RELATED APPLICATION

[0001] This application claims the benefit of U.S. Provisional Application No.

62/664,740, filed on April 30, 2018. The entire teachings of the above application are incorporated herein by reference.

GOVERNMENT SUPPORT

[0002] This invention was made with government support under Grant Nos.

5R01CA226746 and P30CA072720, awarded by the National Cancer Institute, and Leidos Award 18X092, awarded by the National Institutes of Health. The government has certain rights in the invention.

BACKGROUND

[0003] 3D printing (3DP) is a class of processes where successive layers of material are aggregated incrementally to directly form a three-dimensional (3D) object [1] Several 3DP techniques have been introduced over the past several decades [1,2]. While individual processes differ depending on the material and machine technology used, the 3DP processes that use a lithographic technique using a digital light processing (DLP) technology have made great progress in the past several years [3-5]

[0004] Projection micro-stereolithography (PpSL) is a micro additive manufacturing technique based on DLP that has been developed and that can provide for high-resolution, rapid, and scalable printing of 3D objects. PpSL uses a spatial light modulator, typically a digital micro-mirror device (DMD), as a dynamically reconfigurable digital photomask.

PpSL is capable of fabricating complex 3D micro-structures in a bottom-up, layer-by-layer fashion.

SUMMARY

[0005] Expandable arrays that can be manufactured by 3DP techniques, including, for example, by PpSL, and methods of maintaining biological samples in such expandable arrays are provided. The arrays can provide for the streamlined processing of biological samples from collection and/or cell culturing to histological analysis. [0006] An expandable includes a plurality of receptacles configured to receive a biological sample and a plurality of beams comprising a shape-memory polymer. Each beam of the plurality of beams is disposed to extend between and connect at least two receptacles.

[0007] The receptacles of the array can also comprise a shape-memory polymer. The shape-memory polymer can be a thermally responsive polymer, for example, a polymer having a transition temperature of greater than about 37° C and less than about 80°C, or greater than about 37° C and less than about 50°C. The shape-memory polymer can be an acrylate-based polymer or methacrylate-based polymer. Examples of suitable shape-memory polymers include polyacrylic acid, polyethylene glycol diacrylate, polyethylene glycol dimethacrylate, diethylene glycol dimethacrylate, bisphenol A ethoxylate dimethacrylate, tert-butyl acrylate, and n-Butyl methacrylate. The shape-memory polymer can be compatible with PpSL printing methods.

[0008] The beams, or at least a subset of the beams, can be of an expandable shape, including, for example, a serpentine shape, a corrugated shape, a pleated shape, a helical shape, or a folded shape. The beams can be disposed to extend between sides of the receptacles, to extend from a top edge of the receptacles, to extend from a bottom edge, or any combination thereof. Each beam of the plurality of beams can be configured to be disposed in an extended state and a contracted state. A distance between each of the receptacles can be about 2 to about 10 times greater, or about 4 to about 5 times greater, when each beam is in the expanded state than the contracted state. The beams can be configured to revert to the contracted state from the extended state at a transition temperature of the shape memory polymer. Each of the receptacles can be connected to each neighboring receptacle by at least one beam.

[0009] The expandable array can be configured to fit within a histology cassette when the beams are in the contracted state. For example, the array can have a width of about 20 mm to about 30 mm and a length of about 25 mm to about 35 mm when each beam is in the contracted state. In a particular example, the array can have a width of about 24 mm and a length of about 30 mm when each beam is in the contracted state. The expandable array can be further configured to be received by a multiwell plate, such as a 96-well, 24-well, or 6- well plate, when the beams are in the expanded state. For example, the plurality of receptacles can be arranged in an 8 x 12, 4 x 6, or 2 x 3 array.

[0010] The array can further include at least one handle located at its perimeter, such as to provide for easy handling of the array during transport of the array from a multiwell plate to a histology cassette. If at least two handles are included in the array, each handle can be located at an opposing side of a perimeter of the array. Each handle can be connected to at least two receptacles, although the handles may be connected to multiple receptacles, for example, to provide for more secure handling of larger arrays.

[0011] Each receptacle can comprise a mesh structure, such as a mesh structure configured to retain a biological sample. The mesh structure can have a pore size of about 2 pm to about 10 pm. The dimensions of each receptacle can vary. Each receptacle can have a diameter configured to interface with or fit within a diameter of a well. The diameter of each receptacle can be, for example, of about 0.5 mm to about 2.5 mm, of about 0.5 mm to about 1.5 mm, or of about 1 mm. Similarly, each receptacle can have a depth configured to interface with or fit within a well. Each receptacle can have, for example, a depth of about 2 mm to about 15 mm, of about 5 mm to about 15 mm, of about 3 mm to about 5 mm, or of about 11 mm. A height of a combined receptacle and connecting beam(s) can be of about 5 mm to about 15 mm in a contracted state. The wall thickness of each receptacle can be of about 50 pm to about 150 pm, or of about 100 pm.

[0012] A method of maintaining a biological sample includes placing an expandable array in a multiwell plate and placing a biological sample within at least a subset of the plurality of receptacles of the array. The method further includes removing the expandable array containing the biological sample from the multiwell plate and exposing the expandable array to a stimulus. The plurality of beams of the expandable array responsively transition to a contracted state, with the biological sample being maintained within the array during the transition.

[0013] The exposure of the expandable array to a stimulus can include exposure to a temperature change, for example, an increase in temperature, such as provided by a heat source. The method can further include transferring the expandable array containing the biological sample to a histology cassette. During transfer, a relative configuration of the receptacles can be maintained and the biological sample can be maintained within the respective receptacles ( e.g ., in a same or similar orientation).

[0014] The placement of a biological sample within the receptacle(s) of the array can include seeding a cell culture within at least a subset of the receptacles. The biological sample can be, for example, cells, simple spheroids, mixed spheroids, or organoids.

Alternatively, the biological sample can be a tissue specimen. [0015] A kit includes an expandable array, one or more biomolecules and a cell culture medium or the ingredients for making a cell culture medium. The biomolecules can be, for example, a growth factor and/or an extracellular matrix component.

BRIEF DESCRIPTION OF THE DRAWINGS

[0016] The patent or application file contains at least one drawing executed in color. Copies of this patent or patent application publication with color drawing(s) will be provided by the Office upon request and payment of the necessary fee.

[0017] The foregoing will be apparent from the following more particular description of example embodiments, as illustrated in the accompanying drawings in which like reference characters refer to the same parts throughout the different views. The drawings are not necessarily to scale, emphasis instead being placed upon illustrating embodiments.

[0018] FIG. l is a schematic of an expandable array and methods of making and using same.

[0019] FIG. 2A is a top view of an expandable array in a contracted state. Small grid lines are 2 mm and large grid lines are 10 mm.

[0020] FIG. 2B is a top view of the expandable array of FIG. 2A in an expanded state. Small grid lines are 2 mm and large grid lines are 10 mm.

[0021] FIG. 2C is a side view of the expandable array of FIG. 2A. Small grid lines are 2 mm and large grid lines are 10 mm.

[0022] FIG. 3 A is perspective view of an expandable array in a substantially expanded state.

[0023] FIG. 3B is a perspective view of the expandable array of FIG. 3 A during contraction.

[0024] FIG. 3C is a perspective view of the expandable array of FIG. 3A after having further contracted.

[0025] FIG. 3D is a perspective view of the expandable array of FIG. 3 A in a substantially contracted state.

[0026] FIG. 4 A is a graph of temperature dependent modulus change for four shape- memory polymers (SMPs), each of a different mixing ratio of benzyl methacrylate (BMA) and poly (ethylene glycol) dimethacrylate (PEGDMA).

[0027] FIG. 4B is a graph of the shift of glass transition temperature (T _g ) of the SMPs of FIG. 4A as measured by Dynamic Mechanical Analysis (DMA). [0028] FIG. 4C is a graph of glass transition temperatures (T _g ) of four SMPs as a function of percentage of crosslinker. In the legend, B stands for Benzyl methacrylate (BMA), P550 for Poly (ethylene glycol) dimethacrylate (PEGDMA) with molecular weight (Mw) 550,

P750 for Poly (ethylene glycol) dimethacrylate (PEGDMA) with Mw 750, BPA for

Bisphenol A ethoxylate dimethacrylate, and DEG for Di(ethylene glycol) dimethacrylate.

[0029] FIG. 5A is a schematic of another example of an expandable array and example methods of making and using same.

[0030] FIG. 5B illustrates an example of a receptacle that includes connecting beams in a contracted state.

[0031] FIG. 5C illustrates the receptacle of FIG. 5B with connecting beams in an expanded or extended, state.

[0032] FIG. 6A is a graph of storage modulus and loss modulus versus temperature from a dynamic mechanical analysis (DMA) of 3D-printed and molded specimens of a shape memory polymer (SMP).

[0033] FIG. 6B is a graph of failure strain versus temperature from a tensile test of laser- cut molded specimens of the SMP.

[0034] FIG. 6C is a graph of stress, strain, and temperature over time from a shape programming and shape recovery test of the SMP.

[0035] FIG. 7A illustrates an example of a prototype receptacle in contracted and extended states.

[0036] FIG. 7B illustrates schematic of a cassette configuration and a well plate configuration for an array of the prototype receptacles of FIG. 7 A.

[0037] FIG. 7C illustrates ratio of original size of a prototype receptacle to a measured size of the receptacle over time during a heat recovery test of a prototype array according to FIG. 7B.

[0038] FIG. 8 illustrates a process for operation of an expandable array.

[0039] FIG. 9A is a schematic illustrating an expandable array mounted within a stretcher in an initial, contracted configuration.

[0040] FIG. 9B is a schematic illustrating the expandable array and stretcher of FIG. 9B in an expanded configuration.

[0041] FIG. 9C depicts an example array mounted within an example stretcher in the configuration shown in FIG. 9A. [0042] FIG. 9D depicts the example array and stretcher of FIG. 9C in the expanded configuration shown in FIG. 9B.

[0043] FIG. 10A is a schematic illustrating a top-side view of a plate fixture.

[0044] FIG. 10B is a schematic illustrating a side view of the plate fixture of FIG. 10A.

[0045] FIG. 11 A depicts a prototype array in an expanded state with markers at bridge connections for shape recovery mapping.

[0046] FIG. 11B depicts the photographed markers of the prototype array of FIG. 11 A.

[0047] FIG. 11C depicts the detected markers of the prototype array of FIGS. 11 A and

11B.

[0048] FIG. 12A illustrates a test process for histological processing with a prototype expandable array.

[0049] FIG. 12B illustrates Hematoxylin and Eosin (H&E) stained microtome sections obtained from the histological processing shown in FIG. 12A. The scale bar in 100 pm.

[0050] FIG. 13 depicts cross-section and side-section photos of prototype receptacles with and without cells.

[0051] FIG. 14A depicts bright field images of glioblastoma (GBM) spheres derived from EG87 cells in the presence of fetal bovine serum (FBS) and grown with and without receptacle arrays.

[0052] FIG. 14B depicts bright field images of GBM organoids grown in serum -free conditions with growth factors and derived from GBM #50 cells, grown with and without receptacle arrays.

[0053] FIG. 14C depicts bright field images of GBM #50 cells grown in Matrigel spheres, grown with and without receptacle arrays.

[0054] FIG. 15A is a graph of cell titer glo assay results versus component biomaterials for testing to determine GBM cell viability in receptacle arrays.

[0055] FIG. 15B is a low-power bright field image of control EG87 spheres cultured for one week for the control of FIG. 15 A, shown in 5x and 20x magnification.

[0056] FIG. 15C depicts low-power bright field images of EG87 spheres cultured for one week with the biomaterials of FIG. 15 A, shown in 5x and 20x magnification.

[0057] FIG. 16A depicts images of sphere cultures with cut baskets.

[0058] FIG. 16B depicts images of sphere cultures from samples of individually examined basket biomaterials. [0059] FIG. 16C depicts images of cell cultures without basket arrays and with basket arrays soaked in a 100% acetone bath after 3D printing.

[0060] FIG. 16D depicts images of GBM organoid cultures without acetone soak and with 12 h and 24 h acetone soak.

[0061] FIG. 16E depicts bright field images showing no GBM organoid grown in a basket when an acetone bath was not used and GBM organoid growth in a basket soaked in 100% acetone bath after 3D printing.

[0062] FIG. 16F is a graph of the results of the acetone soak trial depicted in FIG. 16D of Relative Light Units (RLU) versus control, 12 hour soak, and 24 hour soak.

DETAILED DESCRIPTION

[0063] A description of example embodiments follows.

[0064] As shown in FIG. 1, expandable arrays comprising a shape-memory polymer can be made using 3D printing techniques, including PpSL techniques. In an expanded state, the receptacles of the expandable array can be configured to interface with, or fit within a multiwell plate. The array can be configured such that, upon exposure to a stimulus, the shape-memory polymer reverts to a contracted state that can fit within a container of a different dimension, such as a histology cassette, as will be described further below.

[0065] PpSL is capable of fabricating complex 3D micro-structures in a bottom-up, layer- by-layer fashion. Generally, PpSL techniques involve the following steps. A digital model created by computer-aided-design (CAD) software is first sliced into a series of closely spaced horizontal planes. These two-dimensional slices are digitized as an image and transmitted to a dynamic mask, which projects the image through a reduction lens into a bath of photosensitive polymer resin. The exposed material cures, and the stage on which it rests is lowered to repeat the process with the next image slice. A schematic representation of this process is shown in FIG. 1 at section (a).

[0066] PpSL processes can rapidly generate complex 3D geometries, for example, within minutes, with photo-curable polymers. The high resolution (<5 pm) offered by PpSL is at least an order of magnitude better than most 3DP techniques. Scalability is another prominent attribute of PpSL over other existing 3D printing techniques. Unlike other widely used 3DP processes where a time-consuming raster scanning of a laser beam or an injection nozzle must be performed for each single layer (a serial process), PpSL solidifies the entire layer with a single illumination of ultra-violet (UV) light within a few seconds (a parallel process). Therefore, fabrication of a complex 3D structure could be completed within an hour, compared to the lengthy processing time of several hours to days for other 3D printing methods. Also, by adopting step-and-repeat process, the build-area of PpSL can be extended to a larger area without compromising resolution.

[0067] Furthermore, being able to modulate UV light intensity digitally and individually at a single pixel level, PpSL provides for the flexibility to generate the desired material properties and refine their spatial distribution. The intensity of the light exposure strongly influences the crosslinking density of photo-polymerized material, which is an important factor in determining and adjusting physical properties of a polymer, such as elastic modulus, molecular permeability and swelling ratio. Molecular diffusivity of the polymer can be adjusted to provide for receptacles that allow for culture medium and growth factors to diffuse across the receptacle wall.

[0068] Smart materials are materials that can actively deform and reconfigure when exposed to external stimuli. 3D printing of shape-shifting materials, such as stimuli- responsive hydrogels and shape memory polymers, has been explored and is termed 4D printing, with the 4 ^th dimension being the time-dependent shape change of 3D printed objects in response to an environmental stimulus [6-8]

[0069] 4D printing of programmable smart material can be used to generate receptacles, and arrays of receptacles, for use in processing biological samples, such as 3D cultures involving cellular spheres and organoids, or tissue samples. Typically, such biological samples are cultured in multi-well plates. Following culturing, or tissue collection, the samples are transferred to a histology cassette for further analysis by microscopy techniques. The transfer of the biological samples from multiwell plates to a histology cassette is time intensive and manually detailed, often taking about four days and requiring multiple steps to preserve the relative orientation of the samples.

[0070] Expandable arrays are described that can interface with or fit within multiwell plates, or other cell-culturing/tissue-collection vessels, and can advantageously provide for streamlined transport of biological samples from the multiwell plates to containers of a different dimension, such as histology cassettes, upon completion of cell-culturing or tissue collection. For example, an expandable array can be configured to transition from a larger footprint ( e.g ., a 96-well plate) to a smaller footprint (e.g, a paraffin embedding block), while retaining the biological sample(s) in a relative orientation. [0071] As used herein, the term“array” applies to any configuration of two or more receptacles for receiving a biological sample, with at least a subset of the receptacles connected to one another by a beam. For example, the array can be a regularly shaped or patterned array, such as an 8 x 12 array configured to interface with a 96-well plate, or an irregularly shaped or patterned array, such as an array of 3 receptacles arranged in a triangle or 7 receptacles arranged in a circle.

[0072] The term“beam,” as used herein, applies to any connecting element extending between receptacles of an array. Beams can extend between upper, lower, and side surfaces of receptacles, in any combination. For example, a beam can be a corrugated or serpentine connecting element extending between sides of receptacles. A beam can also be a helical connecting element that extends from an upper surface of a receptacle. Beams may be integral with the receptacles of an array, integral with other beams, or integral with both receptacles and other beams. Alternatively, beams can be coupled to receptacles and/or to other beams, such as through bonding. Beams may alternatively be referred to as bridges.

[0073] As used herein, the term“receptacle” applies to any structure configured to retain a volume of a fluid or solid, including, for example, cells, cell culture media, and tissue samples. Receptacles may be alternatively referred to as baskets.

[0074] An example of an expandable array 100, including a method of making and using an expandable array, is shown in FIG 1. As illustrated, the array 100 is an 8 x 12 3D cell culture array, which, as printed by PpSL, has a dimension that fits a paraffin embedding cassette 120 ( e.g ., 24 mm x 30 mm x 11 mm). See (1), (2), and (6) of FIG. 1. The array 100 includes a plurality of receptacles 102, illustrated as baskets, each basket having a dimension allowing it to fit within a well of a 96-well plate (e.g., a diameter of 1 mm, a wall thickness of 100 pm, and a U-shaped bottom). See (3) of FIG. 1. Each basket is connected to neighboring baskets with a beam 104, alternatively referred to as a bridge, such as a corrugated or serpentine beam. When the beams 104 are stretched, a center-to-center distance between the baskets matches that of the wells of a multiwell plate, such as the standard 96-well plate illustrated in FIG. 1. In particular, as illustrated, a conversation ratio between the dimensions of the two states (e.g, a contracted/printed state and an expanded state) can be about 1 :4-5 and can be provided by 4D printing. See (3), (4), and (5) of FIG. 1.

[0075] As illustrated, the array is printed in the contracted, or shrunken, configuration (as shown in steps (l)-(3) of FIG. 1) with an original dimension that matches that of an interior of a paraffin-embedding cassette. After printing, the array is mechanically and bidirectionally stretched to the expanded, or extended, configuration with a dimension that is about 4~5 times that of the original dimension and matching that of a standard 96 well plate (as shown in step (3) of FIG. 1). Optionally, the array can include handles, such as right and left handles 106, for ease of manipulation and assistance in maintaining a correct orientation. While a rectangular array is depicted in FIG. 1 with the handles 106 disposed at opposing ends of the array of receptacles, handles may be positioned at orientation for both regularly and irregularly patterned arrays. The handles can be connected to the receptacles 102, to the beams 104, or to both the receptacles and the beams.

[0076] Since the basket array is printed with shape memory polymer, its stretched dimension can be temporarily fixed in the extended configuration. In the extended configuration, the array can be transferred to a standard 96 well plate for 3D cell culturing processes. During the cell culture period, the extended dimension can be retained by itself without any additional aid. PpSL printing advantageously provides for a tunable molecular diffusivity of the basket such that the basket can allow for material exchange while the cell culture is retained inside each basket. Once cell culturing is completed, the culture can then be subjected to formalin fixation and, optionally, the plate can be subjected to brief centrifugation to cause the spheres or organoids to lie at a same level at the bottom of the baskets. The rounded bottom of the baskets can help to maintain the shape of the spheres and organoids during processing.

[0077] The entire array can be taken out of the 96 well plate and placed in an incubator, or exposed to a temperature change. In the case of a thermally responsive shape-memory polymer, the temperature can be gradually increased to above the glass transition temperature of the shape memory polymer, upon which the basket array will return to its shrunken configuration. See (4) and (5) of FIG. 1.

[0078] Another example of a cell culture array is shown in FIGS. 2A-2C in both expanded (FIG. 2B) and contracted (FIGS. 2 A, 2C) states. The array 200 includes four receptacles 202, each receptacle including two beams 204. The beams 204 are shown in a corrugated configuration, extending between sides of the receptacles 202 to each neighboring receptacle. FIGS. 3A-3D illustrate contraction of the cell culture array 200 from an expanded configuration (FIG. 3 A) through intermediary configurations (FIGS. 3B-C) to a shrunken configuration (FIG. 3D), each basket of the array having within it a liquid, which, as shown in the figures, does not spill as the array moves from the expanded state to the contracted state. [0079] Mechanical transformation of the array can occur mostly on the connecting elements, or beams, rather than on the basket itself, so mechanical perturbation or disturbance to the culture inside each basket is minimal. In this process, the geometric expansion is achieved by stretching of the connecting members located between baskets (not the baskets themselves). In such a configuration, with little or no deformation in z-direction during a shape programming process ( e.g ., mechanical extension to the expanded state), there is likewise little to no contortion in the z plane during the shape recovery process (e.g., thermally-induced contraction to the contracted state).

[0080] The receptacles of an array can be formed of a same shape-memory polymer as that of the connecting members during the PpSL printing process. However, the baskets may alternatively be formed of a different material than that of the connecting members, including for example, a non-shape-memory material.

[0081] Furthermore, as illustrated, each basket is connected to each neighboring basket, with the internal baskets of the array of FIG. 1 each connected to each of its four neighboring baskets. In such a configuration, the mechanical force applied to each basket is symmetric, which can help to keep the basket in an upright orientation during expansion and contraction. However, the internal baskets of an array can be connected to fewer neighboring baskets, such alternating rows of missing beams in an x- or y- direction, or in the case of an irregularly shaped array, internal baskets may each have more than four neighboring baskets and, as such, more than four beams may be connected to each internal basked.

[0082] The transition temperature of the shape memory polymer can be tuned to a temperature that is (i) above the 37°C cell culture temperature so that the basket array can retain its extended dimension during 3D cell culture and (ii) <50°C or <80°C as may be needed to prevent any thermal damage to the cell culture or tissue sample. Once the array returns to its originally printed/contracted configuration it can then be transferred to a paraffin-embedding histology cassette for subsequent fixation and paraffin-embedding processes. See (5)-(6) of FIG. 1.

[0083] Furthermore, a stiffness of the shape memory polymer can be tuned during the PpSL process such that it can be easily cut and sliced with a microtome after the paraffin embedding process.

[0084] The polymer can be an acrylate-based or methacrylate-based shape memory polymer. Such polymers advantageously provide for tunability in terms of elastic modulus, extent of deformation, and sensitivity to a stimulus that triggers glassy -rubbery transition. Chemical and thermo-mechanical characterization of the polymers can be assessed by Differential Scanning Calorimetry (DSC), Fourier Transform Infrared (FTIR) spectroscopy, and/or Dynamic Mechanical Analysis (DMA) to ascertain an optimal combination of materials properties.

[0085] Preliminary results are shown in FIGS. 4A-4C for a shape-memory polymer (SMP) or varying composition. As shown in FIGS. 4A-4C, an elasticity of the SMP changes up to 3 orders of magnitude with a mild temperature change between 20°C to 80°C. The effects of chemical composition, molecular weight of polymer, photo-initiator concentration and cross-linking density on the material’s behaviors such as stiffness, strength, toughness, energy absorption, and glass transition temperature can be optimized to obtain desired material properties. The rubbery modulus E _r of the polymer increases with an increase in crosslinking density as expected from entropic elasticity, E _r = (3pRT) / M _c ; where, R is the gas constant, T is absolute temperature, p is polymer density, and M _c is average molecular weight between crosslinks. The ratio p / M _c is the crosslinking density of the polymer network and can be obtained from a photo-polymerization model. Also, the Couchman equation [9] can be used to predict the glass transition temperature T _g of the cured SMP from the prescribed ratio of SMP and crosslinker: 1 / T = Mi / T _g ¹ + M ₂ / T _g ² ; where T _g ¹ and T _g ² are the glass transition temperatures of the respective pure-components, and Mi and M ₂ are the corresponding mass fractions of the SMP and crosslinker, respectively.

[0086] Experimental techniques including Fourier transform infrared spectroscopy (FTIR), Raman spectroscopy and Zetasizer can be used to characterize conversion ratio and molecular weight of the polymer. Experimental techniques including various microscopy, rheometer, differential scanning calorimetry (DSC), dynamic mechanical analysis (DMA), and thermo-mechanical analysis (TMA) can be used to characterize and assess the

performance of synthesized materials. As such, a desired shape transformation at a desired temperature above or below cell culture temperature can be provided for an expandable array. Furthermore, a rubbery modulus can be tuned to a low value such that the receptacles, or baskets, or the array can be easily sectioned using microtomes. In addition, or alternatively, the SMP can be selected or configured to dissolve or degrade, for example, during histology processing.

[0087] Examples of suitable shape-memory polymers include polyacrylic acid, polyethylene glycol diacrylate, polyethylene glycol dimethacrylate, diethylene glycol dimethacrylate, bisphenol A ethoxylate dimethacrylate, tert-butyl acrylate, and n-Butyl methacrylate. The shape-memory polymer can be compatible with PpSL printing methods and can be tuned as described above.

[0088] As shown in FIGS. 1-3D, the beams connecting each of the receptacles of the array have a serpentine shape. However, other shapes are possible. For example, the shape can be pleated or corrugated, or otherwise include an undulating shape that permits both a lengthened and a contracted state. The number of folds, pleats, or turns of each beam, as well as the length of each beam can be adjusted to permit expansion and contraction to varying lengths. As such, expandable arrays can be customized to interface with multiwell plates or other cell-culturing/tissue collection vessels of varying shapes and sizes. Placement of the beams with respect to the receptacles can also be customized to accommodate various cell- culturing and tissue collection vessels. For example, for a multiwell plate, beams may be disposed to extend from an upper surface of the receptacles to enable the receptacles to be disposed within the wells without or with minimal beam interference. In another example, beams may be disposed to extend from a lower surface of the receptacles to accommodate a hanging cell culture apparatus.

[0089] Another example of an expandable array is shown in FIGS. 5A-5C. The array 500 includes a plurality of receptacles 502, or cell tubes, having beams 504 in a helical bridge configuration. The helical bridges 504 are shown in a contracted state in FIG. 5B and in an expanded state in FIG. 5C. The helical bridges 504 can include a joining element 506 disposed at an end of each beam for connection to a neighboring beam, for marker placement, or both. Upon stretching of the array 500, the helical bridges 504 can unwind to

accommodate a dimensional change, as illustrated in FIG. 5 A. When heated, the helical bridges 504 can revert to their original shape.

[0090] The receptacle and beam configuration shown in FIGS. 5A-5C can

advantageously provide for larger-volume receptacles over the configuration shown in FIG. 1 as the beams are disposed above, rather than between, the receptacles in the contracted state.

[0091] For conventional, multiwell plates, such as a 96-well, 24-well, or 6-well plate, the expandable array can include a plurality of receptacles that are arranged in, respectively, an 8 x 12, 4 x 6, or 2 x 3 array. For a conventional histology cassette, the expandable array can have a width of about 20 mm to about 30 mm ( e.g ., 24 mm) and a length of about 25 mm to about 35 mm (e.g., 30 mm) when each beam is in the contracted state.

[0092] The receptacles of an expanded array can also vary to interface with the size and shape of the intended cell-culturing/tissue collection vessel. For a conventional multiwell plate, for example, it may be desirable to have each receptacle comprise a basket-like shape, with a bottom of each basket located approximately 2mm above a bottom of the plate well. For such a conventional multiwell plate, each receptacle of an expandable array can have a diameter of about 0.5 mm to about 1.5 mm ( e.g ., 1 mm), a depth of about 5 mm to about 15 mm (e.g., 11 mm), and a wall thickness of about 50 pm to about 150 pm (e.g. 100 pm).

[0093] Expandable arrays can be included within a kit that further includes materials for cell-culturing, such as one or more biomolecules (e.g, a growth factor, an extracellular matrix component) and/or a cell culture medium or ingredients for making a cell culture medium.

[0094] Stretching of expandable arrays can optionally be performed by a stretching device, alternatively referred to as a stretcher. An example of a stretching device is shown in FIGS. 9A and 9B, and use of the device is shown in FIG. 8. A top plate of the stretcher 900 includes a plurality of straight rails 902; and, a bottom plate of the stretcher 900 includes a plurality of curved rails 904 (shown in transparency in FIG. 9A). As illustrated, the patterns of rails connect locations of distributed baskets 906 of dimensions Al and Bl in a compact state and A2 and B2 in an expanded state. The rails of the upper plate of the stretcher 900 can be of a width to accommodate a diameter of a top portion of an expandable array, and rails of the lower plate can be of a width to accommodate a diameter of a bottom portion of an expandable array. Outer baskets of the array sitting in both rails can move from a compact configuration to an expanded configuration by rotating the top plate against the bottom plate, as shown in FIG. 9B.

[0095] Expandable arrays can optionally be placed in a fixture device prior to placement within a histology cassette, or other vessel. An example of a fixture 800 is shown in FIGS. 10A and 10B. The fixture can have dimensions A x C corresponding to widths of a histology cassette, or other containing vessel in which an expandable array is to be placed. A window 802 can be included in the fixture for viewing of the array. The fixture can further include pins 804 configured to align baskets disposed around an edge of an array with edge wells of a multi-well plate. For example, a distance B between pins can be about 9 mm, corresponding to a distance between wells of a 96-well plate. Fixtures can advantageously prohibit or restrain the SMP of the expandable array from contracting to its compact state during cell culturing processes.

[0096] Methods of making expandable cell culture arrays can include PpSL techniques, as shown in FIGS. 1 and 5A. In particular, the method can include discretizing a 3D computer-aided design (CAD) model of the receptacles and beams of an array and displaying the discretized images on a digital micromirror (DMD™) device to apply a dynamic virtual photomask. UV light, such as illimitation from a light emitting diode (LED), is reflected off the dynamic mask and focused on a surface of a photocurable liquid polymer through a projection lens to form a layer of the array. The arrays can then be built, layer upon layer, by repeating the process under all layers are completed. While PpSL techniques are described in the following Example, other additive manufacturing techniques or molding techniques can be employed for manufacture of cell culture arrays.

[0097] Methods of operating expandable cell culture arrays can include uniformly stretching the arrays to the dimensions of a well plate. The cell culture arrays can thereby be programmed to retain the dimensions of the well plate. The programmed cell culture arrays can then be transferred to the well plate with a one-to-one matching of the receptacles of the array and the wells of the plate. Cells, cell culture media, drug compositions, and other materials, or any combination thereof, can then be placed within the receptacles. For cell culturing, upon cell seeding within the receptacles of the array, the well plate, including the array, can be placed in an incubator or oven for cell culturing. To fix cells within the receptacles, formalin can be introduced. The array can then be removed from the well plate and heated to a shape recovery temperature to cause the array to revert to a compact ( e.g ., printed) configuration. For histology processing the compact configuration of the array can be of a dimension that fits within a histology cassette. The array, including cell contents can then be transferred to the histology cassette. Paraffin wax or other material can then be introduced prior to sectioning. Sectioning can be performed, such as with a microtome to obtain thin, cross-sectional films for analysis.

[0098] While example arrays have been described as receiving biological samples, expandable arrays may also be configured to receive non-biological samples, and methods of using such expandable arrays can include placing a non-biological sample within the receptacles of the array.

[0099] Furthermore, while 3DP techniques have been described as methods by which expandable arrays may be manufactured, molding processes may instead be applied to create such expandable arrays. [00100] Example 1. 4D Cell-Culture Arrays

[00101] Expandable arrays were created for cell culturing, the expandable arrays configured to transform between the size of a histology cassette and the size of a 96-well plate ( e.g ., 3.6x the size of the histology cassette) while maintaining a same layout in both forms. Expandable arrays were manufactured and operated according to the procedure shown in FIG. 5 A.

[00102] Projection Micro-stereolithography (PpSL)

[00103] PpSL techniques were employed for the manufacture of the cell-culture arrays. The resolution of the digital dynamic mask was 1920 x 1080 and the projection area was 24 ^c 14 mm, providing for a nominal resolution of 13 pm. A resolution of 800 x 800 (~ 10 mm x 10 mm) was used in printing to ensure high uniformity in light intensity. To print full basket arrays with a dimension of 30 mm x 20 mm x 11.2 mm, a 3-by-2 stitching of projections within one layer was employed (horizontal movement of printed structure using XY stages).

[00104] A custom-built PpSL system was used in this work. It consisted of a ETV LED (365 nm) (L10561, Hamamatsu), a collimating lens (LBF254-150, Thorlabs), a digital micro- mirror device (DMDTM) (DLPLCR6500EVM, Texas Instruments), three motorized linear stages (MTS50-Z8, Thorlabs), and a projection lens (Thorlabs). Printing parameters we used include a light intensity of 29 mW cm-2, a layer thickness of 50 pm, and a curing time of 1 s. The entire PpSL system was kept in a LTV blocking enclosure.

[00105] Shape Memory Polymer (SMP) Materials

[00106] Shape memory polymer (SMP) was included as a constituent material of the 3D cell-culture basket arrays to enable transformation between configurations.

[00107] All chemicals, including liquid oligomers, photoinitiator (PI), and photo absorber (PA), were purchased from Sigma-Aldrich (St. Louis, MO, LTSA) and used as received. Poly(ethyleneglycol) diacrylate (PEGDA) (Mn250) and Bisphenol A ethoxylate

dimethacrylate (BP A) (Mnl700) were mixed at a ratio of 9: 1 in weight. Phenylbis(2,4,6- trimethylbenzoyl) phosphine and Sudan I were added at the concentration of 2 wt.% and 0.1 wt.% of the precursor solution as PI and PA, respectively. [00108] Postprocessing

[00109] After printing, the arrays were treated using post-processing procedures prior to cell culturing processes.

[00110] Printed structures were rinsed in fresh ethanol for 30 s for 3 times to remove any uncured precursor solution. After being dried in air until the absorbed ethanol evaporated, the structures were rinsed in pentane one more times to avoid adhesion between bridges and baskets. After pentane drying, the structure were post-cured in a UV oven (CL-1000L, UVP, 365 nm) for 2 hours to polymerize all unreacted ethyl group in acrylate/methacrylate . To eliminate toxicity in remained PI and PA, fully crosslinked structures were stored in an Acetone bath for 5 days. Structures taken out from the Acetone bath were rinsed in ethanol one more time for sanitization and were dried overnight at room temperature.

[00111] Dynamic Mechanical Analysis and Failure Strain

[00112] To characterize the SMP’s thermomechanical properties, a photocurable precursor solution was prepared using Poly(ethylene glycol) diacrylate (PEGDA) and bisphenol A ethoxylate dimethacrylate (Mh~1700) (BPA). Upon photo-polymerization, a cross-linked polymer network is formed with these two materials. It has been shown that a glass transition temperature T _g can be tailored by using different ratios of monomer and crosslinker. To maintain shape fixity at 25°C (e.g, room temperature) and trigger shape recovery at 50°C (e.g, an accepted maximum temperature for cell viability), the SMP was designed to have a weight ratio between PEGDA and BPA of 9: 1. Thermomechanical properties of the SMP were then characterized by dynamic mechanical analysis (DMA) tests on both 3D printed and molded specimens.

[00113] For molded samples, an SMP precursor solution without PA was injected into a mold of two glass slides separated by 1 mm spacers. Glass slides were cleaned with ethanol and coated with RainX for easy demolding. The precursor solution in the mold was cured in a UV oven (CL-1000L, UVP, 365 nm) with a light intensity of 5 mW cm-2 for 20 min, yielding a fully crosslinked polymer film with a thickness of 1 mm. Samples were laser cut to 40 mm x 8 mm x lmm rectangular specimens. For 3D printed samples, the same printing parameters and post-processing procedure (except toxicity-eliminating steps) were used. Dimensions of 3D printed samples were 25 mm x 8 mm x 1 mm. DMA was conducted on a dynamic mechanical analyzer (Q800, TA Instruments) using a tensile loading mode. Testing parameters for DMA included strain of 0.2 %, frequency of 1 Hz, preload of 0.001 N, and force track of 150 %. Specimens were heated at 25°C for 10 min prior to each test. Storage modulus, loss modulus, and tan d were measured as a function of temperature while temperature was increased to 75°C at a rate of l°C min ¹ .

[00114] The results from DMA tests on both specimens are shown in FIG. 6A. Note that the storage modulus of the SMP changes from 984 MPa at 25°C to 132 MPa at 75°C. Tan d indicates that the SMP has a T _g of 6l°C. Though T _g is higher than a maximum heating temperature of 50°C, recovery behavior was observed at 50°C and high T _g is desired to for better shape fixity at room temperature.

[00115] For temperature dependent failure strain tests, molded films were made using the same protocol from the DMA test. The molded films were laser cut into a dog-bone shape (gauge section: 16.5 x 3 x 1 mm) to measure strain at failure of material at different temperatures. Two grippers clamped on two ends of rectangular specimens. An air chamber with Peltier heater (CP-061HT, Technology, Inc.) underneath was used to control temperature inside and a thermocouple connected to an NI temperature module on cDAQ (NI 9171 and NI 9211, National Instrument) was used to measure temperature. Two dots were marked in the gauge section of dog-bone specimens and a digital camera (Canon 60D) were set on top to monitor distance between dots. One gripper was then manually moved at an average speed of 0.2% sec ¹ to stretch the sample until failure. Strain at failure was then calculated using final distance divided by initial distance between two dots.

[00116] Using the molded specimens that were laser cut into dog-bone shape,

stretchability of the SMP was tested by tensile test at four different temperatures, the results of which are shown in FIG. 6B. During basket arrays’ transformation from histology cassette configuration to 96-well plate configuration, a global dimensional change of 3.6 times was required. Adequate stretchability can be an important design constraint for limiting local strain to avoid breakage during transformation. Four different temperatures between 25°C to 50°C were tested. Average stretchability at each tested temperature varied from 12% to 14%, and minimum stretchability among all measurements was slightly above 10%. The result indicates local deformation during shape transformation should be limited within 10% of strain.

[00117] To demonstrate SME, shape programming and shape recovery of a 3D printed SMP beam was performed, the results of which are shown in FIG. 6C. Stress, strain and temperature during the process are plotted. The beam was compressed by 5% at 25°C. While maintaining the strain, the beam was heated to 50°C and then cooled down to 25°C again. Note that required stress to maintain the compressive strain reduced significantly due to fixing of deformed shape. After removal of mechanical loading, the deformed strain was retained at 3%. Even though only ~ 60% of strain was fixed after release, it can be further improved using longer holding time and higher heating temperature. Upon heating back to 50°C, the original height of the beam was completely recovered.

[00118] Array Design

[00119] Arrays were designed as shown in FIGS. 5A-5C to meet dimensional

requirements for transport between a 96-well plate and a histology cassette, as well as to satisfy stretchability and cell culture requirements. To fit 12 x 8 basket arrays in the histology cassette, a maximum dimension of one basket unit was restrained to 2.5 mm x 2.5 mm x 11.2 mm. As shown in FIG. 7A, the height of the cell tube was 3.2 mm and the height of the helical bridge was 8 mm. The opening of the cell tube was designed to be 1.8 mm in diameter to accommodate a 20 pL pipette tip used in cell seeding.

[00120] Wall thickness of cell tube and thickness of helical bridge were 200 pm. Width of helical bridge was 1.45 mm. Total length after full extension of helical bridge without considering constraint in local strain can be 22.1 mm. In the 96-well plate configuration, each basket was to be stretched to 9 mm x 9 mm. Height was approximately 10 mm due to unwinding of helical bridges. Results from a numerical simulation with proper constraints of a single unit basket revealed that local strain after stretching to the 96-well plate

configuration was lower than 5.1%, which is half of the smallest measured failure strain from the experiments described with respect to FIG. 6B and which indicated that no breakage would occur during transformation. The receptacle and beam design and the resulting numerical analysis of the design are shown in FIG. 7A.

[00121] Cassette and well-plate configurations of the arrays are shown in FIG. 7B.

Assembly of the basket arrays consisted of unit baskets having alternatively clockwise and counterclockwise helical bridges. Based on trials, such a configuration demonstrated less twisting of helical bridges during stretching than configurations that included only one rotational direction. In the cassette configuration, basket arrays were designed to have an overall dimension of 30 mm x 20 mm x 11.2 mm. In a stretched, well-plate configuration, the basket arrays were designed to have an overall dimension of 101 mm x 65 mm x 10 mm, as shown in FIG. 7B. Edge baskets were intentionally printed without bottoms for fixing onto a well plate during cell culturing (see Array Operation). [00122] Results of heated recovery testing of the designed arrays are shown in FIG. 7C. Heated recovery was measured quantitatively using a customized digital image tracking code. Markers were labeled on the connecting points between bridges and were traced using digital image processing. D ₀ indicates original size of a unit basket, which was 2.5 mm. D indicates measured size at timestamps during heating. Heating started from room temperature at 0 min for capturing size after shape fixing. Once the temperature reached 50°C, the temperature was maintained until the end of experiment. The starting ratio of D ₀ /D at 0 min was 2.9 instead of 3.6 (ratio of size of well plate/size of cassette). This was caused by imperfect shape fixing of SMP during shape programming. After 120 min of heating, the basket arrays recovered to 1.2 times its original size instead of 1. This was due to friction between the bottom surface and basket arrays. From FIG. 7C, it can be seen that recovery mostly happened during the first 20 min of heating and slowed down significantly in the rest of experiment. A lO-min heating time was chosen in further cell-culturing operations as the temperature used for recovery was maintained at 50°C (without heating from room temperature, as in this characterization experiment). Since basket arrays are flexible and can be squeezed to fit into cassettes after recovery, 100% recovery using long-time heating is not necessary and may be undesirable as cells may be negatively affected by exposure to the higher temperature of 50°C than 37°C for an extended period of time.

[00123] For shape recovery characterization, black markers were drawn on connecting parts of helical bridges, as shown in FIG. 11 A. A 45-degree mirror was used on top of basket arrays so a digital camera (Canon 60D) can view the arrays from a horizontal configuration. The basket arrays and mirror were kept inside a temperature oven and the camera was maintained outside the oven. A transparent window at the door of oven was used for visibility during experiment. After obtaining video of shape recovery, an example of which is shown in FIG. 11B, image processing using MATLAB was applied on images at different timestamps to obtain coordinates of markers. Detected markers were indicated using red squares, as shown in FIG. 11C. Distance was then calculated to between corresponding markers to obtain size of baskets. Since there are clockwise (CW) and counterclockwise (CCW) baskets, periodicity in a basket arrays was considered to be a combination of one CW and one CCW basket. Six pairs of markers from a repeating unit (two baskets) were measured at each timestamp. Then results were divided by two to obtain average and standard deviation of size of one basket. [00124] Array Operation

[00125] Operation of the arrays is shown in FIG. 8. At room temperature, a basket array in a cassette configuration was first mounted on a customized stretcher, as shown in FIGS. 9A-9D. The stretcher included eight rails configured to simultaneously move all carriages sitting in the rails between the dimension of a cassette and the dimension of a 96-well plate. To provide for uniform stretching, a number of rails is desired to be the same as the number of edge baskets. However, due to limited space at a cassette configuration, only eight rails were fit in the test device.

[00126] The top acrylic plate was laser cut with eight straight rails. Patterns of rails connected locations of eight evenly distributed baskets in the original configuration (17.5 x 27.5 mm) with locations of same baskets in the stretched configuration (105 x 165 mm) (stretching capability of 6 times). A bottom acrylic plate was laser cut with eight curved rails that are compatible with straight rails. Top rails had a width of 5 mm and bottom rails had a width of 3 mm. Cylindrical carriages had a diameter of 5 mm in top portion and 3 mm in bottom portion. Carriages with 12 needle pins (diameter of 0.8 mm) sitting in both rails can move from a small configuration to a large configuration by rotating the top plate against bottom plate.

[00127] The basket array was stretched to a 96-well plate configuration by rotating the top and bottom plates against each other at room temperature. The helical bridges of each basket unwinded during rotation of the stretcher, as shown in FIGS. 9B and 9D. In the test device, in the compact configuration shown in FIGS. 9A and 9C, a first distance in the x-direction (Al) was 27.5 mm and a first distance in the y-direction (Bl) was 17.5. After rotation, in the expanded configuration shown in FIGS. 9B and 9D, a second distance in the x-direction (A2) was 165 mm and a second distance in the y-direction (B2) was 105 mm.

[00128] After rotation, both the basket array and stretcher were placed in a temperature oven at 50°C for 10 min and then cooled down to room temperature to fix the stretched shape. Then basket arrays were then removed from the stretcher with the temporarily programmed shape.

[00129] At this stage, the temporary shape did not match exactly with 96-well plate.

Basket arrays were then mounted onto a fixture, a schematic of which is shown in FIGS. 10A-10B, by slightly further stretching of the edge baskets to match corresponding pins of the fixture. The fixture was designed to match edge units of basket arrays and a 96-well plate. [00130] The fixture was 3D printed using a fused deposition modeling (FDM) printer (pPrint, Stratasys). The fixture included a window in its center and pins that match edge baskets with edge wells in 96-well plate. A CAD design of fixture the fixture is shown in FIGS. 10A-B. The dimensions of the fixture, with reference to FIG. 10A were as follows: 99 mm (A), 9 mm (B), 64 mm (C).

[00131] Another advantage of including a fixture is to restrain the SMPs recovery behavior over time. After fixing, a SMP will gradually restore its original shape at a temperature dependent speed ( e.g ., higher rate at higher temperature). Since cell culturing processes typically occur at a temperature of 37°C for two weeks, a fixture can ensure that shape recovery of the array does not occur during this period of time.

[00132] The fixture with the basket array was then placed on a 96-well plate for cell seeding. Cells were injected into each basket using micropipette and cell culture media were added into wells and baskets. After cell culture, basket arrays were removed from the fixture and heated to 50°C to induce shape recovery. Once the array reached a cassette configuration, it was ready for histology processing.

[00133] Example 2. Biocompatibility Verification of 4D Cell-Culture Arrays

[00134] Organoid growth in manufactured cell culture arrays was examined to verify biocompatibility of the arrays. In particular, 3D-printed cell-culture arrays were fabricated as described in Example 1 and used for histological analysis of patient derived organoids (PDOs) for glioblastoma (GBM) therapy.

[00135] The biocompatibility of the basket arrays for generating GBM spheres and GBM organoids and histological processing and imaging was examined.

[00136] Sphere and organoid numbers, viability, and differentiation potential were quantified upon basket memory reconfiguration at 50°C. ETse of the cell-culture array was shown to reduce tissue fixation time from, historically, 1-3 days to 6 hours, as shown in the histological processing steps shown in FIG. 12A and obtained microtome sections shown in FIG. 12B. SMP baskets were also determined to be compatible with automated processing methods. Three rounds of histological processing and Hematoxylin and Eosin (H&E) staining determined the processing time and cutting parameters for use with the biomaterial, results of which are shown in FIG. 12B.

[00137] SMP compatibility with 10% neutral buffered formalin fixation was supported, while GBM cell integrity was maintained in the twelve-step histological assay process shown in FIG. 12 A. Individual baskets, intact or sectioned, were used to facilitate cell seeding and organoid formation, as shown in FIG. 13. Cross-section, side-section, and magnified areas of sample baskets without (top views) and with (bottom and right-side magnified views) cells plated as organoids are shown in FIG. 13. Note that the baskets allowed initiations of GBM PDOs within 72 hours, as shown in the magnified view in FIG. 13.

[00138] While SMP components were compatible, PEGDA 700 developed opacity with prolonged fixation and was replaced with PEGDA 250 in the prototype basket arrays.

[00139] The effects of SMP components on cell viability were examined in both EG87 and primary GBM 3D cultures. Formation of EG87 GBM spheres within one week was overall comparable with or without SMP baskets, as shown in FIG. 14 A. Bright field images of GBM spheres derived from EG87 cells in the presence of FBS and grown with no basket and with baskets are shown in the bright field images of FIG. 14 A.

[00140] When primary GBM#50 cells were grown in either serum-free sphere conditions (no matrigel) or as GBM organoids, large GBM spheres and diversified organoids with multicellular connections were detected after one or two weeks, respectively, in the absence of basket arrays. With the basket arrays, the number and size of primary spheres or organoids were significantly reduced (FIGS. 14B-C). GBM organoids grown in serum-free conditions with growth factors derived from GBM#50 cells with no basket and with baskets are shown in the bright field images of FIG. 14B. GBM #50 cells grown in matrigel spheres with no basket and with baskets are shown in the bright field images of FIG. 14C.

[00141] ETnexpectedly, these studies suggested that serum or matrigel could have neutralizing effects on the biomaterial components. To investigate each component, it was first determined, by measuring media levels in prolonged cultures, that baskets were not absorbing media and, thus, were limiting growth factor availability. Notably, prolonged culture media were yellow-tinted and more alkaline compared to control culture, suggesting that the basket biomaterial could be leaching low levels of chemicals that may interfere with long-term organoid cultures.

[00142] SMP components, including poly (Ethylene glycol) diacrylate 250 (PEGDA 250), Bisphenol A (BPA), photo-initiator (PI) and photo-activator (PA) were each examined in the GBM intracellular ATP cell viability assay. Only PEGDA250, when used at three log concentration of median dose (1,000 fold in excess of EC50 at 7.2 mM) showed a significant loss of cell viability (FIGS. 15A-C), suggesting that low PEGDA 250 levels may be leaching from the basket during long-term organoid culture. Preincubation of the basket array after 3D printing into culture media, PBS, 10% BSA, or b-mercaptoethanol (at 10 mM or 50 mM) did not reverse the cell loss phenotype, but presoaking of basket arrays after 3D printing into 100% acetone, followed by PBS and ethanol washes did (FIGS. 16A-F). Based on these data, 3D printed SMP basket arrays were established for PDO generation and drug assays to identify effective treatments for primary GBM.

[00143] FIG. 15A illustrates the results of the cell titer glo assay that utilizes ATP levels and was used to determine GBM viability in the presence of component biomaterials. FIGS. 15B and 15C are low-power images of bright fields of spheres cultured for one week in the presence of the indicated chemicals and concentrations. The insets are higher power (20x) magnification of the 5x images. Only PEGDA250 when used at 7.2 pM induced a significant loss of cell viability.

[00144] Acetone soaking was shown to allow biomaterial basket GBM sphere and organoid long-term culture, as shown in FIGS. 16A-F. Different components of basket biomaterial were individually examined at the final concentrations used in the prototype basket array were shown to allow normal sphere culture (FIG. 16B). Soaking of a basket array in a 100% acetone bath after 3D printing allowed normal sphere culture (FIG. 16C). GBM organoid culture upon soaking for 12-14 h in acetone gradually improved effects (FIG. 16D and 16F). The soaking of a basket array in a 100% acetone bath after 3D printing allowed normal GBM organoid culture (FIG. 16E).

[00145] The platform developed was then examined with GBM tissues for both paraffin embedding for histological analysis and genomic sequencing, and with live GBM tissue for generating spheres and organoids for drug sensitivity testing. GBM tissues were subjected to exome sequencing to simultaneously detect the genetic alterations characteristic for adult GBM (GlioSeq) and identify deregulated pathways to guide the selection of targeted therapies. GlioSeq analyzes 30 genes for single nucleotide variants (SNVs) and indels, 24 genes for copy number variations (CNVs), and 14 types of structural alterations in BRAF, EGFR, and FGFR3 genes in a single workflow. Single cells were seeded at clonal densities in ultra-low attachment plates with basket arrays for sphere formation or in extracellular matrix droplets for organoid formation. GBM spheres or organoids were kept in serum-free growth factor supplemented conditions. The sphere assay is a functional assay to study GICs expressing sternness factors such as NESTIN, SOX2, OLIG2 and ZEB129. When bFGF and EGF were removed or GBM spheres cultured on polyomithine coated-surfaces, GBM cells underwent differentiation with GIC loss. In contrast, 3D cultured GBM organoids were heterogenous and capable of interconnecting (mimicking brain cells) and differentiating into cells with multiple cell phenotypes. Immunofluorescence (IF) for the neural stem cell protein NESTIN, and primitive neuroepithelium neuron-specific TUBULIN-beta-III and mature astrocytic Glial fibrillary acidic protein allowed to distinguish sternness from differentiation.

[00146] The basket arrays were used to deploy rapid single cell derived sphere and organoid assays to assess tumor cell viability, tumor invasion, terminal differentiation and resistance to therapy for cancer drug discovery and drug validation. Single and/or clonal GBM cell derived PDOs formed in 2 weeks and demonstrated invasion of the semisolid matrix by extended invadopodia. PDOs were treated for 72-hours with standard

chemotherapy (TMZ) and/or molecularly targeted agents, targeting mTOR, PI3K, BMI1, EGFR, and DDR, among others. Following treatments, the entire 4D printed basket arrays were evolved, with a lO-min heating step at 50°C, to their programmable cassette size to directly perform histological and IHC validation on the same day, and with the convenience of maintaining the same tissue plate arrangement. The concentrations inhibiting viability by 50% (GI50), real time activated caspase 3 for detection of apoptotic cells and GBM tumor cell invasion in live intact organoid cells were less impacted by standard TMZ than targeted therapies. Critically, treatment with molecularly targeted agents alone or in combination had significantly more GBM organoid cell killing than TMZ, particularly in apparently TMZ resistant organoids, with targeted therapy reducing EGFR expression in organoid cells that were not affected by TMZ treatment, and with effective biomarker responses to targeted therapies, even at lower level combinations.

[00147] The cell-culture array platform allowed the entire patient tissue and drug response assessment to be completed in <20 days. When including exome and/or single cell sequencing, histological, IHC and targeted therapeutic assays, the array platform was demonstrated to offer dynamic, automated and quantitative drug analyses, thus allowing the discovery of novel preclinical therapeutic approaches that can be assessed in clinical trials and may be used to examine and select personalized therapies in precision medicine oncology.

[00148] While example embodiments have been particularly shown and described, it will be understood by those skilled in the art that various changes in form and details may be made therein without departing from the scope of the embodiments encompassed by the appended claims. [00149] References

[00150] 1. Giannitelli SM, Mozetic P, Trombetta M, Rainer A. Combined additive manufacturing approaches in tissue engineering. 2015, Acta Biomater 24: 1-11.

[00151] 2. Truby RL, Lewis JA. Printing soft matter in three dimensions. 2016, Nature

540:371-378.

[00152] 3. Chan V, Jeong JH, Bajaj P, Collens M, Saif T, Kong H, Bashir R. Multi material bio-fabrication of hydrogel cantilevers and actuators with stereolithography. 2012, Lab Chip 12:88-98.

[00153] 4. Tumbleston JR, Shirvanyants D, Ermoshkin N, Janusziewicz R, Johnson AR,

Kelly D, Chen K, Pinschmidt R, Rolland JP, Ermoshkin A, Samulski ET, DeSimone JM. Additive manufacturing. Continuous liquid interface production of 3D objects. 2015, Science 347: 1349-52.

[00154] 5. Zheng X, Deotte J, Alonso MP, Farquar GR, Weisgraber TH, Gemberling S,

Lee H, Fang N, Spadaccini CM. Design and optimization of a light-emitting diode projection micro-stereolithography three-dimensional manufacturing system. 2012, Rev Sci Instrum 83: 125001.

[00155] 6. Gladman AS, Matsumoto EA, Nuzzo RG, Mahadevan L, Lewis JA.

Biomimetic 4D printing. 2016, Nat Mater 15:413-8.

[00156] 7 Raviv D, Zhao W, McKnelly C, Papadopoulou A, Kadambi A, Shi B, Hirsch S,

Dikovsky D, Zyracki M, Olguin C, Raskar R, Tibbits S. Active printed materials for complex self-evolving deformations. 2014, Sci Rep 4:7422. PMC4270353.

[00157] 8. Mao Y, Yu K, Isakov MS, Wu J, Dunn ML, Jerry Qi H. Sequential Self-

Folding Structures by 3D Printed Digital Shape Memory Polymers. 2015, Sci Rep 5: 13616. PMC4562068.

[00158] 9. Couchman, P. R. Compositional Variation of Glass Transition Temperatures. 2.

Application of the Thermodynamic Theory to Compatible Polymer Blends. Macromolecules 11, 1156-1161, doi: l0. l02l/ma60066a0l8 (1978).

[00159] The teachings of all patents, published applications and references cited herein are incorporated by reference in their entirety.