Title: [0001] EVALUATION OF PCL/PEG COMPOSITES FOR RESTORATIVE APPLICATIONS WITHIN THE TRACHEA Cross Reference to Related Application [0002] This application claims the benefit under 35 U.S.C. § 119(e) to U.S. Provisional Application No.61/936,973 filed February 7, 2014, which application is hereby incorporated by reference in its entirety. Statement Regarding Sequence Listing [0003] The Sequence Listing associated with this application is provided in text format in lieu of a paper copy, and is hereby incorporated by reference into the specification. The name of the text file containing the Sequence Listing is 6338-018PCT_ST25.txt. The text file is 1,751 bytes, was created on December 8, 2021, and is being submitted electronically via EFS- Web. Background of the Invention [0004] Prolonged endotracheal intubation, frequently with large diameter endotracheal (ET) tubes, puts adults at risk of long-term breathing, voice, and swallowing related complications and acute laryngeal injury (ALgI), including tracheal or posterior glottic stenosis ^1-5 . Recent evaluation identified incidence of ALgI in more than half of patients intubated for durations greater than 12 hours, with findings persisting for more than two months ⁶ . Since respiratory failure is the leading cause of ICU admission in the United States and over 55,000 adults are treated daily in ICUs, many requiring intubation, the recognition of ALgI as a functional impairment to recovery is expanding ⁷ . Improvement in interventional techniques and in the instrumentation employed have reduced but not eliminated the 5% risk of stenosis after prolonged intubation ^{1, 8-10} . The recent increased number of ventilated patients resulting from the COVID-19 pandemic is projected to further substantially increase the number of patients with ALgI. Evidence suggests that early intervention may be ideal in treating these patients ¹¹ . Studies demonstrate marked improvement in ALgI/stenosis with the adjuvant use of intralesional glucocorticoids ^12-15 . In addition, the application of biological modulators as a therapeutic agent, specifically siRNA targeting smad3 has been studied to downregulate TGFβ1 which has been implicated as the main pro-fibrotic growth factor involved in the development of ALgI ¹⁶ . [0005] Current treatment options for prevention of posterior glottic, subglottic, or tracheal stenosis are limited to minimizing the duration of intubation and by utilizing the smallest endotracheal tube possible. Often, a patient’s medical condition dictates intubation duration and choice of endotracheal tube size. Though glucocorticoids, such as dexamethasone, are known to modulate airway inflammation and are commonly employed in the treatment of airway stenosis, their intralesional or topical applications are limited by access in the acute period where life- threatening injuries are the focus of care. Prolonged oral steroid treatment on the other hand, has adverse systemic side-effects and is limited in terms of efficacious local delivery of target doses at the region of interest. ^{12-15, 17, 18} Furthermore, many of the other topically used agents are not readily available or practical for intravenous use. No technologies currently exist to directly deliver therapeutics to the laryngotracheal complex and throughout the trachea during prolonged intubation. This limitation in current technology around endotracheal tubes limits treatment capacity for ventilator dependent patients and leaves the endotracheal tube as a risk-factor or nidus for biofilm formation and propagation of infection. We aim to transform the endotracheal tube from a functional, mechanical device to a dual-purpose device capable of delivering therapeutics to the local microenvironment, preventing long-term sequelae from prolonged intubation and providing additional therapeutic delivery in the short term to address underlying pathology. Summary of the Invention [0006] A polycaprolactone (PCL)/polyethylene glycol (PEG) composite membranous patch is proposed to (1) attach to the mucous layer within the trachea in a sutureless manner, (2) enable degradation based controlled drug release, and to (3) be capable of production in large batches permitting intra-procedural sizing by a clinician to fit the injury site. Material suitability was determined in terms of being muco-adhesive, and then the mechanical survival properties of that material were benchmarked. [0007] PCL fibers are either left uncoated, are coated by submerging in PEG, or flocked with PEG with 3 different densities (1x, 2x, 3x). Different sample types are tested for stiffness, absorption, degradation, and muco-adhesion. It is found that 1x flocked samples are the most muco-adhesive, and are therefore the most ideal composite to use in creating a patch for tracheal wall injuries Brief Description of the Figures [0008] Fig.1A is a cross-sectional scanning electron micrograph (SEM) of an endotracheal tube (ETT) coated with a 5K molecular weight (MW) PCL-4-arm polyethylene glycol acrylate (4APEGA) composite. [0009] Fig.1B is a cross-sectional scanning electron micrograph (SEM) of an endotracheal tube (ETT) coated with a 10K molecular weight (MW) PCL- 4APEGAcomposite. [0010] Fig.1C is a cross-sectional scanning electron micrograph (SEM) of an endotracheal tube (ETT) coated with a 20K molecular weight (MW) PCL-4APEGA composite. [0011] Fig.2 is a Fourier-Transform infrared (FTIR) spectra of dexamethasone loaded PCL electrospun fibers at three different concentrations of dexamethasone. [0012] Fig.3A is a graph of PCL-4APEGA composite hydrogel swelling behavior for 5K MW 4APEGA composite. [0013] Fig.3B is a graph of PCL-4APEGA composite hydrogel swelling behavior for 10K MW 4APEGA composite. [0014] Fig.3C is a graph of PCL-4APEGA composite hydrogel swelling behavior for 20K MW 4APEGA composite. [0015] Fig.4A is a graph illustrating degradation of 4APEGA (5K MW) hydrogels and the 4APEGA (5K MW)-PCL) composites over a 14 day period with average fiber diameters of 1, 4 and 8 µm. [0016] Fig.4B is a graph illustrating degradation of 4APEGA (10k MW) hydrogels and the 4APEGA (10K MW)-PCL) composites over a 14 day period with average fiber diameters of 1, 4 and 8 µm. [0017] Fig.4C is a graph illustrating degradation of 4APEGA(20k MW) hydrogels and the 4APEGA (20K MW)-PCL) composites over a 14 day period with average fiber diameters of 1, 4 and 8 µm. [0018] Fig.5A is a graph illustrating local mechanical characterization by indentation showing the elastic modulus of PCL electrospun fibers with different average diameters. [0019] Fig.5B is a graph illustrating local mechanical characterization by indentation showing the elastic modulus of 4-APEGA-PCL electrospun fibers of different molecular weights with an average fiber diameter of 4 µm. [0020] Fig.5C is a graph illustrating local mechanical characterization by indentation showing the elastic modulus of 4-APEGA hydrogels with different molecular weights. [0021] Fig.6A is a graph of mucin production after simulated mechanical tracheal mucosal abrasion showing expression of Muc5b for different substrates in contact with the biological sample. [0022] Fig.6B is a graph of mucin production after simulated mechanical tracheal mucosal abrasion showing expression of Muc5ac for different substrates in contact with the biological sample. [0023] Fig.7A is a histological micrograph of the inner lining of a trachea after simulated mucosal damage due to contact with an ETT only. [0024] Fig.7B is a histological micrograph of the inner lining of a trachea after simulated mucosal damage due to contact with an ETT with a 5k MW APEGA hydrogel coating. [0025] Fig.7C is a histological micrograph of the inner lining of a trachea after simulated mucosal damage due to contact with an ETT with a 10k MW APEGA hydrogel coating. [0026] Fig.7D is a histological micrograph of the inner lining of a trachea after simulated mucosal damage due to contact with an ETT with a 20k MW APEGA hydrogel coating. [0027] Fig.8 is a graph illustrating epithelial adhesion of human tracheal fibroblasts (HTFs) to 4APEGA composite hydrogels as compared to a bare ETT, for different molecular weights of 4APEGA hydrogels. [0028] Fig.9A is a graph of the dexamethasone release profile from PCL electrospun fibers having an average diameter of 1 µm at different concentrations of dexamethasone. [0029] Fig.9B is a graph of the dexamethasone release profile from PCL electrospun fibers having an average diameter of 4 µm at different concentrations of dexamethasone. [0030] Fig.9C is a graph of the dexamethasone release profile from PCL electrospun fibers having an average diameter of 8 µm at different concentrations of dexamethasone. [0031] Fig.10 is a graph illustrating HTFs cellular viability after exposure to PCL-PEG and dexamethasone. [0032] Fig.11A is a graph illustrating the effect of dexamethasone on expression of IL-6 over a 7-day period. [0033] Fig.11B is a graph illustrating the effect of dexamethasone on expression of IL- 11 over a 7-day period. [0034] Fig.12 is a graph illustrating the release profile of loaded siRNA polyplex from different molecular weight 4APEGA hydrogels over a 24-hour period. [0035] Fig.13 is a graph illustrating the viability of HTFs exposed to siRNA and polyplex with different nitrogen to phosphate (n/p) ratio values after 24 hours. [0036] Fig.14A is a graph of siRNA polyplex transfection and gene silencing efficacy in HTFs exposed to polyplexes, nonsense siRNA, and siRNA targeting SMAD3 for TGFBR1. [0037] Fig.14B is a graph of siRNA polyplex transfection and gene silencing efficacy in HTFs exposed to polyplexes, nonsense siRNA, and siRNA targeting SMAD3 for Serpine. [0038] Fig.14C is a graph of siRNA polyplex transfection and gene silencing efficacy in HTFs exposed to polyplexes, nonsense siRNA, and siRNA targeting SMAD3 for Col1A1. [0039] Fig.15 is a scanning electron micrograph illustrating fiber morphology of the electrospun hydrogel composite in accordance with the present disclosure. [0040] Fig.16 is a graph of mucoadhesion of the inventive electrospun PCL fibers either soaked in PEG, or flocked with PEG to create 1x, 2x, or 3X flock densities. [0041] Fig.17 is a graph of stiffness of the inventive electrospun PCL fibers either soaked in PEG, or flocked with PEG to create 1x, 2x, or 3X flock densities. [0042] Fig.18 is a graph of adsorption/swelling of the inventive electrospun PCL fibers either soaked in PEG, or flocked with PEG to create 1x, 2x, or 3X flock densities. [0043] Fig.19 is a graph of degradation rate of the inventive electrospun PCL fibers either soaked in PEG, or flocked with PEG to create 1x, 2x, or 3X flock densities. Detailed Description of the Disclosure [0044] The compositions, systems and methods of the present disclosure will be described with reference to certain exemplary embodiments thereof. These exemplary embodiments are intended to be illustrative and non-limiting examples of the present invention. The example embodiments are provided so that this disclosure will be thorough, and will fully convey the scope to those who are skilled in the art. Numerous specific details are set forth such as examples of specific components, devices, and methods, to provide a thorough understanding of embodiments of the present disclosure. It will be apparent to those skilled in the art that specific details need not be employed, that example embodiments may be embodied in many different forms and that neither should be construed to limit the scope of the disclosure. Those of ordinary skill in the art will understand and appreciate that variations in materials, structure, material properties, and tolerances may be made without departing from the scope of the invention, which is defined only by the claims appended hereto and their range of equivalents. In some example embodiments, well-known processes, well-known device structures, and well-known technologies are not described in detail. [0045] Benefits, other advantages, and solutions to problems have been described herein with regard to specific embodiments. Furthermore, the connecting lines shown in the various figures contained herein are intended to represent exemplary functional relationships and/or physical couplings between the various elements. It should be noted that many alternative or additional functional relationships or physical connections may be present in a practical system. However, the benefits, advantages, solutions to problems, and any elements that may cause any benefit, advantage, or solution to occur or become more pronounced are not to be construed as critical, required, or essential features or elements of the disclosure. [0046] The scope of the disclosure is accordingly to be limited by nothing other than the appended claims, in which reference to an element in the singular is not intended to mean “one and only one” unless explicitly so stated, but rather “one or more.” It is to be understood that unless specifically stated otherwise, references to “a,” “an,” and/or “the” may include one or more than one and that reference to an item in the singular may also include the item in the plural. All ranges and ratio limits disclosed herein may be combined. [0047] Moreover, where a phrase similar to “at least one of A, B, and C” is used in the claims, it is intended that the phrase be interpreted to mean that A alone may be present in an embodiment, B alone may be present in an embodiment, C alone may be present in an embodiment, or that any combination of the elements A, B and C may be present in a single embodiment; for example, A and B, A and C, B and C, or A and B and C. Different cross-hatching when used throughout the figures to denote different parts but not necessarily to denote the same or different materials. [0048] For ease of understanding, the present invention is described with reference to the accompanying Figures. [0049] The terminology used herein is for the purpose of describing particular example embodiments only and is not intended to be limiting. As used herein, the singular forms “a,” “an,” and “the” may be intended to include the plural forms as well, unless the context clearly indicates otherwise. The terms “comprises,” “comprising,” “including,” and “having,” are inclusive and therefore specify the presence of stated features, integers, steps, operations, elements, and/or components, but do not preclude the presence or addition of one or more other features, integers, steps, operations, elements, components, and/or groups thereof. The method steps, processes, and operations described herein are not to be construed as necessarily requiring their performance in the particular order discussed or illustrated, unless specifically identified as an order of performance. It is also to be understood that additional or alternative steps may be employed. [0050] When an element or layer is referred to as being “on,” “engaged to,” “connected to,” or “coupled to” another element or layer, it may be directly on, engaged, connected or coupled to the other element or layer, or intervening elements or layers may be present. In contrast, when an element is referred to as being “directly on,” “directly engaged to,” “directly connected to,” or “directly coupled to” another element or layer, there may be no intervening elements or layers present. Other words used to describe the relationship between elements should be interpreted in a like fashion (e.g., “between” versus “directly between,” “adjacent” versus “directly adjacent,” etc.). As used herein, the term “and/or” includes any and all combinations of one or more of the associated listed items. [0051] “Substantially” is intended to mean a quantity, property, or value that is present to a great or significant extent and less than totally. [0052] “About” is intended to mean a quantity, property, or value that is present at ±10%. Throughout this disclosure, the numerical values represent approximate measures or limits to ranges to encompass minor deviations from the given values and embodiments having about the value mentioned as well as those having exactly the value mentioned. Other than in the working examples provided at the end of the detailed description, all numerical values of parameters (e.g., of quantities or conditions) in this specification, including the appended claims, are to be understood as being modified in all instances by the term “about” whether or not “about” actually appears before the numerical value. “About” indicates that the stated numerical value allows some slight imprecision (with some approach to exactness in the value; approximately or reasonably close to the value; nearly). If the imprecision provided by “about” is not otherwise understood in the art with this ordinary meaning, then “about” as used herein indicates at least variations that may arise from ordinary methods of measuring and using such parameters. In addition, disclosure of ranges includes disclosure of all values and further divided ranges within the entire range, including endpoints given for the ranges. [0053] The steps recited in any of the method or process descriptions may be executed in any order and are not necessarily limited to the order presented. Furthermore, any reference to singular includes plural embodiments, and any reference to more than one component or step may include a singular embodiment or step. Elements and steps in the figures are illustrated for simplicity and clarity and have not necessarily been rendered according to any particular sequence. For example, steps that may be performed concurrently or in different order are illustrated in the figures to help to improve understanding of embodiments of the present disclosure. [0054] Any reference to attached, fixed, connected or the like may include permanent, removable, temporary, partial, full and/or any other possible attachment option. Additionally, any reference to without contact (or similar phrases) may also include reduced contact or minimal contact. Surface shading lines may be used throughout the figures to denote different parts or areas but not necessarily to denote the same or different materials. In some cases, reference coordinates may be specific to each figure. [0055] Systems, methods, and apparatus are provided herein. In the detailed description herein, references to "one embodiment," "an embodiment," "various embodiments," etc., indicate that the embodiment described may include a particular feature, structure, or characteristic, but every embodiment may not necessarily include the particular feature, structure, or characteristic. Moreover, such phrases are not necessarily referring to the same embodiment. Further, when a particular feature, structure, or characteristic is described in connection with an embodiment, it is submitted that it is within the knowledge of one skilled in the art to affect such feature, structure, or characteristic in connection with other embodiments whether or not explicitly described. After reading the description, it will be apparent to one skilled in the relevant art(s) how to implement the disclosure in alternative embodiments. [0056] Furthermore, no element, component, or method step in the present disclosure is intended to be dedicated to the public regardless of whether the element, component, or method step is explicitly recited in the claims. No claim element is intended to invoke 35 U.S.C.112(f) unless the element is expressly recited using the phrase “means for.” As used herein, the terms “comprises,” “comprising,” or any other variation thereof, are intended to cover a non-exclusive inclusion, such that a process, method, article, or apparatus that comprises a list of elements does not include only those elements but may include other elements not expressly listed or inherent to such process, method, article, or apparatus. MATERIALS AND METHODS Drug loaded PCL electrospinning. [0057] To fabricate dexamethasone loaded polycaprolactone (PCL) electrospun fibers, PCL pellets (molecular weight: 80,000) were first dissolved in chloroform and ethanol (15:85 v/v) and dexamethasone. Dexamethasone:PCL w/w ratios of 2.5, 5, and 10:100) was then added to the PCL solution. ¹⁹ Final solutions were then loaded into a syringe and a syringe pump (Pump 11 Elite, Harvard Apparatus, Holliston, MA) was used to electrospin fibers with various diameters with each electrospun fiber having a substantially uniform diameter along its length. All chemicals, unless otherwise stated, were purchased from Sigma-Aldrich (St. Louis, MO). [0058] Alternative anti-inflammatory agents may employed instead of or in addition to dexamethasone. Non-limiting examples of alternative anti-inflammatory agents include valcyclovir or roxudastat, which may be added to the PCL in similar w/w ratios as with dexamethasone. PCL-4APEGA composites and morphology assessment [0059] 4APEGA with varying molecular weight (5k, 10k, and 20k) was mixed with the photoinitiator (Irgacure 9599) and filtered with 22µm filters. Then, the 4APEGA hydrogels were cast on top of the electrospun fiber coated ETTs and polymerized for 5 minutes under UV light (UVP CL-1000, Ultraviolet Crosslinkers at a wavelength of 365 nm). Scanning Electron Microscopy (SEM) was used to examine the morphology of the PCL-4APEGA coated ETTs. All specimens were lyophilized and sputter coated with silver-palladium and imaged using an S5500 microscope (Hitachi High-Tech, Schaumburg, IL) under 20 kV applied voltage at 50x, 200x, and 750x magnifications. Samples were imaged in top view and side view of cross section perspectives in order to evaluate surface morphology and layer interfaces respectively. [0060] PCL (Mn= 80,000, Sigma-Aldrich) was spun in random orientation by electrospinning (Fibers diameter: 4µm) and then different coatings were applied. Samples were either soaked in PEG, or flocked with PEG to create different flock densities (1x, 2x, 3x). Samples morphology was characterized by Scanning Electron Microscopy (SEM) and then stiffness, degradation rate, swelling behavior, and mucoadhesion properties were studied for all groups. Samples were placed in a PBS solution and remaining mass was measured over 14 days in order to evaluate the degradation rate. Swelling behavior of the patches were studied as the relative weight change of the wet and dry samples at different time points. Mucoadhesion testing was conducted on fresh porcine trachea tissue followed by testing in lap shear mode (UStretch, CellScale, Waterloo, ON). Quantitative data were compared using one-way Analysis of Variance (ANOVA) followed by Tukey’s test for post hoc determination of significant differences at p<0.05. Stiffness was evaluated by stretching samples (UStretch, CellScale, Waterloo, ON) and measuring the force and displacement. Material Degradation. [0061] To study the degradation rate of PCL-4APEGA composites over time, PCL fibers (n=6 samples per group) were punched to circular specimens (5/16 inch diameter) and the mass of each was obtained. The punched PCL fibers were then soaked in 4APEGA solution containing a photoinitiator (Irgacure 9599) and polymerized for 5 minutes under UV light (UVP CL-1000, Ultraviolet Crosslinkers at a wavelength of 365 nm). Samples were then placed in PBS buffer at 37ºC and observed for 14 days. Mass loss of the samples were measured weekly (using Equation 1, where W _in and W _f are the initial and final sample weights of the sample, respectively). Swelling behavior. [0062] Swelling rate of composite samples were calculated over time to compare the impact of molecular weight of 4APEGA on swelling behavior and to study the impact of swelling ratio on the dexamethasone and siRNA-PEI polyplex release behavior. Dried samples (n=6 samples per group) were weighed prior to the experiment and were then immersed in PBS buffer at 37°C. Samples were then removed from PBS buffer at different time points and their weight was recorded after removing excess PBS. The experiment was continued until the samples reached swelling equilibrium. The swelling ratio was calculated using Equation 2, below,, in which M _i and M _f are the mass of samples in its dried and swollen states, respectively. Local mechanical characterization (microindentation). [0063] The local stiffness of the composites were measured using a microindenter (Piuma Chiaro, Optics11, Amsterdam, The Netherlands). A probe with a tip radius of 8.5 µm and tip spring constant of 0.026^N/ was used to measure substrate elastic modulus. Samples (n=6 specimen per group) were indented using the mapping feature in PBS at room temperature at a scan size of 9 locations (3^×^3)^ with a 10^μm step along both the X and Y axes. The loading and unloading force displacement curves were acquired by the instrument during each indentation process and the Oliver Pharr model was used to calculate tip-substratum area of contact and determine the elastic modulus from the initial linear region of the unloading curve by then assuming Hertzian contact between the indenter and substrate. Since the indentation model resulted in potentially multimodal distribution of elastic modulus across the sample substratum for composite materials, violin plots were used to tabulate the distribution of measurements and statistical testing was performed to identify differences in median values assuming unequal variances and correcting for varying distribution profiles within populations. In-vitro dexamethasone release kinetics. [0064] Dexamethasone release from the PCL fibers was assessed and quantified over a period of 24 days. Samples (n=6 samples per group) were maintained in PBS buffer at 37°C. The PBS buffer was extracted every 4 days and replaced with fresh PBS. The released dexamethasone was collected every day and the absorbance of the collected dexamethasone in the PBS buffer was measured using a plate reader (Synergy2, BioTek, Winooski, VT) at 290 nm ²⁰ . Dexamethasone bioactivity. [0065] The retention of biological activity of dexamethasone after the release from the composites were determined through the measurement of Interleukin 6 (IL-6) and Interleukin 11 expression via enzyme-linked immunosorbent assays (ELISAs) according to the standard sandwich assay protocols provided by the supplier. For this purpose, human Tracheal Fibroblasts (hTF) cells (Cell Biologics Inc, Chicago, IL) were pre-cultured in Dulbecco's Modified Eagle's Medium (DMEM), containing 10% of Fetal Bovine Serum (FBS), and 1% antibiotics. Cells were maintained at 37°C and 5% CO ₂ , and passaged every 3 to 4 days. Cells were then trypsinized after reaching 80% confluency and were subsequently seeded at a density of 1000 cells/well in 96-well plates. The proliferation of the hTF cells were determined after 24 hours by Live/Dead assay in the untreated control group (positive control), and the other groups exposed to dexamethasone eluent treatment (experimental groups for bioactivity), as well as after exposure to an aliquot of eluent from samples not loaded with dexamethasone (carrier control). The images were quantified using a protocol adapted from FIJI open source image analysis software for ImageJ to calculate the number of dead and live cells ²¹ . In addition, media collected from each well was also used to evaluate the expression of IL-6 and IL-11 in the groups tested using ELISA kits according to the manufacturer instructions. All biological reagents, unless otherwise stated, were purchased from ThermoFisher (St. Louis, MO). Cell adhesion to ETT surface coating [0066] To determine the effect of 4APEGA on cell adhesion, the 3 different molecular weights of 4APEGA (5k, 10k and 20k) were mixed with photoinitiator and polymerized in 96 well plates for 5 minutes under sterile conditions as previously described. Samples were then thoroughly rinsed with PBS and seeded with HTF cells at a density of 5,000 per sample. After incubation, the hydrogels were washed with PBS to remove non-adherent cells. To evaluate cell viability, 10% alamarBlue™ Cell Viability Reagent was diluted in fresh growth media and the plate was then incubated for four hours in the media containing the alamarBlue. Then the alamarBlue reduction was measured using a Synergy2 plate reader (BioTek, Winooski, VT). Samples were then fixed with 4% paraformaldehyde for one hour and stained using the Live/Dead assay with calcein AM and ethidium homodimer as previously described. Simulation of potential mucosal damage during intubation. [0067] Fresh porcine trachea were harvested (from animals euthanized in an unrelated preclinical study) and the inner lining of the trachea (distant from the bronchial branch point) was separated from the tracheal cartilage rings and sectioned into 16 pieces and split into four main experimental groups to study the impact of 4APEGA friction on epithelial abrasion and erosion of the inner lining of trachea in an ex vivo experiment. To mimic friction between the coated ETTs and the epithelial mucosa, a mechanoculture MCT6 loading system (CellScale; Ontario, Canada) was programmed to apply cyclic strain of 10% at a frequency of 0.2 Hz in a sinusoidal waveform to mimic physiological breathing in the human lung. Tissue segments were then loaded into a custom-built chamber containing 50% v:v HTF growth media mixed with 50% v:v Airway Epithelial Cell Basal Medium containing the supplementary Bronchial Epithelial Cell Growth Kit. The novel hydrogel coatings and bare ETTs (as the negative control group) were connected to MCT6 loading system. Hydrogels were kept in contact with tissue segments and the loading system applied cyclic strain for 24 hour. [0068] The following day, tissue segments were punched with a biopsy punch (diameter: 0.15cm) and homogenized in 500 µl of PBS. To lysate the tissue, 500 µl of radioimmunoprecipitation assay buffer (RIPA 1X) containing protease inhibitors was added to the homogenized tissue and agitated at room temperature for 30 minutes. The tissue lysate was then centrifuged at 1000 rpm for 5 minutes to remove tissue debris. MUC5b and MUC5AC proteins were quantified using ELISA and the experiment was carried out according to the manufacturer instructions. The remaining tissue segments were fixed in 4% paraformaldehyde solution for histological evaluation. In order to observe possible epithelial abrasion, tissue segments were stained with Alcian Blue and Fast Red Nucleus to visualize the mucus layer. Briefly, samples were perfused with 15% sucrose solution at 4°C for 6 hours followed by an overnight perfusion evaluation in 30% sucrose solution at 4°C to reduce possible damage during the freezing step. Subsequently, samples were mounted in disposable embedding molds filled with OCT compound () and the molds were stored at -80°C prior to sectioning. Frozen tissue segments were cut to a tissue thickness of 8 µm using a cryostat (CM1850, Leica, Wetzlar, Germany) and thaw-mounted on glass slides. Slides were maintained at room temperature overnight to dry. To improve the adhesion of the tissue slices to the glass slides, slides were kept in chilled acetone at -20 ^o C for 10 minutes. Subsequently, slides were hydrated with deionized water prior to staining. Samples were first stained with Alcian Blue 8G solution (1% (w/v) Alcian Blue in 3% (v/v) acetic acid/ deionized H ₂ O (pH 2.5)) for 15 minutes and washed three times to remove excess stain from the slides. Then slides were counterstained with Fast Red Nucleus for 5 minutes and washed with deionized water three times for one minute again before the final mounting with ProLong Diamond Antifade Mountant. Finally, stained tissue cuts were imaged with Lionheart microscope (BioTek, Winooski, VT) at 4X and 10X. See, Figs 6A and 6B. siRNA- PEI polyplex composition. [0069] To load the PCL-4APEGA composites with smad3 silencing siRNA, siRNA was first mixed with polyethyleneamine (linear, molecular weight: 20k) at an n/p ratio of 16 to mediate functional siRNA delivery while avoiding sequence non-specific effects ^22-26 . Equation 3, below, was used to calculate the required amount of siRNA and PEI to obtain the specific n/p value ²⁷ . [0070] siRNA aliquot was prepared in a centrifuge tube by adding HEPES buffer containing 5% glucose. In a separate tube, PEI was dissolved in HEPES buffer of pH 7.2 and then the siRNA aliquot was added to the PEI solution. The final solution was vortexed for 5 seconds and incubated at room temperature for 15 minutes to complete the complex formation. Effective diameters and zeta potential of the polyplex was evaluated by diluting the polyplex with HEPES buffer to a volume of 1 mL. The solution was transferred to a cuvette and analyzed at room temperature using a NanoSizer (Malvern Nano-ZS, UK). The values were calculated based on three independent experiments each consisting of 10 measurements. [0071] Then various polymer/nucleic acid ratios were synthesized (w/w: weight/weight) in separate tubes in HBG (HEPES buffered glucose solution; 20 mM HEPES, 5% glucose). The resulting polyplex aliquot was mixed with 4APEGA polymers (MW: 5k, 10k,and 20k) and photoinitiator solution followed by polymerization under UV light for 5 minutes as previously described above. SiRNA-PEI polyplex release profile. [0072] 4APEGA hydrogels with different molecular weight (5k, 10k, and 20k) combined with polyplex were incubated in PBS at 37 °C. Release of siRNA was monitored at different time intervals over a 24 hour period. PBS buffer was removed at each time point and replaced with fresh PBS. Each sample containing the siRNA polyplex was centrifuged for 15 min at maximum speed and the siRNA content was measured using Quant-iT™ RiboGreen® assay according the supplier’s instructions. siRNA polyplex transfection and gene silencing efficacy. [0073] The transfection efficacy and gene silencing potential of released polyplex on HTF cells was compared with HTF cells exposed to a negative control group (non-sense siRNA), free siRNA targeting smad3, and the free polyplex before loading into the hydrogels. For this purpose, the HTF cells were initially cultured in DMEM, containing 10% of Fetal Bovine Serum (FBS), and 1% antibiotics (penicillin- streptomycin – amphotericin cocktail). Cells were incubated at 37°C and 5% CO ₂ and passaged every 3 to 4 days. T-150 mm flasks were seeded with 1×10 ⁶ cells and maintained at 37°C and 5% CO2 to reach 80% confluency. Then each flask was treated with 100 pmol of siRNA followed by TGFβ1 exposure ²⁸ . Subsequently, cells were lysed using TRIzol™ Reagent and total RNA was extracted using RNeasy Mini Kit (Qiagen, Valencia, CA). RNA concentration and quality was evaluated using a Take3 Micro-Volume Plate (Biotek, Winooski, VT) and spectrophotometer. Next, RNA was reverse transcribed with iScript™ cDNA Synthesis Kit (Bio-Rad, Hercules, CA). Then a fixed amount of complementary DNA (cDNA) and was used with iTaq Universal SYBR Green Supermix (Bio-Rad, Hercules, CA) for real-time reverse transcription polymerase chain reaction (RT-PCR) carried out using a CFX96 Touch Real-Time PCR Detection System (Bio-Rad, Hercules, CA). The data was analyzed using the 2 ^−ΔΔCt method in which the nonsense group was designated as the baseline group and GAPDH expression was used as the loading control. Three main predesigned primers (Sigma-Aldrich) were used to study the transfection efficacy of the polyplex with three different n/p values (1, 10, and 20). Table 1 shows the specific forward and reverse primers sequences for the tested genes. [0074] Table 1. PCR Primer Sequences [0075] As an alternative to or in addition to the siRNA-hydrogel polyplex, the hydrogel may have other bioactive agents or constituents complexed, loaded, or otherwise associated with it. As non-limiting examples, silver nanoparticles, polyethyleneamine nanoparticles, antibiotics, such as levofloxacin. Statistical Analysis [0076] All numerical data were reported as the average ± the standard error of the mean. Material characterization data was acquired for at least 6 technical replicate samples per group, at least 10 replicates for biaxial mechanical testing, and one biological sample with four technical replicates for the cadaveric tissue-material testing. Significant differences in the numerical data for the material characterization analyses were identified using one-way Analysis of Variance (ANOVA), followed by Tukey’s test for post-hoc determination of significance. Statistical analysis was conducted using Prism (v9.0.0, GraphPad Software LLC, San Diego, CA). A value of p<0.05 was considered statistically significant. RESULTS Composite coating characterization. [0077] Scanning electron microscopic micrographs of coated endotracheal tubes with PCL- 4APEGA composites are shown in Figs.1A-C. The outermost layer denoted as a red region of interest (ROI) displays a uniform and substantially smooth coverage of the ETT with 4APEG in all groups. The middle layer (yellow ROI) shows a complete embedding of the electrospun PCL fibers within the 4APEG hydrogels. The innermost layer (green ROI) verifies the attachment of the PCL-4APEG composites to the ETTs. The middle image in all three groups with all 4APEGA hydrogels demonstrated a complete embedding of PCL electrospun fibers within 4APEGA hydrogels. Finally, the contact area between the composites and ETTs were imaged to verify the attachment of the composites to the ETTs. Chemistry of PCL and dexamethasone loaded PCL were also evaluated using FTIR spectroscopy to confirm dexamethasone loading as shown in Fig.2. The presence of PCL was validated by CH ₂ peaks observation at 2936 and 2846 cm ^-1 and a sharp peak of C=O stretching vibration at 1722 cm ^-1 in PCL samples. These peaks were also more intense in groups with dexamethasone due to overlap of spectra between C=O bands, C-O and C-C bands. Swelling behavior. [0078] Figs.3A-3B illustrate the swelling behavior of the composites determines the drug delivery behavior as well as the final weight of the tube once it is placed into the trachea. Composites containing 4APEGA-5k demonstrated the most rapid swelling equilibrium, with the least water absorption and reaching equilibrium after the first 30 minutes (Figs.3A-C). Composites containing 4APEGA-10k showed higher water uptake rate since higher molecular weight leads to an increase in the mesh size and increased water update capacities.4APEGA-10k coatings reached swelling equilibrium after 3 hours. Finally, the group containing 4APEGA-20k showed the highest swelling ratio over time due to the increased molecular weight of the hydrogel. Composites containing 4APEGA-5k reached a swelling rate equilibrium around 30 min. Within this group there were significant (*p<0.05) differences between the composites containing 1µm and 8µm PCL. The composites containing 4APEGA-10k reached equilibrium after 3 hours. Within this group, significant (*P<0.05) differences were observed between the composites containing 1µm and 4µm PCL. The PEG-only group displayed a significantly (*p<0.05) higher swelling ratio than the 4µm and 8µm PEG-containing composites at 30 min. The PEG samples also displayed a higher swelling ratio than all the composites at 60 and 90 min (**p<0.01 and ***p<0.001, respectively). Fig.3C illustrates that the group containing 4APEGA- 20k showed the highest swelling ratio over time due to the increased molecular weight of the hydrogel. Within this MW group, the PEG only displayed the highest swelling ratio at 60 and 90 min (*p<0.05 and **p<0.01, respectively). Inflammatory Markers affected by Dexamethasone Treatment. [0079] Interleukin 6 (IL6) and Interleukin 11 (IL11) are prominent pro inflammatory markers produced during fibroplasia. Fig.11 illustrates tracking of the produced markers over 7 days in groups with and without dexamethasone treatment to evaluate the impact of dexamethasone on controlling the inflammatory markers in HTF cultures in vitro. IL6 secretion increased by day 5 (0.015 ± 0.002 pg/ml) in the control group and decreased to 0.011±0.0005 pg/ml on day 7 and was significantly higher that the dexamethasone treated group (0.0057±0.001 pg/ml) (Fig.11A). IL6 secretion in group without dexamethasone treatment was significantly higher on day 5 compared to the dexamethasone treated group. IL-11 showed a different tend compared to IL6. The highest IL11 secretion was observed on the first day in the control group without treatments (0.0143±0.0006 pg/mol) which was significantly different from the group with the dexamethasone treatment on day 1. IL11 production in the media decreased drastically over time in both group. The lowest IL11 secretion was observed at day 5 in the groups with dexamethasone treatments (0.0029±0.00005 pg/ml). IL11 secretion was found to be time dependent and a significant decrease over time was observed in both groups with an effective impact of dexamethasone being the overall reduction of IL11 secretion (Fig.11B). SiRNA-PEI polyplex release profile. [0080] siRNA release profile was determined over the first 24 hours at 37°C. Fig.12 demonstrates siRNA polyplex release observed from hydrogels with various molecular weights (5k, 10k, and 20k) every 12 hours. Polyplex release from 4APEGA-5k was relatively higher in the first hour compared to the 4APEGA-10k and 4APEGA-20k. However, this trend changed over time and a higher amount of polyplex were released in 4APEGA-10k (41 ± 5% of total loaded polyplex after 24 hours) and 4APEGA-20k (51 ± 3% of total loaded polyplex after 24 hours) which is indicating the impact of molecular weight and 4APEGA chemistry. A higher molecular weight results in a faster drug release due to the larger meshes in the polymeric matrix leading to a faster release of polyplex through the matrix. On the other hand, available carboxylate bonds in 4APEGA hydrogels which serve as crosslinking points will cause an electrostatic attraction toward amine groups in cationic PEI of the polyplex. It is expected to have higher ratio of carboxylate group to PEG chain in 4APEGA-5k compared to 4APEGA with higher molecular weight resulting in higher electrostatic attraction in the matrix between 4APEGA and the polyplex which would lead to lower drug release over time. Zeta potential and polyplex particle size analysis. [0081] Zeta potential (ζP) and the polyplex particle sizes with different n/p values (1-20) are summarized in Table 2. The low number of amine groups compared to phosphate groups in the polyplex resulted in a negative zeta potential in group 1NP which would lead into an incomplete shielding of siRNA. This group also revealed the highest polyplex size (214.7 ± 2.86 nm) compared to other groups with higher n/p values. As expected, ζP increased notably as n/p value increased; however, the polyplex size decreased in group 10P and then increased to 176.5 ± 0.1.86 nm in group 20P. While particle sizes were in an acceptable range (<0.3) ³² in all groups, the 10P group was chosen to continue in further experiments due to a balanced n/p value to provide a shield for siRNa without excess PEI present in the polyplex to produce extra positive charges. [0082] Table 2. Zeta potential (ζP) and the polyplex particle sizes with different n/p values (1- 20) Live/Dead assay for siRNA polyplex. [0083] Cell toxicity of siRNA and polyplex with different n/p values were evaluated (Fig.13) using the Live/Dead assay in which the results were compared with control groups after 24 hours after the treatments. Cell viability percentage showed similar results in control group and groups exposed to free siRNA, polyplex (n/p:1) with no significant differences. However, the increase of n/p value in polyplex resulted in a significant decrease of cell viability in groups treated with polyplex (n/p: 20) indicating a higher rate of apoptotic efficiency compared to polyplex (n/p: 1) and polyplex (n/p: 10). siRNA polyplex transfection and gene silencing efficacy. [0084] The transfection efficacy and gene silencing properties of polyplex with different n/p values were evaluated by testing tgfbr1, serpine1, and col1a1 genes expressed in HTF cells exposed to polyplexes, nonsense siRNA, and siRNA targeting smad3. tgfbr1 indicated no significant difference across treatments which is anticipated since the TGFβ receptor is upstream of smad3, while serpine1 (a pro-fibrotic transcription factor in the TGFβ pathway) expression was at the lowest in groups exposed to 10P polyplex (Fig.14). col1a1 expression revealed a different trend as the group with nonsense siRNA showed the highest col1a1 expression and the gene expression dropped in polyplex groups with the lowest col1a1 expression in HTFs exposed to n/p 20 polyplex. Collagen 1 production is a downstream result of the TGFβ pathway being activated. This suggest the evidence of weak transfection efficacy; however, the optimization of dosing might be required to significantly downregulate fibrosis-related genes. [0085] The composition of polycaprolactone electrospun fibers and 4-arm polyethylene glycol acrylate shows potentials as an anti-fibrotic design for endotracheal tube coating to deliver dexamethasone and small molecules in a controlled release fashion. In addition, we demonstrated that the increase of lubricity of the endotracheal tube’s surface and the reduction of the general stiffness using a hydrogel-based composite has a direct impact on the mucus production, epithelial adhesion, and epithelial layer abrasion. [0086] Laryngotracheal stenosis has been reported to be prominently associated with prolonged endotracheal intubation. The injury is generally initiated with mucosal inflammation followed by fibroplasia which leads to progressive airway lumen narrowing ³³ . In addition, endotracheal intubation causes vocal cord damages due to the clasping movement between vocal cord and the tube and also pressure applied to the vocal cord during the intubation and extubation ³⁴ . It is believed that soft and lubricious surfaces reduce mechanical damages to the soft tissue ³⁵ . Hydrogels as highly water absorbable polymers have been widely used in self-lubricating designs due to their adjustable tribological behavior ³⁶ . In this study, by using PEG-based hydrogels as the contact layer with inner lining of the trachea, we were able to reduce the surface stiffness at contact and provide protection for epithelial layer against contact stiff endotracheal tube surface by interjecting a swellable hydrogel coating. The exposed surface of the composite coating was completely covered with 4APEGA, which also facilitates the direct release of siRNA to the inner epithelial lining of the trachea. The 4APEGA was also substantially less stiff than the PCL electrospun fibers or the bare endotracheal tube (Fig.5) which helps prevent cellular abrasion and further damage (Fig.7). [0087] MUC5AC and MUC5b are the predominent mucins in the human airway and are reported to show a significant increase in response to ventilator-induced lung injuries ³⁰ , To mimic the friction between the testing groups and the inner layer of trachea, mechanical stimulation using the MCT6 was applied for 24 hours during which time MUC5AC and MUC5B production in tracheal ex-vivo samples in contact with ETT, 4APEGA-5k and 4APEGA-10k, and 4APEGA- 20k are illustrated in Figs.6A and 6B. The lowest MUC5AC production was observed in the tissue groups in contact with 4APEGA-5k (4.5 ± 0.2 ng/ml) while MUC5AC production in tissue groups in contact with 4APEGA-10k and 4APEGA-20k were higher compared to the tissue group in contact with ETT (4.7 ± 0.27 ng/ml). According to the results, MUC5AC secretion was significantly higher (*p: 0.039) in group with 4APEGA-10k compared to 4APEGA-5k. MUC5B secretion also showed the highest rate in tissue groups in contact with 4APEGA-10k (45.6 ± 2.29 ng/ml) while the lowest was observed in tissue samples in contact with 4APEGA-20k (36.89 ± 1.28 ng/ml). [0088] However, MUC5B sections were not significantly different between groups. In addition to the quantified mucin productions, histology micrographs at (magnification 4x) (Figs.7A-D) stained with Alcian Blue and Fast Red Nucleus to visualized mucus layer, goblet cells, and basement membrane revealing a general disruption in groups in contact with ETT. Goblet cell hyperplasia, epithelial layer abrasion, and tissue compression are prominent features of endotracheal damage to the inner lining of the trachea ³¹ which is mostly seen in the group in contact with ETT compared to other groups while the tissue group in contact with 4APEGA-5k showed more intact tissue structure after the applied friction. [0089] Surface chemistry of the coatings plays an important role in surface lubrication and cell adhesion properties. There have been multiple studies with modified surfaces with mucin-like glycoprotein lubricin to reduce tribological stress and improve lubricity ^{37, 38} ; however, due to the demand of biological resources for mucin production, the translational of these biological designs into clinical applications are limited. On the other hand, hydrophilic polymers with neutral charge and hydrogen-bond acceptors have shown the lowest cell adhesion among biomaterials. PEG is generally considered to have a low protein absorption rate and neutral nature, which has made it a popular choice for the synthesis of biocompatible coatings.4APEGA is a modified version of the PEG family, and is itself a relatively neutral polymer which has been used in this study to form a 3D matrix phase in the composite coating on ETTs.4APEGA coatings demonstrated significantly lower cell adhesion and water uptake capacities at higher molecular weight (Figs.3 and 8). [0090] Fibroplasia and scar tissue formation in laryngotracheal stenosis are highly associated with TGF-β1 upregulation and deposition of ECM ^{28, 39} . Most of the recent relevant scholarly literature and current clinical treatment regimen involve investigation or use of systematic (typically steroidal) interventions to suppress fibrosis ^40-42 , indicating an acute demand for local treatments of fibroplasia in the affected area. siRNA targeting the SMAD family has shown great potential in downregulation of the TGFβ pathway in laryngotracheal stenosis ^{43, 44} . Local drug delivery for siRNA payloads has been previously developed by incorporation in injectable scaffolds, direct injection to the affected site, and loaded into scaffolds for different applications; however, due to the practical limitation of access to different parts of laryngotracheal anatomy, especially in intubated patients, a design with local drug delivery of biological molecules such as siRNA is essential. The PEI-siRNA polyplex loaded in the 4APEGA coating developed in the current study, has demonstrated the capability to release the siRNA cargo at the topical sites subject to the damage from ETT abrasion. The drug release profile observed indicates that 4APEGA coatings of higher molecular weight facilitate a more rapid siRNA release (Fig.12). due to a reduction of electrostatic attraction between carboxylate bonds and amine groups in the polyplex. [0091] In addition, steroids are highly effective on controlling fibroblast proliferation ^{45, 46} and ECM synthesis and multiple previous studies have reported methods to incorporate steroids into various materials in different forms including solid coating ⁴⁷ and fibers ⁴⁸ to cover endotracheal tube for local drug delivery purposes. However, biofilm production has been a challenging issue in patients with prolonged intubation ^{49, 50} which requires a different approach to avoid biofilm production while deliver the steroid in a sustained released manner. In our study, electrospun fibers embedded in 4APEGA hydrogels have shown successful dexamethasone delivery through the composite without PCL electrospun fibers being exposed to the inner lining of the trachea. [0092] Random fiber structure and surface area was observed in the SEM images (Fig.15). Results from the mucoadhesion test (Fig.16) show that 1x flocked samples were the most mucoadhesive, with an observed cohesive failure stress of more than 6 kPa. The least mucoadhesive were the 3x flocked, although it was not significant compared to the uncoated PCL samples. Absorption swelling testing (Fig.18) showed that the 3x flocked group absorbed the most water, with uncoated PCL absorbing the least. Degradation testing (Figs.4A-4C and Fig.19) showed that 1x flocked samples degrade the most and the quickest, with 3x flocked degrading the slowest and the least. PEG coated samples degraded as fast as 1x flocked initially, but degradation slowed after 7 days. No significant differences in mechanical properties were observed between groups. Stiffness testing showed a stiffness of 1.04 ± 0.02 N/mm, degradation of 31.0 ± 4.8% by 7 days and 46.5 ± 5.7% at 14 days, a water absorption peak of 273 ± 8%, and an average mucoadhesive failure stress of 6.88 ± 4.44 kPa for the 1x flocked samples. [0093] Mucoadhesion – Fig.16 illustrates that uncoated PCL samples had a cohesive failure rate of 1.40 +/- 0.55 kPa. PEG dipped samples had a cohesive failrue rate of 2.73 +/- 0.84 kPa.1x density flocked samples had a cohesive failure rate of 6.88 +/- 1.81 kPa.2x density flocked samples had a cohesive failure rate of 3.03 +/- 0.79 kPa and 3x flocked samples had a cohesive failure rate of 1.18 +/- 0.26 kPa. [0094] Stiffness –Fig.17 illustrates that uncoated PCL fibers had an average stiffness of 1.37 +/- 0.015 N/mm. The fibers dipped in PEG had an average stiffness of 1.64 +/- 0.042 N/mm. The PCL fibers that were flocked with 1x density had a stiffness of 1.03 +/- 0.020 N/mm. Those flocked with 2x density had a stiffness of 0.76 +/- 0.021 N/mm. Those flocked with 3x density had a stiffness of 1.22 +/- 0.028 N/mm. [0095] Swelling Behaviour –Fig.18 illustrates that the uncoated PCL samples mass peaked after 30 minutes, with a mass increase of 66.7 +/- 15.4%. The final mass increase of these samples was 58.3 +/- 19.0% after 90 minutes. The samples regularly coated in PEG peaked after 10 minutes with a mass increase of 113.0 +/- 6.53%. After 90 minutes these samples had a mass increase of 106.5 +/- 7.91%. the 1x density flocked samples peaked after 45 minutes with an increase of 273.4 +/- 8.46%. After 90 minutes, they had a mass increase of 254.9 +/- 12.9%. The 2x flocked peaked at 286.9 +/- 4.38% after 15 minutes and increased 278.0 +/- 7.23% after 90 minutes. The 3x flocked peaked at 426.4 +/- 42.8% after 15 minutes and finished at 403.5 +/- 36.3% after 90 minutes. [0096] Degradation Rate – Fig. 19 illustrates that the average percentage of mass that degraded from uncoated PCL samples was 17.6 +/- 6.32% after 7 days and 24.2 +/- 6.50% after 14 days. The average percentage of mass that degraded from samples dipped in PEG was 28.6% after 7 days and 34.1 +/- 23.0% after 14 days.1x density flocked samples degraded 31.0 +/- 4.80% after 7 days and 46.5 +/- 5.71% after 14 days.2x density flocked samples degraded 14.7 +/- 2.38% after 7 days and 24.6 +/- 3.81% after 14 days.3x flocked samples degraded 7.8 +/- 0.23% after 7 days and 8.0 +/- 1.13% after 14 days. [0097] The most mucoadhesive samples of the composite material tested was the 1x flocked samples, which means that this material will likely be best suited for the intended use, as high muco-adhesion is the most important property of our desired material. Stiffness testing showed that the PEG coated were the stiffest, almost twice as stiff as the 2x flocked samples, which were the least stiff. According to the material design and characterization, PCL-PEG samples with 1x flock density appear to be suitable materials for both in vitro and in vivo functional analyses. [0098] Thus, there is disclosed an endotracheal tube modified using a novel polycaprolactone- 4- arm polyethylene glycol (PCL-4APEGA) composite coating with dual drug delivery capability was developed and fully characterized. This study indicated a significant reduction in stiffness of the contact surface and ability to provide swollen hydrogel coating-based protection to the epithelial mucosa against an otherwise stiff and abrasive endotracheal tube surface. Electrospun polycaprolactone fibers embedded in the 4APEGA hydrogels were an effective platform for tunable dexamethasone delivery through the composite while local drug delivery of siRNA polyplexes from the 4APEGA matrix was also demonstrated. Overall, the novel PCL-4APEGA coated endotracheal tubes are a promising biocompatible platform technology to minimize focal airway damage during intubation and modulate the inflammatory and fibrotic sequelae through multimodal, controlled, local drug delivery. REFERENCES 1. 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