WO2021231904A1

WO2021231904A1 - Detection and indication of covid-19, other viruses and pathogens and vaccine associated efficacy

Info

Publication number: WO2021231904A1
Application number: PCT/US2021/032517
Authority: WO
Inventors: Paul Wolff; Eric Mathur
Original assignee: Diomics Corporation
Priority date: 2020-05-14
Filing date: 2021-05-14
Publication date: 2021-11-18
Also published as: WO2021231904A9

Abstract

A method, treatment substance, treatment fabric and transdermal patch for detecting antibodies are provided. The treatment substance includes a medicament configured to treat a patient over a period of time and a soluble, hydrophilic polycaprolactone coupled to the medicament where the soluble, hydrophilic polycaprolactone is configured to dissolve over the period of time upon contact with the patient.

Description

DETECTION AND INDICATION OF COVID-19, OTHER VIRUSES AND PATHOGENS AND VACCINE ASSOCIATED

EFFICACY

CROSS-REFERENCE TO RELATED APPLICATIONS

[0001] This application claims the benefit of U.S. Provisional Application No. 63/024,517 titled “DETECTION OF COVID-19 AND OTHER VIRUSES AND PATHOGENS” which was filed on May 14, 2020 and is incorporated by reference in its entirety.

FIELD OF THE INVENTION

[0002] This disclosure relates to the field of pathogen detection in a live host.

BACKGROUND

[0003] The COVID-19 pandemic has shattered our beliefs about the type and scope of health information captured and compiled. The lack of volume test data and the corresponding analytics has left decision makers in a tough place, making decisions without ideal tools or data. Data requirements go beyond traditional medical practitioner health info and should include a wider variety of real time data about the health state of that individual as well as other user activities. The pandemic has proved a) that healthcare is not local, regional, national or global - it is all of the above and b) in an environment like today, the ability to capture and hyper analyze individual data and distribute that data to resource allocation planners is beyond necessary.

[0004] According to the Annals of Internal Medicine, the median incubation period for the COVID -19 vims is estimated to be 5.1 days with 97.5% of patients developing symptoms within 11.5 days post infection. These estimates imply that 101 out of every 10,000 cases will develop symptoms after 14 days. The lack of real time monitoring during this base incubation period creates issues for small and large groups alike; a) we are only testing based upon presented symptoms, we are missing asymptomatic shedders of the vims with limited testing and b) since we discover the presence of the virus in an individual late in the incubation sequence, others are being infected and viral control capabilities are reactive as opposed to proactive.

[0005] The use of a reactive PPD has been used in some form since 1890 for the monitoring and detection of Mycobacterium tuberculosis. A small drop of filtered tuberculin liquid containing some components of heat-killed TB bacteria is injected 3mm under the top layer of the forearm skin. The Mantoux tuberculin test is used to determine if an individual has ever been exposed to TB. If exposed to the TB contagion, the skin will react to the antigens by developing a firm red bump at the site within 2 or 3 days. There is a need in the art for applying the Mantoux tuberculin test to detection of various pathogens such as COVID -19 using modern advances in polymer chemistry.

[0006] Synthetic polymers have excellent design flexibility because their composition and structure can be tailored to specific applications. Poly (e-caprolactone) has drawn a great deal of attention in the past several years and has been successfully incorporated as an implantable biomaterial for medical applications, including sutures and wound dressing, cardiovascular tissue engineering, nerve regeneration, and bone tissue engineering. For instance, the use of PCL as a vehicle for controlled delivery of therapeutic molecules (e.g., drug, protein, gene), has also been extensively explored. PCL is a linear aliphatic polyester. It is a hydrophobic, semi crystalline (50%), biocompatible, and relatively slow-degrading polymer, which has been widely used in the biomedical field for the last few decades. It is a thermoplastic polymer with several desirable features, including good stability under ambient conditions, ease of processability (thermal & solution), and has already been approved for use in products by the U.S. Food and Drug Administration. While PCL has a combination of desirable properties including biodegradability, biocompatibility and high permeability, practical therapeutic applications are still hampered by the hydrophobic nature of the polymer. Treating the PCL with a base for a period of time has been shown to make the PCL hydrophilic, which allows the PCL to break down more quickly under aqueous conditions. However, the base treatment is slow and may take several hours to days.

[0007] The following papers are incorporated by reference: [0008] Hongfan Sun, Lin Mei, Cunxian Song, Xiumin Cui, Pengyan Wang. “The in vivo degradation, absorption and excretion of PCL-based implant” (2006) Elsevier; Biomaterials

[0009] Debasish Mondal, May Griffith & Subbu S. Venkatraman, “Polycaprolactone-based biomaterials for tissue engineering and drug delivery: Current scenario and challenges”, International Journal of Polymeric Materials and Polymeric Biomaterials (2016) 65:5, 255-265

[0010] Zhihua Zhou, Wei Wu, Jianjun Fang, Jingbo Yin., “Polymer-based porous microcarriers as cell delivery systems for applications in bone and cartilage tissue engineering”, International Materials Reviews (2020) 0:0, pages 1-373.

[0011] Fatemeh Asghari, Mohammad Samiei, Khosro Adibkia, Abolfazl Akbarzadeh & Soodabeh Davaran, “Biodegradable and biocompatible polymers for tissue engineering application: a review”, Artificial Cells, Nanomedicine, and Biotechnology (2017) 45:2, 185-192

[0012] Eun Kim, Geza Erdos ... Emrullah Korkmaz, Louis D. Falo Jr., Andrea Gambotto, “Microneedle array delivered recombinant coronavirus vaccines: Immunogenicity and rapid translational development”, EBio Medicine (2020) 102743

[0013] Elbay Malikmammadov, Tugba Endogan Tanir, Aysel Kiziltay, Vasif Hasirci & Nesrin Hasirci, “PCL and PCL-based materials in biomedical applications” Journal of Biomaterials Science, Polymer Edition (2018), 29:7-9, 863-893

[0014] Zheng R, Duan H, Xue J, Liu Y, Feng B, Zhao S, et al. “The influence of gelatin/PCL ratio and 3-D construct shape of electro-spun membranes on cartilage regeneration”,

Biomaterials (2014) 35:152-164

[0015] Venugopal & Ramakrishna, “Biocompatible Nanofiber Matrices for the Engineering of a Dermal Substitute for Skin Regeneration” Tissue Engineering (2005) Vol. 11, No.5-6

[0016] Thanh Le T, et. al. “The COVID-19 vaccine development landscape”. Nature Reviews. Drug Discovery 2020: doi: 10.1038/d41573-020-00073-5

[0017] Lurie D., et. al. “Developing COVID-19 vaccines at Pandemic speed”, The New England Journal of Medicine, 2020 doi: 10.1056/NEJNp2005630 [0018] Nicolau P. “Polycaprolactone for the Face”. In: Costa A. (eds) Minimally Invasive Aesthetic Procedures. Springer, Cham 2020

[0019] Maria Ann Wodruff, Dietmar Wemer Humacher “The return of a forgotten polymer”- Polycaprolactone in the 21st century”201035.10,pp 1217-1256

[0020] Rouba Ghobeira, “Plasma Activation of Electrospun Scaffolds for Neural Tissue Engineering” 2018

[0021] “Polycaprolactone and its Application as a Vascular Tissue Engineering Scaffold” (2016) Nova Science Publishers; Polycaprolactones: Properties, Applications and Selected Research.

SUMMARY

[0022] A treatment substance is presented. The treatment substance includes a medicament configured to treat a patient over a period of time and a soluble, hydrophilic polycaprolactone coupled to the medicament where the soluble, hydrophilic polycaprolactone is configured to dissolve on contact with the patient over the period of time. The soluble, hydrophilic polycaprolactone and medicament may be combined in an emulsion. The emulsion may include an adhesive. The medicament may be covalently bonded to the soluble, hydrophilic polycaprolactone. The medicament may be a live cell. The medicament may be a protein antigen. The protein antigen may be configured to cause an immune response in the patient at a point of contact between the patient and the protein antigen.

[0023] Another general aspect is a treatment fabric. The treatment fabric includes soluble, hydrophilic polycaprolactone that is coupled to an active agent where the active agent is configured to treat a patient over a period of time. The soluble, hydrophilic polycaprolactone includes a flat layer that is configured to dissolve on contact with the patient over the period of time. The flat layer may include microfibers of soluble, hydrophilic polycaprolactone that are woven into a gauze. The flat layer may include a web of soluble, hydrophilic polycaprolactone. The flat layer may include a matrix of soluble, hydrophilic polycaprolactone. The active agent may be a live cell. The active agent may be a biologic. The active agent may be a protein antigen. The active agent and soluble, hydrophilic polycaprolactone may be combined in an emulsion. The emulsion may include an adhesive.

[0024] An exemplary embodiment is a transdermal patch. The transdermal patch includes a backing layer adjacent to an active agent-containing layer where the active agent-containing layer includes soluble, hydrophilic polycaprolactone and a medicament. The transdermal patch includes microneedles that are configured to penetrate the area of skin. The microneedles may include soluble, hydrophilic polycaprolactone that dissolves after penetrating the area of skin. The medicament may be coupled to tips of the microneedles. The medicament may be a protein antigen.

[0025] Another general aspect is a method of detecting antibodies in an individual. The method includes administering a protein antigen to the individual and detecting an immune response of the individual to the protein antigen. The protein antigen is coupled to soluble, hydrophilic polycaprolactone. The soluble, hydrophilic polycaprolactone is configured to dissolve responsive to contact with the individual. The protein antigen is configured to be released to the individual as the soluble, hydrophilic polycaprolactone is dissolved. The soluble, hydrophilic polycaprolactone may include a transdermal patch. The transdermal patch may include microneedles where tips of the microneedles comprise soluble, hydrophilic polycaprolactone that is coated with the protein antigen. The soluble, hydrophilic polycaprolactone may include a fabric that is applied to the individual. The soluble, hydrophilic polycaprolactone may be configured to dissolve at a rate between about 5 minutes to about 2 years in an aqueous environment.

BRIEF DESCRIPTION OF THE DRAWINGS [0026] FIG. 1 is an illustration of a magnification of a hydrophilic PCL microbead.

[0027] FIG. 2 is a microscopic image showing a multitude of PCL microbeads.

[0028] FIG. 3 is a reaction diagram of base-catalyzed hydrolysis of the ester linkages present in the backbone of polycaprolactone. [0029] FIG. 4 is a reaction diagram of a coupling of surface-exposed carbonyl groups to amino groups on a polypeptide to create a peptide bond.

[0030] FIG. 5 is an illustration of an embodiment of a surface of a hydrophilic PCL microbead as the hydrophilic PCL microbead binds to stem cells.

[0031] FIG. 6 is an illustration of an embodiment of a PCL dissolving microneedle.

DETAILED DESCRIPTION

[0032] . The disclosed subject matter includes methods and compositions that can deliver active ingredients, medicaments, or other forms of treatment via hydrophilic polycaprolactone (PCL). Hydrophilic PCL may be composed into various forms such as patches, platforms, beads, a bandages. Active ingredients may be incorporated to the hydrophilic PCL composition. In one example, an active ingredient that is an antigen is incorporated into hydrophilic PCL. The hydrophilic PCL is then administered to a patient whereby the antigen is gradually delivered over a period of time. A reaction of the patient to the antigen may be observed at a location of administration.

[0033] After reading this description it will become apparent to one skilled in the art how to implement the invention in various alternative embodiments and alternative applications. However, all the various embodiments of the present invention will not be described herein. It will be understood that the embodiments presented here are presented by way of an example only, and not limitation. As such, this detailed description of various alternative embodiments should not be construed to limit the scope or breadth of the present invention as set forth below.

[0034] Before the present invention is disclosed and described, it is to be understood that the aspects described below are not limited to specific compositions, methods of preparing such compositions, or uses thereof as such may, of course, vary. It is also to be understood that the terminology used herein is for the purpose of describing particular aspects only and is not intended to be limiting.

[0035] The detailed description of the invention is divided into various sections only for the reader's convenience and disclosure found in any section may be combined with that in another section. Titles or subtitles may be used in the specification for the convenience of a reader, which are not intended to influence the scope of the present invention.

DEFINITIONS

[0036] The phrases “modified polycaprolactone” or “modified PCL” is meant to be any polycaprolactone (PCL) that has been treated or modified such that the hydrophilicity of the PCL is increased and/or such that one or more surface features of the PCL have been modified (e.g., chemical and/or physical modifications). Examples of surface features include texture (e.g., roughness, smoothness), holes, dimples, channels, punctures, protrusions, porous, semipermeable, and other irregularities. Any suitable treatment methods, including chemical or physical treatments, for modifying surface features of PCL can be used.

[0037] As used herein, the phrase “soluble, hydrophilic polycaprolactone”, “soluble, hydrophilic PCL”, or “hydrophilic PCL” means polycaprolactone (PCL) that has been treated in some manner to make it absorb water and to increase its solubility (i.e., increase dissolution rate) when used in a composition or medical use such as a medicament delivery substance, stem cell carrier, or an implant. Any suitable treatment methods, including chemical or physical treatments, for increasing hydrophilicity and solubility of PCL can be used. For example, PCL can be subjected to (treated with) a base (e.g. having a pH above 8) as described in WO 2016/025021 Al, which is incorporated herein by reference in its entirety for all purposes, including for all methods of making, modifying, and using PCL and modified PCL. Non-limiting examples of bases include NaHC03 and NaOH.

[0038] As used herein, “polycaprolactone co-polymer” refers to any combination of the polymer made by a ring-opening polymerization of epsilon caprolactone (PCL) and a co polymer. Co-polymers can include polylactide, polyglycolide or polydioxanone. PCL may be copolymerized with other esters such as polylactide to alter properties. In addition to polylactide, PCL may be copolymerized with other lactone-containing polymers such as poly-glycolide, poly (3 tolO-membered) lactone ring-containing compounds, etc. Generally, high molecular weight (MW) biodegradable lactone co-polymers are used, but poly ethylene glycol and poly vinyl styrene can also be used. In a typical embodiment, a molecular weight range of PCL is 5,000 to 300,000. For example, an 80,000 MW PCL polymer can be used. In addition, a co-polymer can include, but not be limited to, any polypeptide, polynucleotide, polylactic acid (PLA), polylactide, L-PLA, L-polylactide, poly(D,L)-lactic acid, poly(D,L)-lactide, polyglycolide (PGA), polydioxane, acrylamide, poly N-isopoly acrylamide, chitosan, polyethylene glycol, poly vinyl alcohol, hydroxyapatite/silk fibrion (HAP/SF), and/or polyurethane. Additional co polymers are described herein.

[0039] As used herein, the term “copolymerized” refers to using two or more monomeric units to form a polymer with inclusion of both in some random order (e.g., AABABBBAABAAABBBBA) or defined order (such as, e.g., AAABAAABAAAB or ABABABAB or ABA ABA ABA ABA ABA ABA). For example, when referring to PCL that is copolymerized with at least one agent such as, e.g., L-lactic acid, the copolymer formed is a polycaprolactide called poly-L-lactic-co-s-caprolactone.

[0040] As used herein, the term “microbead” refers to a shape that is less than 1 mm in diameter in the widest dimension, can be solid or hollow, can be filled with cells/hydrogel/support additives, and can be filled with biologically active substances or have them attached to exterior. The microbead can be comprised of a barrier that has a controlled pore size to limit the inflow of surrounding particles and/or cells based on size (e.g. antibodies), while letting smaller molecules (e.g. peptides, nucleotides, saccharides, salts, small proteins, etc.) in/out of the interior. The barrier can be comprised of soluble, hydrophilic polycaprolactone, and/or a co-polymer comprised of one or more polymers and polycaprolactone (can be cross- linked and/or entangled), and/or can be further functionalized by attaching stem cell support additives.

[0041] As used herein, “hydrophilicity” refers to the physical property of a compound that has an affinity for or is attracted to water. The attractive interaction between water and a surface is further known as wetting. Further, in the field of surface science, hydrophilicity refers to a contact angle of less than about 90 degrees between a droplet of water and the surface it contacts. In various embodiments, a hydrophilicity refers to a contact angle of less than about 75 degrees. The contact angle usually refers to the static contact angle. Hydrophilicity can also be measured using a sliding angle, an advancing angle, and a receding angle of the water droplet contacting the surface of interest, and additional derivations using one or more angle measurements. Further the wetting and adhesion interactions between water and a surface can be measured by calculating the attractive force between the water and surface using a microbalance, goniometer, or atomic force microscopy.

SOLUBLE, HYDROPHILIC POLYCAPROLACTONE (PCL)

[0042] The substrate as provided herein contains soluble, hydrophilic polycaprolactone (PCL). PCL is a monopolymer made by a ring-opening polymerization of epsilon caprolactone. Similar polymers are polylactide, polyglycolide or polydioxanone. PCL may be copolymerized with other esters such as polylactide, polyglycolide polydioxanone, or poly (3 to 10-membered) lactone ring-containing compounds to alter properties. Polymers of acrylamide may also be used, such as poly N-isopropylacrylamide. In some embodiments, the PCL is copolymerized with a polystyrene or a polyvinylidene. Any suitable polystyrene can be used. Any suitable polyvinylidene can be used. Examples of polystyrenes that can be used include polystyrene, polystyrene sulfonate, carboxylated polystyrene, carboxylate modified polystyrene, iodinated polystyrene, brominated polystyrene, chlorinated polystyrene, fluorinated polystyrene, lithium polystyryl modified iodinated polystyrene, iodinated polystyrene derivatives, polystyrene ionomers, polystyrene ion exchange resin, sodium polystyrene sulfonate, polystyrene sulfonate, chlorinated polystyrene derivatives, brominated polystyrene derivatives and derivatives thereof. Examples of polyvinylidene include polyvinylidine fluoride, polyvinylidine chloride, polyvinylidine bromide, polyvinylidine iodide, polyvinylidine acetate, polyvinylidine alcohol and derivatives thereof. Further examples of suitable agents for copolymerizing with PCL include polyvinylpyrrolidone, polyvinylpyrrolidone iodine, polyvinylpyrrolidone bromide, polyvinylpyrrolidone chloride, polyvinylpyrrolidone fluoride, polyethylene, iodinated polyethylene, brominated polyethylene, chlorinated polyethylene, fluorinated polyethylene, polyethylene terephthalate, polypropylene, iodinated polypropylene, brominated polypropylene, chlorinated polypropylene, fluorinated polypropylene and derivatives thereof.

[0043] Soluble, hydrophilic polycaprolactone as described herein can be made, for example, using the methods described in U.S. Patent No. 9,359,600, which is incorporated herein by reference in its entirety. In embodiments, the soluble, hydrophilic polycaprolactone is DIOMAT®. DIOMAT® has been described, for example, in U.S. Patent Nos. 9,708,600; 9,359,600; 8,759,075; 9,662,096; and 8,685,747; and U.S. Pub. Nos. 2016/0025603 and 2016/0047720, each of which is incorporated herein by reference in its entirety.

[0044] In embodiments, a PCL substrate includes any form of PCL, soluble, hydrophilic PCL, PCL and co-polymer composition, conjugated PCL, conjugated PCL and co-polymer composition, in any size, shape, or configuration. The PCL substrate can dissolve in three ranges, short-term, medium-term, and long-term. The short-term range is about 5 minutes up to 24 hours, 30 minutes, 60 minutes, 2 hours, 3 hours, 4 hours, 5 hours, 6 hours, 12 hours, 18 hours, and 24 hours. The medium-term range is about 24 hours up to 1 month, 24 hours, 2 days, 3 days, 4 days, 5 days, 6 days, 1 week, 2 weeks, 3 weeks, and 4 weeks. The long-term range is about 1 month to 2 years, 1 month, 2 months, 3 months, 4 months, 5 months, 6 months, 12 months, 18 months, 2 years.

[0045] In embodiments, the soluble, hydrophilic PCL substrate dissolves in about 5 minutes to about 24 hours. In embodiments, the soluble, hydrophilic PCL substrate dissolves in about 5 minutes to about 30 minutes. In embodiments, the soluble, hydrophilic PCL substrate dissolves in about 5 minutes to about 1 hour. In embodiments, the soluble, hydrophilic PCL substrate dissolves in about 5 minutes to about 24 hours. In embodiments, the soluble, hydrophilic PCL substrate dissolves in about 5 minutes to about 18 hours. In embodiments, the soluble, hydrophilic PCL substrate dissolves in about 5 minutes to about 12 hours. In embodiments, the soluble, hydrophilic PCL substrate dissolves in about 5 minutes to about 6 hours. In embodiments, the soluble, hydrophilic PCL substrate dissolves in about 5 minutes to about 5 hours, 4 hours, 3 hours, 2 hours, and 1 hour. In embodiments, the soluble, hydrophilic PCL substrate dissolves in about 5 minutes to about 24 hours. In embodiments, the soluble, hydrophilic PCL substrate dissolves in about 30 minutes to about 24 hours. In embodiments, the soluble, hydrophilic PCL substrate dissolves in about 30 minutes to about 18 hours. In embodiments, the soluble, hydrophilic PCL substrate dissolves in about 30 minutes to about 12 hours. In embodiments, the soluble, hydrophilic PCL substrate dissolves in about 30 minutes to about 6 hours. In embodiments, the soluble, hydrophilic PCL substrate dissolves in about 30 minutes to about 6 hours, 5 hours, 4 hours, 3 hours, 2 hours, or 1 hour. In embodiments, the soluble, hydrophilic PCL substrate dissolves in about 1 hour to about 24 hours. In embodiments, the soluble, hydrophilic PCL substrate dissolves in about 1 hour to about 18 hours. In embodiments, the soluble, hydrophilic PCL substrate dissolves in about 1 hour to about 12 hours. In embodiments, the soluble, hydrophilic PCL substrate dissolves in about 1 hour to about 6 hours. In embodiments, the soluble, hydrophilic PCL substrate dissolves in about 1 hour to about 6 hours, 5 hours, 4 hours, 3 hours, or 2 hours. In embodiments, the soluble, hydrophilic PCL substrate dissolves in about 2 hours to about 24 hours. In embodiments, the soluble, hydrophilic PCL substrate dissolves in about 2 hours to about 24 hours. In embodiments, the soluble, hydrophilic PCL substrate dissolves in about 2 hours to about 18 hours. In embodiments, the soluble, hydrophilic PCL substrate dissolves in about 2 hours to about 12 hours. In embodiments, the soluble, hydrophilic PCL substrate dissolves in about 2 hours to about 6 hours. In embodiments, the soluble, hydrophilic PCL substrate dissolves in about hours to about 5 hours, 4 hours, or 3 hours. In embodiments, the soluble, hydrophilic PCL substrate dissolves in about 3 hours to about 24 hours. In embodiments, the soluble, hydrophilic PCL substrate dissolves in about 3 hours to about 24 hours. In embodiments, the soluble, hydrophilic PCL substrate dissolves in about 3 hours to about 18 hours. In embodiments, the soluble, hydrophilic PCL substrate dissolves in about 3 hours to about 12 hours. In embodiments, the soluble, hydrophilic PCL substrate dissolves in about 3 hours to about 6 hours. In embodiments, the active agent- containing substrate dissolves in about 3 hours to about 5 hours, or 4 hours. In embodiments, the soluble, hydrophilic PCL substrate dissolves in about 4 hours to about 24 hours. In embodiments, the soluble, hydrophilic PCL substrate dissolves in about 4 hours to about 24 hours. In embodiments, the soluble, hydrophilic PCL substrate dissolves in about 4 hours to about 18 hours. In embodiments, the soluble, hydrophilic PCL substrate dissolves in about 4 hours to about 12 hours. In embodiments, the soluble, hydrophilic PCL substrate dissolves in about 4 hours to about 6 hours. In embodiments, the soluble, hydrophilic PCL substrate dissolves in about 4 hours to about 5 hours. In embodiments, the soluble, hydrophilic PCL substrate dissolves in about 5 hours to about 24 hours. In embodiments, the soluble, hydrophilic PCL substrate dissolves in about 5 hours to about 24 hours. In embodiments, the soluble, hydrophilic PCL substrate dissolves in about 5 hours to about 18 hours. In embodiments, the soluble, hydrophilic PCL substrate dissolves in about 5 hours to about 12 hours. In embodiments, the soluble, hydrophilic PCL substrate dissolves in about 5 hours to about 6 hours. In embodiments, the soluble, hydrophilic PCL substrate dissolves in about 6 hours to about 24 hours. In embodiments, the soluble, hydrophilic PCL substrate dissolves in about 6 hours to about 18 hours. In embodiments, the soluble, hydrophilic PCL substrate dissolves in about 6 hours to about 12 hours. In embodiments, the soluble, hydrophilic PCL substrate dissolves in about 12 hours to about 18 hours. In embodiments, the soluble, hydrophilic PCL substrate dissolves in about 12 hours to about 24 hours. In embodiments, the active agent-containing substrate dissolves in about 4 weeks to about 4 weeks. The dissolution time may be any value or subrange within the recited ranges, including endpoints. For example, the active agent-containing substrate may dissolve in about 5 minutes, 30 minutes, 1 hour, 2 hours, 3 hours, 4 hours, 5 hours, 6 hours, 12 hours, 18 hours, 24 hours, etc.

[0046] In embodiments, the soluble, hydrophilic PCL substrate dissolves in about one day to about one month. Each soluble, hydrophilic PCL layer can have a different dissolution rate than any other soluble, hydrophilic PCL layer in the stem cell carrier. In embodiments, the soluble, hydrophilic PCL substrate dissolves in about 24 hours to about 72 hours. In embodiments, the soluble, hydrophilic PCL substrate dissolves in about 30 hours to about 72 hours. In embodiments, the soluble, hydrophilic PCL substrate dissolves in about 24 hours to about 4 weeks. In embodiments, the soluble, hydrophilic PCL substrate dissolves in about 24 hours to about 3 weeks. In embodiments, the soluble, hydrophilic PCL substrate dissolves in about 24 hours to about 2 weeks. In embodiments, the soluble, hydrophilic PCL substrate dissolves in about 24 hours to about 1 week. In embodiments, the soluble, hydrophilic PCL substrate dissolves in about 24 hours to about 6 days, 5 days, 4 days, 3 days, or 2 days. In embodiments, the soluble, hydrophilic PCL substrate dissolves in about 30 hours to about 1 month. In embodiments, the soluble, hydrophilic PCL substrate dissolves in about 30 hours to about 4 weeks. In embodiments, the soluble, hydrophilic PCL substrate dissolves in about 30 hours to about 3 weeks. In embodiments, the soluble, hydrophilic PCL substrate dissolves in about 30 hours to about 2 weeks. In embodiments, the soluble, hydrophilic PCL substrate dissolves in about 30 hours to about 1 week. In embodiments, the soluble, hydrophilic PCL substrate dissolves in about 30 hours to about 6 days, 5 days, 4 days, 3 days, or 2 days. In embodiments, the soluble, hydrophilic PCL substrate dissolves in about 30 hours to about 1 month. In embodiments, the soluble, hydrophilic PCL substrate dissolves in about 48 hours to about 4 weeks. In embodiments, the soluble, hydrophilic PCL substrate dissolves in about 48 hours to about 3 weeks. In embodiments, the soluble, hydrophilic PCL substrate dissolves in about 48 hours to about 2 weeks. In embodiments, the soluble, hydrophilic PCL substrate dissolves in about 48 hours to about 1 week. In embodiments, the soluble, hydrophilic PCL substrate dissolves in about 48 hours to about 6 days, 5 days, 4 days, or 3 days. In embodiments, the soluble, hydrophilic PCL substrate dissolves in about 3 days to about 1 month. In embodiments, the soluble, hydrophilic PCL substrate dissolves in about 3 days to about 4 weeks. In embodiments, the soluble, hydrophilic PCL substrate dissolves in about 3 days to about 3 weeks. In embodiments, the soluble, hydrophilic PCL substrate dissolves in about 3 days to about 2 weeks. In embodiments, the soluble, hydrophilic PCL substrate dissolves in about 3 days to about 1 week. In embodiments, the soluble, hydrophilic PCL substrate dissolves in about 3 days to about 6 days, 5 days, or 4 days. In embodiments, the soluble, hydrophilic PCL substrate dissolves in about 4 days to about 1 month. In embodiments, the soluble, hydrophilic PCL substrate dissolves in about 4 days to about 4 weeks. In embodiments, the soluble, hydrophilic PCL substrate dissolves in about 4 days to about 3 weeks. In embodiments, the soluble, hydrophilic PCL substrate dissolves in about 4 days to about 2 weeks. In embodiments, the soluble, hydrophilic PCL substrate dissolves in about 4 days to about 1 week. In embodiments, the soluble, hydrophilic PCL substrate dissolves in about 4 days to about 6 days, or 5 days. In embodiments, the soluble, hydrophilic PCL substrate dissolves in about 5 days to about 1 month. In embodiments, the soluble, hydrophilic PCL substrate dissolves in about 5 days to about 4 weeks. In embodiments, the soluble, hydrophilic PCL substrate dissolves in about 5 days to about 3 weeks. In embodiments, the soluble, hydrophilic PCL substrate dissolves in about 5 days to about 2 weeks. In embodiments, the soluble, hydrophilic PCL substrate dissolves in about 5 days to about 1 week. In embodiments, the soluble, hydrophilic PCL substrate dissolves in about 5 days to about 6 days. In embodiments, the soluble, hydrophilic PCL substrate dissolves in about 6 days to about 1 month. In embodiments, the soluble, hydrophilic PCL substrate dissolves in about 6 days to about 4 weeks. In embodiments, the soluble, hydrophilic PCL substrate dissolves in about 6 days to about 3 weeks. In embodiments, the soluble, hydrophilic PCL substrate dissolves in about 6 days to about 2 weeks. In embodiments, the soluble, hydrophilic PCL substrate dissolves in about 6 days to about 1 week. In embodiments, the soluble, hydrophilic PCL substrate dissolves in about 1 week to about 1 month. In embodiments, the soluble, hydrophilic PCL substrate dissolves in about 1 week to about 4 weeks. In embodiments, the soluble, hydrophilic PCL substrate dissolves in about 1 week to about 3 weeks. In embodiments, the soluble, hydrophilic PCL substrate dissolves in about 1 week to about 2 weeks. In embodiments, the soluble, hydrophilic PCL substrate dissolves in about 2 weeks to about 1 month. In embodiments, the soluble, hydrophilic PCL substrate dissolves in about 2 weeks to about 4 weeks. In embodiments, the soluble, hydrophilic PCL substrate dissolves in about 2 weeks to about 3 weeks. In embodiments, the soluble, hydrophilic PCL substrate dissolves in about 3 weeks to about 1 month. In embodiments, the soluble, hydrophilic PCL substrate dissolves in about 4 weeks to about 4 weeks. The dissolution time may be any value or subrange within the recited ranges, including endpoints. For example, the soluble, hydrophilic PCL substrate may dissolve in about 24 hours, 30 hours, 48 hours, 3 days, 4 days, 5 days, 6 days, 7, 8, 9, 10, 11, 12, 13 days, 2 weeks, 3 weeks, 4 weeks, one month, etc. In embodiments, the soluble, hydrophilic PCL substrate dissolves in about one month to about 2 years. Each soluble, hydrophilic PCL layer can have a different dissolution rate than any other soluble, hydrophilic PCL layer in the stem cell carrier. In embodiments, the soluble, hydrophilic PCL substrate dissolves in about 1 month to about 3 months. In embodiments, the soluble, hydrophilic PCL substrate dissolves in about 2 months to about 3 months. In embodiments, the soluble, hydrophilic PCL substrate dissolves in about 1 month to about 2 years. In embodiments, the soluble, hydrophilic PCL substrate dissolves in about 1 month to about 18 months. In embodiments, the soluble, hydrophilic PCL substrate dissolves in about 1 month to about 12 months. In embodiments, the soluble, hydrophilic PCL substrate dissolves in about 1 month to about 6 months. In embodiments, the soluble, hydrophilic PCL substrate dissolves in about 1 month to about 6 months, 5 months, 4 months, 3 months, or 2 months. In embodiments, the soluble, hydrophilic PCL substrate dissolves in about 2 months to about 2 years. In embodiments, the soluble, hydrophilic PCL substrate dissolves in about 2 months to about 18 months. In embodiments, the soluble, hydrophilic PCL substrate dissolves in about 2 months to about 12 months. In embodiments, the soluble, hydrophilic PCL substrate dissolves in about 2 months to about 6 months. In embodiments, the soluble, hydrophilic PCL substrate dissolves in about 2 months to about 6 months, 5 months, 4 months, or 3 months. In embodiments, the soluble, hydrophilic PCL substrate dissolves in about 3 months to about 2 years. In embodiments, the soluble, hydrophilic PCL substrate dissolves in about 3 months to about 18 months. In embodiments, the soluble, hydrophilic PCL substrate dissolves in about 3 months to about 12 months. In embodiments, the soluble, hydrophilic PCL substrate dissolves in about 3 months to about 6 months. In embodiments, the soluble, hydrophilic PCL substrate dissolves in about 3 months to about 6 months, 5 months, or 4 months. In embodiments, the soluble, hydrophilic PCL substrate dissolves in about 4 months to about 2 years. In embodiments, the soluble, hydrophilic PCL substrate dissolves in about 4 months to about 18 months. In embodiments, the soluble, hydrophilic PCL substrate dissolves in about 4 months to about 12 months. In embodiments, the soluble, hydrophilic PCL substrate dissolves in about 4 months to about 6 months. In embodiments, the soluble, hydrophilic PCL substrate dissolves in about 4 months to about 5 months. In embodiments, the soluble, hydrophilic PCL substrate dissolves in about 5 months to about 2 years. In embodiments, the soluble, hydrophilic PCL substrate dissolves in about 5 months to about 18 months. In embodiments, the soluble, hydrophilic PCL substrate dissolves in about 5 months to about 12 months. In embodiments, the soluble, hydrophilic PCL substrate dissolves in about 5 months to about 6 months. In embodiments, the soluble, hydrophilic PCL substrate dissolves in about 6 months to 2 years. In embodiments, the soluble, hydrophilic PCL substrate dissolves in about 6 months to about 18 months. In embodiments, the soluble, hydrophilic PCL substrate dissolves in about 6 months to about 12 months. In embodiments, the soluble, hydrophilic PCL substrate dissolves in about 12 months to about 18 months. In embodiments, the soluble, hydrophilic PCL substrate dissolves in about 12 months to about 2 years. In embodiments, the soluble, hydrophilic PCL substrate dissolves in about 18 months to about 2 years. The dissolution time may be any value or subrange within the recited ranges, including endpoints. For example, the soluble, hydrophilic PCL substrate may dissolve in about 1 month, 2 months, 3 months, 4 months, 5 months, 6 months, 12 months, 18 months, 2 years, etc.

[0047] The PCL or co-polymer may be formed, cut, or molded into any shape. For example, the PCL or co-polymer may be shaped as a microbead, capsule, film, sheet, bandage, adhesive, mesh, netting, anatomical mimic, geometrical shape, dissolving microneedle (DMN), and/or computer-aided designed three-dimensional shape.

[0048] Patches

[0049] Topical patches include, but are not limited to, transdermal patches, as well as patches that can be applied to a mucosal membrane or wound of a subject. Transdermal patches may be applied, for example, to the skin of a subject. Further, patches as described herein may be applied internally to a subject, e.g., subdermal or within a body cavity.

[0050] A patch as described herein may contain one or more layers of soluble, hydrophilic PCL or co-polymer thereof. The patch may also contain one or more layers of an additional polymer. In embodiments, one or more layers of hydrophilic PCL and/or additional polymers contains an active agent. In embodiments, different layers contain different active agents. In embodiments, different layers contain the same active agent.

[0051] In embodiments, the patch includes a reservoir of active agent. Liquid reservoir patches of various designs are well known to researchers in the field of transdermal drug delivery. See, for example, U.S. Pat. No. 4,460,372 and 5,591,767, each of which is incorporated herein by reference in its entirety. In embodiments, a hydrophilic PCL or PCL co-polymer layer is adjacent to the reservoir. In embodiments, a hydrophilic PCL or PCL co-polymer layer is in fluid connection with the reservoir. In embodiments, the reservoir may comprise an emulsion of hydrophilic PCL and an active agent. The emulsion of hydrophilic PCL and an active agent may be incorporated into various embodiments of the disclosed subject matter. For example, the emulsion may be applied to a gauze bandage.

[0052] In embodiments, the patch comprises a film. The film may be positioned between the skin or other area of the subject and the active agent-containing layer. In embodiments, the film contains the first active agent or a different active agent. In embodiments, the film includes hydrophilic PCL or co-polymer thereof. In embodiments, the film includes modified PCL or co polymer thereof. Film includes soluble, hydrophilic PCL or co-polymer thereof. In embodiments, the film acts as a vapor barrier between the subject's skin (or other area) and the active agent- containing layer(s). In embodiments, the film degrades over time after application of the patch to a subject.

[0053] In various embodiments, the patch may comprise one or more outer layers and one or more inner layers. The one or more outer layers may have a molecular weight of hydrophilic PCL between about 80,000g/mol and 120,000g/mol. The one or more outer layers may further have a weight/volume hydrophilic PCL concentration of about 5-8%. A thickness of the one or more outer layers may be about 100-300pm. The one or more outer layers may be sandwiched within the patch. Alternatively, the one or more outer layers may be laminated into the patch. Active agents or other materials may be imbibed into one or more of the outer layers.

[0054] The one or more inner layers may have a molecular weight of hydrophilic PCL between about 20,000g/mol and 80,000g/mol. The one or more inner layers may further have a weight/volume hydrophilic PCL concentration of about 3-5%. Like the outer layers, the one or more inner layers may be sandwiched within the patch or laminated into the patch. A thickness of the one or more inner layers may be about 10-50pm. The one or more inner layers may have a dimensional undersurface that is not flat. Active agents or other materials may be imbibed into one or more of the inner layers.

[0055] The patches may be configured to deliver various active agents. For example, the patches may be configured to deliver nutraceuticals or cosmeceuticals. The patches may be configured to deliver a medicinal or therapeutic agent. The patch may be configured to deliver a long term diagnostic that monitors infectious agents.

[0056] Microbeads

[0057] In various embodiments, the hydrophilic PCL may be prepared into microbeads of various sizes and properties. The microbeads may be prepared into creams or the like for treatment. In an exemplary embodiment, the microbeads may have a molecular weight of between 20,000g/mol and 80,000g/mol. The microbeads may have a weight/volume hydrophilic PCL concentration of about 3-5%. A diameter of the microbeads may be about l-10pm in length. In an exemplary embodiment, the microbeads may be lyophilized to remove solvents or other agents trapped within the microbeads.

[0058] In various embodiments, admixtures of conditioned stem cell media containing exosomes, cytokines, and/or growth factors may be produced with microbeads. Microbeads may be infused with active agents in various ways. For example, the microbeads may be coupled to an active agent through a peptide bond to an N-substituted terminal end of the PCL molecule. The infused microbeads may be mixed into skin creams and applied to the skin of a subject. In one example of a treatment with a microbead cream, stem cell infused microbeads may be applied to skin to fill rhytides (wrinkle crevices) and deliver various active agents through skin resorption over a period of time.

[0059] In an exemplary embodiment, the microbead admixtures may be configured to deliver therapeutic agents through nasal administration. Microbead admixtures that are configured for nasal administration may contain convalescent antiserum, passive immune agents including avian IgY antibodies which can neutralize viral & microbial pathogens or other therapeutic or medicinal agents. The microbeads may be produced with hydrophilic PCL with a molecular weight of about 20,000g/mol and 80,000g/mol, a hydrophilic PCL concentration of about 3-5% weight/volume, and a diameter of about l-10pm. In another exemplary embodiment, microbeads that are formulated with a passive-immune agent may be applied to a subject through intranasal aerosolization. The aerosolized microbeads may provide inactivation of viral or microbial pathogens to effect a short term immunity in the subject.

[0060] In yet another exemplary embodiment, the microbeads may be configured to self monitor and detect pathogen infections. The microbeads may be produced with hydrophilic PCL with a molecular weight of about 80,000g/mol and 120,000g/mol, a hydrophilic PCL concentration of about 5-8% weight/volume, and a diameter of about l-100pm. The microbeads may be lyophilized. Reactive antigens or whole pathogens may be covalently linked to the microbeads. In various embodiments, the microbeads may be implanted into a subject via a 26- gauge syringe for real-time self-monitoring and detection of infection from pathogenic agents.

[0061] Gauze

[0062] In various embodiments, hydrophilic PCL may be formed into microfibers that are electrospun into a gauze to treat and heal wounds. The hydrophilic PCL used to form the microfibers may have a molecular weight of about 20,000g/mol to 80,000g/mol. The microfibers may have a weight/volume PCL concentration of 3-5%. A diameter of the microfibers may be 0.5-10pm. The microfibers may be lyophilized. PCL that is electrospun into microfibers and woven may be used as a replacement for cotton gauze.

[0063] In various embodiments, hydrophilic PCL that is electrospun into microfibers that may be woven into a bandage under coverings. The PCL microfibers may be a hydrophilic PCL gauze that is imbibed with stem-cell biologicals that are tuned for wound and scar healing. In various embodiments, the hydrophilic PCL gauze may be a bandage insert that is never removed from a wound or bum. Instead, the biopolymer is resorbed into the body along with healing agents that were coupled to the hydrophilic PCL gauze. Thus, scabs may not be removed as the gauze is disintegrated. Further, PCL is an FDA approved polymer for surgical replacements. Wound-healing agents and stem cell derived biologicals may be lyophilized or co-polymerized with a hydrophilic PCL gauze and laminated onto an underside of standard bandages. In an exemplary embodiment, a hydrophilic PCL gauze may be wrapped around body parts after a tattooing process.

[0064] Referring to Fig. 1, Fig. 1 is an illustration 100 of a magnification 105 of a PCL microbead 110. The illustration 100 shows the potential change in the surface chemistry of a PCL microbead 110 after treatment with 5% (w/w) NaOH. As shown in Fig. 1, the PCL may be in the form of a PCL microbead 110. In various embodiments, the PCL microbead may be in a variety of sizes. For example, the PCL microbead may have a diameter from about 0.03 pm to about 6.0 pm. In another example, the PCL microbead may have a diameter from about 10 nm to about 0.6 mm.

[0065] The PCL microbead 110 may have a spherical shape, as shown in Fig. 1, or other 3 dimensional shape. Further the PCL microbead 110 may contain pores, which are not shown in Fig. 1, through which various substances may enter. The pores may have various diameters that are smaller than the diameter of the PCL microbead 110. The pores effectively increase the total surface area of the PCL microbead 110 and may result in increased reactivity and/or dissolution rate.

[0066] An illustration of the untreated surface 115 is shown on the left side of the magnification 105. The untreated surface 115 of the PCL microbead 110 may contain a carbonyl group for units of the polymer chain that comprise an ester. Upon treatment with a base such as 5% (w/w) NaOH 125 a portion of the carbonyl groups may be hydrolyzed. Thus, the treated surface 120 may contain hydroxyl groups in place of a portion of the carbonyl groups. The hydrolysis reaction may increase the hydrophilicity of the PCL substrate. Additionally, the hydrolysis may modify the surface of the PCL substrate. A hydrolyzed surface may be rougher and contain more pores and pores of greater size. Reactivity of the hydroxyl groups may result in binding of the PCL substrate to various medicaments. For example, an active agent may form covalent bonds with the treated surface 120. In another example, stem cells may be bound through electrostatic, hydrogen bonding, and/or Van der Waals forces to the treated surface 120.

[0067] Referring to Fig. 2, Fig. 2 is a microscopic image 200 showing a multitude of PCL microbeads suspended in a solution. PCL microbeads may be prepared by stirring polycaprolactone in a solvent at a high rate such as 6000 rpm for about 2 minutes. The microbeads, thus formed, may be isolated by centrifugation. PCL microbeads may be washed and dried. For the preparation of PCL nanospheres of smaller diameter, the above procedure may be modified by increasing the stir rate and time. For example, a stirring speed of 12000 rpm for 5 minutes may result in much smaller microbeads, which may be referred to as nanospheres.

[0068] The PCL microbeads may be treated with a base to prepare a hydrophilic PCL substrate. The strength of the base and the length of base treatment are directly proportional to the hydrophilicity of the resulting PCL substrate. Further, a size of microbead may be indirectly proportional to the dissolution rate of the resulting PCL substrate as the higher surface area to volume of smaller PCL microbeads may result in increased interaction with the basic solution. Further, a longer base treatment increases hydrophilicity of the PCL. In various embodiments, the treatment by a NaOH base cleaves the PCL polymer chain, creating a carboxyl group on one side of the cleaved chain, and a hydroxyl group on the other side of the cleaved chain.

[0069] The surface of the treated PCL microbeads may facilitate layering a medicament on the surface of the microbeads. For example, stem cells, may be bound to the surface. In various embodiments, IgG antibodies may be attached to the treated PCL microbeads. The PCL microbeads with IgG antibodies may have a variety of uses; one of which may be to offer protection from pathogens. PCL microbeads with IgG antibodies may be coated on a surface of a subject, whereby the surface may receive increase protection from one or more pathogens.

[0070] Referring to Fig. 3, Fig. 3 is a reaction diagram 300 of base-catalyzed hydrolysis of the ester linkages present in the backbone of polycaprolactone. The preparation of the hydrophilic PCL material is shown in Figs. 3 and 4. The hydrophilic PCL material may be prepared by a base-catalyzed hydrolysis of the ester linkages present in the backbone of polycaprolactone. The time of treatment with the base may be correlated to the dissolution rate of the hydrophilic PCL material.

[0071] Untreated PCL is a hydrophobic polymer which undergoes dissolution and bioabsorption into human tissues and mineralizes into break down products which are safe for in human use. The base catalyzed ester hydrolysis process generates carboxylic acid and hydroxyl groups resulting from controlled hydrolytic cleavage of the polyester strands in the PCL polymer. The hydrolysis converts PCL from an extremely hydrophobic polymer to a hydrophilic matrix which increases the dissolution rate and imparts a charged characteristic to the microbeads under physiological conditions. The process essentially accelerates the in vivo dissolution of PCL, which occurs naturally in the human body.

[0072] The exposed carboxylic acid and hydroxy groups convert the hydrophobic surface chemistry of the PCL substrate into a weak cation exchanger. The charged surfaces on the PCL substrate will facilitate binding and adsorption of proteins via electrostatic interactions between the negatively charged surface carboxylate groups and positive charged primary amines present on the surface of the protein. Alternatively, carboxylic acids moieties on the PCL substrate can be chemically activated to promote formation of covalent amide bonds between the protein’s primary amines and the carboxylic moieties on the PCL substrate.

[0073] Referring to Fig. 4, Fig. 4 is a reaction diagram 400 is a reaction diagram of a coupling of surface-exposed carbonyl groups to amino groups on a polypeptide to create a peptide bond. Carbonyl groups may be exposed through the base-catalyzed hydrolysis reaction shown in Fig. 6. In an exemplary embodiment, a peptide bond may be created through the reaction of hydrophilic PCL with a polypeptide and l-Ethyl-3-(3-dimethylaminopropyl) carbodiimide (“EDC”). The reaction may produce a peptide bond between a PCL substrate and an amino acid chain, which results in an amide. A urea by-product may be produced as part of the reaction.

[0074] The R-group in Fig. 4 may be various functional groups, amino acid chains, or the like. In various embodiments, the R-group is an amino acid chain that forms a protein. The resulting reaction that forms an amide may be the protein bound to a PCL chain. In various embodiments, the R-group is an amino acid chain in a cell membrane. Also, in various embodiments, the R- group may be an antigen. [0075] Referring to Fig. 5, Fig. 5 is an illustration 500 of an embodiment of a surface 505 of a hydrophilic PCL microbead as the hydrophilic PCL microbead binds to stem cells 510. As shown in Fig. 5, the medicament that is bound to the hydrophilic PCL microbead may be live stem cells 510. In an exemplary embodiment, the medicament may be bound to the surface 505 of a hydrophilic PCL microbead through electrostatic forces. Also, in various embodiments, the medicament may be bound to the hydrophilic PCL microbead through covalent bonding, hydrogen bonding, Van Der Waals forces, entrapment within the lattice of the hydrophilic PCL microbead, or the like. The hydrophilic PCL substrate may comprise a form other than the microbead, such as a foam, PCL rods, a PCL wire, a PCL gauze, or the like.

[0076] In various embodiments, the stem cells 510 may produce stem cell biomaterials when the hydrophilic PCL microbead is administered to a subject. The hydrophilic PCL surface may comprise a structure that is implanted in vivo in a subject. The structure may dissolve in vivo as the stem cell biomaterials are produced. In various embodiments, a PCL and stem cell device may be configured into an organoid. Also, in various embodiments, the PCL and stem cell device may be configured into a biomedical implant. The hydrophilic PCL substrate may comprise the structure of the biomedical implant. Stem cells may coat the surface of the hydrophilic PCL substrate.

[0077] Referring to Fig. 6, Fig. 6 is an illustration 600 of an embodiment of a patch with a PCL dissolving microneedle 605. The PCL material may dissolve in an aqueous solution. The PCL dissolving microneedle 605 is configured to penetrate the skin or other surface of a subject. The dissolving microneedle 605 may thus be subjected to the bodily fluids of the subject. Over time, the bodily fluids of the subject may dissolve the dissolving microneedle.

[0078] The dissolving microneedle may be attached to a support structure 610. In various embodiments, the support structure 610 comprises hydrophilic PCL. Further, the support structure may include an adhesive to bind the support structure 610 to a surface, such as the skin of a patient. Both the microneedles and support structure 610 may be configured to dissolve over time. In various embodiments, a protein antigen is coupled to the tip of the microneedle. When the microneedle is inserted under the skin of a patient, it dissolves at a consistent and controllable rate which is dependent on the hydrophilicity and shape of the PCL material in the microneedle. The PCL material may be configured to dissolve at a preferred rate. For instance, a patch may be designed to be worn for a period of one month. The protein antigen is released into the patient at the rate of PCL dissolution. Thus, a patient may be continuously monitored via the patch.

[0079] The dissolving microneedle 605 may be configured to dissolve in varying lengths of time. The dissolving microneedle 605, which may comprise hydrophilic PCL substrate, may be treated with a base to break down the PCL substrate. The dissolution rate of the PCL substrate may be directly proportional to the strength of the base and the time a base treatment. Further treatment that increases the surface area of the PCL substrate may increase the dissolution rate. Lyophilization may increase the porosity of the PCL substrate, which may increase the dissolution rate.

[0080] Antigen Test

[0081] In an exemplary embodiment, a protein antigen that is coupled to hydrophilic PCL, may be delivered to a patient to test for antibodies. The basic principles used for the Mantoux TB PPD test may be applied to a test that incorporates hydrophilic PCL. For example, an immune response from a patient may indicate the presence of antibodies to a pathogen. In one instance, a test can be used to monitor and detect individuals who have been exposed to COVID-19 or are asymptomatic spreaders. An inexpensive medical device will be developed in both transdermal and clinical implant formats, for real-time monitoring and detection of infected individuals, assisting in control of contagion spread.

[0082] A Purified Protein Derivative (PPD) test developed for COVID -19 would be used to monitor asymptomatic patients or those exposed to pathogens such as COVID -19, which have long incubation periods. This technology is a wearable, self-monitoring diagnostic for early detection of infection, which has utility when combined with a suite of contagion monitoring methods in a triage approach to control the contagion.

[0083] The big difference in the TB PPD test and the materials, systems, technologies and engineering thoughts noted in the paper is that the modern version using hydrophilic PCL can be used to monitor an individual for a year or longer and can be modified quickly to support future viral outbreaks. This is because hydrophilic PCL, which is coupled with a protein antigen, may be configured to release the protein antigen gradually over a long period.

[0084] The hydrophilic PCL protein antigen test can be used to rapidly monitor and identify contagion infections in large segments of our society. A wearable medical device may provide real-time, self & institutional monitoring and detection of pathogens such as Covid-19 in infected individuals.

[0085] A biopolymer system may be developed for a COVID-19 diagnostic medical device based on testing methodologies developed over 100 years ago for monitoring tuberculosis (TB). The disclosed subject matter uses unique material and technology in a system designed to monitor and detect infections of Covid-19 and future contagions. It represents a modernized version of the PPD tuberculosis test developed over 100 years ago. The technology has applications across large segments of our society spanning the public, industrial & governmental sectors.

[0086] An exemplary embodiment includes two primary components; 1) hydrophilic PCL and b) commercially available protein antigens. The hydrophilic PCL has characteristics that are well suited for transdermal delivery and intra-dermal delivery applications. For instance, the hydrophilic PCL can be form factored as a thin, dimensional, micro-webbed structural foam matrix, which will sequester the reactive antigens and provide for accurate depth & precise delivery for optimal display of epitopes for elicitation of an immune response. Coupling of the antigens to a hydrophilic PCL can be accomplished in a number of ways integrating mixed antigens, copolymerized with molten polymer prior to polymerization or covalent coupling. In an exemplary embodiment, the charge character and hydrophilicity of the polymer are increased by cleaving ester groups in the backbone of the polymer and exposing carbonyl groups, which enable binding the polymer to protein antigens.

[0087] In an embodiment to test for COVID-19, reactive COVID-19 antigens are coupled to hydrophilic PCL in transdermal and implant formats. Base-catalyzed etching of the PCL backbone results in exposed carbonyl groups which permit facile coupling to proteins. [0088] The flexible nature of hydrophilic PCL materials systems enable creation of an antigen presentation system in which hydrophilic PCL can be form fashioned into transdermal patches fitted with dimensional surfaces by micro-compressing hydrophilic PCL film in a high volume production line creating a unique number of tips that would then be coupled with antigens such as COVID-19 antigens. These biopolymeric tips allow for the presentation of the reactive antigen under the surface of the skin to a prescribed depth (2-3mm).

[0089] In various embodiments, the patch could be useful as an over the counter, easy to apply product. In an exemplary embodiment, an intra-dermal test that includes hydrophilic PCL comprises a micro sized biopolymer wafer for implantation by medical personnel for long-term monitoring and easy to read detection of the contagion.

[0090] In yet another embodiment, a modem version of the Reactive PPD (Purified Protein Derivative) Tuberculosis test developed over 100 years ago, uses a unique polymer that incorporates hydrophilic PCL. The Mantoux tuberculin test is still in use today to determine if an individual has been exposed to tuberculosis (TB). The test is performed by putting a small amount of TB protein (antigen) 3mm under the skin. The skin will react to the antigens by developing a firm red bump at the site within 2 or 3 days if the individual has been exposed to the TB bacteria (Mycobacterium tuberculosis),

[0091] Similar to the TB test, the hydrophilic PCL test may be performed by covalently linking recombinant Covid-19 protein antigens to hydrophilic PCL to create a novel diagnostic biopolymer. When applied to the patient, the product may enable continuous monitoring and identification of positive individuals for long term physiologic surveillance for one year or more.

[0092] An exemplary embodiment of the hydrophilic PCL antibody test is an intra-dermal, clinician assisted micro-wafer implant to increase the efficacy period for detection. Yet another exemplary embodiment is a transdermal diagnostic patch which penetrates the epidermis for consumer application to determine whether someone has developed an immune response to a pathogen. In one example, a patch comprising hydrophilic PCL coupled to a protein antigen can be deployed as an intra-dermal test for monitoring and detection of infected individuals for a year or potentially more, including asymptomatic patients. [0093] It is understood that the examples and embodiments described herein are for illustrative purposes only and that various modifications or changes in light thereof will be suggested to persons skilled in the art and are to be included within the spirit and purview of this application and scope of the appended claims. All publications, patents, and patent applications cited herein are hereby incorporated by reference in their entirety for all purposes.

Claims

CLAIMS:

1. A treatment substance, the treatment substance comprising: a medicament configured to treat a patient over a period of time; a soluble, hydrophilic polycaprolactone coupled to the medicament; the soluble, hydrophilic polycaprolactone is configured to dissolve over the period of time upon contact with the patient.

2. The treatment substance of claim 1, wherein the soluble, hydrophilic polycaprolactone and medicament are combined in an emulsion.

3. The treatment substance of claim 1, wherein the emulsion comprises an adhesive.

4. The treatment substance of claim 1, wherein the medicament is covalently bonded to the soluble, hydrophilic polycaprolactone.

5. The treatment substance of claim 1, wherein the medicament is a live cell.

6. The treatment substance of any one of claims 1-4, wherein the medicament is a protein antigen.

7. The treatment substance of claim 6, wherein the protein antigen is configured to cause an immune response in the patient at a point of contact between the patient and the protein antigen.

8. A treatment fabric, the treatment fabric comprising: soluble, hydrophilic polycaprolactone that is coupled to an active agent; the active agent configured to treat a patient over a period of time; and the soluble, hydrophilic polycaprolactone comprising a flat layer that is configured to dissolve on contact with the patient over the period of time.

9. The treatment fabric of claim 8, wherein the flat layer comprises micro fibers of soluble, hydrophilic polycaprolactone that are woven into a gauze.

10. The treatment fabric of claim 8, wherein the flat layer comprises a web of soluble, hydrophilic polycaprolactone.

11. The treatment fabric of claim 8, wherein the flat layer comprises a matrix of soluble, hydrophilic polycaprolactone.

12. The treatment fabric of any one of claims 8-11, wherein the active agent is a live cell.

13. The treatment fabric of any one of claims 8-11, wherein the active agent is a biologic.

14. The treatment fabric of any one of claims 8-11, wherein the active agent is a protein antigen.

15. The transdermal fabric of any one of claims 8-11, wherein the active agent and soluble, hydrophilic polycaprolactone are combined in an emulsion.

16. The transdermal patch of claim 15, wherein the emulsion comprises an adhesive.

17. A transdermal patch, the transdermal patch comprising: a backing layer adjacent to an active agent-containing layer; the active agent-containing layer comprising soluble, hydrophilic polycaprolactone and a medicament; and microneedles that are configured to penetrate the area of skin.

18. The transdermal patch of claim 17, wherein the microneedles comprise soluble, hydrophilic polycaprolactone that dissolves after penetrating the area of skin.

19. The transdermal patch of claim 17, wherein the medicament is coupled to tips of the microneedles.

20. The transdermal patch of any one of claims 17-19, wherein the medicament is a protein antigen.

21. A method of detecting antibodies in an individual, the method comprising: administering a protein antigen to the individual; detecting an immune response of the individual to the protein antigen; wherein the protein antigen is coupled to soluble, hydrophilic polycaprolactone; wherein the soluble, hydrophilic polycaprolactone is configured to dissolve responsive to contact with the individual; and wherein the protein antigen is configured to be released to the individual as the soluble, hydrophilic polycaprolactone is dissolved.

22. The method of claim 21, wherein the soluble, hydrophilic polycaprolactone comprises a transdermal patch.

23. The method of claim 22, wherein the transdermal patch comprises microneedles; and wherein tips of the microneedles comprise soluble, hydrophilic polycaprolactone that is coated with the protein antigen.

24. The method of claim 21, wherein the soluble, hydrophilic polycaprolactone comprises a fabric that is applied to the individual.

25. The method of any one of claims 21-24, wherein the soluble, hydrophilic polycaprolactone is configured to dissolve at a rate between about 5 minutes to about 2 years in an aqueous environment.