Patent Application
20200206730
Separation of biomaterial has been applied in a variety of contexts. For example, separation techniques for separating proteins from other biomaterials are used in a number of analytical processes.
Acoustophoresis is a technique for separating particles and/or secondary fluids from a primary or host fluid using acoustics, such as acoustic standing waves. Acoustic standing waves can exert forces on particles in a fluid when there is a differential in density and/or compressibility, known as the acoustic contrast factor. The pressure profile in a standing wave contains areas of local minimum pressure amplitudes at standing wave nodes and local maxima at standing wave anti-nodes. Depending on their density and compressibility, the particles can be driven to and trapped at the nodes or anti-nodes of the standing wave. Generally, the higher the frequency of the standing wave, the smaller the particles that can be trapped.
This disclosure describes technologies relating to methods, systems, and apparatus for acoustic separation of materials. The materials being separated may be biomaterials. The separation may employ material support structures. The support structures may be beads. A functionalized material may be applied to the support structures that has an affinity for one or more materials to be separated. The support structures may be mixed in a fluid that contains the materials. The fluid mixture may be provided to a fluid column or flow chamber. The support structures can be retained in the column against a fluid or fluid mixture flow through the column by provision of an acoustic standing wave at one end of the column that can prevent the support structures from passing.
In accordance with some examples, an acoustic affinity system is implemented that can include the features of being closed, automated and/or single-use. The system can be considered closed if the components can be sealed from an open-air environment. An automated system is able to operate autonomously, with little or no operator intervention. The system is single use when components and materials employed for an affinity separation run, which may include multiple recirculations, are disconnected and discarded after an affinity separation run. A single use system can avoid the additional steps of cleaning and sterilizing the equipment components and materials for subsequent runs.
In some examples, methods, systems, and apparatuses are disclosed for separation of biomaterials accomplished by functionalized material distributed in a fluid chamber that bind the specific target materials. The specific target materials can be particles, including cells, recombinant proteins and/or monoclonal antibodies. The functionalized material, which may be beads and/or microcarrier structures are coated or otherwise provided with an affinity material for attracting and binding the specific target materials. The affinity material may be a protein, ligand or other material that can form a bond with the target material.
In some example implementations, the affinity material and the target material can form antigen-antibody interactions with binding sites on the functionalized material. In some instances, the target material become bound to the functionalized material when a ligand of the target material or the functionalized material is conjugated to a matrix on the complementary material. The functionalized material includes functionalized microbeads. The functionalized microbeads include a particular antigen ligand that has affinity for a corresponding antibody.
In some examples, material adhered to the support structures with the functionalized material remains in the column, while other free material in the fluid may pass through the acoustic standing wave to provide separation of materials. The support structures may be implemented to have a certain acoustic contrast factor based on their density, compressibility, size or other characteristics that permits the support structures to react more strongly to the acoustic standing wave than other materials in the fluid mixture.
The support structures may be agitated in the column to enhance the affinity process. In different modes, the column fluid mixture that passes through the acoustic standing wave can be recirculated to the column or not. The fluid flow in the column can be controlled to flow or not, and when flowing, the rate of flow can be controlled. The fluid may be stationary in the column and may have other processes applied thereto, such as temperature adjustment, agitation, incubation, and/or any other useful process. The volume of the column can be effectively modified, such as with the provision of a plunger or piston in the column. Heating or cooling can be applied to the column or the contents of the column, internally or externally to the column.
The particulates may include beads, and wherein at least one of the beads comprises a sphere with a diameter of about 20 to 300 μm and comprises at least one of DEAE (N, N-diethylaminoethyl)-dextran, glass, polystyrene plastic, acrylamide, collagen, or alginate. The cell-supporting material may include microbubbles that have a surface coating for growth of the cells. The cells may include, for example, T-cells, MRC-5 cells or stem cells.
An acoustic transducer can be used to generate the acoustic standing wave, which can generate pressure forces in one or multiple dimensions. In multiple dimensions, the acoustic standing wave forces can be of the same order of magnitude. For example, forces in the direction of wave propagation may be of the same order of magnitude as forces that are generated in a different direction. An interface region can be generated near a border of the acoustic standing wave that contributes to preventing support structures from passing. Multiple transducers may be used, some for generating an acoustic wave in one or modes, and others for generating an acoustic wave in another, different mode. For example, the acoustic wave can be a standing wave that can generate pressure forces in one dimension or in multiple dimensions. The acoustic wave can be generated in a mode to form an interface region to prevent passage of certain materials while permitting passage of other materials. The acoustic wave can be generated in a mode to trap and cluster certain materials that build in size until the gravity or buoyancy forces on the clusters surpass the other forces on the clusters, such as fluidic or acoustic forces, so that the clusters drop or rise out of the acoustic wave.
Collecting cells may be performed with or without turning off the acoustic transducer. An additive which enhances aggregation of the support structures into the flow chamber may be applied. The method may further include recirculating the support structures, such as beads, to a culturing chamber coupled to the flow chamber. The method may also include processing the collected cells for infusion into a subject patient. Subsequent to preferentially trapping, the method may include allowing the trapped cells and/or cell-supporting material to rise or settle out of the fluid due to a buoyance or gravity force. The rising or settling cells and/or support material may exit the flow chamber. The mode of trapping cells or support material for separation by rising or settling out of the fluid may be accompanied by a mode of preventing or permitting the cells and/or support material from passing through a fluid path. The mode of preventing or permitting passage may be implemented with an acoustic wave with an interface region across the fluid path.
In some example implementations, the material includes target compounds, such as recombinant proteins and monoclonal antibodies, viruses, and/or live cells (e.g., T cells). Beads or microcarriers with or without functionalized material on their surfaces may be the target compounds or components.
An example apparatus may include a flow chamber configured to receive fluid containing functionalized material. The flow chamber may be in the form of a column. An acoustic transducer is arranged in relation to the flow chamber, for example, acoustically coupled to the flow chamber, to provide an acoustic wave or signal into the flow chamber when excited. Excitation of the transducer can generate a multi-dimensional acoustic field inside the chamber that includes first spatial locales where acoustic pressure amplitude is elevated from a base level, such as, for example when the acoustic transducer is turned off, and second spatial locales where acoustic pressure amplitude has little or no elevation from the base level, for example the acoustic pressure amplitude may be equivalent to that when the acoustic transducer is turned off.
In some modes, the functional material may be driven to and retained at the first or second locales of the multidimensional acoustic field. In other modes, the functional material may be prevented from entering the multidimensional acoustic field in accordance with an edge effect at an interface region. Materials to be processed that include target materials for separation may be flowed into the flow chamber where functionalized material is retained such that a portion of the target materials with features complementary to the functionalized material become bound to the functionalized material while other portions of the materials pass through the flow chamber. The chamber may be configured for vertical flow which may be in an upward or downward direction. Fluid paths to the chamber may be provided at a top and/or bottom of the chamber. An acoustic transducer can be coupled to a top and/or bottom of the chamber to generate an acoustic field at that locale.
The functionalized microcarriers may also be circulated after the recombinant proteins or monoclonal antibody is eluted from the surface by a buffer or other process elution. This allows for greater surface area and affinity interaction of the functionalized microcarriers with the expressed proteins from the bioreactor, increasing the efficiency of the acoustic fluidized bed chromatography process.
In some example implementations, the apparatus provides functionalized particles, such as beads, in an arrangement that provides more space between particles, such as beads or cells, than packed columns. The lower density decreases the likelihood that non-target biomaterials will clog flow paths between the functionalized particles. In some example implementations, recirculating media containing the target biomaterials in effect increases the capture surface area of the apparatus by passing free target biomaterials past the functionalized particles multiple times. The reduced contact of non-target biomaterials such as cells can help preserve the viability of cells. The technology described here can be used in high- or low-density cell culture, new research applications, large production culture volumes, e.g., more than 1,000 liters, efficient monitoring and culture control, reduction of costs and contamination in cell culture applications.
The details of one or more implementations of the subject matter described in this specification are set forth in the accompanying drawings and the description below. Other features, aspects, and advantages of the subject matter will become apparent from the description, the drawings, and the claims.
The disclosure is described in greater detail below, with reference to the accompanying drawings, in which:
This disclosure describes methods, systems and apparatuses that employ an acoustic standing wave with nodes and antinodes to separate support structures such as beads or coated microbubbles from other materials in a chamber such as a column. The example implementations described herein may be operated in different modes. For example, in some modes, an acoustic wave is generated with certain characteristics across the chamber. The acoustic wave may be generated by an acoustic transducer, which may be located at one end of the column. The acoustic wave may cause an interface region to be generated that blocks certain materials from entering the acoustic wave, while permitting passage of other materials. The acoustic wave characteristics can be controlled to block or pass materials based on parameters such as compressibility, density, size, acoustic contrast factor, and any other parameter that is responsive to the acoustic waves. In other modes, an acoustic wave is generated with spatial locales that capture materials to form clusters that increase in size to a point where the gravity or buoyancy force on the cluster exceeds that of the acoustic or fluid drag force, causing the cluster to exit the acoustic wave.
The modes discussed herein may be employed together or separately or in combination. The modes may be employed or generated with one or more acoustic transducers. The acoustic field generated by the acoustic wave can be configured to block or permit passage of certain materials. For example, support structures for cells, which may be in the form of beads, bead/cell complexes or particles, may be blocked from passage through the acoustic field. Materials such as cells may be passed through the fluid chamber. The support structures include functionalized material that can bind with at least some of the material passed through the fluid chamber. The material that is bound to the support structures via the functionalized material is retained in the fluid chamber by the support structures being retained in the fluid chamber with the acoustic wave. Material that is not bound to the support structures may pass out of the fluid chamber through the acoustic wave. The technique of using acoustic waves to perform affinity separation obtains a number of advantages as described in more detail herein.
Referring to
In accordance with some examples, an acoustic affinity system is implemented that can include the features of being closed, automated and/or single-use. The system can be considered closed if the components can be sealed from an open-air environment. An automated system is able to operate autonomously, with little or no operator intervention. The system is single use when components and materials employed for an affinity separation run, which may include multiple recirculations, are disconnected and discarded after an affinity separation run. A single use system can avoid the additional steps of cleaning and sterilizing the equipment components and materials for subsequent runs.
Previous systems for affinity separation employed magnetically responsive beads. These beads may incur challenges during manufacturing processes as they do not dissolve or are not readily consumed in vivo and are preferentially completely removed from any treatment supplied to a patient. While such beads may be used in the present acoustic affinity separation system, the use of acoustics offers the possibility for the use of support structures, such as beads, that are tailored to be specifically acoustically responsive. For example, the beads can be nonmagnetic or non-magnetically responsive, and highly acoustically responsive. The acoustically responsive beads can be composed of a variety of materials, significantly increasing the flexibility of the processing system in which they are employed. These acoustic affinity beads can be composed of dissolvable material that is biocompatible, which can alleviate aggressive bead removal processes that are employed with magnetically responsive beads.
The acoustic affinity system can be configured to have increased throughput compared with current systems. For example, the fluid flow rate through the system can be increased over that typically used with conventional affinity systems. The system can be configured with larger channels that permit higher flow rates and volumes. The expansion of the cell population can be implemented within the presently disclosed systems or can be implemented externally and fed to the acoustic affinity system.
The configuration of the acoustic affinity system permits the use of multiple types of support structures or beads that may have different characteristics, such as different ranges of sizes or densities. The different groups of support structures or beads may be provided with different types of functionalized material such as proteins, antigens or antibodies to thereby enable multiplexing of affinity separation. This configuration permits complex, single-pass affinity selections to be realized.
In some example implementations, a column is provided with a volume of beads that have an affinity for a certain type of cell. Cells introduced into the column form a complex with the beads, which complexes can be separated from the column volume using acoustic techniques. The separation may be leveraged to harvest cultured cells of interest, and the extracted cells may be infused into a patient. Using acoustics with an affinity binding system to separate cultured cells of interest can be applicable to a variety of cell therapy applications, e.g., vaccine therapies, stem cell therapies, particularly allogenic and autologous therapies, or regenerative therapies.
An acoustic wave is generated in a flow chamber, such as a column, to effectuate separation of beads and bead complexes from unbound cells or materials in a fluid. The separation can be negative or positive, where the unwanted material to be excluded is bound to the beads, or where the material desired in the separation is bound to the beads, respectively. The material of interest, for either negative or positive selection, may be different types of cells, including adherent cells. Example adherent cells may include human multipotent stem cells (hMSC), human mesenchymal stem cells (also hMSC), human pluripotent stem cells (hPSC), human dermal fibroblasts (hDF), human chondrocytes, and some T lymphocytes. Adherent cells may differ in their antigen specificity (e.g. CD8 adherent cell). The lines used in cell therapy may be mono- or polyclonal (e.g. polyclonal CD8 adherent cell line), and CAR (chimeric antigen receptor) adherent cells (a.k.a. artificial adherent cell receptors, or chimeric adherent cell receptors, or chimeric immunoreceptors. These are T-cells modified to recognize a specific protein. The beads employed in the acoustic affinity separation system can be configured to bind or not bind to these cells or material of interest for negative or positive selection.
The bead technology described here can be used in high density cell culture, new research applications, large production culture volumes, e.g., more than 1,000 liters, efficient monitoring and culture control, reduction of costs and contamination in cell culture applications. The beads used may be commercially available, such as the MAGNE magnetic affinity beads or polystyrene beads supplied by Promega Corporation or MACS (magnetic-activated cell sorting) beads supplied by Miltenyi Biotec. The size of the beads, for example their diameter, may be in the nanometer or micrometer range. Cospheric beads may be used, which are beads with at least two layers. The layers may have different characteristics, such as differing contrast factors, structural rigidity, or any other characteristics that are desired to be combined in a single bead through the use of multiple layers.
Some implementations may use microbubbles as support structures to bind material of interest. The microbubbles can be composed by a shell of biocompatible materials and ligands capable of linking to the cells or material of interest, including proteins, lipids, or biopolymers, and by a filling gas. Low density fluids may be used for relative ease of manufacturing. The microbubble shell may be stiff (e.g., denaturated albumin) or flexible (phospholipids) and presents a thickness from 10 to 200 nm. The filling gas can be a high molecular weight and low-solubility filling gas or liquid (perfluorocarbon or sulfur hexafluoride), which can produce an elevated vapor concentration inside the microbubble relative to the surrounding fluid, such as blood, and increase the microbubble stability in the peripheral circulation. The microbubble shell can have a surface coating such as a lipid layer. The lipid layer may be utilized as scaffolds or substrates for material growth such as cells or biomolecules. Active groups may be easier to conjugate directly to the glass surface. The microbubbles may have a diameter in a range of 2 to 6 micrometers. The coated microbubbles may have a negative contrast factor.
Examples discussed above provide beads as support structures. Other support structures such as coated bubbles or microbubbles can be also used. For the sake of convenience, support structures may be referred to herein collectively as beads, which term is intended to encompass all types of support structures, including beads, bubbles, microcarriers and any other type of affinity material/support structure that can bind to or be bound to a target material of interest.
Cells are bound to beads, e.g., CD3/CD28 activated beads. As discussed in further detail below, the beads can be functionalized with surface chemistry such that the cells or material of interest can be attached to or adherent to the surface of the beads. The beads can include support matrices allowing for the growth of adherent cells in bioreactors or other cell culturing systems. In some cases, adherent cells will bind to the beads without the antigens on the surface and the beads can be functionalized or non-functionalized. Some examples of affinity applications include positive or negative selection of CD3+, CD3+CD4+ and/or CD3+CD8+ affinity selection for apheresis products. Other examples of affinity applications include positive or negative selection of TCR+ or TCR− cells.
Structurally, the beads include spheres with a diameter in a range of 1 to 300 μm, e.g., in the range of 125 to 250 μm. The spheres can have densities in a range of 1.02-1.10 g/cm3. In some instances, the beads can also include rod-like structures. The beads may be smooth or macroporous.
The core of the beads can be made from different materials, such as glass, polystyrene plastic, acrylamide, collagen, and alginate. The bead materials, along with different surface chemistries, can influence cellular behavior, including morphology and proliferation.
The beads can be coated with a variety of coatings such as glass, collagen (e.g., neutral or charged gelatin), recombinant proteins or chemical treatments to enhance cell attachment, which may lead to more desirable cell yields for a number of different cell lines.
Surface chemistries for the beads can include extracellular matrix proteins, recombinant proteins, peptides, and positively or negatively charged molecules. The surface charges of the micro carriers may be introduced from a number of different groups, including DEAE (N, N-diethylaminoethyl)-dextran, laminin or vitronectin coating (extra cellular matrix proteins). In the DEAE-dextran example, a mild positive charge can be added to the surface.
Other examples of bead coatings, for example with functionalized material for use in biological affinity processes, include streptavidin, monomeric avidin, protein A, anti-CD3, as well as other known functionalized material for binding biological material. Various combinations of antibodies, reagents and/or functionalized material can be used with the beads to bind to a cell of interest. A cell of interest may be identified with target proteins or markers, such as CD3, for example.
In some implementations, the beads are formed by substituting a cross-linked dextran matrix with positively charged DEAE groups distributed throughout the matrix. This type of bead can be used for established cell lines and for production of viruses or cell products from cultures of primary cells and normal diploid cell strains.
In some implementations, the beads are formed by chemically coupling a thin layer of denatured collagen to the cross-linked dextran matrix. Since the collagen surface layer can be digested by a variety of proteolytic enzymes, it provides opportunities for harvesting cells from the beads while maintaining increased or maximum cell viability and membrane integrity. The acoustic affinity system discussed herein can be operated with a number of types of beads, three general groupings of which are discussed below.
The beads may be constructed and configured according to cGMP (current good manufacturing practice) standards or regulations. One example group of beads that may be used in the acoustic affinity system are large, dense beads. These large beads may possess the following characteristics.
Another example group of beads are those referred to herein as medium sized beads. These medium sized beads may possess the following characteristics.
Another example group of beads are those referred to herein as small beads. These small beads may possess the following characteristics.
Different types of beads may be chosen for different types of applications. For example, larger beads may be used when the cells are cultured with the beads, or when the affinity binding takes place in a non-flowing mode.
The beads used for the affinity binding can be held back by or passed through an acoustic wave generated by an acoustic transducer. The acoustic transducer may generate a multi-dimensional acoustic standing wave in a flow chamber to create an acoustic field that includes locales of increased pressure radiation forces. The acoustic transducer can include a piezoelectric material that is excited to vibrate and generate an acoustic wave. The acoustic transducer can be configured to generate higher order vibration modes. For example, the vibrating material in the acoustic transducer can be excited to obtain a standing wave on the surface of the vibrating material. The frequency of vibration is directly related to the frequency of the excitation signal. In some implementations, the vibrating material is configured to have an outer surface directly exposed to a fluid layer, e.g., the fluid or mixture of beads and cultured cells in a fluid flowing through the flow chamber. In some implementations, the acoustic transducer includes a wear surface material covering an outer surface of the vibrating material, the wear surface material having a thickness of a half wavelength or less and/or being a urethane, epoxy, or silicone coating, polymer, or similar thin coating. In some implementations, the acoustic transducer includes a housing having a top end, a bottom end, and an interior volume. The vibrating material can be positioned at the bottom end of the housing and within the interior volume and has an interior surface facing to the top end of the housing. In some examples, the interior surface of the acoustic material is directly exposed to the top end housing. In some examples, the acoustic transducer includes a backing layer contacting the interior surface of the acoustic material, the backing layer being made of a substantially acoustically transparent material. One or more of the configurations can be combined in the acoustic transducer to be used for generation of a multi-dimensional acoustic standing wave.
The generated multi-dimensional acoustic standing wave can be characterized by strong gradients in the acoustic field in all directions, not only in the axial direction of the standing waves but also in lateral directions. In some instances, the strengths of such gradients are such that the acoustic radiation force is sufficient to overcome drag forces at linear velocities on the order of mm/s. Particularly, an acoustic radiation force can have an axial force component and a lateral force component that are of the same order of magnitude. As a consequence, the acoustic gradients result in strong trapping forces in the lateral direction.
The multi-dimensional acoustic standing wave can give rise to a spatial pattern of acoustic radiation force. The multidimensional acoustic standing wave may be generated from one transducer and reflector pair due to the multimode perturbations of the piezoelectric material in the transducer. The acoustic radiation force can have an axial force component and a lateral force component that are of the same order of magnitude. The spatial pattern may manifest as periodic variations of radiation force. More specifically, pressure node planes and pressure anti-node planes can be created in a fluid medium that respectively correspond to floor acoustic radiation force planes with maximum and minimum acoustic radiation force planes in between pressure nodal and anti-nodal planes. Pressure nodal planes are also acoustic displacement anti-nodal planes, and vice versa. The spatial pattern may function much like a comb filter in the fluid medium.
In some modes, discussed in greater detail below, the spatial pattern may create an interface region that blocks entry of particles with certain characteristics from entering or crossing the acoustic wave. In other modes of operation, discussed in greater detail below, the spatial pattern may be used to trap particles, for example, of a particular size or size range, while particles of a different size or size range may not be trapped. The modes may be employed separately or together in combination to provide both a barrier and trapping function, in the same or separate locale.
In a multidimensional acoustic standing wave, the acoustic radiation forces within a particular pressure nodal plane are such that particles are trapped at several distinct points within these planes. The trapping of particles leads to the formation of cluster of particles, which continuously grow in size, and, upon reaching a critical size, settle out or rise out of the primary fluid continuously because of enhanced gravitation or buoyancy settling. For example, the spatial pattern can be configured, for example, by adjusting the insonification frequency and/or phase, power, voltage and/or current supplied to the transducer, or fluid velocity or flow rate, to allow the cultured cells to freely flow through while trapping the support structures, such as beads or microbubbles, thereby separating at least the trapped support structures from cells or other materials in the fluid.
In some example implementations, one or more multi-dimensional acoustic standing waves are generated between an ultrasonic transducer and a reflector. An acoustic wave is continually launched from the acoustic transducer and reflected by the reflector to interfere with the launched acoustic wave to form an acoustic standing wave. The formation of the acoustic standing wave may depend on a number of factors, including frequency, power, medium, distance between the transducer and reflector, to name a few. The standing wave can be offset at the transducer or the reflector so that local minima or maxima are spaced from the transducer or from the reflector. The reflected wave (or wave generated by an opposing transducer) can be in or out of phase with the transducer generated wave. The characteristics of the standing wave can be modified and/or controlled by the drive signal applied to the transducer, such as by modifying and/or controlling the phase, amplitude or frequency of the drive signal. Acoustically transparent or responsive materials may also be used with the transducer or reflector to modify and/or control the standing wave.
As the fluid mixture flows between an ultrasonic transducer and reflector, or two facing ultrasonic transducers, between which one or more multi-dimensional acoustic standing waves are established, particles or secondary fluid cluster, collect, agglomerate, aggregate, clump, or coalesce. The clustering of material may take place at the nodes or anti-nodes of the multi-dimensional acoustic standing wave, depending on the particles' or secondary fluid's acoustic contrast factor relative to the host fluid. The particles form clusters that eventually exit the multi-dimensional acoustic standing wave nodes or anti-nodes when the clusters have grown to a size large enough to overcome the holding force of the multi-dimensional acoustic standing wave. For example, the clusters grow in size to a point where the gravity or buoyancy forces become dominant over the acoustic or fluid drag forces, causing the clusters to respectively sink or rise. For fluids/particles that are denser than the host fluid, such as is the case with most cells, the clusters sink and can be collected separately from the clarified host fluid. For fluids/particles that are less dense than the host fluid, the buoyant clusters float upwards and can be collected.
The scattering of the acoustic field off the particles creates secondary acoustic forces that contribute to driving particles or fluid droplets together. The multi-dimensional acoustic standing wave generates a three-dimensional acoustic radiation force, which acts as a three-dimensional trapping field. The acoustic radiation force is proportional to the particle volume (e.g. the cube of the radius) when the particle is small relative to the wavelength. The force is proportional to frequency and the acoustic contrast factor. The force scales with acoustic energy (e.g. the square of the acoustic pressure amplitude). When the acoustic radiation force exerted on the particles is stronger than the combined effect of fluid drag force and buoyancy and gravitational force, the particles are trapped within the acoustic standing wave. The particle trapping in a multi-dimensional acoustic standing wave results in clustering, concentration, agglomeration and/or coalescence of the trapped particles. Relatively large solids of one material can thus be separated from smaller particles of a different material, the same material, and/or the host fluid through enhanced gravitational/buoyancy separation.
The multi-dimensional standing wave generates acoustic radiation forces in a number of directions, including in the direction of acoustic wave propagation and in a direction that is the lateral to the acoustic wave propagation direction. As the mixture flows through the acoustic chamber, particles in suspension experience a strong axial force component in the direction of the standing wave. Since this acoustic force is across (e.g. perpendicular to) the flow direction, it is not aligned with the fluid drag force. The acoustic force can thus quickly move the particles to pressure nodal planes or anti-nodal planes, depending on the contrast factor of the particle. The lateral acoustic radiation force acts to move the concentrated particles towards the center of each planar node, resulting in clustering, agglomeration or clumping. The lateral acoustic radiation force component can overcome fluid drag for such clumps of particles, to continually grow the clusters, which can exit the mixture due to dominant gravity or buoyancy forces. The drop in drag per particle as the particle cluster increases in size, as well as the drop in acoustic radiation force per particle as the particle cluster grows in size, may separately or collectively influence operation of the acoustic separator device. In the present disclosure, the lateral force component and the axial force component of the multi-dimensional acoustic standing wave are of the same or different order of magnitude. In a multi-dimensional acoustic standing wave generated by a single transducer, the axial force can be comparable with the lateral force. The lateral force of such a multi-dimensional acoustic standing wave is much higher than the lateral force of a planar standing wave, usually by two orders of magnitude or more.
The multi-dimensional acoustic standing wave generated for various modes, including to form a barrier or for clustering, is obtained by exciting a piezoelectric material at a frequency that excites a fundamental 3D vibration mode of the transducer. The transducer may be composed of various materials that may be perturbed to generate an ultrasonic wave. For example, the transducer may be composed of a piezoelectric material, including a piezoelectric crystal or poly-crystal. Perturbation of the piezoelectric material, which may be a piezoelectric crystal or poly-crystal, in the ultrasonic transducer to achieve a multimode response allows for generation of a multidimensional acoustic standing wave. A piezoelectric material can be specifically designed to deform in a multimode response at designed frequencies, allowing for generation of a multi-dimensional acoustic standing wave. The multi-dimensional acoustic standing wave may be generated with distinct modes of the piezoelectric material such as a 3×3 mode that generates nine separate multidimensional acoustic standing waves. A multitude of multidimensional acoustic standing waves may also be generated by allowing the piezoelectric material to vibrate through many different mode shapes. Thus, the material can be selectively excited to operate in multiple modes such as a 0×0 mode (i.e. a piston mode), 1×1, 2×2, 1×3, 3×1, 3×3, and other higher order modes. The material can be operated to cycle through various modes, in a sequence or skipping past one or more modes, and not necessarily in a same order with each cycle. This switching or dithering of the material between modes allows for various multidimensional wave shapes, along with a single piston mode shape to be generated over a designated time. The transducers may be composed of a piezoelectric material, such as a piezoelectric crystal or poly-crystal, which may be made of PZT-8 (lead zirconate titanate). Such crystals may have a major dimension on the order of 1 inch and larger. The resonance frequency of the piezoelectric material may nominally be about 2 MHz and may be operated at one or more frequencies. Each ultrasonic transducer module may include single or multiple crystals. Multiple crystals can each act as a separate ultrasonic transducer and are can be controlled by one or multiple controllers, which controllers may include signal amplifiers. The control of the transducer can be provided by a computer control that can be programmed to provide control signals to a driver for the transducer. The control signals provided by the computer control can control driver parameters such as frequency, power, voltage, current, phase, or any other type of parameter used to excite the piezoelectric material. The piezoelectric material can be square, rectangular, irregular polygon, or generally of any arbitrary shape. The transducer(s) is/are used to create a pressure field that generates forces of the same order of magnitude in a lateral and an axial direction.
In some examples, the size, shape, and thickness of the piezoelectric material can determine the transducer displacement at different frequencies of excitation. Transducer displacement with different frequencies can be used to target certain material in an ensonified fluid. For example, higher frequencies with shorter wavelengths can target smaller sized material. Lower frequencies with longer wavelengths can target smaller sized material. In these cases of higher and lower frequencies, material that is not influenced by the acoustic wave may pass through without significant change. Higher order modal displacements can generate three-dimensional acoustic standing waves with strong gradients in the acoustic field in all directions, thereby creating strong acoustic radiation forces in all directions, which forces may, for example be equal in magnitude, leading to multiple trapping lines, where the number of trapping lines correlate with the particular mode shape of the transducer.
The piezoelectric crystals of the transducers described herein can be operated at various modes of response by changing the drive parameters, including frequency, for exciting the crystal. Each operation point has a theoretically infinite number of vibration modes superimposed, where one or more modes are dominant. In practice, multiple vibration modes are present at arbitrary operating points of the transducer, with some modes dominating at a given operating point.
Referring to
Interface region 202 is located at an upstream bounding surface or region of the volume of fluid that is ensonified by acoustic transducer 208. For example, the fluid may flow across interface region 202 to enter the ensonified volume of fluid and continue in a downstream direction. The frequency of acoustic standing wave 206 may be controlled to have desired characteristics, such that, for example, different contrast factor materials may be held back by or allowed through acoustic standing wave 206. Interface region 202 can be generated and controlled to influence, for example, particles of a first size range to be retained. Acoustic standing wave 206 can be generated and controlled to permit, for example, particles of a second size range that is different from the first to pass through. Acoustic standing wave 206 that forms interface region 202 may be modulated so as to block or pass selective materials. The modulation can be employed to block or pass selective materials at different times while fluid flows through the acoustic field generated by acoustic standing wave 206.
In some example implementations, acoustic standing wave 206 produces a three-dimensional acoustic field, which, in the case of excitation by transducer 208 implemented as a rectangular transducer, can be described as occupying a roughly rectangular prism volume of fluid across the direction of fluid flow. Acoustic wave 206 can be generated as a standing wave. The generation of acoustic wave 206 can be achieved with two transducers facing each other across the fluid flow. A single transducer, e.g., transducer 208, may be used to launch acoustic wave 206 through the fluid toward an interface boundary region that provides a change in acoustic properties, such as may be implemented with a chamber wall or reflector 210. The acoustic wave reflected from the interface boundary can contribute to forming a standing acoustic wave with the acoustic wave launched from transducer 208. During operation at different or changing flow rates, the location of interface region 202 may move upstream or downstream.
The acoustic field generated by acoustic standing wave 206 exerts an acoustic radiation pressure (e.g., a pressure rise) and an acoustic radiation force on the fluid and materials at interface region 202. The radiation pressure influences material in the fluid to block upstream materials with certain characteristics from entering the acoustic field. Other materials with different characteristics than the blocked materials are permitted to pass through the acoustic field with the fluid flow. The characteristics that affect whether the materials or particles are blocked or passed by the acoustic field include material compressibility, density, size and acoustic contrast factor. The parameters that can influence the generation or modulation of the acoustic wave include frequency, power, current, voltage, phase or any other drive parameters for operating transducer 208. Other parameters impacting acoustic wave 206 include transducer size, shape, thickness, as well as chamber size and fluid parameters such as density, viscosity and flow rate.
Referring to
In a clustering mode, beads 304, bead complexes 314 and/or particles such as cells cluster, collect, agglomerate, aggregate, clump, or coalesce within multi-dimensional standing wave 306. The clustering may occur at the nodes or anti-nodes of multi-dimensional acoustic standing wave 306, depending on the acoustic contrast factor of beads 304 or the particles relative to the host fluid. For example, beads 304, bead complexes 314 or particles that have a positive acoustic contrast factor are driven to the nodes of multi-dimensional acoustic standing wave 306, while beads 304, bead complexes 314 or particles that have a negative acoustic contrast factor are driven to the anti-nodes. The clustered beads 304, bead complexes 314 or particles form clusters 312 that eventually exit the nodes or anti-nodes of multi-dimensional acoustic standing wave 306 when clusters 312 have grown to a size large enough to overcome the holding force of multi-dimensional acoustic standing wave 306. For example, as clusters 312 grow in size in multi-dimensional acoustic standing wave 306, gravity or buoyancy forces begin to dominate over acoustic and/or fluid drag forces. Once the size of a cluster 312 is large enough to cause the gravity or buoyancy forces on cluster 312 to exceed the acoustic and/or fluid drag forces, cluster 312 exits multi-dimensional acoustic standing wave 306.
For beads 304, bead complexes 314 or particles that, for example, have a positive acoustic contrast factor, clusters 312 typically sink with gravity forces. For beads 304, bead complexes 314 or particles that, for example, have a negative acoustic contrast factor, clusters 312 typically rise with buoyancy forces. Gravity is not depicted in
In this mode of operation, beads 304, and bead complexes 314, are retained in the chamber by sinking or rising out of the acoustic wave. The beads tend to be lightly clustered in this mode and tend to be redistributed in the chamber to permit additional interaction with target material or cells. In addition, an agitator can be provided to the chamber to promote movement and redistribution of the clustered beads.
Particles such as cell Type A are not captured in multi-dimensional acoustic standing wave 306. The characteristics of the Type A cells and multi-dimensional acoustic standing wave 306 permit the Type A cells to pass without being captured and/or clustering. The Type B cells are bound to beads 304 to form bead complexes 314. Accordingly, Type B cells may themselves pass through multi-dimensional acoustic standing wave 306 but may be driven into a cluster 312 if bound to beads 304.
Referring to
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This affinity technique employed with fluidized bed system 500 can be implemented on a single-pass basis. System 500 can be configured with the choice of beads to select for material that passes through and exits column 502, or to select for material that is bound to the beads and retained in column 502. The passed or retained material can be positively or negatively selected.
Referring to
Process 600 offers a number of features that are advantageous for affinity separation of materials. For example, binding of target material to the beads can take place externally, which also permits flexible incubation steps. The acoustic separation provides a gentle and high throughput separation process that quickly reduces the amount of uncombined material in mix with bead complexes. For example, the separation process can be completed in less than one hour. Process 600 is also flexibly scalable and can handle processing volumes in the range of about 10 mL to about 1 L. In addition, all types of beads may be used in process 600, providing significant flexibility for unique or custom affinity separation processes.
Referring to
System 700 offers a number of advantageous features for affinity separation processes, including internal bead binding and low shear forces imposed on the material in column 702. The internal bead binding with low shear forces can be important when larger beads are used due to potentially greater binding energy that is associated with larger beads. For example, it may take longer, or a greater amount of energy, for targeted cellular material to be captured by the larger beads. Lower shear forces can thus help to avoid impeding binding with larger beads. System 700 can employ acoustic transducer 704 to create an acoustic edge effect, which can lead to improved throughput. For example, the processes of binding and separation can be completed in under 2 hours. System 700 is scalable and can handle processing volumes in the range of about 10 mL to about 1 L. The fluidized bed employed in system 700 can be used with beads or with cells for the purposes of affinity separation and/or separation alone.
Referring to
During the wash process and the introduction of the cellular material, transducer 806 may be operated in different modes or with different characteristics to, in one case, block the affinity beads from exiting during the wash process, and in another case, block both of the affinity beads and the cellular material from exiting. For example, the frequency used to drive transducer 806 may be different to retain the affinity beads than the frequency when both the cells and affinity beads are retained.
Once column 802 is loaded with affinity beads and cellular material, stirring mechanism 804 can be employed to agitate column 802. The agitation contributes to moving the affinity beads and the cellular material within column 802. As the affinity beads and cellular material move within column 802 the affinity binding process for targeted material can be enhanced. This incubation step can be implemented with no fluid flow and with transducer 806 being unenergized.
Once the incubation/binding process is completed, the affinity bead/targeted material complexes can be washed, and nontargeted material can be removed from column 802. The targeted material may be separated from the affinity beads with a solution provided to column 802 that promotes detachment of the targeted material from the affinity beads. For example, the solution can include enzymes (e.g., trypsin) in a buffer. For example, The targeted material may then be removed from column 802, while the affinity beads are retained with the acoustic field generated by the acoustic transducer 806.
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The column parameters were: volume—40 ml; height—20 cm; and diameter—1.6 cm. The expanded void fraction was 70% with a starting bead concentration of 7.86 E+05 cells/ml. Operating parameters were: frequency—1 MHz and power—3 W.
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System 1400 is operated similarly to those discussed above. For example, system 1400 may be used for positive or negative selection and can employ different modes of operation with the acoustic transducer 1404. System 1400 illustrates the use of recirculation to improve target cell recovery, by providing more opportunities for target cells to bind with beads in column 1402. After the beads are loaded into column 1402 and washed, a pass 1 feed is supplied to column 1402. The outflow of column 1402 resulting from the pass 1 feed is collected for use as a pass 2 feed. The pass 2 feed is used as the input for a feed supply in a follow-on recirculation pass. Although not shown, the pass 2 feed can generate an outflow that can be collected for another follow-on recirculation pass. Any number of recirculations can be employed. Each of the example systems and fluidized beds discussed herein can be configured to have multiple recirculation passes.
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Several experimental tests for acoustic affinity cell separation were conducted. The results of the tests are tabulated as examples below.
Four fluidized bed platform tests were performed with different cell concentrations (100 e6/mL and 10 e6/mL) and different capturing antibody combinations (Anti-TCR a/b only vs Anti-TCR a/b and Anti-CD52) on the first day of testing. The initial feed concentration (100 e6/mL and TCR a/b- population was 74-78%).
All samples were incubated with the corresponding capturing antibody combinations listed in Table 1 in 2% BSA in PBS for 20 minutes on the IKA roller (30 rpm). Cells were washed twice with 2% BSA in PBS and finally re-suspended in 10 mL 2% BSA in PBS. A sample was removed for flow cytometry and used as the initial population for tests A through D. Next, 4 ml of a 50% solid Promega bead slurry were loaded into the fluidized bed column and washed with 30 ml of a 2% BSA in PBS solution to remove residual ethanol and particulates. This initial washing step was performed at a flow rate and power of 1 ml/min and 0.75 W.
The feed cell population was then separated using the fluidized bed unit packed with avidin-conjugated methacrylate beads (Promega) which operated at the following conditions; flow rate—1 mL/min and power—0.75 W. The first fraction, denoted as the outflow, was collected after the entire sample was loaded into the fluidized bed. A second fraction, denoted as the flush, was collected after flushing the fluidized bed with 30 ml of a 2% BSA in PBS solution at 1 ml/min and 0.75 W. This flushing step is implemented to ensure all uncaptured cells are recovered. Once this process was completed, the remaining contents of the column were retrieved and collected as the third fraction, denoted as the holdup. Samples from all three fractions were collected for flow cytometry. For the purposes of conducting a mass balance, the mass and cell count for each fraction was recorded.
The purity increased by approximately 15% for all samples after separation by the fluidized bed unit, where the initial cell population consisted of 76% TCR knockout cells. In tests conducted at a higher cell concentration (100 E6 cells/mL), samples A and B yielded a purity of 13% and 10% in the outflow and 11% and 8% in the flush respectively showing a slight decrease in purity in the second fraction. The purity in the holdup fraction was 73.2% and 68.1% for samples A and B indicating that 100% purity was not achieved.
Tests conducted at lower cell concentrations (10 E6 cells/mL) yielded a higher purity of 90.5% and 92.4% in the outflow fraction and even higher purity in the flush fraction of 94.8% and 93.2% in samples C and D respectively. This result showed that lower cell concentrations were better with current conditions used with the fluidized bed unit. Overall employing the combination of anti-TCR and anti-CD52 as capturing antibodies did not yield significantly different purity compared to using anti-TCR as the sole capturing antibody.
The total TCR-recovery for each test is equal to the sum of TCR-cells in the flow-through and flush fractions divided by the starting TCR-cell count (See Eq. 6 in Appendix). There are two mechanisms by which TCR-cells could be retained in the fluidized bed system: acoustic retention and inefficient flushing. Acoustic retention occurs when a free cell experiences a greater force from the acoustic field compared to the drag force exerted by the fluid flow. This happens at high power to flow rate ratios and can be prevented by optimizing operating conditions. Cells also tend to disperse into the volume of the system, making a flush step necessary to improve recovery. The flushing step should have a uniform velocity distribution, otherwise a large volume of buffer is needed to recover TCR-cells as the incoming wash buffer mixes with the fluidized bed. This type of cell retention can be reduced by increasing flush velocity and volume and improving the fluidized bed inlet design.
For each fluidized bed test the total TCR-cell recovery can be seen in Table 2.
The lowest recoveries were seen while testing high cell densities (100 e6/ml). Tests A and B had TCR-recoveries of 7% and 5% respectively. A “clogging” effect in the column was observed during these tests where beads and cells agglomerated together in very large clumps. Rather than acting as a fluid these solid clumps caused channeling in the column and prevented cells from escaping. It is also possible that non-specific binding occurred as the column fouled.
Tests C and D had similar recoveries, 34% and 33%. The two tests with 10 e6/ml behaved as expected but still had relatively low TCR-cell recoveries. This is due to the low fluid velocity and inefficient flush step described previously and can be improved by optimizing operating conditions and improving the fluidized bed inlet design. Changing the antibody had a minimal effect on cell recovery.
Four Acoustic Separator unit tests were performed with different affinity bead types (Promega, Dynabead, PolyStyrene 6 um and 14 um). On Day 2, fixed antibody combination (Anti-TCR and Anti-CD52) and antibody volume of 0.15 mL and 0.052 mL, respectively) were used. The initial TCR a/b-population was 77%.
All samples were incubated with anti-TCR and anti-CD52 in 2% BSA in PBS for 20 minutes on the IKA roller (30 rpm). Cells were washed twice with 2% BSA in PBS. A sample was removed for flow cytometry and used as the initial population for tests L through Q. Samples were incubated with the corresponding bead candidate listed in Table 3. for 30 minutes on the IKA roller (30 rpm) in 10 mL of 2% BSA in PBS and then separated using the Acoustic Separator unit operated at the following conditions; flow rate—1 mL/min and power—0.75 W. The first fraction, denoted as the outflow was collected after the entire sample passed through the acoustic field. A second fraction denoted as the flush was collected after flushing the fluidized bed with 30 ml of a 2% BSA in PBS solution. Once this process was completed, the remaining contents of the column were retrieved and collected as the third fraction, denoted as the holdup. Samples from all three fractions were collected for flow cytometry. For the purposes of conducting a mass balance, the mass and cell count for each fraction was recorded.
The purity increased by approximately 13% for all samples after separation by the Acoustic Separator unit, where the initial cell population consisted of 77% TCR knockout cells. The sample incubated with Dyna beads resulted in the highest purity of 89.4% in the outflow fraction while the sample incubated with Polystyrene (10-14 μm) beads resulted in the lowest purity of 84.3%. This trend was also observed in the flush fraction where samples incubated with Dyna beads yielded 91.1% purity and Polystyrene beads yielded 84.5% purity. The purity in all samples increased slightly from the outflow (84.3%-89.8%) to the flush fraction (84.6%-91.1%).
The total TCR-cell recoveries for each acoustic separator system test can be seen in Table 4. In this figure it appears that the recovery is affected by the bead type, with 50 um Promega beads having an 80% TCR-cell recovery and 4.5 um Dyna-beads having just 17% recovery. Both polystyrene particles had similar recoveries, 26% and 27% for 6 um and 14 um beads respectively. Since every test was performed with the same operating conditions, similar recoveries were expected so this relationship should be confirmed in future work. Like in the fluidized bed, TCR-recovery in the Acoustic Separator system can be increased by increasing flow velocity and by improving the inlet and collector designs.
Two Fluidized Bed (FB) processes and two Acoustic Separator(AS) processes were performed. Different pump systems (Syringe pump and peristaltic pump) were tested on the Fluidized Bed unit and two new bead candidates were tested on the Acoustic Separator unit on the first day of testing. The initial feed concentration was 107 cells/mL and TCR a/b-population was about 80%.
Sample preparation and acoustic unit operating procedures were the same as previous examples. Briefly, feed samples for the Fluidized Bed were incubated with biotinylated anti-TCR a/b antibody (Table 5) in 2% BSA in PBS for 20 minutes on the IKA roller (30 rpm). Cells were washed twice with 2% BSA in PBS and finally re-suspended in 10 mL 2% BSA in PBS. For the feed samples for the Acoustic Separator unit, bead incubation was followed by antibody-cell incubation. 1×106 cells from each feed sample were collected separately for flow cytometry and used as the initial population for each test.
The fluidized bed column was loaded with 2 ml Promega bead slurry (avidin-conjugated methacrylate beads) and then washed with 30 ml of a 2% BSA in PBS solution to remove residual ethanol and particulates. This initial washing step was performed at 3 mL/min and 2.25 W. Two different pumps (Syringe pump —FB_A and Peristaltic pump—FB_B) were evaluated on day 1. The feed cell population was then separated using the fluidized bed unit packed with Promega beads which operated at 3 mL/min and 4 mL column volume. For the Acoustic Separator unit operation, bead labeled feed were separated at the following conditions; flow rate—1 mL/min and power—0.75 W.
For the performance evaluation, processed samples from both units were collected and analyzed from three different fractions—outflow, flush and holdup (Table 6). The first fraction of the processed sample, denoted as the outflow, was collected after the entire sample was loaded into the fluidized bed. A second fraction, denoted as the flush, was collected after flushing the fluidized bed with 30 ml of 2% BSA in PBS solution. This flushing step is necessary to ensure all uncaptured cells are recovered. Once this process was completed the remaining contents of the column were retrieved and collected as the third fraction, denoted as the holdup. Samples from all three fractions were collected for flow cytometry. The mass and cell concentration count for each fraction was recorded for the cell recovery evaluation.
The purity increased by approximately 11˜12% for all samples after separation by the Fluidized Bed unit and almost no change after separation by the Acoustic Separator unit, where the initial cell population consisted of 80% TCR knockout cells (Table 6). For the Fluidized Bed tests, both peristaltic pump(FB_A) and syringe pump(FB_B) resulted in similar level of purity (90˜92%) in the flow through and flush fraction. In addition to fluidized bed testing, two different micron sized bio-degradable particle candidates (AS_A—PLGA and AS_B—Wax) were tested in Acoustic Separator unit.
Table 6 also shows recovery results. Fluidized Bed with peristaltic pump (FB_A) and syringe pump (FB_B) showed 78% and 61% of TCR—recovery, respectively. Based on the results, FDS decided to use peristaltic pump for upcoming platform validation. Peristaltic pump enables flexibility of further process optimization and closed system development. Acoustic Separator for PLGA and Wax resulted low recovery (50% and 38%, respectively).
Four fluidized bed unit tests were performed with different operation procedures. The residence time of feed cells in the column was increased by re-circulation of the processed sample or by holding samples in the column for a longer time period. The initial feed concentration was 107 cells/mL and TCR a/b-population was about 80%.
The same procedure was performed for feed and initial bead loading of the Fluidized Bed unit as in day 1. Table 7 shows four different operation procedures, no recirculation (FB_E, no recirc.), one recirculation (FB_F, 1 recirc.), 4 recirculations (FB_G, 4 recirc.) and stop and flow (FB_H, Stop and Flow). Specifically, in the stop and flow condition, 2.5 mL of feed samples were loaded with (3 mL/min) and flow stopped for 3 min 20 sec. This procedure was repeated until all the feed volume was loaded into the column. All the feed cells were held in the column by higher power condition (4.5 W) for a total of 13 min 20sec. Once the recirculation steps and stop and flow steps were finished, the column was flushed with 30 mL of 2% BSA solution. The processed samples were collected and analyzed as in day 1.
The purity increased by approximately 9-18% for all samples after separation, where the initial cell population consisted of 80% TCR knockout cells (Table 8). One recirculation (FB_F) resulted 95.6% and 97.7% of purity in Flow through and Flush portion, respectively. Notably, 4 recirculations (FB_G) showed low purity and we observed some temperature increase due to the 4 times of recirculation. The temperature rising also happened in stop and flow condition (FB_H).
For the TCR a/b-recovery, Recirculation and Stop and Flow condition showed good results. Adding more recirculation steps showed better recovery (one recirc.—82.64% and 4 recirc. 98.89%) and stop and flow condition also resulted high recovery (85.75%).
In accordance with the present disclosure, an acoustic affinity system is discussed that provides a number of advantageous features. For example, the systems and methods discussed herein can provide increased recovery and purity for target cellular material. The systems and methods are scalable, capable of handling a relatively wide range of material volumes. Positive and negative selection can be implemented in accordance with the present disclosure. Positive selection can include implementations with apheresis products. Negative and positive selection can be implemented on a multiplexed basis, where multiple types of cellular material can be selected in one pass. The systems and processes discussed herein can be fully automated and can be figured to be used with consumable components. The acoustic affinity cell selection system can be integrated with a cellular concentrate-wash device and/or system for downstream applications.
Gene and cell therapy shows great promise in treating life-threatening diseases such as cancer and auto-immunity. Therapy development, e.g., stem cell transplants or Chimeric Antigen Receptor T-cell (CAR-T) therapies for blood cancers, may use cell selection from an initial population from blood or apheresis products.
To develop a CAR-T therapy, peripheral blood mononuclear cells (PBMCs) comprising T-cells, B-cells, mono-cytes, NK cells and other cells such as basophils, neutrophils, eosinophils, dendritic cells, are isolated from blood or apheresis products. Prior isolation techniques include density gradient centrifugation (physical, label-free selection) and selection based on surface marker expression (affinity, labelled selection). These techniques can be used to isolate CD3+ T-cells or CD4+/CD8+ subsets of the CD3+ T-cells. The T-cells, which may number in an inclusive range of from about 500 million to about one billion, may be activated, transduced with a virus to express a cancer cell targeting Chimeric Antigen Receptor (CAR) and further expanded before final formulation of a dosage to the patient. The formulated cell product is infused into the same patient from whom cells were collected for an autologous therapy or into multiple patients for an allogeneic therapy.
The above described techniques for such cell-based therapies tend to involve elaborate, long, and costly manufacturing processes. Moreover, the quality control processes for a final products in such CAR-T manufacture add to the overall time, which may cumulatively two weeks and cost ˜$400K per patient. The process becomes longer and more costly as finer separations into cell sub-types are implemented. For example, animal studies strongly suggest that using defined T-cell subsets within the CD4+ and CD8+ populations may have therapeutic advantages such as in vivo persistence in CAR-T therapies, whereas other combinations of T-cell subsets which include effector and memory phenotypes can influence the T-cell therapy short term efficiency and long term persistence. In a commercial example, Juno Therapeutics is using defined CD4/CD8 T-cell subsets to target CD19+ B-cells to treat Non-Hodgkins Lymphoma.
Density gradient centrifugation, one of the more popular current cell separation techniques, is a manual, low resolution and non-scalable process. Cell selection using magnetic-activated cell sorting (MACS), which uses labeling via potentially cytotoxic magnetic nanoparticles, has limited throughput. In practice, multiple MACS cell selections are performed sequentially (e.g. CD4+ first and CD8+ afterwards) and they tend to collect all the target cells. This condition means that any desired starting ratios for CAR-T manufacturing are manually prepared by counting each cell type obtained from the MACS process and then mixing the right quantities of cells together to obtain the desired starting ratio. This process becomes more problematic given the variability of the PBMC composition from patient to patient.
The acoustic-oriented cell selection process discussed herein offers a number of advantages over prior cell selection techniques. The acoustic techniques applied to cell selection discussed herein tend to create processes that are faster, safer, e.g. less toxic, closed, cost-efficient, robust, and better able to perform finer sub-separations, with better quality to obtain more accessible cell and gene therapies, including improved CAR-T cell therapies.
One cell selection technique includes the use of angled acoustic wave-based technology for immune cell capture and elution from apheresis products. This technique has the potential to greatly reduce cost and process time in cell separation and production for cell and gene therapies. The technique enables label-free separation based on physical properties, such as density, size, compressibility and other factors, and permits multiplexed selection of defined cell subsets at high throughput and low shear rates.
The fluidized bed system discussed previously can implement acoustic affinity cell selection (AACS) cell sorting. The AACS discussed herein employs acoustic radiation forces that are exerted on a cell for affinity labeled cell selection at process scale, for example, at more than one million cells per second. This approach to cell manipulation is scalable and nominally shear-free. The AACS fluidized bed consists of a column containing affinity beads which are suspended in the column due to the balance between the bottom inlet flow drag force and the pressure generated by the acoustic standing wave. The fluidized bed can be operated as an expanded bed system, where the beads in the column are expanded throughout the column volume. A packed bed system such as the MACS will always yield high shear or low flow rates due to the narrow channels between the beads. Since the AACS fluidized bed can be operated as an expanded bed, the shear forces are significantly lower, and much higher flow rates can be attained. The higher flow rates and the scalability of this system contributes to reducing the time constraints around affinity cell selection in CAR-T manufacturing. For example, prior cell selection techniques may have an eight hour process time, which is likely to compromise the cellular product quality. The AACS system has the potential to perform these cell separations in less than two hours.
The AACS system can be used for CAR-T manufacturing with the beneficial advantage of multiplexed cell selection. The system can be configured to permit T-cell subsets to be selected at defined ratios. Prior cell selection systems are unable to achieve such multiplexed cell selection. For example, a MACS system has a packed bed that consists of large beads that get magnetized to attract the paramagnetic nanoparticles that are attached to the affinity targeted cells. This packed column attracts all the nanoparticles, regardless of the actual antibody-antigen pair that is being selected, which means that if more than one target cell type is being isolated, a sequential labeling step may be used. The AACS system can have beads functionalized with antibodies for different targets. The fluidized bed permits free movement and mixture of cells and beads, while maintaining the beads in the column using acoustics. A ratio of beads functionalized with different antibodies may be employed in the column, which obtains a ratio of cells with the corresponding different antigens that are isolated, thus enabling the simultaneous, multiplexed, selection of, for example, CD4/CD8 cells at defined ratios.
A multiplexed positive cell selection system based on AACS is discussed herein. The multiplexed AACS works back from the desired starting cell population, defined by total number of T-cells and the ratio of CD4 to CD8 T-cells. Assuming that a total of 200 million T-cells are used to start a process at a 1:1 ratio, 100 million of both CD4+ and CD8+ T-cells are isolated from an apheresis product. It may be desirable to have three times this number, for example, 300 million of each T-cell subtype, such that there is always the option of re-starting the manufacturing process with the remaining cells in case of an instance of manufacturing failure. In practice, there is a significant variability in the patient's PBMC quantity and ratios of CD4/CD8 cells obtained in an apheresis product. The subtypes may be 5% of the total PBMCs obtained in the apheresis bag from patients, and preferably is at least 5% of the total. Assuming the lowest number of PBMCs in a patient's blood is 10 billion, it is expected that there will be at least 500 million CD4+ and 500 million CD8+ T-cells in every apheresis bag. As such, the total CD4+ and CD8+ desired cell recovery is at least 60% (including final purity) in the AACS multiplexed cell selection system.
Two different methods may be employed to obtain pre-determined ratios of different cell surface marker cell types. The first method is to have different ratios of beads that will bind and elute the cells equally (the “bead ratio method”). The second method consists of having a differential release mechanism or operation for two different bead types, with a first and second elution. A first elution buffer 1 is used to elute cell type 1, e.g., CD4, from bead 1 and elution buffer 2 will elute cell type 2, e.g., CD8, from bead type 2, where 1 and 2 are defined by the target cell surface marker, in this case CD4 and CD8. This second method is referred to as a differential release method.
In both methods it is preferable for the antibody to be attached to the beads and not to the cells, although either attachment may be used. In some circumstances, for example when a biotin-biotinylated antibodies arrangement is used, attachment of the antibody to the cells may cause the capture of both target cell types. The bindings used may be i) cell-biotinylated antibody binding followed by monomeric avidin bead binding system (“cells first”) or ii) monomeric avidin bead-biotinylated antibody binding followed by affinity cell capture in the fluidized bed column (“beads first”). The beads first technique is preferred to enable multiplexed cell selections based on beads functionalized with different antibodies. In some implementations, multiple columns (e.g., a column for CD4 and a column for CD8) may be used. Other implementations may use a single column (e.g., a CD4/CD8 single column mixture). Different release methods may be used depending on the implementation. For example, serial column release may be employed in the case of multiple columns, while a differential release method may be employed for a single column. In some implementations, a bead-antibody linker that can be cleaved may be used. The multiplexed cell selection AACS processes may be performed using apheresis product T-cells (or PBMCs) with primary cells that are CD4+ and CD8+ cells, or may use a mixed cell line (e.g. with two different markers) to select the desired cell types.
Referring to
The methods, systems, and devices discussed above are examples. Various configurations may omit, substitute, or add various procedures or components as appropriate. For instance, in alternative configurations, the methods may be performed in an order different from that described, and that various steps may be added, omitted, or combined. Also, features described with respect to certain configurations may be combined in various other configurations. Different aspects and elements of the configurations may be combined in a similar manner. Also, technology evolves and, thus, many of the elements are examples and do not limit the scope of the disclosure or claims.
Specific details are given in the description to provide a thorough understanding of example configurations (including implementations). However, configurations may be practiced without these specific details. For example, well-known processes, structures, and techniques have been shown without unnecessary detail to avoid obscuring the configurations. This description provides example configurations only, and does not limit the scope, applicability, or configurations of the claims. Rather, the preceding description of the configurations provides a description for implementing described techniques. Various changes may be made in the function and arrangement of elements without departing from the spirit or scope of the disclosure.
Also, configurations may be described as a process that is depicted as a flow diagram or block diagram. Although each may describe the operations as a sequential process, many of the operations can be performed in parallel or concurrently. In addition, the order of the operations may be rearranged. A process may have additional stages or functions not included in the figure.
Having described several example configurations, various modifications, alternative constructions, and equivalents may be used without departing from the spirit of the disclosure. For example, the above elements may be components of a larger system, wherein other structures or processes may take precedence over or otherwise modify the application of the invention. Also, a number of operations may be undertaken before, during, or after the above elements are considered. Accordingly, the above description does not bound the scope of the claims.
A statement that a value exceeds (or is more than) a first threshold value is equivalent to a statement that the value meets or exceeds a second threshold value that is slightly greater than the first threshold value, e.g., the second threshold value being one value higher than the first threshold value in the resolution of a relevant system. A statement that a value is less than (or is within) a first threshold value is equivalent to a statement that the value is less than or equal to a second threshold value that is slightly lower than the first threshold value, e.g., the second threshold value being one value lower than the first threshold value in the resolution of the relevant system.
This application claims the benefit of U.S. Patent Application Ser. No. 62/725,256, filed Aug. 30, 2018, and claims the benefit of U.S. Patent Application Ser. No. 62/733,556, filed on Sep. 19, 2018. This application is a continuation-in-part application of and claims priority to U.S. patent application Ser. No. 15/983,823, filed on May 18, 2018, which claims the benefit of U.S. Patent Application Ser. No. 62/508,385, filed on May 8, 2017, and which is a continuation-in-part application of and claims priority to U.S. patent application Ser. No. 15/963,809, filed on Apr. 26, 2018, which claims the benefit of U.S. Patent Application Ser. No. 62/490,574, filed on Apr. 26, 2017, and which is a continuation-in-part application of and claims priority to U.S. patent application Ser. No. 15/222,800, filed on Jul. 28, 2016, which claims the benefit of U.S. Patent Application Ser. No. 62/197,801, filed on Jul. 28, 2015. The entire contents of each of the above applications is hereby incorporated herein by reference.
| Number | Date | Country | |
|---|---|---|---|
| 62508385 | May 2017 | US | |
| 62490574 | Apr 2017 | US | |
| 62197801 | Jul 2015 | US | |
| 62725256 | Aug 2018 | US | |
| 62733556 | Sep 2018 | US |
| Number | Date | Country | |
|---|---|---|---|
| Parent | 15983823 | May 2018 | US |
| Child | 16557994 | US | |
| Parent | 15963809 | Apr 2018 | US |
| Child | 15983823 | US | |
| Parent | 15222800 | Jul 2016 | US |
| Child | 15983823 | US |
