250 mTorr using a vacuum pump and then sealed. The oven was heated at 110° C. for 18-24 h. This introduced a covalently modified surface to the beads, where the modified surface had a structure of Formula I:
After pump-purging the oven three times, the covalently modified beads were removed from the oven and cooled. The covalently modified azide functionalized beads were dispersed at a concentration 15 mg/50 microliters in DMSO. To this, a 450 microliter solution of DBCO-labeled streptavidin (SAV) (Compound 1) at a concentration of 9.9 micromolar were added. The solution was then incubated at 30° C./1000 RPM in a thermomixer for 18 hours. The SAV modified beads were washed three times in PBS. FTIR analysis determined that SAV was added to the surface as shown in
Streptavidin functionalized (covalently coupled) DynaBeads™ (ThermoFisher Catalog #11205D), bead stock at 6.67e8/mL, convoluted (as described above) polymeric beads) were delivered (15 microliters; 1e7 beads) to 1.5 mL microcentrifuges tube with 1 mL of Wash Buffer (DPBS (No Magnesium+2, No Calcium+2, 244 mL); EDTA (1 ml, final concentration 2 mM); and BSA (5 ml of 5%, final concentration 0.1%), and separated using a magnetic DynaBead rack. The wash/separation with 1 mL of the Wash Buffer was repeated, and a further 200 microliters of Wash Buffer was added with subsequent pulse centrifugation. Supernatant Wash Buffer was removed.
Wash Buffer (600 microliters) containing 0.5 micrograms biotinylated Monomer MHC (HLA-A*02:01 MART-1 (MBL International Corp., Catalog No. MR01008, ELAGIGILTV) was dispensed into the microcentrifuge tubes, and the beads were resuspended by pipetting up and down. The monomer was allowed to bind for 30 min at 4° C. After 15 minutes, the mixtures were pipetted up and down again. The tubes were pulse-centrifuged and the supernatant liquid removed, and the tubes were placed within the magnetic rack to remove more supernatant without removing beads.
Solutions of biotinylated anti-CD28 (Biolegend, Catalog #302904) and biotinylated anti-CD2 (Biolegend, Catalog #300204) in 600 microliters Wash Buffer were added to the microcentrifuge tubes. Solutions contained a total of 3 micrograms of antibody. The solutions contained: 3 micrograms of anti-CD28 and 0 micrograms of anti-CD2, 2.25 micrograms of anti-CD28 and 0.75 micrograms of anti-CD2, 1.5 micrograms of anti-CD28 and 1.5 micrograms of anti-CD2, 0.75 micrograms of anti-CD28 and 2.25 micrograms of anti-CD2, or 0 micrograms of anti-CD28 and 3 micrograms of anti-CD2. The beads were resuspended by pipetting up and down. The beads were incubated at 4° C. for 30 min, then resuspended after 15 min with another up and down pipetting. At the end of the incubation period, the tube was briefly pulse centrifuged. After placing back into the magnetic rack, and allowing separation for 1 min, the Buffer solution was aspirated away from the functionalized beads. The MHC monomer/anti CD28 antigen presenting beads were resuspended in 100 microliters Buffer Wash, stored at 4° C., and used without further manipulation. The 1e7 2.80 micron diameter functionalized DynaBeads have a nominal surface area of about 24e6 square microns available for contact with T lymphocyte cells, but as described above, these convoluted spherical beads have a practical surface area of more than 10% above that of the nominal surface area.
In the first step of the manufacturing process, M-450 Epoxy-functionalized paramagnetic convoluted polymeric beads (DynaBeads™, ThermoFisher Cat. #14011 (convoluted having the same meaning as above)) were reacted with Tetrabutylammonium Azide to prepare polymeric beads presenting azide reactive moieties capable of reacting with functionalizing reagents having Click chemistry compatible reactive groups.
The azide-prepared convoluted beads from Example 16 were then reacted with dibenzocyclooctynyl (DBCO)-coupled Streptavidin to attach Streptavidin covalently to the polymeric beads. The DBCO-Streptavidin reagent was generated by reacting Streptavidin with amine-reactive DBCO-polyethylene glycol (PEG)13-NHS Ester, providing more than one attachment site per Streptavidin unit.
Further Reaction with Surface-Blocking Molecules.
The resulting covalently functionalized polymeric beads presenting streptavidin functionalities from Example 17 may subsequently be treated with DBCO functionalized surface-blocking molecules to react with any remaining azide reactive moieties on the polymeric bead. In some instances, the DBCO functionalized surface-blocking molecule may include a PEG molecule. In some instances, the DBCO PEG molecule may be a DBCO PEG5-carboxylic acid. Streptavidin functionalized polymeric beads including additional PEG or PEG-carboxylic acid surface-blocking molecules provide superior physical behavior, demonstrating improved dispersal in aqueous environment. Additionally, the surface-blocking of remaining azide moieties prevents other unrelated/undesired components present in this or following preparation steps or activation steps from also covalently binding to the polymeric bead. Finally, introduction of the surface-blocking molecular ligands can prevent surface molecules present on the T lymphocytes from contacting reactive azide functionalities.
Further Generalization.
It may be desirable to modify the azide functionalized surface of Example 16 with a mixture of DBCO containing ligand molecules. For example, DBCO-polyethylene glycol (PEG)13-streptavidin (Compound 1, prepared as in Example 3) may be mixed with DBCO-PEG5-COOH (surface-blocking molecules) in various ratios, and then placed in contact with the azide functionalized beads. In some instances, the ratio of DBCO-streptavidin molecules to DBCO-PEG5-COOH may be about 1:9; about 1:6, about 1:4 or about 1:3. Without wishing to be bound by theory, surface-blocking molecular ligands prevent excessive loading of streptavidin molecules to the surface of the bead, and further provide enhanced physico-chemical behavior by providing additional hydrophilicity. The surface-blocking molecules are not limited to PEG5-COOH but may be any suitable surface-blocking molecule described herein.
Materials: A. Antigen Bearing Major Histocompatibility Complex (MHC) I Molecule.
Biotinylated peptide-Human Leukocyte Antigen complexes (pMHC), were commercially available from MBL, Immunitrack or Biolegend. The biotinylated peptide-HLA complex included an antigenic peptide non-covalently bound to the peptide-binding groove of a Class I HLA molecule, which was produced and folded into the HLA complex at the manufacturer. The biotinylated peptide-HLA complex was also non-covalently bound to Beta2-Microglobulin. This complex was covalently biotinylated at the side chain amine of a lysine residue introduced by the BirA enzyme at a recognized location on the C-terminal peptide sequence of the HLA, also performed by the manufacturer.
B. Co-Activating Molecules
Biotinylated antibodies were used for costimulation and were produced from the supernatants of murine hybridoma cultures. The antibodies were conjugated to biotin through multiple amine functionalities of the side chains of lysines, randomly available at the surfaces of the antibodies. The biotinylated antibodies were commercially available (Biolegend, Miltenyi, or Thermo Fisher).
Biotinylated anti-CD28 useful in these experiments were produced from clone CD28.2, 15e8, or 9.3.
Biotinylated anti-CD2 useful in these experiments were produced from clone LT2 or RPA-2.10. Other clones may also be used in construction of covalently modified antigen presenting synthetic surfaces such as these polymeric beads.
Conjugation of the Primary Activating and Co-Activating Molecules to a Covalently Functionalized Surface of a Bead.
The MHC molecule (containing the antigenic molecule) and the co-activating molecules were conjugated to beads produced in a two-step process. In various experiments, the ratio of the co-activating molecules—in this case, biotinylated anti-CD28 and biotinylated anti-CD2—may be varied in a range from about 100:1 to about 1:100; or from about 20:1 to about 1:20. In other experiments, the ratio of the co-activating molecules was from about 3:1 to about 1:3 or about 1:1. See
Pmhc Loading.
Streptavidin functionalized (covalently coupled) DynaBeads™ (ThermoFisher Catalog #11205D), bead stock at 6.67e8/mL, convoluted (as described above) polymeric beads) were washed with Wash Buffer (Dulbecco's Phosphate-Buffered Saline without Calcium or Magnesium; 0.1% Bovine Serum Albumin; 2 mM Ethylenediaminetetraacetic Acid). Wash buffer was pipetted into a tube, to which the Streptavidin beads were added. Typically, ˜1e7 beads were pipetted into 1 mL of Wash Buffer. The beads were collected against the wall of the tube using a magnet (e.g., DYNAL DynaMag-2, ThermoFisher Cat. #12-321-D). After the beads migrated to the wall of the tube, the Wash Buffer was removed via aspiration, avoiding the wall to which the beads were held. This wash process was repeated twice more. After the third wash, the beads were resuspended at 1.67e7 beads/mL in Wash Buffer.
The beads were then mixed with pMHC. The pMHC was added to the beads in Wash Buffer at a final concentration of 0.83 micrograms of pMHC/mL. The beads and pMHC were thoroughly mixed by vortexing, then incubated at 4° C. for 15 minutes. The beads were again vortexed, then incubated at 4° C. for an additional 15 minutes.
Co-Activating Molecule Loading.
The pMHC-functionalized beads were again captured via magnet, and the pMHC reagent mixture removed by aspiration. The beads were then brought to 1.67e7/mL in Wash Buffer. Biotinylated Anti-CD28 and biotinylated anti-CD2 (if used) were then added to the beads at a final concentration of 5 micrograms/mL of total antibody. If both anti-CD28 and anti-CD2 were used, then each antibody was added at 2.5 micrograms/mL.
The beads and pMHC were thoroughly mixed by vortexing, then incubated at 4° C. for 15 minutes. The beads are again vortexed, then incubated at 4° C. for an additional 15 minutes.
After modification by the biotinylated antibodies, the beads were captured via magnet, and the antibody mixture was removed by aspiration. The beads were resuspended in Wash Buffer at a final density of 1e8 beads/mL. The beads were used directly, without further washing.
Characterization.
To assess the degree of loading and homogeneity of the resulting antigen-presenting beads, the beads were stained with antibodies that bind the pMHC and co-activating CD28/CD2 (if present) antibodies on the beads. The resulting amount of staining antibody was then quantified by flow cytometry. The number of pMHC and costimulatory antibodies on the beads was then determined using a molecular quantification kit (Quantum Simply Cellular, Bangs Labs) according to the manufacturer's instructions.
To analyze the beads, 2e5 beads were added to each of two microcentrifuge tubes with 1 mL of Wash Buffer. The pMHC quantification, and costimulation antibody quantification were performed in separate tubes. In each separate experiment, the beads were collected against the wall of the tube using a magnet, and the Wash Buffer removed. The beads were resuspended in the respective tubes in 0.1 mL of Wash Buffer, and each tube was briefly vortexed to separate the beads from the wall of the tube. To detect pMHC, 0.5 microliters of anti-HLA-A conjugated to APC (Clone BB7.2, Biolegend) was added to the first tube. The first tube was again vortexed briefly to mix the beads and detection antibody. To detect the costimulation antibodies, 0.5 microliters of anti-mouse IgG conjugated to APC was added to the second tube. Depending on the costimulation antibody clones used, different anti-mouse antibodies were used, e.g., RMG1-1 (Biolegend) is used to detect CD28.2 (anti-CD28) and RPA-2.10 (anti-CD2). The detection antibodies were incubated with the beads for 30 minutes in the dark at room temperature for each tube.
For each tube, the beads were then captured against the wall of the tube via magnet, and the staining solution was removed by aspiration. 1 mL of Wash Buffer was added to each tube, then aspirated to remove any residual staining antibody. The beads in each tube were resuspended in 0.2 mL of Wash Buffer and then the beads from each tube was transferred to a 5 mL Polystyrene tube, keeping the two sets of beads separate.
To quantify the loading of the different species, the beads were analyzed on a flow cytometer (FACS Aria or FACS Celesta, BD Biosciences). First, a sample of unstained product antigen-bearing beads is collected. A gate is drawn around the singlet and doublet beads. Doublet beads are discriminated from singlet beads based on their higher forward and side scatter amplitudes. Typically, approximately 10,000 bead events were recorded. The beads stained for pMHC and costimulation antibodies are then analyzed in separate experiments. Again, approximately 10,000 bead events were collected for each sample, and the APC median fluorescence intensity (MFI) and coefficient of variation of the APC MFI (100*[Standard Deviation of the MFI]/[MFI]) of the singlet bead events was recorded.
To determine the number of pMHC and costimulation antibodies per bead, a molecular quantification kit is used. The kit (Quantum Simply Cellular (Bangs Laboratories) included a set of beads with specified antibody binding capacities (determined by the manufacturer). These beads are used to capture the detection antibody. Briefly, the quantification beads are incubated with saturating amounts of the detection binding, then washed thoroughly to remove excess antibody. The beads with different binding capacities are mixed, along with negative control beads and resuspended in Wash Buffer. The mixed beads are then analyzed by Flow Cytometry. The APC MFI of each bead with specified binding capacity is recorded, and a linear fit of the MFI vs binding capacity is generated. The MFI of the aAPCs is then used to determine the number of detection antibodies bound per aAPC. This number is equal to the number of (pMHC or costimulation) antibodies on the bead. The following table shows results for:
A. Antigen-presenting convoluted polymeric beads produced in Examples 16-17 and functionalized above in this experiment.
B. Antigen-presenting substantially spherical silica beads as produced in Example 10B
Input Cell Populations.
To increase the number of antigen-specific, CD8+ T cells plated per well, CD8+ T cells were first isolated from Peripheral Blood Mononuclear Cells using commercially available reagents. The cells can be isolated using negative selection, e.g., EasySep™ Human CD8+ T Cell Isolation Kit (StemCell Technologies) or by positive selection, e.g., CliniMACS CD8 Reagent (Miltenyi Biotec). The CD8+ T cells were isolated according to the manufacturers recommended protocol. Alternatively, different subsets of T cells can be isolated, e.g., Naïve CD8+ T cells only, or a less-stringent purification can be performed, e.g., depletion of Monocytes by CliniMACS CD14 Reagent (Miltenyi Biotec). Alternatively, if T cells specific for a Class II-restricted antigen are desired, CD4+ T cells can be isolated by corresponding methods.
First T Cell Stimulation Period.
The enriched CD8+ T cells were resuspended at 1e6/mL in media with IL-21 at 30 nanograms/mL (R&D Systems). The media used for T cells was Advanced RPMI 1640 Medium (Thermo Fisher) supplemented with 10% Human AB Serum (Corning CellGro) plus GlutaMax (Thermo Fisher) and 50 micromolar Beta-MercaptoEthanol (Thermo Fisher) or ImmunoCult™-XF T Cell Expansion Medium (StemCell Technologies).
Antigen-presenting beads were prepared as described in Example 18, where the convoluted polymeric beads were loaded at a final concentration of 0.83 micrograms of pMHC/mL. The resulting lot of beads was split into five portions, loading the costimulating ligands in the following proportions:
Set 1: CD28 at 3.00 micrograms/mL and CD2 at zero concentration.
Set 2: CD28 at 2.25 micrograms/mL and CD2 at 0.75 micrograms/mL.
Set 3: CD28 at 1.50 micrograms/mL and CD2 at 2.25 micrograms/mL.
Set 4: CD28 at 0.75 micrograms/mL and CD2 at 2.25 micrograms/mL.
Set 5: CD28 at 0.00 micrograms/mL and CD2 at 3.00 micrograms/mL.
To the T cells in media, an aliquot of each set of antigen-presenting beads were added to separate wells to a final concentration of 1 antigen-presenting bead per cell. The cells and antigen-presenting beads were mixed and seeded into tissue culture-treated, round-bottom, 96-well microplates. 0.2 mL (2e5 cells) was added to each well of the plate, which was then placed in a standard 5% 002, 37° C. incubator. Typically, 48-96 wells were used per plate. Two days later, IL-21 was diluted to 150 nanograms/mL in media. 50 microliters of IL-21 diluted in media was added to each well, and the plate was returned to the incubator.
After culturing the cells for an additional 5 days (seven days total), the cells were analyzed for antigen-specific T cell expansion. Alternatively, the cells were-stimulated in a second stimulation period as described in the following paragraphs to continue expanding antigen specific T cells.
Second T Cell Stimulation Period.
From each well of the above well plate at the conclusion of the first stimulation period, 50 microliters of media were removed, being careful not to disturb the cell pellet at the bottom of the well. IL-21 was diluted to 150 ng/mL in fresh media, and the antigen-presenting beads as produced above were added to the IL-21/media mixture at a final density of 4e6 antigen-presenting beads/mL. 50 microliters of this IL-21/antigen-presenting bead/media mixture was added to each well, resulting in an additional 2e5 antigen-presenting beads being added to each well. Optionally, the wellplate can be centrifuged for 5 minutes at 400×g to pellet the antigen-presenting beads onto the cells. The wellplate was returned to the incubator.
The next day (8 days from start of stimulation experiments), the wellplate was removed from the incubator, and 50 microliters of media was removed from each well. IL-2 (R&D Systems) was diluted into fresh media to 50 Units/mL. To this, media containing IL-2, IL-7 (R&D Systems) was added to a final concentration of 25 ng/mL. 50 microliters of this IL-2/IL-7/media mixture was added to each well, and the wellplate was returned to the incubator.
The following day (9 days from start of stimulation experiments), the wellplate was removed from the incubator, and 50 microliters of media was again removed from each well. IL-21 was diluted into fresh media to 150 nanograms/mL. 50 microliters of this IL-21/media mixture was added to each well, and the wellplate was returned to the incubator.
After culturing the cells for an additional 5 days (14 days from the start of stimulation experiments), the cells were typically analyzed for antigen-specific T cell expansion. However, the cells can be re-stimulated with more antigen-presenting beads for another period of culturing as above to continue expanding antigen specific T cells.
Analysis of Antigen-Specific T Cell Stimulation and Expansion.
Once the desired number of T cell stimulations were performed, the cells were analyzed for expansion of T cells specific for the pMHC complex used to prepare the antigen-presenting beads. Antigen-specific T cells are detected using Phycoerythrin (PE) conjugated Streptavidin, which is bound to 4 pMHC complexes. These complexes are referred to as tetramers. Typically, a tetramer manufactured with the same peptide used in the pMHC of the antigen-presenting beads was used to detect the antigen-specific T cells.
To detect and characterize the antigen-specific T cells, a mixture of PE-tetramer (MBL, Intl) and antibodies specific for various cell surface markers with various fluorophores, e.g., FITC-conjugated anti-CD28, PerCP-Cy5.5-conjugated anti-CD8, was prepared in FACS Buffer (Dulbecco's Phosphate-Buffered Saline without Calcium or Magnesium; 2% Fetal Bovine Serum; 5 mM Ethylenediaminetetraacetic Acid, 10 mM HEPES). The amount of antibody used was determined by titration against standard cell samples. The surface markers typically used for characterization used are: CD4, CD8, CD28, CD45RO, CD127 and CD197. Additionally, a Live/Dead cell discrimination dye, e.g., Zombie Near-IR (Biolegend) and Fc Receptor blocking reagent, e.g., Human TruStain FcX™ (Biolegend) were added to distinguish live cells and prevent non-specific antibody staining of any Fc-Receptor expressing cells in the culture, respectively.
Typically, the wells were mixed using a multi-channel micro-pipettor, and 50 microliters of cells from each well were transferred to a fresh, non-treated, round-bottom, 96-well microplate. The cells were washed by addition of 0.2 mL of FACS buffer to each well. Cells were centrifuged at 400×g for 5 minutes at room temperature, and the wash removed. To each well, 25 microliters of the Tetramer, Antibody, Live/Dead, Fc blocking reagent mixture was added. The cells were stained for 30 minutes under foil at room temperature. The cells were then washed again, and finally resuspended in FACS Buffer with CountBright Absolute Counting Beads (Thermo Fisher). The cells were then analyzed by Flow Cytometry (FACS Aria or FACS Celesta, BD Biosciences). The frequency of antigen-specific T cells was determined by gating first on Single/Live cells, then gating on CD8+/Tetramer+ cells. Appropriate gating conditions were determined from control stains, such as a negative control Tetramer with no known specificity (MBL, Intl) or antibody isotype controls. Within the antigen-specific T cell population, the frequency of CD45RO+/CD28High cells was determined, as well as the number of cells expressing CD127. Activated T cells, which express CD45RO, that continue to express high levels of CD28 and CD127 have been shown to include memory precursor effector cells. Memory precursor cells have been shown to be less differentiated and have higher replicative potential than activated T cells that do not express these markers.
It was observed that production of antigen specific T cells was possible with a wide range of proportions of the costimulatory ligands anti-CD28 and anti-CD2. Production was possible using only one of the two costimulatory ligands. However, a combination of anti-CD28 and anti-CD2, including at ratios of anti-CD28:anti-CD2 from about 3:1 to about 1:3, provided increased measurements of each of the above characteristics.
Cytotoxicity:
Killing of target tumor cells and non-target tumor cells by SLC45A2-specific T cells expanded using Dendritic cells pulsed with SLC45A2 antigen (DCs, Black bars) or antigen-presenting beads (presenting SLC45A2 antigen) produced as described above (gray hatched bars). See
20A. Preparation of an antigen presenting surface of a bead with lysine-biotinylated CD80 and CD58
Streptavidin functionalized (covalently coupled, convoluted (as described above) polymeric) DynaBeads™ (ThermoFisher Catalog #11205D, bead stock at 6.67e8/mL) were delivered (15 microliters; 1e7 beads) to 1.5 mL microcentrifuges tube with 1 mL of Wash Buffer (DPBS (No Magnesium+2, No Calcium+2, 244 mL); EDTA (1 ml, final concentration 2 mM); and BSA (5 ml of 5%, final concentration 0.1%), and separated using a magnetic DynaBead rack. The wash/separation with 1 mL of the Wash Buffer was repeated, and a further 200 microliters of Wash Buffer was added with subsequent pulse centrifugation. Supernatant Wash Buffer was removed.
Wash Buffer (600 microliters) containing 0.5 micrograms biotinylated Monomer MHC (HLA-A*02:01 SLC45A2 (Biolegend, Custom Product, SLYSYFQKV) was dispensed into the microcentrifuge tubes, and the beads were resuspended by pipetting up and down. The monomer was allowed to bind for 30 min at 4° C. After 15 minutes, the mixtures were pipetted up and down again. The tubes were pulse centrifuged and the supernatant liquid removed, and the tubes were placed within the magnetic rack to remove more supernatant without removing beads.
A solution of biotinylated recombinant CD80 protein (R&D Systems, Custom Product) and biotinylated recombinant CD58 (R&D Systems, Custom Product) in 600 microliters Wash Buffer was added to the microcentrifuge tubes. The CD80 was prepared as an N-terminal fusion to a human IgG1 Fc domain and biotinylated on random Lysine residues by the manufacturer. The CD58 was biotinylated in the same manner. The solution contained a total of 4.5 micrograms of CD80 and 1.5 micrograms of CD58. The beads were resuspended by pipetting up and down. The beads were incubated at 4 C for 30 min, resuspending after 15 min with another up and down pipetting. At the end of the incubation period, the tube was briefly pulse centrifuged. After placing back into the magnetic rack, and allowing separation for 1 min, the Buffer solution was aspirated away from the functionalized beads. The MHC monomer/CD80/CD58 antigen presenting beads were resuspended in 100 microliters Wash Buffer, stored at 4° C., and used without further manipulation. The 1e7 2.80 micron diameter functionalized DynaBeads have a nominal surface area of about 24e6 square microns available for contact with T lymphocyte cells, which, as described herein, does not reflect the total surface occupied by pMHC and costimulatory molecular ligands.
20B. Preparation of an Antigen Presenting Surface of a Bead with BirA Biotinylated CD80 and CD58
Streptavidin functionalized (covalently coupled, convoluted (as described above) polymeric) DynaBeads™ (ThermoFisher Catalog #11205D, bead stock at 6.67e8/mL) were delivered (15 microliters; 1e7 beads) to 1.5 mL microcentrifuges tube with 1 mL of Wash Buffer (DPBS (No Magnesium+2, No Calcium+2, 244 mL); EDTA (1 ml, final concentration 2 mM); and BSA (5 ml of 5%, final concentration 0.1%), and separated using a magnetic DynaBead rack. The wash/separation with 1 mL of the Wash Buffer was repeated, and a further 200 microliters of Wash Buffer was added with subsequent pulse centrifugation. Supernatant Wash Buffer was removed.
Wash Buffer (600 microliters) containing 0.5 micrograms biotinylated Monomer MHC (HLA-A*02:01 MART1 (Biolegend, Custom Product, ELAGIGILTV) was dispensed into the microcentrifuge tubes, and the beads were resuspended by pipetting up and down. The monomer was allowed to bind for 30 min at 4° C. After 15 minutes, the mixtures were pipetted up and down again. The tubes were pulse centrifuged and the supernatant liquid removed, and the tubes were placed within the magnetic rack to remove more supernatant without removing beads.
A solution of biotinylated recombinant CD80 protein (BPS Biosciences, Catalog Number 71114) and biotinylated recombinant CD58 (BPS Biosciences, Catalog Number 71269) in 600 microliters Wash Buffer was added to the microcentrifuge tubes. The recombinant proteins were prepared as N-terminal fusions to a human IgG1 Fc domain, with a final C-terminal BirA biotinylation site, and biotinylated by the manufacturer. The solution contained a total of 1.5 micrograms of recombinant CD80 and 1.5 micrograms of recombinant CD58 proteins. The beads were resuspended by pipetting up and down. The beads were incubated at 4° C. for 30 min, then resuspended after 15 min with another up and down pipetting. At the end of the incubation period, the tube was briefly pulse centrifuged. After placing back into the magnetic rack, and allowing separation for 1 min, the Buffer solution was aspirated away from the functionalized beads. The MHC monomer/CD80/CD58 antigen presenting beads were resuspended in 100 microliters Wash Buffer, stored at 4° C., and used without further manipulation. The 1e7 2.80 micron diameter functionalized DynaBeads have a nominal surface area of about 24e6 square microns available for contact with T lymphocyte cells, which, as described herein, does not reflect the total surface occupied by pMHC and costimulatory molecular ligands.
Cells: CD8+ T lymphocytes were enriched in a medium including RPMI plus 10% fetal bovine serum (FBS) from commercially available PBMCs following manufacturer's directions for EasySep™ Human CD8+ T Cell Isolation Kit, commercially available kit from StemCell Technologies Canada Inc. (Catalog #17953), by negative selection.
Culture medium and diluent for reagent additions: Advanced RPMI (ThermoFisher Catalog #12633020, 500 mL); lx GlutaMAX (ThermoFisher Catalog #35050079, 5 mL); 10% Human AB serum (zen-bio, Catalog # HSER-ABP 100 mL, 50 mL); and 50 nM beta-mercaptoethanol (ThermoFisher Catalog #31350010, 50 nm stock, 0.5 mL, final conc 50 micromolar).
Experimental Setup: For each activating species, a single 96-well tissue-culture treated plate (VWR Catalog #10062-902) was used:
Wellplate 1. Antigen presenting beads with antibody costimulation).
Wellplate 2. Antigen presenting beads with random biotinylated recombinant protein co-activation.
Wellplate 3. Antigen presenting beads with BirA biotinylated recombinant protein co-activation.
CD8+ T lymphocytes (2e5) (80-90% pure) were added to each individual well.
Antigen presenting surface beads (2e5), prepared by a similar preparation as described in Example 15, presenting pMHC including MART1, anti-CD28 antibody and anti-CD2 antibody, were added to each of the wells in wellplate 1. pMHC was loaded at 0.5 micrograms/1e7 beads. Anti-CD28 antibody was loaded at 1.5 micrograms/1e7 beads. Anti-CD2 antibody was loaded at 1.5 micrograms/1e7 beads.
Antigen presenting surface beads (2e5), prepared as in Example 20A, presenting pMHC including MART1, recombinant CD80 and recombinant CD58, were added to each of the wells in wellplate 2. pMHC was loaded at 0.5 micrograms/1e7 beads. Recombinant CD80 was loaded at 4.5 micrograms/1e7 beads. Recombinant CD58 was loaded at 1.5 micrograms/1e7 beads.
Antigen presenting surface beads (2e5), prepared as in Example 20B, presenting pMHC including MART1, BirA biotinylated recombinant CD80 and recombinant CD58, were added to each of the wells in wellplate 3. pMHC was loaded at 0.5 micrograms/1e7 beads. Recombinant CD80 was loaded at 1.5 micrograms/1e7 beads. Recombinant CD58 was loaded at 1.5 micrograms/1e7 beads.
Each wellplate was cultured at 37° C. On day 0, IL-21 (150 ng/milliliter) in CTL media, was added to each well of wellplates 1 and 2, providing a final concentration in each well of 30 ng/mL. On day 2, IL21 was added to each well of the wellplates, to a final concentration of 30 ng/mL. Culturing was continued to day 7.
Day 7. Restimulation. A second aliquot of antigen presenting beads with antibody costimulation or recombinant protein costimulation was delivered to each occupied well in wellplate 1, wellplate 2 and wellplate 3, respectively. IL21 was added to each well of the wellplate to a final concentration of 30 ng/mL. Culturing was continued.
Day 8. Addition of 50 microliters of IL-2 (50 IU/mL) and IL-7 (25 ng/mL) was made to each well in each wellplate to provide a final concentration of 10 IU/mL and 5 ng/mL respectively. Culturing was continued.
Day 9. Addition of 50 microliters of IL-21(150 ng/mL) was made to each occupied well of each well plate to a final concentration of 30 ng/mL. Culturing was continued.
Day 14. The wells from each wellplate were individually stained for MHC tetramer (Tetramer PE, MBL Catalog # T02000, 1 microliter/well), CD4 (Biolegend Catalog #300530, 0.5 microliters/well); CD8 (Biolegend Catalog #301048, 0.5 microliters/well); CD28(Biolegend Catalog #302906, 0.31 microliters/well); CD45RO (Biolegend Catalog #304210, 0.63 microliters/well); CCR7 (CD197, Biolegend Catalog #353208, 0.5 microliters/well); and viability (BD Catalog #565388, 0.125 microliters/well). Resuspend each well with 150 microliters FACS buffer and 10 microliters of Countbright™ beads (ThermoFisher Catalog # C36950). FACS analysis was performed on a FACSCelesta™ flow cytometer (BD Biosciences).
Amounts of pMHC and costimulation antibodies that could be deposited onto Polymer and
Silica beads was measured.
Streptavidin functionalized (covalently coupled) DynaBeads™ (ThermoFisher Catalog #11205D, bead stock at 6.67e8/mL) were delivered (15 microliters; 1e7 beads) to 1.5 mL microcentrifuges tube with 1 mL of Wash Buffer (DPBS (No Magnesium+2, No Calcium+2, 244 mL); EDTA (1 ml, final concentration 2 mM); and BSA (5 ml of 5%, final concentration 0.1%), and separated using a magnetic DynaBead rack. The wash/separation with 1 mL of the Wash Buffer was repeated, and a further 200 microliters of Wash Buffer was added with subsequent pulse centrifugation. Supernatant Wash Buffer was removed.
Biotin functionalized (covalently coupled) smooth silica beads were first coated with Streptavidin by storage in 100 micromolar Streptavidin. Approximately 5e6 beads were washed by dilution into 1 milliliter of Wash Buffer in a microcentrifuge tube, followed by centrifugation at 1,000×g for 1 minute. The supernatant was carefully removed by aspiration, and the wash process repeated twice more. Supernatant Wash Buffer was removed.
To prepare antigen presenting beads, Wash Buffer (600 microliters) containing 0.5 micrograms biotinylated Monomer MHC (HLA-A*02:01 SLC45A2 (Biolegend, Custom Product, SLYSYFQKV) was dispensed into the tubes with the DynaBeads and Silica beads, and the beads were resuspended by pipetting up and down. The monomer was allowed to bind for 30 min at 4° C. After 15 minutes, the mixtures were pipetted up and down again. The tubes were centrifuged at 1,000×g for one minute, and the supernatant liquid removed.
Wash Buffer (600 microliters) with 1.5 micrograms of biotinylated anti-CD28 and 1.5 micrograms of biotinylated anti-CD2 was used to resuspend each bead sample, and the beads were resuspended by pipetting up and down. The antibodies were allowed to bind for 30 min at 4 C. After 15 minutes, the mixtures were pipetted up and down again. The tubes were centrifuged at 1,000×g for one minute, and the supernatant liquid removed. Finally, the beads were resuspended in 100 microliters of Wash Buffer.
Two samples of approximately 2e5 Polymer antigen presenting beads or 1e5 Silica antigen presenting beads were washed with Wash Buffer (1 milliliter). The bead samples were resuspended in 100 microliters of Wash Buffer and stained by addition of 1 microliter of APC-conjugated anti-HLA-A (Biolegend, Catalog Number 343308) or 1 microliter of APC-conjugated monoclonal anti-Mouse-IgG1 (Biolegend, Catalog Number 406610). The beads were mixed with the antibody and allowed to stain for 30 minutes in the dark. After staining, beads were washed, resuspended in Wash Buffer (200 microliters) and transferred to tubes for analysis by Flow Cytometry.
A set of Quantum Simply Cellular fluorescence quantitation beads (Bangs Labs, Catalog Number 815) was then prepared to determine the number of anti-HLA-A antibodies and anti-Mouse IgG1 antibodies bound to each antigen presenting bead sample. The quantitation beads have antibody binding capacities determined by the manufacturer. A drop of each bead with pre-determined binding capacity was placed in microcentrifuge tubes with 50 microliters of Wash Buffer. To the tubes, 5 microliters of APC-conjugated anti-HLA-A or APC-conjugated anti-Mouse IgG1 was added and mixed by vortexing. The beads were stained for 30 minutes in the dark, washed using the same method as above. The beads with different binding capacities were then pooled into one sample and transferred to a single tube. A drop of blank beads (no antibody binding capacity) was added and the beads were analyzed by Flow Cytometry.
The quantitation beads were analyzed by Flow Cytometry (BD FACSCelesta, Becton Dickinson and Company) by recording 5,000 events. The quantitation beads were identified by Forward Scatter and Side Scatter, and the median intensity in the APC channel of each bead recorded. This data was recorded in a proprietary Excel spreadsheet provided by the manufacturer (Bangs) that calculates a standard curve of APC intensity versus antibody binding capacity. After verifying that the calibration was linear, the antigen presenting bead samples were analyzed. The beads were identified by Forward and Side Scatter, and the median intensity in the APC channel recorded on the spreadsheet. The spreadsheet calculates the number of APC anti-HLA-A antibodies or APC anti-Mouse IgG1 on each antigen presenting bead. Assuming that 1 anti-HLA-A antibody binds to one pMHC on the antigen presenting bead, this value represents the number of pMHC molecules on each bead. Similarly, the number of costimulation antibodies can be determined.
From the nominal surface area of each antigen presenting bead, the density (number of molecules/square micron of bead surface) of each species can be determined. The total number of pMHC on the Silica microspheres was determined to be approximately 800,000 pMHC/antigen presenting bead. The total number of costimulation antibodies was determined to be about 850,000 antibodies/bead. As there is no way to distinguish the anti-CD28 and anti-CD2 clones used to prepare the antigen presenting beads (they are the same isotype), it is assumed that the ratio of the two antibodies is 1:1. Due to the regularity of the Silica bead surfaces, the surface area can be reasonably modeled from a sphere. For a 4.08 micron diameter microsphere, this corresponds to a surface area of about 52.3 square microns. From this, it can be estimated that about 15,000 pMHC and 15,000 costimulation antibodies per square micron of bead surface are presented by the Silica antigen presenting beads as shown in Table 1. The distribution across each bead population for each ligand class is shown in
For Polymer beads, the convoluted surface makes the relationship between bead diameter and surface area less straightforward. From the quantitation, it was determined that Polymer antigen presenting beads based on M-280 DynaBeads had about 480,000 pMHC molecules and 425,000 costimulation antibodies on their surface. For a sphere of radius 1.4 microns (equal to the nominal radius of M-280 DynaBeads, this corresponds to about 20,000 pMHC and 17,000 costimulation antibodies per square micron, as shown in Table 1. However, due to the convoluted surface of the Polymer beads, the actual surface area is likely larger, and thus the actual density lower. From
Antigen presenting beads were prepared in the same manner using M-450 Epoxy DynaBeads modified with Streptavidin. From flow cytometry, antigen presenting beads prepared from M-450 beads had approximately the same number of pMHC and costimulation antibody molecules as antigen presenting beads prepared with M-280 DynaBeads. As the M-450 DynaBeads are larger than the M-280 beads, this implies that the density of the activating species on the M-450 antigen presenting beads was about 2-3 times lower than on M-280 antigen presenting beads. However, as can be seen from
Expansion of antigen-specific T cells using Silica antigen presenting beads was tested and compared to convoluted polymeric beads (polystyrene).
Streptavidin functionalized (covalently coupled, convoluted) DynaBeads™ (ThermoFisher Catalog #11205D, bead stock at 6.67e8/mL) were delivered (15 microliters; 1e7 beads) to 1.5 mL microcentrifuges tube with 1 mL of Wash Buffer (DPBS (No Magnesium+2, No Calcium+2, 244 mL); EDTA (1 ml, final concentration 2 mM); and BSA (5 ml of 5%, final concentration 0.1%), and separated using a magnetic DynaBead rack. The wash/separation with 1 mL of the Wash Buffer was repeated, and a further 200 microliters of Wash Buffer was added with subsequent pulse centrifugation. Supernatant Wash Buffer was removed.
Biotin functionalized (covalently coupled) smooth silica beads, prepared as in Example 10B, were first coated with Streptavidin by storage in 100 micromolar Streptavidin. Approximately 5e6 beads were washed by dilution into 1 milliliter of Wash Buffer in a microcentrifuge tube, followed by centrifugation at 1,000×g for 1 minute. The supernatant was carefully removed by aspiration, and the wash process repeated twice more. Supernatant Wash Buffer was removed.
To prepare antigen presenting beads, Wash Buffer (600 microliters) containing 0.5 micrograms biotinylated Monomer MHC (HLA-A*02:01 SLC45A2 (Biolegend, Custom Product, SLYSYFQKV) was dispensed into the tubes with the DynaBeads and Silica beads, and the beads were resuspended by pipetting up and down. The monomer was allowed to bind for 30 min at 4° C. After 15 minutes, the mixtures were pipetted up and down again. The tubes were centrifuged at 1,000×g for one minute, and the supernatant liquid removed.
Wash Buffer (600 microliters) with 1.5 micrograms of biotinylated anti-CD28 and 1.5 micrograms of biotinylated anti-CD2 was used to resuspend each bead sample, and the beads were resuspended by pipetting up and down. The antibodies were allowed to bind for 30 min at 4° C. After 15 minutes, the mixtures were pipetted up and down again. The tubes were centrifuged at 1,000×g for one minute, and the supernatant liquid removed. Finally, the beads were resuspended in 100 microliters of Wash Buffer.
Cells: CD8+ T lymphocytes were enriched in a medium including RPMI plus 10% fetal bovine serum (FBS) from commercially available PBMCs following manufacturer's directions for EasySep™ Human CD8+ T Cell Isolation Kit, commercially available kit from StemCell Technologies Canada Inc. (Catalog #17953), by negative selection.
Culture medium and diluent for reagent additions: Advanced RPMI (ThermoFisher Catalog #12633020, 500 mL); lx GlutaMAX (ThermoFisher Catalog #35050079, 5 mL); 10% Human AB serum (zen-bio, Catalog # HSER-ABP 100 mL, 50 mL); and 50 nM beta-mercaptoethanol (ThermoFisher Catalog #31350010, 50 nm stock, 0.5 mL, final conc 50 micromolar).
Experimental Setup: For each type of antigen presenting bead (Silica or Polymer, as prepared above in this example), a single 96 tissue-culture treated wellplate (VWR Catalog #10062-902) was used. Silica antigen presenting beads were mixed with CD8+ T lymphocytes at ˜1:2 beads:cell. CD8+ T lymphocytes (2e5) (80-90% pure) were added to each well with approximately 1e5 antigen presenting beads (wellplate 1). Polymer antigen presenting beads were mixed with CD8+ T lymphocytes at ˜1:1 beads:cell. CD8+ T lymphocytes (2e5) (80-90% pure) were added to each well with approximately 2e5 antigen presenting beads (wellplate 2).
Each wellplate was cultured at 37° C. On day 0, IL-21 (150 ng/milliliter) in CTL media, was added to each well of wellplates 1 and 2, providing a final concentration in each well of 30 ng/mL. On day 2, IL21 was added to each well of the wellplates, to a final concentration of 30 ng/mL. Culturing was continued to day 7.
Day 7. Restimulation. A second aliquot of antigen presenting beads was added to the corresponding wells in wellplate 1 and wellplate 2. For the Silica beads, approximately 1e5 beads (Silica beads as prepared above in this example) were added. For the Polymer beads, approximately 2e5 beads (convoluted polymer beads as prepared above in this example) were added. IL21 was added to each well of the wellplate to a final concentration of 30 ng/mL. Culturing was continued.
Day 8. Addition of 50 microliters of IL-2 (50 IU/mL) and IL-7 (25 ng/mL) was made to each well in wellplate 1 and wellplate 2 to provide a final concentration of 10 IU/mL and 5 ng/mL respectively. Culturing was continued.
Day 9. Addition of 50 microliters of IL-21(150 ng/mL) was made to each occupied well of wellplate 1 and wellplate 2 to a final concentration of 30 ng/mL. Culturing was continued.
Day 14. The wells from each wellplate were individually stained for MHC tetramer (Tetramer PE, MBL Catalog # T02000, 1 microliter/well), CD4 (Biolegend Catalog #300530, 0.5 microliters/well); CD8 (Biolegend Catalog #301048, 0.5 microliters/well); CD28(Biolegend Catalog #302906, 0.31 microliters/well); CD45RO (Biolegend Catalog #304210, 0.63 microliters/well); CCR7 (CD197, Biolegend Catalog #353208, 0.5 microliters/well); and viability (BD Catalog #565388, 0.125 microliters/well). Each well was resuspended with 150 microliters FACS buffer and 10 microliters of Countbright™ beads (ThermoFisher Catalog # C36950). FACS analysis was performed on a FACSCelesta™ flow cytometer (BD Biosciences).
For Polymer beads, the convoluted surface makes the relationship between bead diameter and surface area less straightforward. From the quantitation, it was determined that Polymer antigen presenting beads based on M-280 DynaBeads had about 480,000 pMHC molecules and 425,000 costimulation antibodies on their surface. For a sphere of radius 1.4 microns (equal to the nominal radius of M-280 DynaBeads, this corresponds to about 20,000 pMHC and 17,000 costimulation antibodies per square micron. However, due to the convoluted surface of the Polymer beads, the actual surface area is likely larger, and thus the actual density lower. However, from
Three-fold serial dilutions of pMHC (HLA-A*02:01 SLC45A2 (Biolegend, Custom Product, SLYSYFQKV) in Wash Buffer were prepared. 20 microliters of Wash Buffer was added to a microcentrifuge tube for each serial dilution to be performed. Into the first serial dilution tube, 10 microliters of the pMHC were added. The diluted pMHC was mixed by vortexing. 10 uL of the diluted pMHC mixture was then used to prepare the subsequent serial dilution for a total of seven dilutions.
To determine the relationship between concentration of pMHC in solution and the density (molecules/unit area) deposited on the beads, Biotin functionalized (covalently coupled) smooth (e.g., substantially spherical as described above) 4 micron monodisperse silica beads (Cat. # SiO2MS-1.8 4.08 um-1 g, Cospheric), prepared as in Example 10B, were first coated with Streptavidin by storage in 100 micromolar Streptavidin. Approximately 1e7 beads were washed by dilution into 1 milliliter of Wash Buffer in a microcentrifuge tube, followed by centrifugation at 1,000×g for 1 minute. The supernatant was carefully removed by aspiration, and the wash process repeated twice more. After washing, approximately 1e6 beads were delivered into eight microcentrifuge tubes, centrifuged again, and the supernatant carefully removed.
Wash Buffer (120 microliters) containing 4.5 micrograms biotinylated Monomer MHC (HLA-A*02:01 SLC45A2 (Biolegend, Custom Product, SLYSYFQKV) was dispensed into one of the microcentrifuge tubes, and the beads were resuspended by pipetting up and down. The undiluted pMHC and serial dilutions of pMHC were further diluted into Wash Buffer (120 microliters) and used to resuspend beads, resulting in beads suspended in solutions with 4.5, 1.5, 0.5, 0.167, 0.056, 0.019, 0.006, or 0.002 micrograms of pMHC monomer per 5e6 beads. The monomer was allowed to bind for 30 min at 4° C. After 15 minutes, the mixtures were pipetted up and down again. The tubes were centrifuged, the supernatant liquid removed, and the beads resuspended at approximately 5e7/milliliter.
Approximately 1e5 beads prepared with each concentration of pMHC were washed with Wash Buffer (1 milliliter). The bead samples were resuspended in 100 microliters of Wash Buffer and stained by addition of 1 microliter of APC-conjugated anti-HLA-A (Biolegend, Catalog Number 343308). The beads were mixed with the antibody and allowed to stain for 30 minutes in the dark. After staining, beads were washed, resuspended in Wash Buffer (200 microliters) and transferred to tubes for analysis by Flow Cytometry.
A set of Quantum Simply Cellular fluorescence quantitation beads (Bangs Labs, Catalog Number 815) was then prepared to determine the number of anti-HLA-A antibodies bound to each antigen presenting bead sample. The quantitation beads have antibody binding capacities determined by the manufacturer. A drop of each bead with pre-determined binding capacity was placed in a microcentrifuge tube with 50 microliters of Wash Buffer. To the tube, 5 microliters of APC-conjugated anti-HLA-A was added and mixed by vortexing. The beads were stained for 30 minutes in the dark, washed using the same method as above. The beads with different binding capacities were then pooled into one sample and transferred to a single tube. A drop of blank beads (no antibody binding capacity) was added and the beads were analyzed by Flow Cytometry.
The quantitation beads were analyzed by Flow Cytometry (BD FACSCelesta, Becton Dickinson and Company) by recording 5,000 events. The quantitation beads were identified by Forward Scatter and Side Scatter, and the median intensity in the APC channel of each bead recorded. Quantitation was calculated as described in Example 22A, using the proprietary methodology provided by the quantitation bead manufacturer. From the antigen presenting bead standard, it is then possible to determine the concentration of pMHC in solution with beads that generates antigen presenting beads with a targeted density of pMHC, e.g., beads with approximately 10,000, 1,000, or 100 pMHC molecules per square micron, as seen in
Three-fold serial dilutions of biotinylated anti-CD28 and anti-CD2 in Wash Buffer were prepared. 20 microliters of anti-CD28 was mixed with 20 microliters of anti-CD2 in a microcentrifuge tube. Wash Buffer (20 microliters) was then added to a microcentrifuge tube for each serial dilution. The anti-CD28/anti-CD2 mixture (10 microliters) was then added to the first serial dilution tube. The solution was mixed using a vortexer, and 10 uL of the diluted anti-CD28/anti-CD2 mixture was then used to prepare the subsequent serial dilution for a total of seven dilutions.
To quantify the relationship between costimulation antibody in solution and the density (molecules/unit area) deposited on the beads, approximately 1e7 substantially spherical 4 micron silica beads, prepared as in Example 23A.1, having streptavidin binding moieties, were first washed by dilution into 1 milliliter of Wash Buffer in a microcentrifuge tube, followed by centrifugation at 1,000×g for 1 minute. The supernatant was carefully removed by aspiration, and the wash process repeated twice more. After washing, approximately 1e6 beads were delivered into eight microcentrifuge tubes, centrifuged again, and the supernatant carefully removed.
The beads were first functionalized with 1.0 micrograms of pMHC in Wash Buffer (1,200 microliters). After washing, the beads were resuspended in Wash Buffer (1,000 microliters). Into eight microcentrifuge tubes, 100 microliters of pMHC functionalized beads was dispended. The beads were centrifuged, and the supernatant carefully removed.
The undiluted mixed anti-CD28 and anti-CD2 and serial dilutions of anti-CD28/anti-CD2 were further diluted into Wash Buffer (120 microliters) and used to resuspend the beads, resulting in beads suspended in solutions with 4.5, 1.5, 0.5, 0.167, 0.056, 0.019, 0.006, or 0.002 micrograms of mixed costimulation antibodies monomer per 5e6 beads. The monomer was allowed to bind for 30 min at 4° C. After 15 minutes, the mixtures were pipetted up and down again. The tubes were centrifuged, the supernatant liquid removed, and the beads resuspended at approximately 5e7/milliliter.
Approximately 1e5 beads prepared with each concentration of costimulation antibodies was washed with Wash Buffer (1 milliliter). The bead samples were resuspended in 100 microliters of Wash Buffer and stained by addition of 1 microliter of APC-conjugated monoclonal anti-Mouse-IgG1 (Biolegend, Catalog Number 406610). The beads were mixed with the antibody and allowed to stain for 30 minutes in the dark. After staining, beads were washed, resuspended in Wash Buffer (200 microliters) and transferred to tubes for analysis by Flow Cytometry.
A set of Quantum Simply Cellular fluorescence quantitation beads (Bangs Labs, Catalog Number 815) was then prepared to determine the number of APC anti-Mouse IgG1 antibodies bound to each antigen presenting bead sample. A drop of each bead with pre-determined binding capacity was placed in a microcentrifuge tube with 50 microliters of Wash Buffer. To the tube, 5 microliters of APC-conjugated anti-Mouse IgG1 was added and mixed by vortexing. The beads were stained for 30 minutes in the dark, washed using the same method as above. The beads with different binding capacities were then pooled into one sample and transferred to a single tube. A drop of blank beads (no antibody binding capacity) was added and the beads were analyzed by Flow Cytometry.
The quantitation beads were analyzed by Flow Cytometry (BD FACSCelesta, Becton Dickinson and Company) by recording 5,000 events. The quantitation beads were identified by Forward Scatter and Side Scatter, and the median intensity in the APC channel of each bead recorded. Quantitation was performed as described in Example 22A, using proprietary methods provided by the quantitation bead manufacturer. This quantitation method calculates the number of APC anti-Mouse IgG1 antibodies on each antigen presenting bead. Assuming that 1 anti-Mouse IgG1 antibody binds to one costimulation antibody on the antigen presenting bead, this value represents the number of costimulation antibodies on each bead. From the antigen presenting bead standards, it is then possible to determine the concentration of costimulation antibodies in solution with beads that generates antigen presenting beads with a targeted density of costimulation antibodies, e.g., beads with approximately 10,000, 1,000, or 100 costimulation molecules per square micron, as seen in
Using the plots of pMHC and costimulation antibody concentration versus density on the resulting antigen presenting beads (
Biotin functionalized (covalently coupled) smooth silica beads, prepared as in Example 23.A.1 were first coated with Streptavidin by storage in 100 micromolar Streptavidin. Approximately 5e7 beads were washed by dilution into 1 milliliter of Wash Buffer in a microcentrifuge tube, followed by centrifugation at 1,000×g for 1 minute. The supernatant was carefully removed by aspiration, and the wash process repeated twice more. After washing, approximately 5e6 beads were delivered into three microcentrifuge tubes, centrifuged again, and the supernatant carefully removed.
To prepare antigen presenting beads with titrated pMHC, Wash Buffer (600 microliters) containing 0.5, 0.056, or 0.006 micrograms biotinylated Monomer MHC (HLA-A*02:01 MART-1 (MBL International Corp., Catalog No. MR01008, ELAGIGILTV) was dispensed into three microcentrifuge tubes, and the beads were resuspended by pipetting up and down. The monomer was allowed to bind for 30 min at 4° C. After 15 minutes, the mixtures were pipetted up and down again. The tubes were centrifuged at 1,000×g for one minute, and the supernatant liquid removed.
Wash Buffer (600 microliters) with 1.0 microgram of mixed biotinylated anti-CD28 and biotinylated anti-CD2 was used to resuspend each bead sample, and the beads were resuspended by pipetting up and down. The antibodies were allowed to bind for 30 min at 4° C. After 15 minutes, the mixtures were pipetted up and down again. The tubes were centrifuged at 1,000×g for one minute, and the supernatant liquid removed. Finally, the beads were resuspended in 100 microliters of Wash Buffer. The loading of the beads with the desired order of magnitude of pMHC and antibodies was verified by Flow Cytometry analysis and comparison to quantitation beads.
Wash Buffer (600 microliters) with 1.0 micrograms of anti-CD28 and anti-CD2 was used to resuspend each bead sample, and the beads were resuspended by pipetting up and down. The monomer was allowed to bind for 30 min at 4° C. After 15 minutes, the mixtures were pipetted up and down again. The tubes were centrifuged at 1,000×g for one minute, and the supernatant liquid removed. Finally, the beads were resuspended in 100 microliters of Wash Buffer. The loading of the beads with the desired order of magnitude of pMHC was verified by Flow Cytometry analysis and comparison to quantitation beads.
To prepare antigen presenting beads with titrated costimulation antibodies, Wash Buffer (1,200 microliters) containing 1.5 micrograms biotinylated Monomer MHC (HLA-A*02:01 MART-1 (MBL International Corp., Catalog No. MR01008, ELAGIGILTV) was dispensed into a microcentrifuge tube containing 1.5e7 washed beads from Example 23.111, and the beads were resuspended by pipetting up and down. The monomer was allowed to bind for 30 min at 4° C. After 15 minutes, the mixtures were pipetted up and down again. The tubes were centrifuged at 1,000×g for one minute, and the supernatant liquid removed.
The beads were then resuspended in Wash Buffer (900 microliters), and 300 microliters of the beads transferred to 3 microcentrifuge tubes.
Wash Buffer (300 microliters) with 1.0 microgram of mixed anti-CD28 and anti-CD2, 0.111 micrograms of mixed antiCD28 and anti-CD2, or 0.012 micrograms of mixed anti-CD28 and anti-CD2 was mixed into the three bead samples, and the beads were thoroughly mixed by pipetting up and down. The antibodies were allowed to bind for 30 min at 4° C. After 15 minutes, the mixtures were pipetted up and down again. The tubes were centrifuged at 1,000×g for one minute, and the supernatant liquid removed. Finally, the beads were resuspended in 100 microliters of Wash Buffer. The loading of the beads with the desired order of magnitude of costimulation antibodies was verified by Flow Cytometry analysis and comparison to quantitation beads.
Stimulation. Cells: CD8+ T lymphocytes were enriched in a medium including RPMI plus 10% fetal bovine serum (FBS) from commercially available PBMCs following manufacturers directions for EasySep™ Human CD8+ T Cell Isolation Kit, commercially available kit from StemCell Technologies Canada Inc. (Catalog #17953), by negative selection.
Culture medium and diluent for reagent additions: Advanced RPMI (ThermoFisher Catalog #12633020, 500 mL); 1× GlutaMAX (ThermoFisher Catalog #35050079, 5 mL); 10% Human AB serum (zen-bio, Catalog # HSER-ABP 100 mL, 50 mL); and 50 nM beta-mercaptoethanol (ThermoFisher Catalog #31350010, 50 nm stock, 0.5 mL, final conc 50 micromolar).
Experimental Setup: For each activation species titration (pMHC or costimulation antibodies), a single 96 tissue-culture treated wellplate (VWR Catalog #10062-902) was used. Antigen presenting beads with ˜10,000, ˜1,000 or ˜100 pMHC per square micron of bead surface and with ˜10,000 costimulation antibodies per square micron of bead surface (from Example 23.6.2) were mixed with CD8+ T lymphocytes at ˜1:2 beads:cell. CD8+ T lymphocytes (2e5) (80-90% pure) were added to each well with approximately 1e5 antigen presenting beads (wellplate 1). Antigen presenting beads with ˜10,000 pMHC per square micron of bead surface and with ˜10,000, ˜1,000 or ˜100 costimulation antibodies per square micron of bead surface (from Example 23.6.3) were mixed with CD8+ T lymphocytes at ˜1:2 beads:cell. CD8+ T lymphocytes (2e5) (80-90% pure) were added to each well with approximately 1e5 antigen presenting beads (wellplate 2).
Each wellplate was cultured at 37° C. On day 0, IL-21 (150 ng/milliliter) in CTL media, was added to each well of wellplates 1 and 2, providing a final concentration in each well of 30 ng/mL. On day 2, IL21 was added to each well of the wellplates, to a final concentration of 30 ng/mL. Culturing was continued to day 7.
Day 7. Restimulation. A second aliquot of antigen presenting beads with the targets density of pMHC or costimulation antibody was added to the corresponding wells in wellplate 1 and wellplate 2. IL21 was added to each well of the wellplate to a final concentration of 30 ng/mL. Culturing was continued.
Day 8. Addition of 50 microliters of IL-2 (50 IU/mL) and IL-7 (25 ng/mL) was made to each well in wellplate 1 and wellplate 2 to provide a final concentration of 10 IU/mL and 5 ng/mL respectively. Culturing was continued.
Day 9. Addition of 50 microliters of IL-21(150 ng/mL) was made to each occupied well of wellplate 1 and wellplate 2 to a final concentration of 30 ng/mL. Culturing was continued.
Day 14. The wells from each wellplate were individually stained for MHC tetramer (Tetramer PE, MBL Catalog # T02000, 1 microliter/well), CD4 (Biolegend Catalog #300530, 0.5 microliters/well); CD8 (Biolegend Catalog #301048, 0.5 microliters/well); CD28 (Biolegend Catalog #302906, 0.31 microliters/well); CD45RO (Biolegend Catalog #304210, 0.63 microliters/well); CCR7 (CD197, Biolegend Catalog #353208, 0.5 microliters/well); and viability (BD Catalog #565388, 0.125 microliters/well). Each well was resuspended with 150 microliters FACS buffer and 10 microliters of Countbright™ beads (ThermoFisher Catalog # C36950). FACS analysis was performed on a FACSCelesta™ flow cytometer (BD Biosciences).
Experimental Design: Tumor cell lines obtained from melanoma cells, including Mel 526 cells and A375 cells, were tested in an on-chip T cell killing assay. Each cell line was grown up in vitro according to standard procedures, then labeled with CellTrace™ Far Red dye (Cat. #034572, ThermoFisher Scientific), which provides stable intracellular labelling. Each population of labeled tumor cells were flowed into an individual microfluidic chip (Berkeley Lights, Inc.) in T cell media (Adv. RPMI+10% Human AB serum (Cat. #35-060-Cl, Corning)+Gln+50 uM 2-mercaptoethanol (BME, Cat. #31350-010, Gibco, ThermoFisher Scientific) supplemented with 10 uM fluorogenic Caspase-3 substrate (DEVD, Green) (Nucview® 488, Cat. #10403, Biotium). Groups of labeled tumor cells (˜2-10) were loaded into each of a plurality of sequestration pens on each of the two microfluidic chips (one for Mel 526 cells, and one for A375 cells) by tilting the microfluidic chip and allowing gravity to pull the tumor cells into the sequestration pens, providing a final concentration of the Caspase-3 substrate at 5 uM at Time=0 for the assay for each microfluidic chip. The Caspase-3 substrate provides no fluorescent signal until cleaved, so at Time=0, there was no fluorescent signal due to this reagent. T cells expanded against the SLC45A2 antigen, according to an endogenous T cell (ETC) protocol as described above, were flowed into each of the two microfluidic chips and gravity loaded on top of the tumor cells of each respective chip. Typically, after loading the tumor cells and T cells, each sequestration pen contained 0-5 tumor cells per T cell. As shown in the brightfield image (BF) for each time point and for each microfluidic chip containing SLC45A2-specific T cells and Mel526 tumor cells (
Results:
Mel526 tumor cells (
Typically after completion of antigen specific T lymphocyte activation as described in the preceding experiments, the antigen specific enriched T cells were sorted by FACS on an FACSAria Fusion System (Becton Dickinson, San Jose, Calif.) after staining 30 min RT in FACS buffer (1×DPBS w/o Ca2+Mg2+ (Cat. #4190250, ThermoFisher), 5 mM EDTA (Cat. # AM9260G, ThermoFisher), 10 mM HEPES (Cat. #15630080, ThermoFisher), 2% FBS) with anti-CD8-PerCPCy5.5 (Clone RPA-T8, 301032, Biolegend, San Diego, Calif.), Tetramer-PE (MBL International, Woburn, Mass.) specific to the antigen, and Zombie NIR (Cat. #423106, Biolegend, San Diego, Calif.) to exclude dead cells. Desired cells were purity sorted by gating: size, singles, live, CD8 positive, and Tetramer positive into CTL media (Advanced RPMI (Cat. #12633020, ThermoFisher), 1× Glutamax (Cat. #35050079, ThermoFisher), 10% Human Serum (Cat. # MT35060Cl, ThermoFisher), 50 uM b-Mercaptoethanol (Cat. #31350010, ThermoFisher) with 2 mM HEPES.
The sorted antigen-specific T cells were then expanded in at least one round of Rapid Expansion Protocol (REP), as described in Riddell, U.S. Pat. No. 5,827,642. Lymphoblastoid Cell Line cells (LCL, the LCL cell line was a gift from Cassian Yee, M. D. Anderson Cancer Center) were irradiated with 100 Gy and PBMC from 3 donors were irradiated with 50 Gy using an X-ray irradiator. Irradiated cells were washed in RPMI containing 10% FBS and mixed in a ratio of 1:5 (LCL:PBMC). These irradiated cells were added to either FACS-sorted T cells (for a first cycle of REP), or to the product of a first cycle of REP in 200 to 500-fold excess. Cultures were set up in T cell media (Advanced RPMI, 10% Human AB Serum, GlutaMax, 50 uM b-mercaptoethanol) supplemented with 50 U/mL IL-2 (Cat. #202-IL, R&D Systems) and 30 ng/mL anti-CD3 antibody (Cat. #16-0037-85, ThermoFisher). Cells were fed with fresh IL-2 on days 2, 5 and 10, and expanded according to their growth rates.
Expansion is typically 1,000-fold during a first REP cycle. Expansion during REP1 varied highly (316-7,800-fold, data not shown). Inaccurate quantification of low input cell numbers may have contributed to this variability. Shown here in
In
In
In
Therefore, the processes of activation via antigen presentation on a synthetic surface as described herein can provide well controlled, reproducible and characterizable cellular products suitable for use in immunotherapy. The antigen-presenting surfaces described herein provide lower cost of manufacture for these individualized therapies compared to currently available experimental processes.
Recitation of Some Embodiments of the Disclosure.
1. An antigen-presenting surface for activating a T lymphocyte (T cell), including:
a plurality of primary activating molecular ligands, wherein each primary activating molecular ligand includes a major histocompatibility complex (MHC) Class I molecule configured to bind to a T cell receptor (TCR) of the T cell; and
a plurality of co-activating molecular ligands each including a TCR co-activating molecule or an adjunct TCR activating molecule, wherein each of the plurality of primary activating molecular ligands and the plurality of co-activating molecular ligands is specifically bound to the antigen presenting surface.
2. The antigen-presenting surface of embodiment 1, wherein the plurality of co-activating molecular ligands comprises TCR co-activating molecules and adjunct TCR activating molecules.
3. The antigen-presenting surface of embodiment 1 or 2, wherein a ratio of the TCR co-activating molecules to the adjunct TCR activating molecules of the plurality of co-activating molecular ligands is about 100:1 to about 1:100.
4. The antigen-presenting surface of embodiment 1 or 2, wherein a ratio of the TCR co-activating molecules to the adjunct TCR activating molecules of the plurality of co-activating molecular ligands is 100:1 to 90:1, 90:1 to 80:1, 80:1 to 70:1, 70:1 to 60:1, 60:1 to 50:1, 50:1 to 40:1, 40:1 to 30:1, 30:1 to 20:1, 20:1 to 10:1, 10:1 to 1:1, 1:1 to 1:10, 1:10 to 1:20, 1:20 to 1:30, 1:30 to 1:40, 1:40 to 1:50, 1:50 to 1:60, 1:60 to 1:70, 1:70 to 1:80, 1:80 to 1:90, or 1:90 to 1:100, wherein each of the foregoing values is modified by “about.”
5. The antigen-presenting surface of embodiment 1 or 2, wherein the ratio of the TCR co-activating molecules to the adjunct TCR activating molecule is about 10:1 to about 1:20.
6. The antigen-presenting surface of embodiment 1 or 2, wherein a ratio of the TCR co-activating molecules to the adjunct TCR activating molecules of the plurality of co-activating molecular ligands is about 10:1 to about 1:10.
7. The antigen-presenting surface of any one of the preceding embodiments, wherein the plurality of primary activating molecular ligands is disposed upon at least a portion of the antigen-presenting surface at a density from about 4×102 to about 3×104 molecules per square micron, in each portion or sub-region where it is attached.
8. The antigen-presenting surface of embodiment 7, wherein the plurality of primary activating molecular ligands is disposed upon at least a portion of the antigen-presenting surface at a density from about 4×102 to about 2×103 molecules per square micron.
9. The antigen-presenting surface of embodiment 7, wherein the plurality of primary activating molecular ligands is disposed upon at least a portion of the antigen-presenting surface at a density from about 2×103 to about 5×103 molecules per square micron.
10. The antigen-presenting surface of embodiment 7, wherein the plurality of primary activating molecular ligands is disposed upon at least a portion of a surface of the antigen-presenting surface at a density from about 5×103 to about 2×104 molecules per square micron, about 1×104 to about 2×104 molecules per square micron, or about 1.25×104 to about 1.75×104 molecules per square micron.
11. The antigen-presenting surface of any one of embodiments 7-10, wherein the plurality of primary activating molecular ligands is disposed upon substantially all of the antigen-presenting surface at the stated density.
12. The antigen-presenting surface of any one of embodiments 1-11, further including a plurality of surface-blocking molecular ligands.
13. The antigen-presenting surface of any one of embodiments 1-12, wherein the adjunct TCR activating molecule is configured to provide adhesion stimulation.
14. The antigen-presenting surface of any one of embodiments 1-13, wherein the plurality of co-activating molecular ligands is disposed upon at least a portion the antigen-presenting surface at a density from about 5×102 to about 2×104 molecules per square micron or about 5×102 to about 1.5×104 molecules per square micron.
15. The antigen-presenting surface of any one of embodiments 1 to 14, wherein the plurality of co-activating molecular ligands is disposed upon at least a portion of the antigen-presenting surface at a density from about 5×103 to about 2×104 molecules per square micron, about 5×103 to about 1.5×104 molecules per square micron, about 1×104 to about 2×104 molecules per square micron, about 1×104 to about 1.5×104 molecules per square micron, about 1.25×104 to about 1.75×104 molecules per square micron, or about 1.25×104 to about 1.5×104 molecules per square micron.
16. The antigen-presenting surface of any one of embodiments 1-14, wherein the plurality of co-activating molecular ligands is disposed upon at least a portion of the antigen-presenting surface at a density from about 2×103 to about 5×103 molecules per square micron.
17. The antigen-presenting surface of any one of embodiments 1-14, wherein the plurality of co-activating molecular ligands is disposed upon at least a portion of a surface of the antigen-presenting surface at a density from about 5×102 to about 2×103 molecules per square micron.
18. The antigen-presenting surface of any one of embodiments 14-17, wherein the plurality of co-activating molecular ligands is disposed upon substantially all of the antigen-presenting surface at the stated density.
19. The antigen-presenting surface of any one of embodiments 1-18, wherein a ratio of the primary activating molecular ligands to the co-activating molecular ligands present on the antigen-presenting surface is about 1:10 to about 2:1, about 1:5 to about 2:1, about 1:2 to about 2:1, about 1:10 to about 1:1, about 1:5 to about 1:1, about 1:1 to about 2:1, or about 1:2 to about 1:1.
20. The antigen-presenting surface of any one of embodiments 1-19, wherein the antigen-presenting surface includes glass, metal, ceramic, and/or a metal oxide or any combination thereof.
21. The antigen-presenting surface of any one of embodiments 1-20, wherein the antigen-presenting surface includes a polymeric surface.
22. The antigen-presenting surface of embodiment 20 or 21, wherein the surface includes a magnetic material.
23. The antigen-presenting surface of any one of embodiments 1 to 22, wherein each of the plurality of primary activating molecular ligands is noncovalently bound to a binding moiety, and further wherein the binding moiety is covalently bound to the antigen-presenting surface.
24. The antigen-presenting surface of embodiment 23, wherein each of the plurality of primary activating molecular ligands comprises a biotin and is noncovalently bound to a biotin-binding agent, and further wherein the biotin-binding agent is covalently bound to the antigen-presenting surface.
25. The antigen-presenting surface of any one of embodiments 1 to 22, wherein each of the plurality of primary activating molecular ligands is noncovalently bound to a binding moiety, and further wherein the binding moiety is noncovalently bound to the antigen-presenting surface.
26. The antigen-presenting surface of embodiment 25, wherein each of the plurality of primary activating molecular ligands comprises a biotin moiety, the binding moiety comprises a biotin-binding agent, and the biotin-binding agent is noncovalently bound to a second biotin moiety covalently attached to the antigen-presenting surface.
27. The antigen-presenting surface of 24 or 26, wherein the biotin-binding agent is streptavidin.
28. The antigen-presenting surface of any one of embodiments 1 to 27, wherein the MHC molecule includes an MHC protein sequence and a beta microglobulin.
29. The antigen-presenting surface of any one of embodiments 1 to 28, wherein the MHC molecule further includes a tumor specific antigen.
30. The antigen-presenting surface of embodiment 29, wherein the tumor specific antigen is non-covalently associated with the MHC molecule.
31. The antigen-presenting surface of embodiment 29 or 30, wherein the antigen is SLC45A2, TCL1, VCX3A, MART1 or NYESO1.
32. The antigen-presenting surface of any one of embodiments 1-31, wherein the TCR co-activating molecule includes a protein.
33. The antigen-presenting surface of embodiment 32, wherein the TCR co-activating protein molecule includes a CD-28 binding protein or a fragment thereof which retains binding ability with CD28.
34. The antigen-presenting surface of embodiment 32 or 33, wherein the TCR co-activating molecule further comprises a site-specific C-terminal biotin moiety.
35. The antigen-presenting surface of embodiment 33 or 34, wherein the CD28 binding protein includes a CD80 molecule or a fragment thereof, wherein the fragment retains binding ability to CD28.
36. The antigen-presenting surface of any one of embodiments 32-35 wherein the TCR co-activating molecule includes an anti-CD28 antibody or fragment thereof, wherein the fragment retains binding activity with CD28.
37. The antigen-presenting surface of any one of embodiments 1-36, wherein the adjunct TCR activating molecular ligand includes a CD2 binding protein or a fragment thereof, wherein the fragment retains binding ability with CD2.
38. The antigen-presenting surface of embodiment 37, wherein the CD2 binding protein further comprises a site-specific C-terminal biotin moiety.
39. The antigen-presenting surface of embodiment 37 or 38, wherein the adjunct TCR activating molecular ligand includes a CD58 molecule or fragment thereof, wherein the fragment retains binding activity with CD2.
40. The antigen-presenting surface of any one of embodiments 1-39, wherein the adjunct TCR activating molecule includes an anti-CD2 antibody or a fragment thereof, wherein the fragment retains binding activity with CD2.
41. The antigen-presenting surface of any one of embodiments 1-40, wherein each of the plurality of co-activating molecular ligands is non-covalently attached to a streptavidin wherein the streptavidin is non-covalently attached to a streptavidin binding molecule, further wherein the streptavidin binding molecule is covalently attached via a linker to the antigen-presenting surface, optionally wherein the streptavidin binding molecule comprises biotin.
42. The antigen-presenting surface of any one of embodiments 1-40, wherein each of the plurality of co-activating molecular ligands is covalently connected to the surface via a linker.
43. The antigen-presenting surface of embodiment 41 or 42, wherein the linker links the streptavidin binding molecule and/or co-activating molecular ligands to the surface through a series of about 15, 20, 25, 30, 35, 40, 45, 50, 55, 60, 65, 70, 75, 80, 85, 95, 100, 200 bond lengths, or any number of bond lengths therebetween bonds.
44. The antigen-presenting surface of any one of embodiments 1-40, wherein each of the plurality of co-activating molecular ligands is non-covalently attached to a streptavidin moiety; and the streptavidin moiety is covalently attached to the antigen-presenting surface.
45. The antigen-presenting surface of embodiment 42, wherein the streptavidin moiety is linked by a linker to the surface through a series of about 15, 20, 25, 30, 35, 40, 45, 50, 55, 60, 65, 70, 75, 80, 85, 95, 100, 200 bond lengths, or any number of bond lengths therebetween.
46. The antigen-presenting surface of any one of embodiments 5-45, wherein:
(i) each of the plurality of surface-blocking molecular ligands includes a hydrophilic moiety, an amphiphilic moiety, a zwitterionic moiety, and/or a negatively charged moiety;
(ii) each of the plurality of surface-blocking molecular ligands includes a linker and a terminal surface-blocking group, optionally wherein the linkers of the plurality of surface-blocking molecular ligands are of the same length or are of different lengths; or
(iii) each of the plurality of surface-blocking molecular ligands includes a linker and a terminal surface-blocking group, wherein the terminal surface-blocking group comprises a hydrophilic moiety, amphiphilic moiety, zwitterionic moiety, and/or negatively charged moiety, optionally wherein the linkers of the plurality of surface-blocking molecular ligands are of the same length or are of different lengths.
47. The antigen-presenting surface of embodiment 46, wherein:
(i) the plurality of surface-blocking molecular ligands all have the same terminal surface-blocking group; or
(ii) the plurality of surface-blocking molecular ligands have a mixture of terminal surface-blocking groups; optionally wherein each of the plurality of surface-blocking molecular ligands includes a polyethylene glycol (PEG) moiety, a carboxylic acid moiety, or a combination thereof, further optionally wherein the PEG moiety of each of the surface-blocking molecular ligands has a backbone linear chain length of about 10 atoms to about 100 atoms.
48. The antigen-presenting surface of any one of embodiments 5-47, wherein:
(i) each of the plurality of surface-blocking molecular ligands is covalently connected to the antigen-presenting surface; and/or
(ii) the plurality of the surface-blocking molecular ligands and may include 2, 3, or 4 different surface-blocking groups and/or 2, 3, 4, or more different lengths of linkers, chosen in any combination.
49. The antigen-presenting surface of any one of embodiments 1-48, further including a plurality of adhesion stimulatory molecular ligands, optionally wherein each adhesive molecular ligand includes a ligand for a cell adhesion receptor comprising an ICAM protein sequence.
50. The antigen-presenting surface of embodiment 49, wherein the adhesion stimulatory molecular ligand is covalently connected to the antigen-presenting surface via a linker.
51. The antigen-presenting surface of embodiment 50, wherein the adhesion stimulatory molecular ligand is non-covalently attached to a streptavidin moiety, wherein the streptavidin moiety is covalently attached via a linker to the antigen-presenting surface.
52. The antigen-presenting surface of embodiment 50, wherein the adhesion stimulatory molecular ligand is non-covalently attached to a streptavidin, wherein the streptavidin is noncovalently attached to a biotin and the biotin is covalently attached via a linker to the antigen-presenting surface.
53. The antigen-presenting surface of any one of embodiments 1-52, wherein the ratio of the TCR co-activating molecules to the adjunct TCR activating molecules of the plurality of co-activating molecular ligands is from about 3:1 to about 1:3.
54. The antigen-presenting surface of any one of embodiments 1-53, wherein the ratio of the TCR co-activating molecules to the adjunct TCR activating molecules of the plurality of co-activating molecular ligands is about 1:2 to about 2:1.
55. The antigen-presenting surface of any one of embodiments 1-54, wherein the ratio of the TCR co-activating molecules to the adjunct TCR activating molecules of the plurality of co-activating molecular ligands is about 1:1.
56. The antigen-presenting surface of any one of embodiments 1-55, further including a plurality of growth-stimulatory molecular ligands, wherein each of the growth-stimulatory molecular ligands includes a growth factor receptor ligand.
57. The antigen-presenting surface of embodiment 56, wherein the growth factor receptor ligand includes a cytokine or fragment thereof, wherein the fragment retains receptor binding ability, optionally wherein the cytokine comprises IL-21.
58. The antigen-presenting surface of any one of the embodiments 1-57, which is an antigen-presenting surface of a bead.
59. The antigen-presenting surface of embodiment 58, wherein the bead has a surface area within 10% of the surface area of a sphere having an equal volume or diameter.
60. The antigen-presenting surface of embodiment 58, wherein the bead has a surface area exceeding by more than 10% the surface area of a sphere having an equal volume or diameter.
61. The antigen-presenting surface of any one of the embodiments 1-57, which is an antigen-presenting surface of a microfluidic device, wafer, or tube.
62. The antigen-presenting surface of embodiment 61, further including a first portion and a second portion, wherein the distribution of the plurality of primary activating molecular ligands and the distribution of the plurality of co-activating molecular ligands are located in the first portion of the antigen-presenting surface, and the second portion is configured to substantially exclude the primary activating molecular ligands.
63. The antigen-presenting surface of embodiment 62, wherein at least one plurality of surface-blocking molecular ligands is located in the second portion of the at least one inner surface of the antigen-presenting surface.
64. The antigen-presenting surface of 62 or 63, wherein the first portion of the antigen-presenting surface further includes a plurality of first regions, each first region including at least a subset of the plurality of the primary activating molecular ligands, wherein each of the plurality of first regions is separated from another of the plurality of first region by the second portion configured to substantially exclude primary activating molecular ligands.
65. The antigen-presenting surface of embodiment 64, wherein each of the plurality of first regions including the at least a subset of the plurality of the primary activating molecular ligands further includes a subset of the plurality of the co-activating molecular ligands.
66. The antigen-presenting surface of embodiment 64 or 65, wherein each of the plurality of first regions including at least the subset of the plurality of the primary activating molecular ligands has an area of about 0.10 square microns to about 4.0 square microns.
67. The antigen-presenting surface of any one of embodiments 64-66, wherein the area of each of the plurality of first regions including at least the subset of the plurality of the primary activating molecular ligands is about 4.0 square microns to about 0.8 square microns.
68. The antigen-presenting surface of any one of embodiments 64-67, wherein each of the plurality of first regions further includes at least a subset of a plurality of adhesion stimulatory molecular ligands, and optionally wherein each of the adhesion stimulatory molecular ligands includes a ligand for a cell adhesion receptor comprising an ICAM protein sequence.
69. The antigen-presenting surface of any one of embodiments 63-68, wherein the second portion configured to substantially exclude the primary activating molecular ligands is also configured to substantially exclude co-activating molecular ligands.
70. The antigen-presenting surface of any one of embodiments 62-69, wherein the second portion configured to substantially exclude the primary activating molecular ligands is further configured to include a plurality of growth stimulatory molecular ligands, wherein each of the growth stimulatory molecular ligands includes a growth factor receptor ligand.
71. The antigen-presenting surface of any one of embodiments 62-70, wherein the second portion configured to substantially exclude the primary activating molecular ligands includes a plurality of adhesion stimulatory molecular ligands, wherein each of the adhesion stimulatory molecular ligands includes a ligand for a cell adhesion receptor including an ICAM protein sequence.
72. The antigen-presenting surface of any one of embodiments 61-71, which is an antigen-presenting surface of a wafer.
73. The antigen-presenting surface of any one of embodiments 61-71, which is an antigen-presenting surface of a tube.
74. The antigen-presenting surface of any one of embodiments 61-71, which is an antigen-presenting surface of a microfluidic device.
75. The antigen-presenting microfluidic device of embodiment 74, wherein each of the plurality of first regions including at least a subset of the plurality of primary activating molecular ligands is disposed at least one surface within a chamber of the antigen-presenting microfluidic device.
76. The antigen-presenting microfluidic device of embodiment 75, wherein the chamber is a sequestration pen.
77. The antigen-presenting microfluidic device of embodiments 74-76, wherein the microfluidic device further comprises a flow region for containing a flow of a first fluidic medium; and the sequestration pen comprises an isolation region for containing a second fluidic medium, the isolation region having a single opening, wherein the isolation region of the sequestration pen is an unswept region of the microfluidic device; and a connection region fluidically connecting the isolation region to the flow region; optionally wherein the microfluidic device comprises a microfluidic channel comprising at least a portion of the flow region.
78. The antigen-presenting microfluidic device of embodiment 77, wherein the microfluidic device comprises a microfluidic channel comprising at least a portion of the flow region, and the connection region comprises a proximal opening into the microfluidic channel having a width Wcon ranging from about 20 microns to about 100 microns and a distal opening into the isolation region, and wherein a length Lcon of the connection region from the proximal opening to the distal opening is as least 1.0 times a width Wcon of the proximal opening of the connection region.
79. The antigen-presenting microfluidic device of embodiment 78, wherein the length Lcon of the connection region from the proximal opening to the distal opening is at least 1.5 times the width Wcon of the proximal opening of the connection region.
80. The antigen-presenting microfluidic device of embodiment 78, wherein the length Lcon of the connection region from the proximal opening to the distal opening is at least 2.0 times the width Wcon of the proximal opening of the connection region.
81. The antigen-presenting microfluidic device of any one of embodiments 78-80, wherein the width Wcon of the proximal opening of the connection region ranges from about 20 microns to about 60 microns.
82. The antigen-presenting microfluidic device of any one of embodiments 78-81, wherein the length Lcon of the connection region from the proximal opening to the distal opening is between about 20 microns and about 500 microns.
83. The antigen-presenting microfluidic device of any one of embodiments 78-82, wherein a width of the microfluidic channel at the proximal opening of the connection region is between about 50 microns and about 500 microns.
84. The antigen-presenting microfluidic device of any one of embodiments 78-83, wherein a height of the microfluidic channel at the proximal opening of the connection region is between 20 microns and 100 microns.
85. The antigen-presenting microfluidic device of any one of embodiments 77-84, wherein the volume of the isolation region ranges from about 2×104 to about 2×106 cubic microns.
86. The antigen-presenting microfluidic device of any one of embodiments 77-85, wherein the proximal opening of the connection region is parallel to a direction of the flow of the first medium in the flow region.
87. The antigen-presenting microfluidic device of any one of embodiments 77-86, wherein the microfluidic device comprises an enclosure comprising a base, a microfluidic circuit structure disposed on the base, and a cover which collectively define a microfluidic circuit, and the microfluidic circuit comprises the flow region, the microfluidic channel, and the sequestration pen.
88. The antigen-presenting microfluidic device of any one of embodiments 77-87, wherein the microfluidic circuit further comprises one or more inlets through which the first medium can be input into the flow region and one or more outlets through which the first medium can be removed from the flow region.
89. The antigen-presenting microfluidic device of embodiment 87, wherein the cover is an integral part of the microfluidic circuit structure.
90. The antigen-presenting microfluidic device of embodiment 87 or 88, wherein barriers defining the microfluidic sequestration pen extend from a surface of the base of the microfluidic device to a surface of the cover of the microfluidic device.
91. The antigen-presenting microfluidic device of any one of embodiments 87-90, wherein the cover and the base are part of a dielectrophoresis (DEP) mechanism for selectively inducing DEP forces on a micro-object.
92. The antigen-presenting microfluidic device of any one of embodiments 87-91, wherein the microfluidic device further comprises a first electrode, an electrode activation substrate, and a second electrode, wherein the first electrode is part of a first wall of the enclosure and the electrode activation substrate and the second electrode is part of a second wall of the enclosure, wherein the electrode activation substrate comprises a photoconductive material, semiconductor integrated circuits, or phototransistors.
93. The antigen-presenting microfluidic device of embodiment 92, wherein the first wall of the microfluidic device is the cover, and wherein the second wall of the microfluidic device is the base.
94. The antigen-presenting microfluidic device of embodiment 92 or 93, wherein the electrode activation substrate comprises phototransistors.
95. The antigen-presenting microfluidic device of any one of embodiments 87-94, wherein the cover and/or the base is transparent to light.
96. The antigen-presenting microfluidic device of any one of embodiments 61-95, wherein the second portion is disposed at at least one surface of a microfluidic channel of the antigen-presenting microfluidic device.
97. A covalently functionalized synthetic surface including at least one plurality of biotin-binding agent or biotin functionalities and at least one plurality of surface-blocking molecular ligands, wherein each of the biotin-binding agent or biotin functionalities and each of the plurality of surface-blocking molecular ligands are covalently attached to the covalently functionalized synthetic surface.
98. The covalently functionalized synthetic surface of embodiment 97, wherein the surface includes the plurality of biotin functionalities.
99. The covalently functionalized synthetic surface of embodiment 98, wherein the surface further includes a plurality of biotin-binding agent functionalities noncovalently attached to the surface through the biotin functionalities.
100. The covalently functionalized synthetic surface of any one of embodiments 97-99, wherein each of the plurality of biotin functionalities is attached to the covalently functionalized surface via a linker.
101. The covalently functionalized synthetic surface of any one of embodiments 97-100, wherein the biotin-binding agent is streptavidin.
102. The covalently functionalized synthetic surface of embodiment 97 or 101, wherein each of the plurality of biotin or biotin-binding agent functionalities is attached to the covalently functionalized surface via a linker.
103. The covalently functionalized synthetic surface of embodiment 102, wherein the linker linking the biotin or biotin-binding agent functionality has a length of about 20 Angstroms to about 100 Angstroms.
104. The covalently functionalized synthetic surface of embodiment 102 or 103, wherein the linker links the biotin-binding agent functionality to the surface through a series of about 15, 20, 25, 30, 35, 40, 45, 50, 55, 60, 65, 70, 75, 80, 85, 95, 100, 200 bond lengths, or any number of bond lengths therebetween.
105. The covalently functionalized synthetic surface of embodiment 102 or 103, wherein the linker links the biotin to the surface through a series of about 15, 20, 25, 30, 35, 40, 45, 50, 55, 60, 65, 70, 75, 80, 85, 95, 100, 200 bond lengths, or any number of bond lengths therebetween.
106. The covalently functionalized synthetic surface of any one of embodiments 102-105, wherein the linker of each biotin or biotin-binding agent functionality includes a polyethylene glycol (PEG) moiety.
107. The covalently functionalized synthetic surface of embodiment 106, wherein the PEG linker includes a (PEG)13 repeating sequence, optionally wherein the surface includes the plurality of biotin-binding agent functionalities.
108. The covalently functionalized synthetic surface of embodiment 106, wherein the PEG linker includes a (PEG)4 repeating sequence, optionally wherein the surface includes the plurality of biotin functionalities.
109. The covalently functionalized synthetic surface of any one of embodiments 97-108, wherein:
(i) each of the plurality of surface-blocking molecular ligands includes a hydrophilic moiety, an amphiphilic moiety, a zwitterionic moiety, and/or a negatively charged moiety;
(ii) each of the plurality of surface-blocking molecular ligands includes a linker and a terminal surface-blocking group, optionally wherein the linkers of the plurality of surface-blocking molecular ligands are of the same length or are of different lengths; or
(iii) each of the plurality of surface-blocking molecular ligands includes a linker and a terminal surface-blocking group, wherein the terminal surface-blocking group comprises a hydrophilic moiety, amphiphilic moiety, zwitterionic moiety, and/or negatively charged moiety, optionally wherein the linkers of the plurality of surface-blocking molecular ligands are of the same length or are of different lengths;
(iv) each of the plurality of surface-blocking molecular ligands is covalently connected to the antigen-presenting surface; and/or
(v) the plurality of the surface-blocking molecular ligands and may include 2, 3, or 4 different surface-blocking groups and/or 2, 3, 4, or more different lengths of linkers, chosen in any combination.
110. The covalently functionalized synthetic surface of embodiment 109, wherein:
(i) the plurality of surface-blocking molecular ligands all have the same terminal surface-blocking group; or
(ii) the plurality of surface-blocking molecular ligands have a mixture of terminal surface-blocking groups; optionally wherein each of the plurality of surface-blocking molecular ligands includes a polyethylene glycol (PEG) moiety, a carboxylic acid moiety, or a combination thereof.
111. The covalently functionalized synthetic surface of embodiment 108, wherein the PEG moiety of each of the surface-blocking molecular ligands has a backbone linear chain length of about 10 atoms to about 100 atoms.
112. The covalently functionalized synthetic surface of any one of embodiments 97-111, wherein the at least one plurality of streptavidin moieties is disposed upon the covalently functionalized synthetic surface in a density from about 4×102 to about 3×104 molecules per square micron, in each portion or sub-region where it is attached.
113. The covalently functionalized synthetic surface of any one of embodiments 97-111, wherein the at least one plurality of streptavidin moieties is disposed upon the covalently functionalized synthetic surface in a density from about 5×103 to about 3×104 molecules per square micron, in each portion or sub-region where it is attached.
114. The covalently functionalized synthetic surface of any one of embodiments 97-111, wherein the at least one plurality of streptavidin moieties is disposed upon the covalently functionalized synthetic surface from about 6×102 to about 5×103 molecules per square micron, about 5×103 to about 2×104 molecules per square micron, about 1×104 to about 2×104 molecules per square micron, or about 1.25×104 to about 1.75×104 molecules per square micron, in each portion or sub-region where it is attached.
115. The covalently functionalized synthetic surface of any one of embodiments 97-114, wherein the surface includes glass, polymer, metal, ceramic, and/or a metal oxide.
116. The covalently functionalized synthetic surface of any one of embodiments 97-115, wherein the covalently functionalized synthetic surface is a covalently functionalized wafer, a covalently functionalized inner surface of a tube, or a covalently functionalized inner surface of a microfluidic device.
117. The covalently functionalized synthetic surface of embodiment 116, wherein the tube is a glass or polymer tube.
118. The covalently functionalized synthetic surface of any one of embodiments 97 to 115, wherein the covalently functionalized synthetic surface is a covalently functionalized bead.
119. The covalently functionalized synthetic surface of embodiment 118, wherein the covalently functionalized bead includes a magnetic material.
120. The covalently functionalized synthetic surface of embodiment 118 or 119, wherein the bead has a surface area within 10% of the surface area of a sphere of an equal volume or diameter.
121. The covalently functionalized synthetic surface of any one of embodiments 118-120, wherein the at least one plurality of streptavidin or biotin moieties is disposed upon substantially all of the covalently functionalized synthetic surface.
122. The covalently functionalized synthetic surface of any one of embodiments 97-117, further including a first portion and a second portion, wherein the distribution of the at least one plurality of streptavidin or biotin functionalities is located in the first portion of the covalently modified synthetic surface, and the distribution of the at least one plurality of the surface-blocking molecular ligands is located in the second portion.
123. The covalently functionalized synthetic surface of embodiment 122, wherein a second plurality of surface-blocking molecular ligands is disposed in the first portion of the covalently functionalized synthetic surface.
124. The covalently functionalized synthetic surface of embodiment 123, wherein the second plurality of surface-blocking molecular ligands limits the density of functionalizing moieties of an antigen-presenting synthetic surface formed from the covalently functionalized synthetic surface.
125. The covalently functionalized synthetic surface of embodiment 123 or 125, wherein the first portion of the covalently functionalized synthetic surface further includes a plurality of first regions, each first region including at least a subset of the plurality of the streptavidin or biotin functionalities, wherein each of the plurality of first regions is separated from another of the plurality of first regions by the second region configured to substantially exclude the streptavidin or biotin functionalities.
126. The covalently functionalized synthetic surface of embodiment 125, wherein each of the plurality of first regions including at least the subset of the plurality of the streptavidin or biotin functionalities has an area of about 0.10 square microns to about 4.0 square microns.
127. The covalently functionalized synthetic surface of embodiment 125 or 126, wherein the area of each of the plurality of first regions including at least the subset of the plurality of the primary activating molecular ligands is about 4.0 square microns to about 0.8 square microns.
128. The covalently functionalized synthetic surface of any one of embodiments 97-116 or 122-127, wherein the covalently functionalized synthetic surface is at least one inner surface of a microfluidic device.
129. The covalently functionalized synthetic surface of embodiment 128, wherein each of the plurality of first regions including at least a subset of the plurality of biotin-binding agent or biotin functionalities includes at least one surface within a chamber of the microfluidic device.
130. The covalently functionalized synthetic surface of embodiment 129, wherein the chamber is a sequestration pen.
131. A kit for preparing an antigen-presenting synthetic surface for activating a T lymphocyte (T cell), including:
a. the covalently functionalized synthetic surface of any one of embodiments 95-128, which includes a plurality of noncovalently or covalently associated first coupling agents; and
b. a first modification reagent including a plurality of major histocompatibility complex (MHC) I molecules configured to bind with a T cell receptor of the T cell, and further wherein the MHC molecules are configured to bind to one of a first subset of the plurality of noncovalently or covalently associated first coupling agents of the covalently functionalized synthetic surface;
optionally wherein the first coupling agents are biotin-binding agents.
132. The kit of embodiment 131, wherein each of the plurality of MHC molecules further includes at least one biotin functionality.
133. The kit of embodiment 131 or 132, further including a reagent including a plurality of co-activating molecules, each configured to bind one of a second subset of the plurality of noncovalently or covalently associated first coupling agents of the covalently functionalized synthetic surface.
134. The kit of embodiment 133, wherein each of the plurality of co-activating molecules includes a biotin functionality.
135. The kit of embodiment 134, wherein each of the plurality of co-activating molecules further comprises a site-specific C-terminal biotin moiety.
136. The kit of any one of embodiments 133-135, wherein each of the co-activating molecules includes a T cell receptor (TCR) co-activating molecule, an adjunct TCR activating molecule, or any combination thereof.
137. The kit of embodiment 136, wherein the plurality of co-activating molecular ligands comprises TCR co-activating molecules and adjunct TCR activating molecules.
138. The kit of embodiment 136 or 137, wherein a container containing the reagent including a plurality of co-activating molecules contains the TCR co-activating molecules and/or the adjunct TCR activating molecules of the plurality of co-activating molecular ligands in a ratio from about 100:1 to about 1:100 or in a ratio of about 3:1 to about 1:3.
139. The kit of any one of embodiments 136-138, wherein a container containing the reagent including a plurality of co-activating molecules contains the TCR co-activating molecules and the adjunct TCR activating molecules of the plurality of co-activating molecular ligands in a ratio from about 10:1 to about 1:10 or from about 10:1 to about 1:20.
140. The kit of any one of embodiments 136-139, wherein the ratio of the TCR co-activating molecules to the adjunct TCR activating molecules of the plurality of co-activating molecular ligands is 100:1 to 90:1, 90:1 to 80:1, 80:1 to 70:1, 70:1 to 60:1, 60:1 to 50:1, 50:1 to 40:1, 40:1 to 30:1, 30:1 to 20:1, 20:1 to 10:1, 10:1 to 1:1, 3:1 to 1:3; 1:1 to 1:10, 1:10 to 1:20, 1:20 to 1:30, 1:30 to 1:40, 1:40 to 1:50, 1:50 to 1:60, 1:60 to 1:70, 1:70 to 1:80, 1:80 to 1:90, or 1:90 to 1:100, wherein each of the foregoing values is modified by “about”.
141. The kit of any one of embodiments 136-140, wherein a container containing the reagent including a plurality of co-activating molecules contains the TCR co-activating molecules and the adjunct TCR activating molecules of the plurality of co-activating molecular ligands in a ratio from about 20:1 to about 1:20.
142. The kit of embodiment 136, wherein the reagent including a plurality of co-activating molecules is contained in two containers, wherein the first container contains T cell receptor (TCR) co-activating molecules, and the second container contains adjunct TCR activating molecules.
143. The kit of any one of embodiments 136-142, wherein the TCR co-activating molecule is a CD28 binding protein or a fragment thereof which retains binding ability with CD28.
144. The kit of any one of embodiments 136-143, wherein the adjunct TCR co-activating molecule is a CD2 binding protein or a fragment thereof.
145. The kit of any one of embodiments 131-144, further including a reagent including adhesion stimulatory molecules, wherein each adhesion stimulatory molecule includes a ligand for a cell adhesion receptor including an ICAM protein sequence configured to react with a third subset of the plurality of noncovalently or covalently associated first coupling agent functionalities of the covalently functionalized synthetic surface.
146. The kit of embodiment 145, wherein the adhesion stimulatory molecule includes a biotin functionality.
147. The kit of any one of embodiments 131-146, further including a reagent including growth stimulatory molecules, wherein each growth stimulatory molecule includes a includes a growth factor receptor ligand.
148. The kit of embodiment 147, wherein the growth factor receptor ligand includes a cytokine or a fragment thereof.
149. The kit of embodiment 148, wherein the cytokine includes IL-21 or a fragment thereof.
150. The kit of any one of embodiments 147-149, further including one or more additional growth-stimulatory molecules.
151. The kit of embodiment 150, wherein the one or more additional growth-stimulatory molecules include IL2 and/or IL7, or fragments thereof.
152. The kit of any one of embodiments 148-151, wherein the growth stimulatory molecule is attached to a covalently modified bead.
153. The kit of any one of embodiments 131-152, wherein the first coupling agent is streptavidin.
154. A method of preparing a covalently functionalized surface including a plurality of biotin-binding agent or biotin functionalities and at least a first plurality of surface-blocking molecular ligands, wherein the method includes: reacting at least a first subset of reactive moieties of an intermediate reactive synthetic surface with a plurality of linking reagents, each linking reagent including biotin-binding agent or biotin; and reacting at least a second subset of reactive moieties of the intermediate reactive synthetic surface with a plurality of surface-blocking molecules, thereby providing the covalently functionalized synthetic surface including at the least one plurality of biotin-binding agent or biotin functionalities and at the least first plurality of surface-blocking molecular ligands.
155. The method of embodiment 154, wherein the linking reagents comprise biotin and the method further comprises noncovalently associating a biotin-binding agent with the biotin functionalities.
156. The method of embodiment 154 or 155, wherein the reactive moieties of at least first region of the intermediate reactive synthetic surface include azide moieties.
157. The method of any one of embodiments 154-156, wherein the reacting of the surface-blocking molecules is performed after the reacting of the linking reagents including biotin-binding agent or biotin functionalities.
158. The method of any one of embodiments 154-156, wherein the reacting of the surface-blocking molecules is performed at the same time as the reacting of the plurality of linking reagents.
159. The method of any one of embodiments 154-158, wherein the plurality of biotin-binding agent or biotin functionalities and the at least first plurality of surface-blocking molecular ligands are disposed in at least a first region of the covalently functionalized synthetic surface.
160. The method of embodiment 159, wherein the covalently functionalized synthetic surface includes a second region wherein the plurality of biotin-binding agent or biotin functionalities is excluded.
161. The method of embodiment 160, wherein the at least first plurality of surface-blocking molecular ligands are disposed in the second region of the covalently functionalized synthetic surface.
162. The method of embodiment 161, wherein the reacting of the reagent including surface-blocking molecules in the second region of the intermediate reactive synthetic surface is performed before the reacting of the linking reagents including biotin-binding agent or biotin functionalities in the at least first region of the intermediate reactive synthetic surface.
163. The method of embodiment 162, further including reacting a second plurality of surface-blocking molecules with a second subset of reactive moieties in the at least first region of the intermediate reactive synthetic surface.
164. The method of any one of embodiments 159-163, wherein the reacting of the plurality of biotin-binding agent or biotin functionalities and the reacting of the at least first plurality of surface-blocking molecules is performed at a plurality of sub-regions of the at least first region of the covalently prepared synthetic surface including reactive moieties.
165. The method of any one of embodiments 154-164, further including preparing the intermediate reactive synthetic surface, including: reacting at least a first surface preparing reagent including azide reactive moieties with surface-exposed moieties disposed at at least a first region of a reactive synthetic surface.
166. The method of embodiment 165, further including reacting a second portion of surface-exposed moieties disposed in a second region of the reactive synthetic surface with a plurality of surface-blocking molecules.
167. The method of embodiment 165 or 166, wherein the surface-exposed moieties of the at least first region of the reactive synthetic surface and the surface-exposed moieties of the second region of the reactive synthetic surface are not the same surface-exposed moieties.
168. The method of embodiment 166 or 167, wherein the second portion of the reactive synthetic surface includes surface exposed moieties configured to substantially not react with the pluralities of the primary activating and co-activating molecules.
169. The method of any one of embodiments 166-168, wherein the reacting the surface-exposed moieties of the second portion of the reactive synthetic surface with the plurality of surface-blocking molecules is performed before reacting the surface exposed moieties of the first portion of synthetic surface with the at least first surface preparing reagent to provide a covalently prepared surface at the first portion of the surface.
170. The method of any one of embodiments 165-169, wherein the surface-exposed moieties are nucleophilic moieties.
171. The method of any one of embodiments 165-170, wherein the surface-exposed moieties are displaceable moieties.
172. The method of any one of embodiments 154-171, wherein the distribution of the plurality of biotin-binding agent or biotin functionalities on the covalently functionalized synthetic surface is from about 6×102 to about 5×103 molecules per square micron, in each region where it is attached.
173. The method of any one of embodiments 154-171, wherein the distribution of the plurality of biotin-binding agent or biotin functionalities on the covalently functionalized synthetic surface is from about 5×103 molecules to about 1×104 molecules per square micron, in each region where it is attached.
174. The method of any one of embodiments 154-171, wherein the distribution of the plurality of biotin-binding agent or biotin functionalities on the covalently functionalized synthetic surface is from about 5×103 to about 3×104 molecules per square micron, about 5×103 to about 2×104 molecules per square micron, about 1×104 to about 3×104 molecules per square micron, about 1×104 to about 2×104 molecules per square micron, or about 1.25×104 to about 1.75×104 molecules per square micron, in each region where it is attached.
175. The method of any one of embodiments 154-174, wherein the surface is metal, glass, ceramic, polymer, or a metal oxide.
176. The method of any one of embodiments 154-175, wherein the surface is a surface of a bead, a surface of a wafer of any configuration, an inner surface of a tube, or at least one inner surface of a microfluidic device.
177. The method of embodiment 176, wherein the bead has a surface area within 10% of the surface area of a sphere of an equal volume or diameter.
178. The method of embodiment 176, wherein the tube is a glass or polymer tube.
179. The method of any one of embodiments 154 or 156-178, wherein the linking reagents include the biotin-binding agent.
180. The method of any one of embodiments 154-179, further comprising preparing an antigen-presenting surface for activating a T lymphocyte (T cell), including:
opening of the connection region ranges from about 20 microns to about 60 microns.
378. The surface, kit, or method of any one of embodiments 373-376, wherein the length Lcon of the connection region from the proximal opening to the distal opening is between about 20 microns and about 500 microns.
379. The surface, kit, or method of any one of embodiments 373-378, wherein a width of the microfluidic channel at the proximal opening of the connection region is between about 50 microns and about 500 microns.
380. The surface, kit, or method of any one of embodiments 373-379, wherein a height of the microfluidic channel at the proximal opening of the connection region is between 20 microns and 100 microns.
381. The surface, kit, or method of any one of embodiments 373-380, wherein the volume of the isolation region ranges from about 2×104 to about 2×106 cubic microns.
382. The surface, kit, or method of any one of embodiments 373-381, wherein the proximal opening of the connection region is parallel to a direction of the flow of the first medium in the flow region.
383. The surface, kit, or method of any one of embodiments 363-382, wherein the microfluidic device comprises an enclosure comprising a base, a microfluidic circuit structure disposed on the base, and a cover which collectively define a microfluidic circuit, and the microfluidic circuit comprises the flow region, the microfluidic channel, and the sequestration pen.
384. The surface, kit, or method of embodiment 383, wherein the microfluidic circuit further comprises one or more inlets through which the first medium can be input into the flow region and one or more outlets through which the first medium can be removed from the flow region.
385. The surface, kit, or method of embodiment 383 or 384, wherein the cover is an integral part of the microfluidic circuit structure.
386. The surface, kit, or method of any one of embodiments 383-385, wherein barriers defining the microfluidic sequestration pen extend from a surface of the base of the microfluidic device to a surface of the cover of the microfluidic device.
387. The surface, kit, or method of any one of embodiments 383-386, wherein the cover and the base are part of a dielectrophoresis (DEP) mechanism for selectively inducing DEP forces on a micro-object.
388. The surface, kit, or method of any one of embodiments 383-387, wherein the microfluidic device further comprises a first electrode, an electrode activation substrate, and a second electrode, wherein the first electrode is part of a first wall of the enclosure and the electrode activation substrate and the second electrode is part of a second wall of the enclosure, wherein the electrode activation substrate comprises a photoconductive material, semiconductor integrated circuits, or phototransistors.
389. The surface, kit, or method of embodiment 388, wherein the first wall of the microfluidic device is the cover, and wherein the second wall of the microfluidic device is the base.
390. The surface, kit, or method of embodiment 388 or 389, wherein the electrode activation substrate comprises phototransistors.
391. The surface, kit, or method of any one of embodiments 383-390, wherein the cover and/or the base is transparent to light.
392. One or more activated T cells produced by the method of any one of embodiments 265 to 337.
393. A population of T cells comprising activated T cells produced by the method of any one of embodiments 265-337.
394. The cell or population of embodiment 392 or 393, wherein the activated T cells are CD45RO+.
395. The cell or population of any one of embodiments 392-394, wherein the activated T cells are CD28+.
396. The cell, population, or method of any one of embodiments 265-337 or 392-395, wherein the activated T cells are CD28high.
397. The cell, population, or method of any one of embodiments 265-337 or 392-396, wherein the activated T cells are CD127+.
398. The cell, population, or method of any one of embodiments 265-337 or 392-397, wherein the activated T cells are CD197+.
399. The cell, population, or method of any one of embodiments 265-337 or 392-398, wherein the activated T cells are CD8+.
400. A microfluidic device comprising the cell or population of any one of embodiments 392-399.
401. The microfluidic device of any one of embodiments 61-96, comprising the cell or population of any one of embodiments 392-399.
402. A pharmaceutical composition comprising the cell or population of any one of embodiments 392-399.
403. The method of any one of embodiments 257-327, 362-381. or 382-389, wherein the method produces a population of T cells, wherein at least 1%, 1.5%, 2%, 3%, 4%, 5%, 6%, 7%, 8%, 9%, or 10% of the population of T cells are antigen-specific T cells, wherein each of the foregoing values are modified by “about.”.
404. The method of embodiment 403, wherein 1%-2%, 2%-3%, 3%-4%, 4%-5%, 5%-6%, 6%-7%, 7%-8%, 8%-9%, 9%-10%, 10%-11%, or 11%-12% of the T cells are antigen-specific T cells wherein each of the foregoing values are modified by “about.”.
405. The method of embodiment 403 or 404, wherein at least 65%, 70%, 75%, 80%, 85%, 86%, 87%, 88%, 89%, 90%, 91%, 92%, 93%, 94%, 95%, 96%, 97%, or 98% of the antigen-specific T cells are CD45RO+/CD28High cells, wherein each of the foregoing values are modified by “about.”
406. A method of treating a subject in need of treating a cancer; including: obtaining a plurality of T lymphocytes (T cells) from the subject; contacting the plurality of T cells with an antigen-presenting synthetic surface including a plurality of major histocompatibility complex (MHC) I molecules configured to bind to a T cell receptor of each of the plurality of T cells, wherein the MHC molecules include an antigen specific for the cancer of the subject and wherein the antigen-presenting synthetic surface is the antigen-presenting synthetic surface of any one of embodiments 1-96 or produced according to a method of any one of embodiments 181-264; producing a plurality of activated T cells, wherein the activation is configured to be specific against the cancer of the subject; separating the plurality of specific activated T cells from unactivated cells; and, introducing the plurality of antigen-specific activated T cells into the subject.
407. The method of embodiment 406, wherein the T cells are activated using the method of any one of embodiments 365-337.
408. The method of embodiment 406 or 407, further including enriching the sample including T lymphocytes before contacting the T lymphocytes with the covalently modified synthetic surface.
409. The method of any one of embodiments 406-408, wherein the separating the plurality of antigen-specific activated T cells further includes detecting a plurality of surface biomarkers of the antigen-specific activated T cells.
410. The method of embodiment 409, wherein the plurality of surface biomarkers comprises CD45RO+.
411. The method of embodiment 409 or 410, wherein the plurality of surface biomarkers comprises CD28+.
412. The method of any one of embodiments 409-411, wherein plurality of surface biomarker comprises CD28high.
413. The method of any one of embodiments 409-412, wherein plurality of surface biomarkers comprises CD8.
414. The method of any one of embodiments 409-413, wherein plurality of surface biomarkers comprises CD127.
415. The method of any one of embodiments 409-414, wherein plurality of surface biomarkers comprises CD197.
416. The method of any one of embodiments 406-415, further including rapidly expanding the antigen-specific activated T cells to provide an expanded population of antigen-specific activated T cells.
417. The method of embodiment 416, wherein the rapid expansion is performed after separating the specific activated T cells from the unactivated T cells.
418. The method of any one of embodiments 406-417, wherein the method of treating the subject delays or stops progression of the cancer in the subject.
This application is a continuation of International Patent Application No. PCT/US2018/043146, filed Jul. 20, 2018, which claims priority from U.S. Provisional Application No. 62/664,279, filed Apr. 30, 2018; U.S. Provisional Application No. 62/660,779, filed Apr. 20, 2018; and U.S. Provisional Application No. 62/535,742, filed Jul. 21, 2017, the contents of each of which are incorporated herein by reference in their entirety.
| Number | Date | Country | |
|---|---|---|---|
| 62664279 | Apr 2018 | US | |
| 62660779 | Apr 2018 | US | |
| 62535742 | Jul 2017 | US |
| Number | Date | Country | |
|---|---|---|---|
| Parent | PCT/US2018/043146 | Jul 2018 | US |
| Child | 16743849 | US |
