Patent Application
20220125930
Regenerated silk fibroin (RSF) is a protein biopolymer with biocompatibility, aqueous processability, and useful mechanical characteristics for biomaterials in the forms of films, hydrogels, sponges, fibers, and particles. RSF-based particles (RSFPs) with tunable morphologies and physical-chemical properties are useful as drug delivery systems (DDSs). For example, RSFPs less than 200 nm in diameter can be used as intravenous DDSs with extended half-lives in circulation, for controlled pharmacokinetics. Particles several microns in diameter can be used subcutaneously and intravenously to localize at injection sites. Large biopolymer-based particles with diameters 50 to 1,000 μm have a broad range of potential applications in photonic materials, as chromatography column solid supports for separations, in field-responsive rheological fluids, and as injectable DDSs for chemotherapeutic treatment of tumors and bacterial infections.
Spherical and cubical meso-particles for drug release are conventionally produced from gelatin, polyvinyl alcohol, polyacrylamide, and silicone. Polyacrylic and polyvinylalcohol-co-acrylamide spheres, 100 to 800 μm in dimeter, have been produced by double emulsion polymerization. Microfluidic coagulation and mechanical grinding of PVA-sheets have been shown to produce drug eluting polyvinyl alcohol-based particles of about 180-900 μm in diameter. A similar coagulation approach has been successfully applied to fabricate silk sericin/lignin blended beads up to 2,000 μm in diameter for the removal of Cr(IV) from waste water.
Silk-based materials bind doxorubicin (DoxR), with beta-sheet content of the SF controlling release kinetics. Silk-based micro- and meso-spheres has been explored, including those generated by salting-out, self-assembly, spray-drying, and mechanical grinding. Microfluidic techniques using laminar flow encapsulation and electrospinning offered effective control over the particle size over the range of 100-2,000 μm. The bulk emulsification-based assembly of silk particles by a drop dissolution techniques have produced spheres with monolith internal morphology. However, continuous production of polymeric meso-particles by microfluidic approaches using a double emulsion processes require precise tuning of the injector nozzle diameter and control over the rheology and fluid dynamics of the injected polymer solutions. In addition, such techniques require careful selection of the starting monomer-to-initiator ratio, stirring rate, temperature and pH of the emulsification bath.
Faster granulation techniques based on high shear phase separation of liquefied RSF in supercritical CO2 produced monodisperse silk nano-particles have also been studied and are suggestive of an alternative for the assembly of silk. However, there is a large expense of scale-up when using CO2-assisted setups for high shear emulsification of silk solutions.
Thus, what is needed are novel, simplified systems and methods for quickly forming regenerated silk fibroin particles that may be useful for drug delivery systems.
Systems and methods described herein relate to, inter alia, production of porous drug-eluting particles using cryogranulation. Consequently, the present disclosure addresses the aforementioned drawbacks by providing novel systems and methods for the fabrication of large sized silk particles using cryogelation. These advancements are useful for many applications, including drug delivery. The size distribution, morphology, and cross-linking efficiency of the resulting RSFPs depends upon the concentration of a cross-linking agent, a silk solution concentration, a coagulation bath temperature, and an injection pressure.
In one aspect, the present disclosure provides a method of making drug-eluting particles. The method can comprise injecting a mixture into a super-cooled fluid, the mixture comprising regenerated silk fibroin and at least one medicament, wherein the super-cooled fluid has a temperature of less than −40 degrees Celsius. The super-cooled fluid can be an organic solvent, organic mixture, or organic solution.
In another aspect, the present disclosure provides a method of making drug-eluting particles. The method can comprise injecting a mixture into a super-cooled fluid, the mixture comprising regenerated silk fibroin and at least one medicament, wherein the super-cooled fluid consists essentially of butane, pentane, hexane, heptane, octane, nonane, decane, or a mixture thereof.
In one aspect, the present disclosure provides a method of treating a subject. The method can comprise administering a drug-eluting particles made by one of the methods described herein to the subject.
In another aspect, the present disclosure provides a regenerated silk fibroin particle for drug elution. The regenerated silk fibroin particle may be characterized by being formed by one of the methods provided herein.
In another aspect, the present disclosure provides a system for making drug-eluting particles. The system may include a coagulation container system configured to maintain a temperature below −40 degrees Celsius for the fluid retained therein; a super-cooled fluid located within the coagulation container system; a source of a mixture comprising at least one medicament and regenerated silk fibroin, the mixture optionally comprising a cross-linking agent; and an injection unit positioned above a surface of the super-cooled fluid and configured to inject the mixture into the super-cooled fluid.
In one aspect, the present disclosure provides a system for making drug-eluting particles. The system can comprise one or more components described herein for the automatic execution of any of the method steps described herein.
These and other advantages and features of the present invention will become more apparent from the following detailed description of the preferred aspects of the present invention when viewed in conjunction with the accompanying drawings. In the description, reference is made to the accompanying drawings which form a part hereof, and in which there is shown by way of illustration a preferred embodiment of the invention. Such embodiment does not necessarily represent the full scope of the invention, however, and reference is made therefore to the claims and herein for interpreting the scope of the invention. It should be understood, that the detailed description, while indicating embodiments of the present invention, is given by way of illustration only, not limitation. Various changes and modifications within the scope of the invention will become apparent to those skilled in the art from the detailed description.
The drawings described herein are for illustration purposes only and are not intended to limit the scope of the disclosed embodiments in any way. The drawings described herein are for illustrative purposes only of selected embodiments and not all possible implementations, and are not intended to limit the scope of any of the various embodiments. It is understood that the drawings are not drawn to scale.
Before the present invention is described in further detail, it is to be understood that the invention is not limited to the particular embodiments described. It is also to be understood that the terminology used herein is for the purpose of describing particular embodiments only, and is not intended to be limiting. The scope of the present invention will be limited only by the claims. As used herein, the singular forms “a”, “an”, and “the” include plural embodiments unless the context clearly dictates otherwise.
Specific structures, devices and methods relating to RSF-based particles are disclosed. It should be apparent to those skilled in the art that many additional modifications beside those already described are possible without departing from the inventive concepts. In interpreting this disclosure, all terms should be interpreted in the broadest possible manner consistent with the context. Variations of the term “comprising” should be interpreted as referring to elements, components, or steps in a non-exclusive manner, so the referenced elements, components, or steps may be combined with other elements, components, or steps that are not expressly referenced. Embodiments referenced as “comprising” certain elements are also contemplated as “consisting essentially of” and “consisting of” those elements. When two or more ranges for a particular value are recited, this disclosure contemplates all combinations of the upper and lower bounds of those ranges that are not explicitly recited. For example, recitation of a value of between 1 and 10 or between 2 and 9 also contemplates a value of between 1 and 9 or between 2 and 10.
As used herein, the term “super-cooled fluid” has its ordinary meaning in the art. In one some aspects, a “super-cooled fluid” defines a fluid, such as a liquid or a gas, that has a temperature below its freezing point, yet it maintains fluid state and does not solidify.
As used herein, the term “biocompatible” refers to materials that do not cause significant harm to living tissue when placed in contact with such tissue, e.g., in vivo. In certain embodiments, materials are “biocompatible” if they are not toxic to cells. In certain embodiments, materials are “biocompatible” if their addition to cells in vitro results in less than or equal to 20% cell death, and/or their administration in vivo does not induce significant inflammation or other such adverse effects.
As used herein, the term “biodegradable” refers to materials that, when introduced into cells, are broken down (e.g., by cellular machinery, such as by enzymatic degradation, by hydrolysis, and/or by combinations thereof) into components that cells can either reuse or dispose of without significant toxic effects on the cells. In certain embodiments, components generated by breakdown of a biodegradable material are biocompatible and therefore do not induce significant inflammation and/or other adverse effects in vivo.
As used herein, the term “macroparticle” refers to a particle having a diameter of at least 1 millimeter. In some embodiments, a population of particles is considered a population of macroparticles if the mean diameter of the population is equal to or greater than 1 millimeter.
As used herein, the term “microparticle” refers to a particle having a diameter between 1 micrometer and 1 millimeter. In some embodiments, a population of particles is considered a population of microparticles if the mean diameter of the population is between 1 micrometer and 1 millimeter.
As used herein, the term “nanoparticle” refers to a particle having a diameter of less than 1000 nanometers (nm). In some embodiments, a nanoparticle has a diameter of less than 300 nm, as defined by the National Science Foundation. In some embodiments, a nanoparticle has a diameter of less than 100 nm as defined by the National Institutes of Health. In some embodiments, a population of particles is considered a population of nanoparticles if the mean diameter of the population is equal to or less than 1000 nm.
As used herein, a material, additive, and/or entity is “pure” if it is substantially free of other components. For example, a preparation that contains more than about 90% of a particular agent or entity is typically considered to be a pure preparation. In some embodiments, an agent or entity is at least 91%, at least 92%, at least 93%, at least 94%, at least 95%, at least 96%, at least 97%, at least 98%, or at least 99% pure.
As used herein, the term “substantially” refers to the qualitative condition of exhibiting total or near-total extent or degree of a characteristic or property of interest. One of ordinary skill in the biological arts will understand that biological and chemical phenomena rarely, if ever, go to completion and/or proceed to completeness or achieve or avoid an absolute result. The term “substantially” is therefore used herein to capture the potential lack of completeness inherent in many biological and chemical phenomena.
Described herein are systems and methods related to the production of drug-eluting regenerated silk fibroin particles using cryogranulation. The simplified method of fabrication is capable of creating drug-eluting silk particles having various sizes and porosities. The produced particles have many practical uses, such as in chromatography column solid supports for separations, in field-responsive rheological fluids, and as injectable DDSs for treatment of a subject, such as chemotherapeutic treatment of tumors and bacterial infections.
Although not depicted, the method 100 may further comprise the step of incubating the drug eluting particles in the super-cooled fluid to promote cryogelation. This incubation may occur for about 5, 10, 15, 20, 25, 30, or 60 minutes. The super-cooled fluid incubation may specifically occur for between 5 and 15 minutes. After this incubation period, the method 100 may further comprise a step of extracting the drug eluting particles from the super-cooled fluid. A basket or liquid-permeable membrane may be positioned in the super-cooled fluid and be used to extract the drug-eluting particles. The rapid formation of particles allows for the above steps to be incorporated into a batch, semi-batch, or continuous production process. The super-cooled fluid can have a temperature of less than −40 degrees Celsius, less than −50 degrees Celsius, less than −55 degrees Celsius, less than −60 degrees Celsius, less than −65 degrees Celsius, or less than −70 degrees Celsius.
After extraction, the method 100 may comprise a step of further incubating the drug-eluting particles in a cooling chamber in order to facilitate internal cryogelation of the silk fibroin. Residual super-cooled fluid may also be removed during this step. The cooling chamber may have a temperature of about −10, −15, −20, −30, −35, or −40 degrees Celsius. The temperature may be specifically maintained around −20 degrees Celsius. The incubation in the cooling chamber may be for a period of at least 10 hours, 20 hours, 30 hours, or longer. The method may further comprise a step of lyophilizing the drug eluting particles, which may take place after the cooling chamber incubation. The lyophilization may occur at a pressure below 0.1, 0.05, 0.01, 0.05, or 0.001 kilopascal. The lyophilization may occur for a period of about 6, 12, 24, or 48 hours.
The super-cooled fluid of the method may comprise butane, pentane, hexane, heptane, octane, nonane, decane, or a mixture thereof. The super-cooled fluid may specifically be hexane. The super-cooled fluid may consist essentially of butane, pentane, hexane, heptane, octane, nonane, decane, or a mixture thereof. The super-cooled fluid may consist of butane, pentane, hexane, heptane, octane, nonane, decane, or a mixture thereof. The super-cooled fluid may be agitated to prevent freezing. In some aspects, the super-cooled fluid may be substituted with a super-cooled fluid having a low freezing point. The temperature of the super-cooled fluid may be below −40, −50, −55, −60, −65, or −70 degrees Celsius. The temperature may be specifically between −60 and −65 degrees Celsius. The super-cooled fluid may specifically have a temperature of less than −40 degrees Celsius.
The mixture of the method 100 may further comprise at least one cross-linking agent in addition to the regenerated silk fibroin and at least one medicament. The at least one cross-linking agent may be selected from the group consisting of ethylene glycol diglycidyl ether, poly(propyleneglycol)dyglycidyl ether, acetone, polyethylene glycol (PEG-400), or mixtures thereof. The method 100 may further comprise a step of mixing the cross-linking agent with an aqueous solution of the at least one medicament and the silk fibroin to form the mixture, wherein this step occurs prior to the injection of the mixture. This preliminary step may initiate gelation. The mixing may comprise vortexing the crosslinking agent and the aqueous solution. The aqueous solution may include a buffer, or specifically a basic buffer. The weight percent of silk fibroin in the mixture may be between 2 and 10 percent, between 3 and 6 percent, or between 4 and 5 percent.
The mixture may be injected in the method 100 using a needle positioned above the super-cooled fluid. The needle may be positioned at a sufficient distance above the super-cooled fluid to allow particle formation. The outlet of the needle may be positioned 1, 5, 10, 30, 40, or 50 millimeters above the super-cooled fluid. The mixture may be injected using a needle having an internal diameter between 0.2 and 0.8, between 0.3 and 0.6, or between 0.4 and 0.5 millimeters. The mixture may be injected at a pressure sufficient to produce a jet. For instance, the mixture may be injected between 80 and 300 kilopascals. The mixture may have a shear viscosity below at least 0.5, 1, 2, 3, 4, or 5 poise.
The medicament of the method 100 may be a therapeutic agent. For instance, the medicament may be selected from the group consisting of proteins, peptides, nucleic acids, nucleic acid analogs, nucleotides or oligonucleotides, peptide nucleic acids, aptamers, antibodies or fragments or portions thereof, antigens or epitopes, hormones, hormone antagonists, growth factors or recombinant growth factors and fragments and variants thereof, cell attachment mediators, cytokines, enzymes, antibiotics or antimicrobial compounds, viruses, toxins, prodrugs, chemotherapeutic agents, small molecules, drugs, and combinations thereof. The medicament may specifically be an antibiotic. If an antibiotic, the medicament may be selected from the group consisting of doxorubicin chloride, gentamicin sulfate, tobramycin sulfate, and kanamycin sulfate.
As shown in this depiction, the system 400 may further comprise a processor 410 coupled to the system and configured to control one or more of the following operational parameters: the temperature of the coagulation container system 401 and/or the super-cooled fluid 404; an injection pressure of the injection unit 408; an injection gage of the injection unit 408; a medicament concentration of the mixture 406; a regenerated silk fibroin concentration of the mixture 406; or a cross-linking agent concentration of the mixture 406.
The coagulation container system 401 may be configured to hold a fluid of variable volume and maintain a low temperature. For instance, the container system may maintain a temperature of about −40, −50, −55, −60, −65, or −70 degrees Celsius. The container system 401 may maintain such fluid temperatures using refrigeration techniques commonly known in the art, such as a dry ice bath or cooling jacket 405 surrounding a coagulation container 402. The super-cooled fluid located within the coagulation container system may have the same composition as the super-cooled fluids of the methods described herein. The coagulation container system may have a super-cooled fluid inlet and outlet, wherein super-cooled fluid may be introduced and removed from the system. This can allow for continuous production of particles without degeneration and contamination of the super-cooled fluid over time. The coagulation container system may have an agitation component, such as a stirrer, to maintain a liquid state super-cooled fluid.
The injection unit 408 may have a needle having an orifice or a comparable component for introducing the mixture. Such an orifice may be positioned about 1, 5, 10, 30, 40, or 50 millimeters above the top surface of the super-cooled fluid 404. The injection unit may be configured to continuously provide a uniform pressure to introduce the mixture. Suitable uniform pressures include those discussed for the methods herein. The coagulation system may further comprise an extraction system to assist in the removal of the particles. The extraction system may operate in a continuous, automated manner.
In another aspect, a system for making drug-eluting particles is provided. The system may comprise one or more components described herein for the automatic execution of any of the method steps described herein.
The following examples set forth, in detail, ways in which the drug-eluting silk particles may be synthesized, and will enable one of skill in the art to more readily understand the principles thereof. The following examples are presented by way of illustration and are not meant to be limiting in any way.
A method for the preparation of large, microporous, drug-loaded particles was discovered and evaluated through an experimental study. High shear bollus injections of silk with cross-linker and drug colloids into super-cooled hexane were utilized to trigger phase separation of silk droplets, followed by immediate freezing at −60° C. A subsequent −20° C. freeze-thaw of the frozen droplets resulted in self-assembly (crystallization) of the silk. The silk particles developed an internal interconnected microporous morphology with 0.1-10 μm in diameter pores. The silk particles ranged in diameter from 100 to 1,300 μm, with particle mean diameter and polydispersity controlled by the starting concentration of the cross-linking agent and silk, the rheology of the reaction mixture, and the injection pressure (80-300 kPa). Cryogranulation provided a one-step process to produce microporous meso-scale silk particles with encapsulated drugs, such as doxorubicin chloride (DoxR), tobramycin sulfate (TS), kanamycin sulfate (KS) or gentamicin sulfate (GS). Almost 100% drug encapsulation efficiency was achieved in the process, and subsequent release profiles depended on the starting concentration of both the drug, silk, and pH of the elution medium. Kirby-Bauer tests and bioluminescent imaging confirmed the retention of anti-bacterial potency of the antibiotics pre-encapsulated in the cryo-particles, and macroparticles cytocompatibility towards human fibroblast and kidney cells.
The following materials were used in the study: hexanes, for analysis (Thermo Fisher Scientific Co., US), ethylene glycol diglycidyl ether (EGDE, Tokyo Chemical Industry Co., Ltd.), poly(propyleneglycol)dyglycidyl ether (pPGDE, average Mn 500), gentamicin sulfate; acetone for HPLC, GC and residue analysis, ≥99.9%, tobramycin sulfate (all Sigma-Aldrich, 650501); kanamycin sulfate (Thermo Fisher Scientific Co., US); borate buffer was prepared using BupH™ Borate Buffer Packs (Thermo Fisher Scientific Co., US).
To obtain regenerated silk fibroin (RSF), Bombyx mori cocoons were extracted for 45 min in boiling aqueous solutions of sodium carbonate (0.02 M), then rinsed quickly with distilled water three times to remove the excess salt and sericins. The extracted silk was loosened and dehydrated overnight at 25° C. under airflow. The dried silk mass was then dissolved in lithium bromide solution (9.3 M) for 4 h at 60° C. with occasional gentle agitation to yield a 20% w/v solution which was then cooled to 25° C. and dialyzed against distilled water for 48 h using cellulose dialysis tubing (molecular weight cutoff, MWCO, 3,500, Fisherbrand by Fisher Scientific Co., Pittsburgh, Pa.) to remove the salt. Thus obtained aq. solution of fibroin (ASF) was then subjected to the dialysis against borax buffer (pH 8.5) for 24 hours. The resulting basic solution of fibroin was checked visually for optical clarity and centrifuged and decanted 3 times at 9,000 rpm at 4° C. to remove residual solids or debris. The final concentration of aqueous silk solution was 9.5% wt., determined gravimetrically based on the residual dry solids weight.
Each batch of RSFPs was produced using the custom designed silk cryogranulation assembly comprised of the coagulation bath, cooling jacket, 5 mL syringe, pressure switch unit, and the air compressor (
Doxorubicin chloride (DoxR), gentamicin sulfate (GS), tobramycin sulfate (TS), or kanamycin sulfate (KS) were dissolved in BupH buffer (pH 8.5) and blended with the stock ASF and 10% vol. acetone to obtain final drug concentrations in range from 1 to 20 mg/mL. The resulting drug/RSF/cross-linker was immediately injected at 150 kPa into the supercooled hexane bath. The frozen RSF/drug droplets were harvested from hexane, incubated for 20 hours at −20° C. and freeze-dried to remove traces of hexane, water, and acetone. The total antibiotic content in the RSF beads was determined gravimetrically by subtracting the average dry weight of the blank RSFPs from the average dry weight of drug-loaded RSFPs.
To synthesize silk nanoparticles, 45-minute extracted RSF solution in BuPh buffer (pH 8.5) was used. In brief, the ASF was diluted to 5% wt. of RSF and mixed dropwise (0.2 drop/s; ca. 100 μL/drop) to pure acetone, with the final acetone fraction accounting for 80% (v/v). Silk particulated were left to precipitate overnight, then centrifuged for 30 min at 9,000 rpm, followed by aspiration of the supernatant and re-suspension/vortexing of the pellet in 35 mL of DI water. Crude SF suspensions were then sonicated for 30 s at 30% amplitude with a Branson Digital Sonifier 450 (Branson Ultrasonics, Danbury, Conn., USA). The centrifugation-washing-suspension cycle was repeated twice to obtain silk nano-suspensions (nRSF). A 0.5-mL aliquot of the n-RSF was freeze-dried and the dry solids content was determined gravimetrically. Prior to cryo-granulation, the n-RSF suspension was subjected to a 15 s sonication at 30% amplitude followed by size and zeta potential assessments with a Microbrook 2000 L laser particle-size analyzer (BrookHaven Instruments Corporation, NY). A calculated volume of the n-RSF suspension was mixed with the DoxR for 2 hours at 25° C. with constant agitation (200 rpm). The resulting system, containing free DoxR and DoxR-loaded nRSFs was added to the ASF stock to reach concentrations of n-RSF in the system in range from 3 to 6 mg/mL. These mixtures were immediately mixed with 10% vol. acetone and subjected to the above cryo-granulation process at 150 kPa, to produce nano-modified DoxR-loaded RSFPs.
IR-Spectra of the lyophilized RSFPs as well as pure RSF and cross-linking agents (in liquid from) were acquired using a single bounce diamond attenuated total refractance (ATR) module on a Fourier-transform infrared (FTIR) spectrometer (JASCO FTIR 6200 Spectrometer, JASCO, Tokyo, Japan) equipped with a MIRacle Ge crystal cell in the reflection mode. Air was used as the reference and subtracted automatically from sample readings. Each sample was analyzed in the frequency range from 400 to 4,000 cm−1 with each measurement adding 32 interferograms with a resolution of 4 cm−1. The fractions of secondary structures, including random coil, alpha-helices, beta-pleated sheets, and turns, were ascribed to the amide I region from 1,595 to 1,705 cm−1. Random coil, alpha-helices and β-turns were ascribed to the absorption bands in the frequency ranges of 1,638-1,655 cm−1, 1,656-1,663 cm−1 and 1,663-1,695 cm−1, respectively.
An estimate of 3 mg of lyophilized RSFPs was packed in aluminum pans and measured in a Q600 TGA/DSC instrument (TA Company, New Castle, Del.). The chamber of the instrument was purged with dry nitrogen at 50 ml/min. The instrument was calibrated with indium for heat flow and temperature. Aluminum and sapphire reference standards were used for calibration of the heat capacity. The measurements were performed using a standard mode at a heating rate of 8° C./min.
The shear viscosity of each freshly prepared injectable RSF/cross-linker system was measured by rotational rheometry (AR 2000, TA Instruments) using two 50 mm circular titanium plates at 25° C. The normal force applied on the sample during lowering of the top plate was limited to 0.1 N. The shear rate was linearly increased from 0.1 to 5,000 l/s at the steady state deformation of 15%.
Direct estimation of mean size distribution of RSFPs was performed using a combination of fluorescence microscopy and the following automated image processing with the ImageJ. The micrographs of cryo-RSFPs were recorded using a BZ-X710, All-in-One Fluorescence Microscope (Keyence, USA) with a DAPI filter and at 42× magnification. The recorded scans were further stitched and processed by contrasting and grain analysis using the ImageJ open access software.
A 100 mg load of DoxR/RSF particles with sizes between 200-800 μm was sealed in water-permeable rayon membranes and incubated in 5 mL of PBS buffer at 37° C. and constant agitation of the elution medium at 50 rpm. At determined time points, 100 μl aliquots of the elution medium were collected and the absorbance at 477 nm (DoxR) and 480 nm (DNR) was measured. The concentration of DoxR at each time point (20 min. to 14 days) was determined by extrapolation of the absorption to standard curves obtained for known concentrations of drug from 0.01 to 1 mg/mL. Non-drug cryo-RSFPs were used as negative controls.
Antimicrobial activity of tobramycin sulfate (TS), gentamicin sulfate (GS) and kanamycin sulfate (KS) encapsulated in RSFPs sized 100-500 mcm was assessed by Kirby-Bauer disc diffusion tests, performed according to methods outlined in the NCCLS Approved Standard M2-A7. A stock suspension of bioluminescent S. aureus Xen29 was prepared in sterile physiological solution and turbidity (expressed as optical density; OD) was adjusted against the McFahrland standard to match the 0.5 level. A sterilized cotton swab was immersed in the bacterial suspension, and a lawn of bacteria was applied on the Luria Bertani (LB) plates. A 10-mm biopsy punch was used to cut two circular fragments from each of the freshly infected plates, and both fragments were coated with antibiotic-loaded RSFPs by quick blotting against the pool of particles. The freshly mounted samples were inserted back into the circular slots of the bacteria-seeded plates and further cultured for 48 hours at 37° C. In vitro imaging of the plates was performed after 24 hours of incubation using a Caliper IVIS Lumina II system (Caliper life Science, America). The exposure time (1 s), excitation filter (430 nm), and emission filter with emission wavelength from 575 to 650 nm (DsRed) were set prior to detection.
The morphology of the particle's surface and inner phase of was visualized by field emission scanning electron microscopy (FE-SEM, JEOL, JSM-6490, Japan) at a voltage of 5 kV. Before analysis, the freshly lyophilized particles were positioned onto a carbon paint adherent to the aluminum sample holder. Cryo-sectioning of large (500-1,000 μm) meso-particles was used to prepare samples for the in-depth study of microporous morphology: RSF-particles were quenched in liquid nitrogen and manually crushed using a pre-cooled porcelain mortar and pestle. The resulting crushed samples were freeze-dried and fixed on the sample holder. All samples were made conductive by sputtering a thin layer of gold onto their surface.
The silk-based scaffolds were fabricated using the cryogelation protocol to closely mimic the conditions applied to RSF during the cryo-granulation procedures. Solutions of RSF were mixed with either EGDE or acetone, to give a final 4.5% wt. of RSF, 30 mmol/g of EGDE or 20% vol of acetone. These mixtures were molded in a 48-well plate and frozen using dry ice as coolant. The vitrified samples were incubated at −20° C. overnight in hexane, then thawed at 4° C. and washed extensively with DI water to obtain the chemically (EGDE) or physically (acetone) cross-linked RSF-sponges, sized 8 mm in diameter and 5 mm thick. Prior to cell seeding, the compressive modulus of each type of scaffold was measured at 10 Hz with 25% compressive strain using the TA Instruments RSA3.
Immortalized human renal cortical epithelial cells (RPTEC/TERT1, ATCC, Manassas, Va., USA) and human fibroblasts (HNF) were cultured in DMEM:F12 (ATCC), 5 pM triiodo-L-tyronine sodium salt (Sigma-Aldrich, St. Louis, Mo., USA), 10 ng/ml recombinant human epidermal growth factor (Life Technologies, Grand Island, N.Y.), 1% ITS (Life Technologies), 25 ng/ml prostaglandin El (Millipore, Billerica, Ma.), 25 ng/ml hydrocortisone (Sigma-Aldrich), 0.1 mg/ml G418 (Life Technologies), and penicillin-streptomycin (Life Technologies). The RSF sponges were sterilized by autoclaving and then seeded with 2.5×105 cells/scaffold (P=4). The cultures were maintained for 21 days with the RPTEC media.
Cell viability was assessed on Days 10 and 21 using a LIVE/DEAD™ Viability/Cytotoxicity Kit for mammalian cells (L3224, Thermo Fischer Scientific). PBS (300 μl) supplemented with 10 mM calcein AM green and 1 mM ethidium homodimer-1 was added to the cells and incubated for 45 min. The samples were visualized using a BZ-X710, All-in-One Fluorescence Microscope (Keyence, USA).
After 10 and 21 days of culture, the RSF-constructs were fixed with 10% formaldehyde for 15 min, washed with three times with PBS. For immunohistochemistry, the constructs were blocked with 10% bovine serum albumin for 30 min at room temperature and incubated with primary antibodies against E-cadherin (ab1416/abcam), actin (ab3280/abcam), smooth muscle actin (ab5694/abcam) and 4′,6′-diamidino-2-phenylindole (DAPI/D1306/Thermo Scientific) was used to stain the nucleus. Alexa Fluor 546 goat anti-mouse IgG (1:200, Invitrogen) was used for fluorescent labelling. Following this step, specimens were rinsed three times with PBS/Triton and mounted for visualization by Confocal Laser Scanning Microscope (Leica TCS SP5, Germany).
Particle size measurements were obtained in triplicate for two parallel batches of RSFPs, fabricated with the given set of parameters, with and expressed as mean±standard deviation (SD). Rheological properties of the silk/cross-linker colloids and the drug release kinetics were acquired as three parallel measurements.
The main steps of the experimental batch-based silk cryo-granulation process are presented in
Hexane has a melting point between −94 and −96° C. and remains liquid upon cooling with dry ice to −60° C. and −65° C., enabling rapid separation of the RSF 50-2,000 μm droplets and stabilization of external shape and dimensions through freezing. Unlike previous cooled petroleum ether bath methods implemented for the continuous production of PVA-based meso-spheres, the process described in the present work supports processing of up to 10 mL/min of the starting RSF mixture, significantly faster compared to the prior co-flow assisted jetting devices. The residual hexane was successfully removed from the frozen RSFPs by air convection in the freezing chamber, followed by 24-hour lyophilization.
Concentrations of RSF above 6% wt. resulted in premature gelation and clogging of the injector's needle, and below 2.5% wt. RSF poorly shaped granules were produced with a tendency to shrink and disintegrate upon drying (
Apart from the emulsification of the starting RSF solutions, the additions of either diepoxides (EGDE, pPGDE) or desolvating agents (acetone, PEG-400) facilitated further solidification of silk within the frozen droplets. Structural stabilization of silk was achieved via internal cryogelation by a 20-hour freeze-thaw aging of the quenched droplets at −20° C. Cryogelation of RSF was triggered by covalent cross-linking with 5 or 30 mmol/g of EGDE. Identical concentrations of the oligomeric pPGDE were used to differentiate between cross-linker type and the morphology of the resulting epoxide-cross-linked RSFPs. Physical cryogelation of RSF within the frozen droplets was achieved through addition of acetone or PEG-400, which initiate the transition of the water-soluble Silk I conformation (characterized by a mixture of random coil, α-helix and β-turn structures), into stable and water insoluble Silk II, predominantly composed of the β-sheets. The lyophilized RSFPs, cross-linked both physically and chemically, were water-insoluble and had a powdery consistency. According to the post-granulation gravimetry, internal cryogelation with acetone resulted in gel fraction yields (mass ratio between the starting dry weight of the RSF being cross-linked and the final RSFPs weight) in range from 85 to 95%, whereas cryogelation in the presence of PEG-400 cross-linked between 68 and 75% RSF, while the EGDE- and pPGDE-assisted cryogelation cross-linked between 45 and 51% and between 59 and 74% of the starting silk, respectively. Thus, acetone/RSF mixtures were used as the matrix media to pre-disperse drug compounds to produce drug eluting beads.
The FTIR-spectra of lyophilized water soluble RSF (
Differential scanning calorimetry was used to characterize the thermal properties of the RSFPs. All particles released water, as indicated by a broad endothermal peak around 60-80° C. Further, heating the silk samples to 350° C. resulted in thermal degradation of the cross-linked protein matrix as indicated by the sharp exotherms at 285-295° C. (
Without being bound by theory, the dynamics of droplet break up, as well as droplet size and shape, are governed by the competition between the interfacial tension holding the jet of the silk colloid intact, and the Rayleigh-Plateau instability within the focused jet, which increases at higher flow rates. The cryo-granulation used here controls the size and polydispersity of the final RSFPs by both flow rate of the reactive colloid (injected under the pressures tuned within the range of 80 to 300 kPa) and the rheological properties of the colloids, in turn, defined by the cross-linker type and the cross-linker/RSF mass ratio.
The numerical data and size distribution curves (
The injection pressure and the composition of the starting RSF/cross-linker systems controlled the morphologies of the meso-RSFPs formed through the high-shear self-assembly. The non-solvent dispersion coupled with internal cryogelation generated the microporous inner morphology and wrinkled surface topology with the obtained meso-RSFPs. The textured surfaces covered the spherical RSFPs, which for most combinations of RSF/cross-linker revealed an interconnected microporous morphology of the cores (
No direct correlation between injection pressure and the surface topology of the cryo-RSFPs was observed. However, an increase of starting RSF concentration from 4 to 5.5% wt. yielded particles with more textured surfaces, including cracks, dimples or fractures. In particular, 5.5% wt. RSF with 10% vol. acetone resulted in coalesced beads, which slowed the dispersion step, quenched at the intermediate stage by the −50° C.-cooled coagulant. SEM micrographs did not reveal a decrease in RSFP size with increased RSF content. RSFPs stabilized with oligomeric PEG-400 and PPGDE displayed less static repulsion and thus more facile processability in the dry state, compared to the EGDE- and acetone-cured particles. RSFPs pre-encapsulated with DNR and DoxR displayed smooth surfaces with occasional micropores.
To evaluate the cytocompatibility of the RSFPs, we studied 30-day proliferation of RPTEC/TERT1 kidney and human normal fibroblast cell lines. Cell proliferation on the particles was characterized by confocal imaging. EGDE- and PPGDE-stabilized constructs supported cell growth over one month (
The affinity of silk towards anthracyclines provided prolonged release of DoxR, with faster release achieved at low pH levels. We obtained DoxR-encapsulated RSFPs with varying starting concentrations of RSF (4 and 5.5% wt.) and DoxR (2.25 and 4.5 mg/mL) to trace the impact of the drug/biopolymer ratio on pH-dependent pharmacokinetics. We assumed that the entire dosage of the drug was encapsulated within the resulting RSFPs as DoxR and the model antibiotics were poorly soluble in hexanes and had limited elution during the DEB cryo-fabrication step. The DoxR release from RSFPs was pH-dependent; 10-20% higher at pH 5.2, compared to the release profiles obtained at the pH 7.2. After 14 days, the total amount of DoxR released at pH 7.2 was 28-46%, depending on the starting formulation, whereas the cumulative release at pH 5.2 ranged from 38-62% (
Susceptibility tests were used to confirm post-processing antimicrobial activity of cryoencapsulated antibiotics, including tobramycin sulfate (TS), gentamicin sulfate (GS) and kanamycin sulfate (KS). The antibiotic function was preserved, evaluated by bacterial zones of inhibition (
In summary, forceful injections of RSF/cross-linker/drug compositions into water immiscible hexanes were used for production of silk beads with diameters ranging from 300 to 1,000 μm. Cryo-conditioning of the injection step by cooling the coagulation bath to ca. −65° C. arrested the shape and surface morphology of the droplets, originated from the spontaneous self-assembly after contact of emulsified RSF with the non-solvent phase. Additions of either diepoxide ethers, acetone, or polyethylene glycol played a dual function by emulsifying the reactive system enabling droplet formation and facilitating the process of either chemical (in the case of diepoxide ethers) or non-covalent internal cryogelation of silk. The freeze-thawed RSFPs had a microporous morphology resulting from ice templating which accompanied cryogelation, with pore sizes from ca. 0.1 to 10 μm in diameter. Mean diameter and width of the RSFPs distribution could be controlled by adjusting the bollus injection pressure from 80-300 kPa and by varying the viscosities of the starting reactive colloids. Injection pressures higher than 200 kPa favored the self-assembly of smaller particles of ca. 300-500 μm, while injections at lower than 100 kPa yielded the silk beads as large as 1,000 μm. The RSFPs obtained from the RSF/acetone and RSF/PPGDE mixtures had spherical morphologies with solid outer shells and spongy cores, while particles obtained with additions of EGDE- and PEG-400 had rough surfaces and prolonged or angular shapes. Drug-loaded particles demonstrated retention of bioactivity.
The present disclosure has described one or more preferred embodiments, and it should be appreciated that many equivalents, alternatives, variations, and modifications, aside from those expressly stated, are possible and within the scope of the invention.
This application is based on, claims priority to, and incorporates herein by reference in its entirety, U.S. Provisional Patent Application Ser. No. 62/804,406, filed on Feb. 12, 2019 and entitled “System and Method for Fabrication of Large, Porous Drug-Eluting Silk Materials Using Cryogranulation”.
This invention was made with government support under grant number FA9550-17-1-0333 awarded by the United States Air Force and grant numbers NS094218 and AR070975 awarded by the National Institutes of Health. The government has certain rights in the invention.
| Filing Document | Filing Date | Country | Kind |
|---|---|---|---|
| PCT/US2020/018006 | 2/12/2020 | WO | 00 |
| Number | Date | Country | |
|---|---|---|---|
| 62804406 | Feb 2019 | US |
